HK1261718B - Dental implant, insertion tool for dental implant and combination of dental implant and insertion tool - Google Patents

Description

Dental implants, dental implant insertion tools, and combinations of dental implants and insertion tools

Technical Field

The present invention relates to a dental implant, in particular for insertion into a patient's bone tissue, the dental implant comprising: a core having a top end, a coronal end, and an outer surface extending in a longitudinal direction between the top end and the coronal end; and at least one thread located on at least the threaded portion of the outer surface and extending outward from the core. The present invention also relates to a dental implant, in particular for insertion into a patient's bone tissue, the dental implant comprising a core having a top end and a coronal end, wherein the core comprises a channel leading to the coronal end and extending from the coronal end toward the top end along the longitudinal direction of the implant. In addition, the present invention relates to an insertion tool for inserting a dental implant into a patient's bone tissue. In addition, the present invention also relates to a combination of such an implant and such an insertion tool.

Background Art

Dental implants are widely used in reconstructive treatment to replace missing teeth. They are generally inserted into the jawbone at the site of an extracted or dislodged tooth, in order to retain a prosthetic component, such as a denture or crown, there after a healing period of approximately four to twelve weeks. To this end, such dental implants are usually constructed as suitably shaped metal bodies that are screwed into the jawbone or bone tissue at a predetermined location. Typically, the top of the dental implant includes a thread, in most cases a self-cutting thread, which is used to insert the dental implant into the corresponding prepared implant bed.

The dental implant can be of one-piece design, wherein the prosthesis is attached directly to the implant after the implant has been inserted into the jawbone. In an alternative, in particular in order to facilitate insertion into the patient's mouth and in particular in order to enable particularly extensive preparation of the prosthesis, which is then fixed to the implant before the patient's treatment, for example in a dental laboratory, the dental implant system can also be of multi-component design. In particular, a generally two-component design can be provided, the dental implant system comprising a first implant component, also referred to as the actual implant or post, provided for insertion into the jawbone, and, in addition thereto, an associated second implant component, also referred to as a mounting component or abutment, to which a prosthesis component provided as a prosthesis or the like can in turn be mounted.

The outer surface of the actual implant or post is usually provided with a thread, which may or may not be designed as a self-cutting thread. The implant or post is usually anchored in a correspondingly prepared implant bed in the jawbone. The configuration of the thread provided in the outer area of the dental implant is usually designed to provide a high degree of stability of the structure and a uniform transmission of the forces generated by the dental implant under masticatory loads into the jawbone.

For this reason, specifically, for the high primary stability after implant is inserted into bone tissue, various methods for constructing threads and implant bodies are known from the prior art. Various thread geometries and combinations thereof can be provided, for example, threads with different thread types or different thread parameters are formed in different zones of the implant body. According to WO 2008/128757A2, implants of the type mentioned above are known to be characterized by additional spiral grooves on the outer surface of the corresponding threads and/or directly on the implant body between two adjacent threads. In other systems, compression threads characterized by narrow grooves can be provided. High primary stability can also be achieved by reducing the size of the hole drilled into the patient's bone at the position provided for the implant, so that when the implant is screwed into the core of the implant together with the threads arranged thereon, the surrounding bone material is compressed. However, too strong compression can cause the blood vessels in the bone to collapse, thereby hindering bone healing after insertion.

Another common purpose of the specific design of the implant and the threads provided thereon is the so-called secondary stability or osseointegration, which is the regeneration of the bone material in direct contact with the implant surface.

US 2007/0190491 A1 discloses an implant design having a non-circular cross-sectional geometry of the implant body. For this design, it is recognized that most natural teeth are also non-circular in cross-section, and it is assumed that a similar cross-sectional structure of the implant body better matches the natural location of blood vessels in bone tissue, thereby supporting good and rapid osseointegration.

Dental implants (such as those described above) are typically inserted into the patient's bone tissue using an insertion tool (e.g., an implant driver). To this end, the distal portion of the insertion tool is introduced into a socket provided in the coronal portion of the implant. This distal portion cooperates with the implant socket so that when the insertion tool is rotated about its longitudinal axis, the implant is screwed into the bone tissue.

In order to achieve reliable and accurate placement of the implant in the bone tissue, the insertion tool must be correctly seated, i.e. fully engaged in the implant. Any mismatch or misalignment between the insertion tool and the dental implant complicates the insertion of the implant into the bone tissue and leads to the risk of incorrect implant placement.

Insertion tools are used to pick up implants and transport them to the implant site, where they are inserted into the bone tissue. In this case, if there is a mismatch or misalignment between the tool and the implant, the implant may become dislodged from the insertion tool before reaching the desired position. Such incidents could even pose serious risks to the patient's health if the implant is swallowed or inhaled.

In order to achieve a friction fit between the insertion tool and the implant, US 7,131,840 B2 teaches the use of an O-ring at the distal portion of the implant driver. However, the configuration taught in this document does not allow the clinician to reliably assess whether the insertion tool and the implant are correctly engaged with each other.

US Pat. No. 8,864,494 B2 discloses another method for improving the connection between an insert and an implant, which utilizes a retainer for connecting an insertion tool to the implant. After the implant is inserted into the bone tissue, the retainer must be removed from the implant. This method requires the use of an additional dental component in the form of a retainer and an additional step from the clinician, making the implant insertion process complex and cumbersome.

Thus, there remains a need for a reliable, effective and simple method of attaching an insertion tool, such as an implant driver, to a dental implant that provides a clear indication of whether the insertion tool and the dental implant are correctly attached to each other.

Furthermore, there remains a need for an insertion tool which allows a reliable insertion of an implant into bone tissue while minimizing the risk of damage or breakage of the implant, in particular its socket.

Furthermore, there remains a need for a dental implant which allows reliable insertion thereof into bone tissue while minimizing the risk of damage or breakage of the implant, in particular of its socket or channel.

As already detailed above, dental implants are usually inserted into the patient's jaw or bone tissue at the desired location by screwing in. To this end, the top of the dental implant comprises a thread, in most cases a self-cutting thread, with which the dental implant is inserted into the corresponding prepared implant bed.

The thread plays an important role in the reliable and accurate placement and engagement of the implant in the jaw or bone tissue. Specifically, the thread must allow the implant to be smoothly and accurately inserted into the jaw or bone tissue and ensure stable engagement of the implant with the jaw or bone tissue after insertion.

To this end, WO 2016/125171 A1 teaches the use of a threaded dental implant in which the top surface of the thread has a top surface depression extending proximally toward the coronal surface of the thread. However, the configuration disclosed in this document only provides improvements in implant placement and stability over a limited range of thread angles, i.e., thread angles greater than approximately 15°.

Therefore, there remains a need for a dental implant that allows for reliable and accurate placement and engagement of the dental implant in the jawbone or bone tissue at various implant thread angles, particularly small thread angles.

Summary of the Invention

In view of the above-explained aspects, one object of the present invention is to provide a dental implant of the type mentioned above, which has improved properties with respect to primary and secondary stability. Another object of the present invention is to provide a dental implant that allows for reliable insertion of the dental implant into the jawbone or bone tissue while minimizing the risk of damage or breakage of the implant, in particular its socket or channel. Furthermore, the present invention aims to provide a dental implant that allows for reliable and accurate placement and engagement of the dental implant in the jawbone or bone tissue at various implant thread angles, in particular small implant thread angles.

Another object of the present invention is to provide an insertion tool for inserting a dental implant into a patient's bone tissue that effectively provides a reliable indication of whether the insertion tool and the dental implant are properly attached to each other. Furthermore, the present invention aims to provide an insertion tool for inserting a dental implant into a patient's bone tissue that enables reliable insertion while minimizing the risk of damage or breakage to the implant, particularly its socket or passage. The present invention also provides a combination of such an insertion tool and a dental implant.

According to the present invention, in one embodiment, this object is achieved by a dental implant (1), in particular for insertion into bone tissue of a patient, said dental implant (1) comprising:

a core (2) having a top end (4), a coronal end (6) and an outer surface (8) extending in a longitudinal direction between the top end (4) and the coronal end (6);

- at least one thread (12) extending outwardly from said core (2), and

a characteristic implant volume defined by the core (2) or by the extra-thread volume (28) defined by the thread (12), wherein for each value of a parameter characteristic of a coordinate in the longitudinal direction of the implant, a cross section of the characteristic implant volume is characterized by an eccentricity parameter defined as the ratio of the maximum distance of the profile of this cross section from its center to the minimum distance of the profile of this cross section from its center;

The characteristic volume includes

at least one coronal region, in which the eccentricity parameter has a maximum value, preferably a constant value, said coronal region extending along the longitudinal axis of the implant over a coronal region length of at least 10% of the total length of the implant;

at least one apical region, in which the eccentricity parameter has a minimum value, preferably a constant value, said apical region extending along the longitudinal axis of the implant over a length of the apical region of at least 30% of the total length of the implant, and

At least one transition zone is positioned between the coronal zone and the apical zone, wherein the eccentricity parameter varies continuously, preferably linearly, from a minimum value near the apical zone to a maximum value near the coronal zone according to the parameter characteristics of the coordinates in the longitudinal direction, and the transition zone extends along the longitudinal axis of the implant over a transition zone length of at least 10% of the total length of the implant.

In other words, in this embodiment, the implant defined by its core or its threaded outer volume comprises at least three functional sectors, each of which has a certain minimum functional length in order to provide its assigned function. The first of these functional zones or sectors is a coronal zone, in which the core and/or the threaded outer volume have a certain eccentricity in their geometry, thereby providing a plurality of maxima and minima of the radius, as seen in cross section. The second functional zone or sector is an apical zone, in which the core and/or the threaded outer volume have a minimum eccentricity, preferably even an approximately circular cross section. The third functional zone, positioned between the first and second zones, is a transition zone, in order to provide a smooth transition of eccentricity (and cross-sectional symmetry) over its length between said first and said second zones. This design supports smooth and easy insertion of the implant into the bone material due to the low eccentricity of the implant's preferably even circular cross-section at its apex, while in the final stage of insertion, when the implant is already deeply anchored in the bone material, the relatively highly eccentric coronal region of the implant, due to its eccentricity, provides alternating compression and relaxation phases in the surrounding bone material when being screwed in. The transition zone, in turn, provides a highly desirable smooth transition and thus a smooth increase in the alternating compression/relaxation phases in the bone material during insertion.

In a preferred embodiment, the implant is designed in its eccentric part to achieve a particularly smooth pulsation between the compression phase and the relaxation phase in the bone material when being screwed in. To this end, in a preferred embodiment, the cross section of the characteristic implant volume in the coronal region and/or the shaping region and/or the transition region has a plurality of main directions in which the radius measuring the distance between the center of the cross section and its outer contour assumes a relative maximum and therefore a higher value than in adjacent orientations.

According to the invention, in one embodiment, this object is achieved by a design in which the core of the implant comprises at least one first core region, in particular designed in the manner of a shaped core region, in which the cross section of the core has a plurality of main directions in which the radius, measuring the distance between the center of the cross section and its outer contour, takes a relative maximum value and therefore a higher value than in adjacent orientations. Furthermore, in this embodiment, the core comprises a second core region, in particular a circular core region, in which the cross section of the core is essentially circular, and a transition region, positioned between the first, shaped region and the second, circular region, as seen in the longitudinal direction of the implant, in which the geometry of the cross section of the core changes from the essentially circular shape in the vicinity of the second, circular region to a shape in which the cross section of the core corresponds to the shape of the cross section in the first or shaped region, in particular with regard to the general geometry of the cross section and/or the values of its characteristic parameters.

In other words, the dental implant according to the present invention includes a circular region with a circular or substantially circular cross-section, which, in a preferred embodiment, is located near or adjacent to the apex of the implant. In this context, and for the contexts mentioned below, "substantially circular" defines a shape that closely approximates a circle, thereby allowing for minimal distortion or deviation, such as slight eccentricity due to manufacturing tolerances. Due to its circular cross-section, this circular region allows for relatively easy engagement of the thread with the bone material without applying excessive stress to the bone tissue during the initial screwing of the implant into the bone material. In contrast, in another region of the implant, located closer to the center of the implant or even near the other end of the implant in a preferred embodiment, the core is designed with a non-circular cross-section characterized by multiple lobes or local maxima of the radius. In this region, when the implant body is screwed into the bone tissue, the compressive force exerted on the bone tissue varies in an oscillatory manner between maximum compression (when the local radius of the cross-section is maximum (due to the rotational motion of the implant body)) and minimum compression (when the local radius of the cross-section is minimum). Specifically, in the top region characterized by relatively hard bone tissue, after insertion, this shaped profile characterized by a local minimum will produce an area of low bone stress near the minimum, allowing enhanced regeneration of bone material and significantly minimizing the negative impact of excessive compression on blood vessels.

To allow for a smooth and beneficial transition between two different of these zones, the implant according to the invention provides an additional zone of the core located between a pair of circular and non-circular zones. This transition zone is provided with a transient cross-section that changes from a circular cross-section to a non-circular, leaf-shaped cross-section (as viewed in the longitudinal direction). The circular cross-section matches the cross-section of the respective circular zone in the vicinity thereof, and the non-circular, leaf-shaped cross-section matches the cross-section of the respective zone of non-circular cross-section in the vicinity thereof. Due to this transition zone, direct and abrupt changes in geometry, shearing effects on the bone tissue, and other damaging effects on the bone tissue are avoided.

In combination and in particular in the preferred embodiment in which the circular area is positioned close to or adjacent to the top of the implant, the implant thus provides a relatively easy engagement of the thread with the bone tissue in a first stage of screwing in, and an oscillating compression effect on the bone tissue in a later stage.

In an alternative embodiment of the present invention, a similar or equivalent effect can be achieved by designing the core in which the transition between the rounded area and the shaped area is achieved in a stepwise manner. This alternative embodiment is considered to be inventive in itself and can be used in accordance with the present invention separately from or in combination with the first embodiment.

In this alternative embodiment of the invention, the objects identified above are achieved by a design in which the core of the implant comprises at least one first shaped core region in which the cross section of the core has a plurality of main directions in which the radius measuring the distance between the center of the cross section and its outer contour takes a relative maximum value and therefore takes a higher value than in adjacent orientations. Furthermore, in this embodiment, the core comprises: a second core region, in particular a circular core region, in which the cross section of the core is essentially circular, which in a preferred embodiment is positioned close to or adjacent to the apex of the implant; and a second core shaping region in which the cross section of the core has a plurality of main directions in which the radius measuring the distance between the center of the cross section and its outer contour takes a relative maximum value and therefore takes a higher value than in adjacent orientations, wherein in the first core shaping region a core eccentricity parameter, defined as the ratio of the maximum radius of the cross section of the core to its minimum radius, is greater than the core eccentricity parameter in the second core shaping region. In other words, in this embodiment, by providing two or more non-circular shaped regions having different eccentricity parameters, the transition from a substantially circular or round geometry to a shaped or non-circular geometry can be achieved in a stepwise manner.

In another alternative embodiment of the present invention, a similar or equivalent effect can be achieved by designing the outer profile of the thread similar to the design of one or both of the above-described embodiments for the core. This alternative embodiment is considered to be inventive in itself and can be used in accordance with the present invention separately from or in combination with the first embodiment.

In particular, for the purpose of explanation, the outer contour of the thread can be described by means of the outer volume or envelope volume defined by the thread. In this alternative embodiment of the invention, the above-identified object is achieved by a design in which the thread of the implant comprises a first thread zone, in particular designed in the form of a first thread forming zone, in which the cross section of the outer volume enclosing the thread has a plurality of main directions in which the radius measured between the center of the cross section and its outer contour takes a relative maximum value and therefore takes a higher value than in adjacent orientations. Furthermore, in this embodiment, the thread comprises a thread circular zone, which in a preferred embodiment is located near the apex of the implant, in which the cross section of the outer envelope volume is substantially circular, and a transition zone, located between the first forming zone and the circular zone, in which, as seen in the longitudinal direction of the implant, the geometry of the cross section of the outer volume enclosing the thread changes from the substantially circular shape near the thread circular zone to a shape in which the cross section of the envelope volume corresponds to the shape of the cross section in the first forming zone, in particular with respect to the general geometry of the cross section and/or the values of its characteristic parameters. Alternatively or additionally, a gradual transition may also be provided by providing a second thread forming zone having a different eccentricity than the first thread forming zone.

In a preferred embodiment, the first or shaped area of the core and/or thread is configured as a top platform area and is positioned near the coronal end of the implant. Specifically, the top platform area can be designed to be connected directly to the prosthesis, i.e., for a one-piece version of the implant, or to a base supporting the prosthesis, i.e., for a two-piece or multi-piece version of the implant. In another preferred embodiment (which is itself considered to be an independent invention), the shaped top platform area provided by the outer profile of the core or thread has a length of at least 2.5 mm, preferably at least 3 mm, as seen in the longitudinal direction of the implant. It was surprisingly found that the shaped, non-circular area causes smaller or reduced stresses in the bone tissue at the local minimum compared to a circularly shaped profile, resulting in less cell death and less bone remodeling after insertion of the implant, faster bone attachment and improved maintenance of key bone structures, defined as the top plate, buccal wall and lingual wall. Therefore, by providing local minima of the shaping zone in the area of critical bone structure, the regeneration of bone material and bone integration are significantly improved, and it is considered very beneficial to provide these effects to at least the top 2.5mm or even better at least 3mm of the top plate for the purpose of bone integration.

The cross-section of the core and/or of the outer volume enclosing the thread can be characterized by an eccentricity parameter characteristic of the deviation of the corresponding cross-section from a circular shape. For the purposes of this description and disclosure and according to the invention, this eccentricity parameter is defined as the ratio of the maximum radius of the cross-section to its minimum radius, so that the eccentricity parameter takes the value 1 for a circular shape. This eccentricity parameter can be evaluated for each value of the parameter characteristic of the coordinate in the longitudinal direction (e.g., the longitudinal axis (y) of the implant). In order to provide a particularly smooth transition between the tip zone (=circular cross-section, eccentricity parameter=1) and the first or forming zone (=lobate or non-circular cross-section, eccentricity parameter>1), in a preferred embodiment, the eccentricity parameter in said transition zone of the core and/or the outer thread has a linear dependence on the coordinate parameter in the longitudinal direction.

The main directions of the core and/or thread transition zone and/or the first or forming zone—in which the corresponding radius of the cross section has a local maximum—can be positioned in the direction of rotation depending on the desired effect on the bone tissue, specifically at individually selected angles. However, in another preferred embodiment, they are positioned symmetrically (axisymmetrically) about the central longitudinal axis of the core or the outer envelope volume, respectively. This design allows for a relatively smooth and regular variation in the degree of compression exerted on the surrounding bone tissue as a result of the screwing process.

In a particularly preferred embodiment under consideration, the outer contour of the implant - as defined by the outer contour or enveloping volume of the thread - matches the outer contour of the core about the longitudinal center axis of the core and about local maxima or minima. In other words, in this preferred embodiment, in those orientations about the longitudinal axis in which the radius of the core has a local maximum, the outer contour of the outer volume enclosing the thread also adopts a local maximum. This matching of the contours can be achieved by overlapping the corresponding main directions within a tolerance range of preferably +/- 20° and can be exact in a preferred embodiment. The particular advantage of the "matching" design is that when the implant is inserted into the bone tissue, the bone compresses and relaxes on both the outer surface of the core and the outer surface of the thread, depending on the external geometry of the implant. The relaxation of the bone tissue at the smallest radius between the main directions (on both the outer surface of the core and the outer surface of the thread) allows for particularly high bone-implant contact and enhanced initial stability.

Advantageously, the number of main directions in the transition zone and/or forming zone is three, i.e., the core in the forming zone and/or transition zone has a triangular oval cross-section. In conjunction with the preferred embodiment of symmetrical positioning of the main directions with respect to the longitudinal direction, this triangular oval shape results in a rotational offset angle of 120° between two adjacent main directions.

Due to its transition zone, the implant is specifically designed to achieve a smooth and beneficial transition (during the screwing process) between the first engagement of the thread in the bone tissue (in the rounded zone) and the shaping and direct processing of the bone tissue by varying compression (in the shaping zone, preferably in the top platform zone). In a particularly advantageous embodiment, the smooth transition between these zones can be further improved, wherein the core in the transition zone is conical or tapered, preferably with a cone angle / taper angle between 1 ° and 12 °, preferably between 4 ° and 8 °. In a particularly preferred embodiment, the cone angle / taper angle is selected according to the overall length and diameter of the implant.

In view of the appropriate and convenient size that the implant requires for the bone environment, in a preferred embodiment, as seen in the longitudinal direction, the transition zone begins at a distance of approximately 2mm to 4mm from the top of the implant. In other words, in an alternative or alternative preferred embodiment, the positioning of the circular zone and/or threaded zone in the apical portion of the implant is considered to be highly beneficial so as to maximize the possibility of high primary stability. In general, but also more specifically in extraction sockets this is beneficial, where immediate loading schemes may be preferred. In order to provide significant apical engagement, as seen in the longitudinal direction of the implant, the circular zone preferably has a length of at least 2.5mm.

In addition to the geometric design of the core, in a particularly preferred embodiment, the thread itself is also specially designed to support reliable engagement with bone tissue under high primary stability. For this reason, the thread is preferably a flat thread. Even more advantageously, the free width of the flat thread increases continuously with increasing distance from the top, according to the coordinate parameters in the longitudinal direction of the implant and starting from the top of the core. In this design, the thread in the area near the top can be characterized by a relatively sharp small outer width, thereby providing high cutting power when the thread enters the bone tissue. As the implant is further screwed in (that is, the implant further enters the bone tissue), at a given position in the bone tissue, the width of the flat thread increases continuously, thereby continuously widening the corresponding local gap in the bone tissue and constantly increasing the contact area between the bone tissue and the implant.

In an alternative or alternative preferred embodiment, further improvements in implant properties can be achieved by supplementing the thread profile with a modification. In this modification, which is also considered inventive in its own right and, in particular, an independent invention, the thread preferably has a profile with a top surface and a coronal surface, wherein the top surface is oriented substantially orthogonally to the longitudinal axis of the implant, i.e., the plane normal of the top surface is oriented substantially parallel to the longitudinal axis of the implant. This design ensures that reliable contact between the top surface and the surrounding bone material is maintained even when the lateral extension of the thread top surface varies between a minimum radius and a maximum radius as a result of the non-circular outer profile. In this embodiment, the orientation of the coronal surface is preferably selected according to the requirements of the surrounding bone structure. Preferably, it is oriented at an angle of preferably approximately 60° relative to the longitudinal axis, i.e., the plane normal of the top surface is oriented at an angle of preferably approximately 30° relative to the longitudinal axis of the implant, so that the thread generally forms a buttress thread. Due to this inventive geometry, and in particular the orientation of the top surface, the top surface can very effectively absorb the loads of occlusal forces. In turn, the top surface of this geometry provides a relatively small and sharp free edge to improve the process of cutting bone, and a relatively wide and large base for stronger threads and to provide compression when the implant is inserted.

In particular, this design of the thread profile is advantageously combined with the outer contour of the core and/or the cross-sectional shape of the outer volume enclosing the thread. When the implant is screwed into the bone material, this profile, in particular the triangular oval cross-section, generates an oscillatory effect of bone compression in the longitudinal direction of the implant, the effect of which can be limited or reduced by using the orientation of the top surface.

In an alternative or alternative preferred embodiment, a plurality of cutting grooves, preferably equal to the number of main directions, are provided in the transition zone and/or the forming zone of the implant. These cutting grooves allow the cutting ability of the implant to be enhanced during the screwing-in process. Preferably, these cutting grooves are positioned symmetrically about the central longitudinal axis of the core. In particular, in an embodiment which is considered to be an independent invention and which can also be used according to the invention to improve other cutting groove systems, each cutting groove is positioned at a given rotational offset from an adjacent main direction, as seen in the orientation direction around the central longitudinal axis of the core.

Preferably, the cutting groove is positioned in the orientation direction with respect to the adjacent main direction of the core and/or the external thread, taking into account that the local maximum associated with the main direction will lead to the maximum compression of the bone material when the implant is screwed in, and the relaxation after the maximum has passed will allow the bone material to flow back to a certain extent towards the central axis of the implant. This relaxation according to this aspect of the invention serves to selectively improve the cutting effect of the cutting groove. Preferably, the position of the cutting groove relative to the local maximum is such that a normalizing effect of the bone is achieved. In other words: by positioning the cutting groove in the rotational direction, the relaxed bone material engages with the cutting groove with a particularly high efficiency when cutting hard bone, but not in the case of soft bone, so that the stability of the implant in the softer bone properties is maintained.

In a preferred, inventive embodiment, this is achieved by positioning the cutting grooves at an offset angle α with respect to the respective main direction. In this embodiment, the angle α is selected according to a selection criterion, which is itself considered to be an independent invention. According to this selection criterion, the cutting edge 48 should be positioned so that the cutting edge radius defined by the outer limits of the radial extension of the cutting edge and the longitudinal axis of the implant is between 20 μm and 75 μm smaller than the maximum radius in the respective main direction. This criterion takes into account the characteristic elastic properties of bone, which, depending on its density, rebounds or relaxes by approximately this amount after compression. In a preferred embodiment, the cutting edge radius is selected to be approximately 35 μm smaller than the maximum radius, which, according to the remaining geometric parameters of the core, translates into a preferred offset angle α of approximately 106°. With respect to the typical properties of bone tissue and the typical dimensions and rotational speeds when screwing the implant into the jawbone, the rotational offset of the groove position with respect to the adjacent main direction is preferably 80°-120°, in particular approximately 108°.

Specifically, the advantages achieved by the present invention are that both high primary and secondary stability can be achieved through a specific geometric design. The implant according to the present invention is characterized by a circular zone of the core and/or thread with a substantially circular cross-section, thereby allowing smooth engagement of the thread with the bone tissue while reducing roll or wobble of the implant, combined with a profiled zone with a non-circular cross-section, preferably triangular-oval, to allow subsequent compression and relaxation of the bone tissue, thereby helping to maintain the cheek bone in the apical or coronal region. Transition zones with different eccentricities and/or additional profiled zones provided between these zones allow for a smooth transition, thereby allowing the bone tissue to gently adapt to the compression effect and reducing friction and undesirable bone grinding or cutting.

According to one aspect of the present invention, an insertion tool for inserting a dental implant, in particular a dental implant according to the present invention, into bone tissue of a patient is provided. The insertion tool comprises a proximal portion and a distal portion, the distal portion being adapted to cooperate with the implant. The distal portion has a retaining element, and the retaining element comprises an attachment portion for attaching the insertion tool to the dental implant. The retaining element is elastically deformable at least in all directions perpendicular to the longitudinal direction of the insertion tool. The attachment portion comprises at least one protrusion extending in one or more directions substantially perpendicular to the longitudinal direction of the insertion tool.

The retaining element may be integrally formed with the insertion tool or integrally attached to the insertion tool, eg, the remainder of the insertion tool.

The entire retaining element of the insertion tool is elastically deformable. The retaining element is elastically deformable along its entire length. The length of the retaining element extends along its longitudinal direction, i.e., along its axis, i.e., the longitudinal direction of the insertion tool, i.e., the direction from the proximal portion of the insertion tool towards the distal portion of the insertion tool.

The proximal portion of the insertion tool is the portion that is closer to the clinician when the insertion tool is in use. The distal portion of the insertion tool is the portion that is closer to the implant site when the insertion tool is in use.

The distal portion of the insertion tool is used to cooperate with the implant. Specifically, the distal portion can cooperate with a corresponding part of the coronal portion of the implant, such as a socket. The distal portion can be at least partially introduced into the socket. The distal portion of the insertion tool cooperates with the implant, for example, the implant socket, so that when the insertion tool is rotated about its longitudinal axis, the implant is screwed into the bone tissue. Due to the cooperation or interaction between the distal tool portion and the implant, a rotational force applied to the insertion tool about its longitudinal axis, for example manually or by using a motor, is transmitted to the implant so that the implant is screwed into the bone tissue.

The distal portion of the insertion tool may have a transmission component as a component for cooperating with the implant. The transmission component may include or may be an anti-rotation structure. The anti-rotation structure is configured to prevent relative rotation between the insertion tool and the implant around the longitudinal axis of the tool when the tool and the implant are engaged with each other, for example, by at least partially introducing the distal portion of the tool into the implant socket. Therefore, the rotational force applied to the insertion tool around its longitudinal axis is transmitted to the implant. The anti-rotation structure of the insertion tool may have a cross-section perpendicular to the longitudinal axis of the insertion tool, i.e., an outer cross-section, which is non-rotationally symmetrical, for example, it is non-circular. The anti-rotation structure of the distal portion of the insertion tool may cooperate with a corresponding anti-rotation structure of the implant. The anti-rotation structure of the implant may have a cross-section perpendicular to the longitudinal axis of the implant, such as an inner cross-section, which is non-rotationally symmetrical, for example, it is non-circular. The cross-sections of the anti-rotation structures of the tool and the implant may be substantially the same, or may have the same or corresponding shapes.

For example, the transmission component of the distal portion of the insertion tool can be a transmission area and/or a transmission segment, as will be described in further detail below. The transmission area and/or transmission segment of the insertion tool can respectively cooperate with the transmission part and/or transmission area of the implant.

Thus, the entire retaining element is elastically deformable at least in or along all directions perpendicular to the longitudinal direction of the insertion tool, ie in or along all transverse directions of the retaining element, ie all radial directions of the retaining element.

The remainder of the distal portion of the insertion tool may be less elastically deformable than the retaining element in a direction perpendicular to the longitudinal direction of the insertion tool.The remainder of the distal portion of the insertion tool may not be elastically deformable in a direction perpendicular to the longitudinal direction of the insertion tool.

The retaining element may be formed integrally with the insertion element or integrally attached to the insertion tool, for example the remainder of the insertion tool. Thus, the retaining element may form an integral part of the insertion tool.

The attachment portion of the retaining element comprises at least one protrusion or projection extending from an outer surface of the remainder of the retaining element in one or more directions that are substantially perpendicular to the longitudinal direction of the insertion tool.

The at least one protrusion or projection of the attachment portion is configured to be received in a corresponding cavity formed in the coronal portion of the dental implant.

The insertion tool is attached to the dental implant by attaching the attachment portion of the retaining element to the dental implant.

When attaching the attachment portion of the retaining element to the dental implant, the retaining element is first elastically deformed (i.e., elastically compressed) in a transverse direction (i.e., radial direction) of the retaining element and then returns to its original shape due to the restoring force of the retaining element when the at least one protrusion or projection has been received in the corresponding cavity of the dental implant. Thus, the attachment portion can be attached to the dental implant in a reliable and effective manner by a snap fit. The engagement of the at least one protrusion or projection of the attachment portion with the corresponding cavity of the dental implant provides audible and/or tactile feedback to the user (such as, for example, a clinician or technician in a dental laboratory), thereby providing a clear and unambiguous indication that the retaining element and the insertion tool are correctly attached to the dental implant.

The entire retaining element, not just a portion thereof, is elastically deformable in its transverse direction. This achieves a particularly high degree of flexibility in the retaining element. Furthermore, the entire retaining element elastically deforms when attaching the insertion tool to the dental implant, thereby minimizing the risk of wear or breakage of the retaining element, even if the retaining element is repeatedly engaged with and removed from different dental implants.

Thus, the insertion tool of the present invention provides a clear, reliable and effective indication of whether the insertion tool is correctly attached to the dental implant.

The retaining element may be integrally formed with the insertion tool, for example, the rest of the insertion tool. In this document, the term "integrally formed" represents that the retaining element and the insertion tool, for example, the rest of the insertion tool, are formed as a one-piece configuration.

Forming the retaining element with the insertion tool as a one-piece configuration allows the insertion tool to be manufactured in a particularly simple and efficient manner, for example by injection molding, milling, such as CNC milling, or the like.

The retaining element may be integrally attached to the insertion tool, e.g., the rest of the insertion tool. In this document, the term "integrally attached" refers to a retaining element that is attached to the insertion tool in such a manner that the retaining element cannot be removed or separated from the insertion tool without damaging or destroying the retaining element and/or the insertion tool.

A particularly robust and stable construction of the insertion tool is achieved if the retaining element is formed integrally with the insertion tool or is integrally attached to the insertion tool.

The retaining element may have a substantially cylindrical shape, for example with a substantially circular cross-section perpendicular to the longitudinal direction of the insertion tool.

The at least one projection or protrusion of the attachment portion of the retaining element extends in one or more directions substantially perpendicular to the longitudinal direction of the insertion tool, i.e., in one or more transverse directions thereof. Specifically, the attachment portion may include at least one projection or protrusion extending in multiple transverse directions of the retaining element, i.e., extending along a portion of the outer surface of the remainder of the retaining element in the circumferential direction of the retaining element. The at least one projection or protrusion may extend along 1% or more, 1.5% or more, 2% or more, 5% or more, 10% or more, 20% or more, or 30% or more of the outer circumference of the remainder of the retaining element.

The insertion tool may be made of, for example, a metal such as stainless steel, a polymer, or a composite material.

The remaining part of holding element and insertion tool can be made of the same material or different materials.If holding element is made of a material different from the remaining part of insertion tool, the holding force provided by holding element can be set in a particularly simple manner so.

The retaining element may include at least one portion extending from the distal end of the retaining element toward the proximal end of the retaining element, which is more flexible than the remainder of the retaining element. This flexible portion of the retaining element contributes to or even provides for the elastic deformability of the retaining element. Thus, the retaining element can be constructed in an elastically deformable manner in a simple and effective manner.

At least one portion extending from the distal end of the retaining element to the proximal end of the retaining element may be made of or formed from a material that is more flexible than the material of the remaining portion of the retaining element. Alternatively or alternatively, the at least one portion may have a construction or structure that is more highly flexible than the construction or structure of the remaining portion of the retaining element. For example, the at least one portion may be made more flexible by providing, for example, perforations, recesses, openings, etc. In addition, for example, the at least one portion may have a smaller thickness, i.e., a smaller wall thickness, than the remaining portion of the retaining element.

The retaining element may have two or more, three or more, or four or more portions extending from the distal end of the retaining element to the proximal end of the retaining element that are more flexible than the remainder of the retaining element.

The retaining element may include at least one cutout or recessed portion extending from the distal end of the retaining element to the proximal end of the retaining element. This at least one cutout or recessed portion facilitates or even provides elastic deformability of the retaining element. Forming a retaining element having such at least one cutout or recessed portion provides a particularly flexible design of the retaining element. Furthermore, the retaining element has a particularly simple structure.

The retaining element may be a hollow and/or tubular body, wherein at least one cutout or recess partially penetrates the outer wall of the retaining element. The retaining element may have an open ring shape or an open annular shape in a cross section perpendicular to the longitudinal direction of the retaining element (i.e., the longitudinal direction of the insertion tool), i.e., a ring shape with an opening in its circumference, or a substantially C-shape.

The retaining element may have a closed ring shape or a closed annular shape, ie the shape of a ring without openings in its circumference.

The retaining element may be integrally formed with or integrally connected to the insertion tool, e.g., the rest of the insertion tool, by one or more coupling portions arranged between the retaining element and the insertion tool (e.g., the rest of the insertion tool). The one or more coupling portions may be arranged between the retaining element and the insertion tool in the longitudinal direction of the retaining element. Each of the one or more coupling portions may extend along only a portion of the retaining element in the circumferential direction of the retaining element.

In this way, the holding element can be integrated with the insertion tool in a particularly simple and reliable manner.

At least one or some of the one or more coupling portions may extend along 1% or more, 1.5% or more, 2% or more, 5% or more, 10% or more, 20% or more, 30% or more, or 40% or more of the circumference of the retaining element. Each of the one or more coupling portions may extend along 10% or more, 20% or more, 30% or more, or 40% or more of the circumference of the retaining element.

The retaining element can be formed integrally with the insertion tool or integrally attached to the insertion tool by a plurality of coupling portions (e.g., two coupling portions, three coupling portions, four coupling portions, or five coupling portions) arranged between the retaining element and the insertion tool (e.g., the rest of the insertion tool). The coupling portions can be separated from each other in the circumferential direction of the retaining element, that is, they are respectively arranged so that there is a gap between adjacent coupling portions in the circumferential direction of the retaining element. The coupling portions can be equidistant from each other in the circumferential direction of the retaining element, or can be spaced apart from each other at different intervals in the circumferential direction of the retaining element. The coupling portions can have the same or different extensions along the circumference of the retaining element (i.e., in the circumferential direction of the retaining element).

The retaining element may be integrally formed with the insertion tool (e.g., the rest of the retaining element) or integrally attached to the insertion tool via a single coupling portion. The retaining element may have a single portion extending from the distal end of the retaining element to the proximal end of the retaining element, the single portion being more flexible than the rest of the retaining element. The single coupling portion may be arranged opposite the single portion in a radial direction of the retaining element or adjacent to the single portion in a circumferential direction of the retaining element.

The retaining element may be integrally formed with the insertion tool or integrally attached to the insertion tool via a single coupling portion. The retaining element may have a single cutout or recessed portion extending from the distal end of the retaining element to the proximal end of the retaining element. The single coupling portion may be arranged to be opposite the cutout or recessed portion in the radial direction of the retaining element, or adjacent to the cutout or recessed portion in the circumferential direction of the retaining element.

The retaining element may be formed integrally with the insertion tool or integrally attached to the insertion tool via a single coupling portion. The single coupling portion may be arranged opposite to at least one protrusion or projection of the attachment portion in a radial direction of the retaining element, or adjacent to at least one protrusion or projection of the attachment portion in a circumferential direction of the retaining element.

The retaining element may be formed integrally with the insertion tool or integrally attached to the insertion tool via at least two coupling portions.The at least two coupling portions may be arranged opposite to each other in a radial direction of the retaining element.

The attachment portion of the insertion tool may include multiple (e.g., two or more, three or more, four or more, or five or more) protrusions or projections, each protrusion or projection extending in one or more directions substantially perpendicular to the longitudinal direction of the insertion tool.

The plurality of protrusions or projections may have the same or different extensions in the circumferential direction of the retaining element. The plurality of protrusions or projections may have the same or different projection heights from the outer surface of the rest of the retaining element, i.e., from this surface in one or more directions substantially perpendicular to the longitudinal direction of the insertion tool.

The plurality of protrusions or projections of the attachment portion may be arranged sequentially or continuously in the circumferential direction of the retaining element, i.e., arranged one after the other in this circumferential direction. The plurality of protrusions or projections may be spaced equidistantly from one another in the circumferential direction of the retaining element, or spaced at different intervals from one another.

The plurality of protrusions or projections of the attachment portion are configured to be received in one or more corresponding cavities formed in the coronal portion of the dental implant.

As already described in detail above, the retaining element may have at least one portion extending from the distal end of the retaining element to the proximal end of the retaining element, which is more flexible than the rest of the retaining element. The retaining element may have or may define at least one cutout or recessed portion extending from the distal end of the retaining element to the proximal end of the retaining element. At least one protrusion or projection of the attachment portion of the insertion tool may be arranged adjacent to the at least one more flexible portion or the at least one cutout or recessed portion of the retaining element. In this way, a particularly reliable and effective snap-fit connection between the retaining element and the dental implant can be ensured.

The insertion tool may have a visual indicator, such as a marking, configured to provide further indication of whether the insertion tool and the dental implant are correctly attached to each other. For example, the visual indicator may include or may be a coating, a laser marking, a groove, etc. The visual indicator may be provided on the distal portion of the insertion tool.

The retaining element can be formed from a single material. The retaining element can be made of, for example, a metal such as titanium, a titanium alloy or stainless steel, a polymer or a composite material. In this way, the retaining element can be constructed in an elastically deformable manner in a particularly simple and reliable manner.

The material of the retaining element may be metal, superelastic, amorphous, etc.

The retaining element can be manufactured, for example, by injection molding, milling (such as CNC milling), etc. For example, the retaining element can be manufactured by injection molding using a colored plastic, for example, to provide a color code as a marking. If the retaining element is made of metal, such as titanium, a titanium alloy, or stainless steel, the retaining element can be anodized.

According to one aspect of the present invention, an insertion tool is provided for inserting a dental implant, in particular a dental implant according to the present invention, into bone tissue of a patient. The insertion tool comprises a proximal portion and a distal portion, the distal portion being adapted to engage the implant. The distal portion has a transmission region, wherein a cross section of the distal portion perpendicular to the longitudinal direction of the insertion tool has a plurality of main directions in which a radius, measured between the center of the cross section and its outer contour, takes a relatively maximum value and therefore a higher value than in adjacent orientations.

A transmission region of the distal portion of the insertion tool engages the implant. The transmission region comprises an anti-rotation feature, such as the anti-rotation feature described in detail above. The transmission region is configured to prevent relative rotation between the insertion tool and the implant about the longitudinal axis of the tool when the tool and the implant are engaged with each other, for example, by at least partially introducing the distal portion of the tool into the implant socket.

The cross-sectional shape of the transmission region, as described above, allows rotational forces applied to the insertion tool about its longitudinal axis to be effectively, reliably, and uniformly transmitted to the implant. Thus, the insertion tool is able to reliably insert the implant into the patient's bone tissue while minimizing the risk of damage or breakage to the implant, particularly its socket.

The transmission region of the distal portion of the insertion tool is configured to cooperate with a corresponding anti-rotation structure, specifically, a transmission portion of the implant. In the transmission portion of the implant, a cross-section of the socket or channel of the implant perpendicular to the longitudinal direction of the implant (i.e., an inner cross-section) has a plurality of principal directions in which the radius measuring the distance between the center of the cross-section and its outer contour takes a relative maximum value and therefore takes a higher value than in adjacent orientations. The cross-sections of the transmission region of the insertion tool and the transmission portion of the implant can be substantially identical.

The cross-section of the transmission region of the insertion tool can be characterized by an eccentricity parameter characteristic of the deviation of the corresponding cross-section from a circular shape. For the purposes of this description and disclosure and in accordance with the present invention, this eccentricity parameter is defined as the ratio of the maximum radius of the cross-section to its minimum radius, such that the eccentricity parameter assumes a value of 1 for a circular shape. The eccentricity parameter of the cross-section of the transmission region of the insertion tool is greater than 1. The eccentricity parameter can be, for example, in the range of 1.1 to 1.6, 1.2 to 1.5, or 1.3 to 1.4.

This eccentricity parameter can be evaluated for each value of the parameter characteristic of the coordinate in the longitudinal direction of the insertion tool. The eccentricity parameter of the transmission region can be constant in the longitudinal direction of the insertion tool. Alternatively, the eccentricity parameter of the transmission region can vary in the longitudinal direction of the insertion tool, for example, decreasing in the direction from the proximal end of the tool toward the distal end of the tool. The eccentricity parameter of the transmission region can have a linear dependence on the coordinate parameter in the longitudinal direction of the insertion tool.

In some embodiments, a main direction in the transmission region of the insertion tool, in which main direction the corresponding radius of the cross section has a local maximum, is located symmetrically, in particular axially symmetrically, with respect to a central longitudinal axis of the insertion tool.

The number of main directions in the transmission area of the insertion tool can be three or more, four or more, five or more, or six or more.

In some embodiments, the number of main directions in the transmission region of the insertion tool can be three, i.e., the transmission region has a triangular oval cross-section. Combined with the symmetrical positioning of the main directions with respect to the longitudinal direction of the insertion tool, as detailed above, this triangular oval shape results in a rotational offset angle of 120° between two adjacent main directions.

The transmission region may have a tapered configuration such that in the transmission region a lateral dimension or extension of a cross section of the distal portion perpendicular to the longitudinal direction of the insertion tool decreases in a direction from the proximal end of the insertion tool towards the distal end of the insertion tool.

In the transmission region, a cross-sectional area of the distal portion perpendicular to the longitudinal direction of the insertion tool (ie, a cross-sectional area of the distal portion) may decrease in a direction from the proximal end of the insertion tool toward the distal end of the insertion tool.

According to one aspect of the present invention, an insertion tool for inserting a dental implant, in particular a dental implant according to the present invention, into a patient's bone tissue is provided. The insertion tool comprises a proximal portion and a distal portion, the distal portion being adapted to cooperate with the implant. The distal portion comprises a transmission section. In the transmission section, a cross section of the distal portion perpendicular to the longitudinal direction of the insertion tool comprises a plurality of radially projecting portions and a plurality of radially recessed portions, which are arranged alternately along the circumference of the cross section. Each of the radially outermost points of the radially projecting portions lies on a corresponding circle surrounding the center of the cross section. At least two of these circles have different radii from one another.

A transmission section of the distal portion of the insertion tool engages the implant. The transmission section comprises an anti-rotation feature, such as the anti-rotation feature described in detail above. The transmission section is configured to prevent relative rotation between the insertion tool and the implant about the longitudinal axis of the tool when the tool and the implant are engaged with each other, for example, by at least partially introducing the distal portion of the tool into the implant socket.

The cross-sectional shape of the transmission section, as described above, allows rotational forces applied to the insertion tool about its longitudinal axis to be efficiently, reliably, and uniformly transmitted to the implant. Thus, the insertion tool can reliably insert the implant into the patient's bone tissue while minimizing the risk of damage or breakage to the implant, particularly its socket.

The transmission section of the distal portion of the insertion tool is configured to cooperate with a corresponding anti-rotation structure, specifically, a transmission zone of the implant. In the transmission zone of the implant, a cross-section of the socket or channel of the implant perpendicular to the longitudinal direction of the implant, i.e., the inner cross-section, has a plurality of radially raised portions and a plurality of radially recessed portions, which are arranged alternately along the circumference of the cross-section, wherein each of the radially outermost points of the radially raised portions lies on a corresponding circle around the center of the cross-section, and at least two of these circles have different radii from each other. The cross-sections of the transmission section of the insertion tool and the transmission zone of the implant can be substantially identical or correspond to each other.

The radially innermost points of the radially concave portion may lie on a single circle around the center of the cross section. Thus, all radially innermost points of the radially concave portion may lie on the same circle around the center of the cross section. Alternatively, at least two radially innermost points of the radially concave portion may lie on different circles having different radii around the center of the cross section.

The cross section of the distal portion of the insertion tool in the transmission section may have the same number of radial protrusions and radial recesses. The number of radial protrusions and/or radial recesses may be 2 or more, 3 or more, 4 or more, 5 or more, 6 or more, 7 or more, 8 or more, or 9 or more. In a particularly preferred embodiment, the cross section has 6 radial protrusions and 6 radial recesses.

The radially raised portion may include one or more first radially raised portions and one or more second radially raised portions, wherein the one or more radially outermost points of the one or more first radially raised portions are all on a single first circle around the center of the cross-section, and the one or more radially outermost points of the one or more second radially raised portions are all on a single second circle around the center of the cross-section.

The radius of the second circle may be smaller than the radius of the first circle.

The first radially convex portions and the second radially convex portions may be alternately arranged along the circumference of the cross section with corresponding radially concave portions provided therebetween.

The number of the first radially protruding portions may be the same as the number of the second radially protruding portions.

The radially protruding portion of the cross section of the distal portion of the insertion tool in the transmission section may include only the first and second radially protruding portions, ie, except for the first and second radially protruding portions, no further radially protruding portions may exist in the cross section.

The radially convex portion and/or the radially concave portion of the cross section of the transmission segment may each have a curved shape, for example at least partially circular, at least partially elliptical, at least partially oval, etc.

The radially convex portion and the radially concave portion of the cross section of the transmission section may be arranged directly or immediately adjacent to each other.One radially convex portion may be directly or immediately adjacent to two radially concave portions, and vice versa.

The distal portion of the insertion tool of the present invention may have a transmission region and a transmission section as described in detail above.The transmission region may be arranged in the vicinity of the transmission section.

By providing a distal part of the insertion tool with both a transmission area and a transmission section, any damage or breakage to the implant, in particular to its socket, when the implant is inserted into the bone tissue can be avoided particularly reliably. Specifically, due to the presence of two anti-rotation structures (i.e., the transmission area and the transmission section) on the distal part of the insertion tool, which can cooperate with two corresponding anti-rotation structures on the implant (e.g., the transmission part and the transmission area), the rotational force or load applied to the implant when the implant is inserted into the bone tissue can be shared by the two structures. Thereby, any damage to either of the two structures in the implant can be minimized. Therefore, after the implant has been inserted into the bone tissue, one or both of these structures in the implant can be reliably and effectively used as an indicator for a base, scanning column, impression column, etc.

The distal portion of the insertion tool of the present invention may have a retaining element and a transmission region as described in detail above.The transmission region may be arranged in the vicinity of the retaining element.

The distal portion of the insertion tool of the present invention may have a retaining element and a transmission section as described in detail above.The transmission section may be arranged distal to the retaining element.

The distal portion of the insertion tool of the present invention may include a retaining element, a transmission region, and a transmission section as described in detail above. The transmission section may be disposed distally of the retaining element. The transmission region may be disposed adjacent to the retaining element. The transmission section, retaining element, and transmission region may be arranged in this order, moving from the distal end of the insertion tool toward the proximal end of the insertion tool.

The insertion tool can be made up of a single piece of material. In this case, all parts of the insertion tool are formed integrally with each other.

The insertion tool may consist of two separate parts, eg a distal part and a proximal part, which are attached to each other, in particular, releasably attached to each other.

The two separate parts of the insertion tool may be permanently attached to each other.

For example, the distal component of the insertion tool may have a protrusion that fits into a corresponding recess in the proximal component of the insertion tool. By inserting the protrusion into the recess, the distal component and the proximal component can be attached to each other, in particular, releasably attached to each other.

The protrusion and the recess may have corresponding anti-rotation features or structures to prevent any rotation of the distal component and the proximal component relative to each other about the longitudinal axis of the insertion tool.

The anti-rotation structure of the distal component may have a cross-section perpendicular to the longitudinal direction of the insertion tool, for example, the outer cross-section of the protrusion, which is not rotationally symmetrical, for example, it is non-circular, such as elliptical, oval, polygonal, such as rectangular, square or hexagonal, etc. The anti-rotation structure of the distal component of the insertion tool can cooperate with the corresponding anti-rotation structure of the proximal component of the insertion tool. The anti-rotation structure of the proximal component of the insertion tool may have a cross-section perpendicular to the longitudinal direction of the insertion tool, for example, the inner cross-section of the recessed portion, which is not rotationally symmetrical, for example, it is non-circular, such as elliptical, oval, polygonal, such as rectangular, square or hexagonal, etc. The cross-sections of the anti-rotation structures of the distal component and the proximal component may be substantially the same.

Providing the insertion tool in the form of two separate parts (e.g., a distal part and a proximal part) as detailed above makes the production of the insertion tool, in particular the production of the retaining element, simpler and easier. This applies in particular to the case where the retaining element is provided on the proximal part of the insertion tool. For example, the retaining element can be produced by milling.

One of the two independent parts of the insertion tool, in particular, the distal part, can include the transmission section, and the other of the two independent parts, in particular, the proximal part, can include the retaining element and the transmission area. In this way, the production of the insertion tool, in particular the production of the retaining element, can be further simplified.

The retaining element may be formed integrally with the other of the two separate components, in particular the proximal component.

The retaining element may be integrally attached to the other of the two separate components, in particular the proximal component.

The invention further provides a combination of a dental implant according to the invention and an insertion tool according to the invention.

The explanations, features and definitions provided above for the dental implant and the insertion tool of the present invention fully apply to the combination of the present invention.

The combination of the present invention provides the effects and advantages already described in detail above for the dental implant and insertion tool of the present invention.

The dental implant may have at least one cavity formed in its coronal portion for receiving at least one protrusion or projection of the attachment portion of the retaining element.

According to one aspect of the present invention, a dental implant is provided, in particular for insertion into bone tissue of a patient, comprising a core having a top end and a coronal end. The core comprises a channel or socket leading to the coronal end and extending from the coronal end toward the top end along the longitudinal direction of the implant. The core has a transmission zone, in which the cross section of the channel perpendicular to the longitudinal direction of the implant has a plurality of radial protrusions arranged along the circumference of the cross section. Thus, each of the radially outermost points of the radial protrusions is on a corresponding circle around the center of the cross section. At least two of these circles have radii that are different from each other. The inner cross section of the socket or channel of the implant perpendicular to the longitudinal direction of the implant may have a plurality of radial protrusions and a plurality of radial recesses arranged alternately along the circumference of the cross section.

The longitudinal direction of the dental implant extends from the coronal end of the implant toward the apex of the implant. The cross section of the channel perpendicular to the longitudinal direction of the implant is the inner cross section of the channel.

The transmission region of the implant core cooperates with an insertion tool, specifically, the insertion tool of the present invention described in detail above, i.e., with its transmission section. The transmission region constitutes an anti-rotation structure, such as the anti-rotation structure described in detail above. The transmission region is configured to prevent relative rotation between the insertion tool and the implant about the longitudinal axis of the tool when the tool and the implant are engaged with each other, for example, by at least partially introducing the distal portion of the tool into a channel or socket of the implant.

The cross-sectional shape of the transmission zone, as described above, allows for efficient, reliable, and uniform transmission of rotational forces applied to the insertion tool about its longitudinal axis to the implant. Consequently, the implant can be reliably inserted into the patient's jaw or bone tissue while minimizing the risk of damage or breakage to the implant, particularly its channel or socket.

The transmission zone of the implant is configured for cooperating with a corresponding anti-rotation structure, in particular a transmission section, of the distal portion of the insertion tool.The cross-sections of the transmission zone of the implant and the transmission section of the insertion tool may be substantially identical.

The radially innermost points of the radially concave portions of the channel cross-section in the transmission region may lie on a single circle around the center of the cross-section. Thus, all radially innermost points of the radially concave portions may lie on the same circle around the center of the cross-section. Alternatively, at least two radially innermost points of the radially concave portions may lie on different circles having different radii around the center of the cross-section.

The cross section of the channel in the transmission zone may have the same number of radial projections and radial recesses. The number of radial projections and/or radial recesses may be 2 or more, 3 or more, 4 or more, 5 or more, 6 or more, 7 or more, or 8 or more. In a particularly preferred embodiment, the cross section has 6 radial projections and 6 radial recesses.

The radially raised portion may include one or more first radially raised portions and one or more second radially raised portions, wherein the one or more radially outermost points of the one or more first radially raised portions are all on a single first circle around the center of the cross-section, and the one or more radially outermost points of the one or more second radially raised portions are all on a single second circle around the center of the cross-section.

The radius of the second circle may be smaller than the radius of the first circle.

At least one of the one or more radially outermost points of the one or more first radially projecting portions may be located at an angular position that matches the angular position of the relative maximum of the core of the dental implant within an angular tolerance range. The tolerance range may be approximately +-10°, preferably approximately +-5°. The radially outermost points of the one or more first radially projecting portions may be located at the same (or substantially the same) angular position as the relative maximum of the core of the dental implant.

The number of radially outermost points of the one or more first radially projecting portions may be the same as the number of relative maxima of the implant core.

At least one of the one or more radially outermost points of the one or more second radially projecting portions may be located at an angular position that matches the angular position of the minimum value of the core of the dental implant within an angular tolerance range. The tolerance range may be approximately +-10°, preferably approximately +-5°. The radially outermost points of the one or more second radially projecting portions may be located at the same (or substantially the same) angular position as the relative maximum value of the core of the dental implant.

The above-mentioned configuration of the outermost point of the transmission zone ensures that, in a given cross section, a maximum amount of material is present between said outermost point and the outer edge of the core of the implant.

The first radially convex portions and the second radially convex portions may be alternately arranged along the circumference of the cross section with corresponding radially concave portions provided therebetween.

The number of the first radially protruding portions may be the same as the number of the second radially protruding portions.

The radially protruding portion of the cross section of the channel in the transmission area may include only the first radially protruding portion and the second radially protruding portion, ie, apart from the first radially protruding portion and the second radially protruding portion, no further radially protruding portion may exist in the cross section.

The radially convex portion and/or the radially concave portion of the cross section of the channel in the transmission region may each have a curved shape, for example at least partially circular, at least partially elliptical, at least partially oval, etc.

The radially convex portion and the radially concave portion of the cross section of the channel in the transmission area can be arranged directly or immediately adjacent to each other. One radially convex portion can be directly or immediately adjacent to two radially concave portions, and vice versa.

The core may further comprise a transmission portion in which a cross section of the channel perpendicular to the longitudinal direction of the implant has a plurality of main directions in which the radius measuring the distance between the centre of the cross section and its outer contour takes a relatively maximum value and therefore a higher value than in adjacent orientations.

The transmission portion of the implant core engages an insertion tool, specifically, the insertion tool of the present invention described in detail above, i.e., its transmission region. The transmission portion comprises an anti-rotation feature, such as the anti-rotation feature described in detail above. The transmission portion is configured to prevent relative rotation between the insertion tool and the implant about the longitudinal axis of the tool when the tool and the implant are engaged with each other, for example, by at least partially introducing the distal portion of the tool into the implant channel or socket.

The cross-sectional shape of the transmission portion, as described above, allows for efficient, reliable, and uniform transmission of rotational forces applied to the insertion tool about its longitudinal axis to the implant. Consequently, the implant can be reliably inserted into the patient's jaw or bone tissue while minimizing the risk of damage or breakage to the implant, particularly its channel or socket.

The transmission portion of the implant is configured to cooperate with a corresponding anti-rotation structure of the distal portion of the insertion tool, in particular the transmission region. The transmission portion of the implant and the transmission region of the insertion tool may be substantially identical in cross-section.

The cross-section of the transmission portion of the implant can be characterized by an eccentricity parameter characteristic of the deviation of the corresponding cross-section from a circular shape. For the purposes of this description and disclosure and in accordance with the present invention, this eccentricity parameter is defined as the ratio of the maximum radius of the cross-section to its minimum radius, such that the eccentricity parameter takes a value of 1 for a circular shape. The eccentricity parameter of the cross-section of the transmission portion of the implant is greater than 1. The eccentricity parameter can be in the range of, for example, 1.1 to 1.6, 1.2 to 1.5, or 1.3 to 1.4.

This eccentricity parameter can be evaluated for each value of the parameter characteristic of the coordinate in the longitudinal direction of the dental implant. The eccentricity parameter of the transmission part can be constant in the longitudinal direction of the implant. Alternatively, the eccentricity parameter of the transmission part can vary in the longitudinal direction of the implant, for example, decreasing in the direction from the coronal end of the implant towards the apex of the implant. The eccentricity parameter of the transmission part can have a linear dependence on the coordinate parameter in the longitudinal direction of the implant.

In some embodiments, a main direction in the transmission portion of the implant, in which main direction the corresponding radius of the cross section has a local maximum, is located symmetrically, in particular axially symmetrically, with respect to a central longitudinal axis of the implant.

The number of main directions in the transmission part of the implant may be three or more, four or more, five or more, or six or more.

In some embodiments, the number of main directions in the transmission portion of the implant is three, i.e., the transmission portion has a triangular oval cross-section. Combined with the symmetrical positioning of the main directions with respect to the longitudinal direction of the implant, as detailed above, this triangular oval shape results in a rotational offset angle of 120° between two adjacent main directions.

The transmission portion may have a tapered configuration such that in the transmission portion, the lateral dimension or extension of a cross section of the channel perpendicular to the longitudinal direction of the implant decreases in a direction from the coronal end of the core towards the apical end of the core.

In the transmission portion, an area of a cross section of the channel perpendicular to the longitudinal direction of the implant (ie, a cross-sectional area of the channel) may decrease in a direction from a coronal end of the core toward an apical end of the core.

Therefore, the core of the implant of the present invention may have a transmission area and a transmission part as described in detail above. The transmission area may be arranged at the top end of the transmission part.

By providing a core body of the implant having both a transmission zone and a transmission portion, any damage or breakage of the implant, in particular of its channel or socket, when the implant is inserted into the jaw or bone tissue can be avoided particularly reliably. In particular, due to the presence of two anti-rotation structures (i.e., the transmission zone and the transmission portion) on the core body of the implant, which can cooperate with two corresponding anti-rotation structures (e.g., the transmission section and the transmission area) on the distal part of the insertion tool, the rotational force or load applied to the implant when the implant is inserted into the bone tissue can be shared by the two structures. Thereby, any damage to either of the two structures in the implant can be minimized. Therefore, after the implant has been inserted into the jaw or bone tissue, one or both of these structures in the implant can be reliably and effectively used as an indicator for a base, scanning column, impression column, etc.

The core may have an outer surface extending along a longitudinal direction of the implant between an apical end and a coronal end.

The dental implant may further include at least one thread extending outwardly from the core, wherein the thread has a top surface facing toward the apical end of the core, and a coronal surface facing toward the coronal end of the core.

The thread may have a groove formed therein, ie, a cutting groove, wherein the groove extends from the apical end of the thread toward the coronal end of the thread.

The thread may have, at its apical portion, a recess formed in its coronal surface, which extends along a portion of the thickness of the thread in a direction from the coronal surface towards the apical surface, wherein the recess opens into the groove, ie into the groove.

According to one aspect of the present invention, a dental implant is provided, in particular for insertion into bone tissue of a patient, comprising a core having a top end, a coronal end, and an outer surface extending between the top end and the coronal end along the longitudinal direction of the implant. The implant further comprises at least one thread extending outwardly from the core. The thread has a top surface facing the top end of the core, and a coronal surface facing the coronal end of the core. The thread has a groove formed therein, i.e. a cutting groove. The groove extends from the top end of the thread toward the coronal end of the thread. The thread has a recessed portion formed in its coronal surface at its top side portion, the recessed portion extending along a portion of the thickness of the thread in a direction from the coronal surface toward the top surface. The recessed portion leads to the groove, i.e. to the groove.

The thickness of the thread extends from the coronal surface of the thread toward the top surface of the thread. The width of the thread extends in the radially outward direction from the core. The length of the thread extends in the longitudinal direction of the implant.

By providing a thread with grooves and depressions, as detailed above, the implant is made self-cutting. Furthermore, the arrangement of the grooves and depressions helps reduce the insertion torque or rotational force required to insert the implant into the jawbone or bone tissue. This is particularly advantageous in cases of hard bone. No axial pressure is required when inserting the implant. Instead, the implant effectively and reliably pulls itself into the implantation site as it rotates.

The recess has a cutting function, ie a function of cutting bone tissue. Thus, the recess helps to effectively cut and remove bone material and further transfer the removed bone material towards the coronal end of the core.

In particular, when inserting an implant into an implantation site (e.g., a tooth extraction site) where the implant must be cut sideways due to an inclined or angled arrangement between the implant and the bone tissue, the implant of the present invention ensures smooth and accurate placement in the bone. Furthermore, the recessed portion greatly facilitates inserting the implant into poorly prepared holes in the bone tissue or into extraction sockets where the bone walls are uneven and the cylindrical osteotomy typically produced by drilling is therefore not possible.

Therefore, the implant of the present invention allows to be inserted into the bone tissue with reduced force and high precision. In this way, a particularly stable and robust connection or engagement of the implant with the bone tissue, ie a high implant stability, can be achieved.

Due to the arrangement of the depressions in the coronal surface of the thread, the advantageous effects indicated above can be achieved over a wide range of implant thread angles, ie for substantially all implant thread angles, in particular for small implant thread angles.

Therefore, the present invention provides a dental implant that enables reliable and accurate placement and engagement of the dental implant in jawbone or bone tissue at various implant thread angles, particularly small implant thread angles.

The dental implant comprises at least one thread.The dental implant may comprise a plurality of threads, for example, two or more threads, three or more threads, or four or more threads.

At least one thread has at least one groove formed therein, i.e., at least one cutting groove. The at least one groove extends along the length of the at least one groove from the apex of the thread toward the coronal end of the thread. The at least one groove begins at the apex of the thread and extends from there toward the coronal end of the thread. The at least one groove may extend over 20% or more, 30% or more, 40% or more, 50% or more, or 60% or more of the length of the thread.

The at least one groove may extend in a direction substantially parallel to the longitudinal direction of the implant or in a direction inclined or skewed with respect to the longitudinal direction of the implant. In the latter case, the angle between the extension direction of the at least one groove and the longitudinal direction of the implant may be in the range of 2° to 20°, 5° to 15°, or 8° to 12°.

The at least one groove extends along a portion of the core circumference in the width direction of the at least one groove. The at least one groove may extend over 10% to 30%, 15% to 25%, or 18% to 22% of the core circumference. The thread may have a plurality of grooves formed therein, i.e., a plurality of cutting grooves. One of the plurality of grooves extends from the apex of the thread toward the coronal end of the thread. The thread may have two or more grooves, three or more grooves, or four or more grooves formed therein.

The plurality of grooves may be arranged in a staggered or shifted configuration along the length of the thread and/or along the circumference of the thread (ie, the circumference of the core).

The thread has at least one recess formed in its coronal surface, extending along a portion of the thread's thickness in a direction from the coronal surface toward the apex surface. Thus, the at least one recess begins at the coronal surface and extends from there toward the apex surface. The at least one recess does not completely penetrate the thread in the direction of its thickness. The at least one recess opens onto the coronal surface of the thread, i.e., onto the coronal surface of the thread.

Furthermore, the recess opens into the groove, ie opens into the groove.The recess is arranged adjacent to the groove, ie directly or immediately adjacent to the groove.

The at least one recess may extend along 20% to 90%, 30% to 80%, 40% to 70%, or 50% to 60% of the thread thickness in a direction from the coronal surface toward the top surface. In this way, it can be ensured that the recess can effectively assist the bone cutting process while maintaining sufficient stability of the implant.

If the first thread is allowed to cut into the bone, then in situations where less bone is available (eg, an extraction socket), the drill size may be reduced, resulting in better stability of the implant from the tip.

An extension of the at least one recess in a direction from the coronal surface toward the top surface (ie, a depth of the at least one recess) may be constant along a direction parallel to the coronal surface or the top surface.

The extension of the at least one recess in the direction from the coronal surface toward the top surface (i.e., the depth of the at least one recess) may vary along a direction parallel to the coronal surface or the top surface. In this case, the maximum extension of the at least one recess in the direction from the coronal surface toward the top surface may be in the range of 20% to 90%, 30% to 80%, 40% to 70%, or 50% to 60% of the thread thickness. The maximum extension of the at least one recess in the direction from the coronal surface toward the top surface may exist at a portion of the recess that is arranged directly adjacent to the groove.

The extension of the at least one recess in the direction from the coronal surface towards the top surface may decrease along the circumferential direction away from the groove into which the recess opens. In this way, a particularly effective cutting function of the recess may be achieved.

The at least one recess may have a curved shape. For example, the at least one recess may have the shape of a portion or segment of a sphere or ellipsoid, for example, a quarter sphere or a quarter ellipsoid. This shape of the at least one recess allows for particularly simple and cost-effective manufacture of the recess and the implant.

The at least one recess may extend over 50% to 90%, 60% to 80%, or 65% to 75% of the thread width in a width direction of the recess.

The at least one recessed portion may be arranged on an upstream side of the groove in a rotational direction of the implant. The rotational direction of the implant is a direction in which the implant is screwed into bone tissue.

The at least one recess may be formed in the coronal surface of the thread at the first full or complete turn of the thread. The first full or complete turn of the thread is the first complete turn when counting the number of complete turns from the apex of the thread toward the coronal end. Thus, the first full turn of the thread is the topmost full turn of the thread. This arrangement of the at least one recess allows for a particularly stable and robust engagement of the implant with the jawbone or bone tissue.

The at least one recess may be formed in the coronal surface of the thread at a second full or complete turn of the thread.The at least one recess may be formed in the coronal surface of the thread at a third full or complete turn of the thread.

The thread may have a plurality of recesses formed in its coronal surface. For example, one of the plurality of recesses may be formed in each coronal surface of the thread at the first and second full or complete turns of the thread. One of the plurality of recesses may be formed in each coronal surface of the thread at the first, second, and third full or complete turns of the thread.

The thread angle, i.e. the inclination angle of the thread relative to a plane perpendicular to the longitudinal direction of the implant, can be 25° or less, 20° or less, 15° or less, 12° or less, or 10° or less. In a particularly preferred embodiment, the thread angle is 10° or less.

Such a small thread angle offers the advantage of a slower introduction of the implant into the bone tissue, ie each turn of the implant has less forward movement, thus allowing a particularly smooth and accurate placement of the implant.

As noted above, the recessed portion of the implant of the present invention works particularly well with threads having such a small thread angle. Specifically, due to the presence of the recessed portion, the arrangement of the recessed portion in the coronal surface of the thread can provide a localized increase in the thread angle. For example, the thread angle can be locally increased to 20° to 40°, or 25° to 35°.

Therefore, the recess may greatly assist in cutting bone tissue.

The foregoing and other features of the present disclosure will become more fully apparent from the following description and the appended claims, taken in conjunction with the accompanying drawings. It should be understood that these drawings depict only several embodiments according to the present disclosure and are not to be construed as limiting the scope of the present disclosure, which will be described more clearly and in more detail through the use of the accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG1 is a side perspective view of a dental implant according to one embodiment of the present invention,

FIG2 is a side perspective view of an alternative dental implant according to the present invention,

FIG3 is a side view of an embodiment of a dental implant according to the present invention with a zoned area,

FIG4 is a longitudinal cross-sectional view of the implant of FIG3 ,

FIG5 is a longitudinal cross-sectional view of the implant of FIG2 ,

6a, 6b, 6c, 6d, 6e, 7a, 7b, 7c, 7d, 7e, 8a, 8b, 8c, 8d, 8e, 9a, 9b, 9c, 9d, 9e, 10a, 10b, 10c, 10d, 10e, 10f, 11, 12a, 12b, 12c, 12d, 12e, 12f, 12g, 12h, 12i, and 12j are views of different embodiments of an implant according to the present invention, respectively.

13-18 are side views of different embodiments of implants according to the present invention provided with cutting grooves,

FIG. 19 is a side perspective view of a coronal section of the preferred embodiment of the implant of FIG. 11 ,

FIG20 is a side view of a dental implant according to one embodiment of the present invention,

FIG21 is a schematic cross-section of the implant shown in FIG20 ,

FIG22 is a longitudinal cross-sectional view of the implant of FIG1, 2, and 11,

FIG23 is an enlarged view of a portion of FIG22 ,

FIG. 24 is a longitudinal section of a portion of the implant of FIG. 1 , 2 , 11 after insertion into bone material,

Figures 25a and 25b are two views of the implant of Figures 1, 2, and 11 from a top perspective,

FIG26 is a longitudinal cross-sectional perspective view of the implant of FIG1, 2 and 11,

27 is a longitudinal sectional perspective view of the top section of the implant of FIG. 1 , 2 , 11 showing the internal connection,

28 is a longitudinal sectional perspective view of a top segment of a dental implant according to another embodiment of the present invention showing an alternative internal connection of the implant,

FIG29 is a side perspective view of a coronal section of a dental implant according to another embodiment of the present invention,

FIG30 is a side perspective view of the dental implant of FIG29,

FIG31 is a side view of the dental implant of FIG29,

FIG32 is a side view of a tip portion of a dental implant according to another embodiment of the present invention,

FIG33 is a bottom perspective view of a dental implant according to another embodiment of the present invention,

FIG34 is a side perspective view of a dental implant according to another embodiment of the present invention,

FIG35 is a graph showing possible variations in the eccentricity of certain portions of an implant along the longitudinal axis of the implant,

36a , 36b , and 36c illustrate an insertion tool according to a first embodiment of the present invention, wherein FIG36a is a side view of the entire insertion tool, FIG36b is an enlarged side view of a distal portion of the insertion tool, and FIG36c is a perspective view of the distal portion of the insertion tool,

37a , 37b , 37c , and 37d illustrate an insertion tool according to a first embodiment of the present invention, wherein FIG37a is an exploded perspective view of a distal portion of the insertion tool, FIG37b is an exploded side view of the distal portion of the insertion tool, FIG37c is an exploded sectional view of the distal portion of the insertion tool, and FIG37d is a sectional view showing a state in which a portion of the distal portion of the insertion tool is inserted into a dental implant.

Figures 38a, 38b, 38c, 38d, 38e and 38f show an insertion tool according to a first embodiment of the present invention, wherein Figure 38a is a side view of the entire insertion tool, Figure 38b is a sectional view of the distal portion of the insertion tool taken along line C-C in Figure 38a, Figure 38c is a side view of the distal portion of the insertion tool, Figure 38d is a sectional view of the distal portion of the insertion tool taken along line A-A in Figure 38c, Figure 38e is a sectional view of the distal portion of the insertion tool taken along line A-A in Figure 38c for a modification of the first embodiment of the insertion tool, and Figure 38f is a sectional view of the distal portion of the insertion tool taken along line B-B in Figure 38c,

39a, 39b, and 39c illustrate a combination of an insertion tool and a dental implant according to a first embodiment of the present invention, wherein FIG39a is a side view of the combination in a state in which the insertion tool is attached to the implant, FIG39b is a sectional view of the distal portion of the insertion tool and the coronal portion of the implant taken along line D-D in FIG39a), and FIG39c is a sectional view of the coronal portion of the implant taken along line E-E in FIG39b.

40a and 40b show an insertion tool according to a second embodiment of the present invention, wherein FIG. 40a and FIG. 40b are perspective views of a distal portion of the insertion tool taken from different angles,

41a , 41b , and 41c illustrate a dental implant according to one embodiment of the present invention, wherein FIG41a is a side view of the implant, FIG41b is a bottom view of the implant, and FIG41c is a cross-sectional view of the implant taken along line H-H in FIG41b ,

42a , 42b , 42c , and 42d illustrate a dental implant according to an embodiment of the present invention, wherein FIG42a is a side view of the top side portion of the implant in the direction of arrow K shown in FIG41c , FIG42b is a side view of the top side portion of the implant in the direction of arrow J shown in FIG41c , FIG42c is an enlarged view of a circled area M shown in FIG41c , and FIG42d is an enlarged view of a circled area G shown in FIG41b , and

Figures 43a, 43b and 43c show a dental implant according to another embodiment of the present invention, wherein Figure 43a is a side view of the implant, Figure 43b is a cross-sectional view of the implant taken along line B-B in Figure 43a, and Figure 43c is a top view of the implant.

DETAILED DESCRIPTION

Preferred embodiments of the present invention will now be described with reference to the accompanying drawings.

In all the figures, like parts are marked with like reference numerals. The individual features shown may be combined in further variations, all of which are considered to be within the scope of the invention.

The dental implant 1 shown in Figure 1 is provided for use in the jawbone of a patient in place of an extracted or fallen tooth in order to retain therein a prosthetic component serving as a denture or crown. In the exemplary embodiment shown, the dental implant 1 is designed to be used in a so-called multi-component configuration and is constructed as a so-called post for insertion into the bone tissue of the patient. The dental implant system in which the dental implant 1 is intended to be used also comprises a second implant component (not shown) associated therewith, which is also called a mounting component or a base, which is provided for fixing a denture or any other prosthetic component with which the implant 1 can cooperate. Alternatively, however, and still in accordance with the invention, the dental implant 1 can also be configured for use in an integrated dental implant system, in which the dental implant 1 also carries, in its top region, means for directly attaching a denture or prosthetic component.

The implant 1 comprises a core 2 as its main body, the core 2 having an apex 4, a coronal end 6, and an outer surface 8 extending between the apex 4 and the coronal end 6 along the longitudinal direction of the core 2. In a one-piece configuration, the coronal end 6 of the core 2 can be appropriately designed so that the prosthesis can be properly attached and has high mechanical stability. However, in the illustrated example, due to the multi-piece configuration of the dental implant system, the coronal end 6 is designed to form a highly mechanically stable connection with a second implant component or abutment. To provide such high mechanical stability, the implant 1 features a receiving channel 10 into which a corresponding connecting pin of the abutment can be inserted after the prosthesis component or prosthesis is appropriately fixed to the mounting component or abutment. By pushing the connecting pin into the receiving channel 10, the implant 1 and the abutment are mechanically connected to each other. The mechanical connection between the implant 1 and the abutment is achieved by an associated connecting screw, the external thread of which is screwed into the internal thread provided in the implant 1, whereby the screw head of the connecting screw presses the abutment onto the implant 1.

On its outer surface 8, the core 2 of the implant 1 is provided with an external thread 12 extending outward from the core 2. The thread 12 (particularly in the area near the apex 4) is configured as a self-cutting thread, with which the implant 1 can be inserted into the jawbone by screwing it into the desired position. The pitch of the thread 12 can be uniform or variable.

In particular, the implant 1 including its threads 12 is specifically designed according to the desired high primary and secondary stability and uniform progression of the forces generated under masticatory loads on the dental implant 1 into the jawbone. To this end, the implant comprises a plurality of dedicated zones or segments, each of which is designated to make a specific contribution to high primary stability or high secondary stability.

Firstly, the core 2 of the dental implant 1 comprises a circular area 20, which in the preferred embodiment shown is located near the top 4. In the core circular area 20, the core 2 of the implant 1 is designed for relatively easy engagement of the thread 12 with the bone material without applying too much stress to the bone tissue during the first moments of screwing the implant 1 into the bone material. To this end, in the core circular area 20, the core 2 has a circular cross-section. The positioning of the core circular area 20 in the apical part of the implant 1 is considered to be highly beneficial in order to maximize the possibility of high primary stability. In general, but also more specifically in extraction sockets this is beneficial, where an immediate loading solution may be preferred. In order to provide significant apical engagement, the circular area 20 has a length of at least 2.5 mm in the embodiment shown, as seen in the longitudinal direction of the implant.

Secondly, in contrast, the core 2 comprises a core-forming region 22. In the embodiment shown in the figures, the core-forming region 22 is located adjacent to the other end of the implant 2, i.e., close to the coronal end 6, and thus constitutes a top platform region 24, but it can alternatively be located in some central or intermediate area of the core 2. In this region 22 (in the embodiment shown, close to the coronal end 6 designed to be connected to the abutment bearing the prosthesis), the core 2 is designed to feature a non-circular cross-section in several main directions, wherein the radius measuring the distance between the center of the cross-section and its outer contour takes a relatively maximum value and therefore has a higher value than in adjacent orientations.

Due to this design of the cross-section in the core forming zone 22, when the core 2 is screwed into the bone tissue, the compressive force exerted on the bone tissue varies in an oscillating manner between a maximum compression (when the local radius of the cross-section becomes maximum (due to the rotational movement of the implant body)) and a minimum compression (when the local radius of the cross-section becomes minimum). Therefore, when the implant body is screwed in, in this zone, the surrounding bone tissue is in a fluctuating state of compression, varying between periods of high compression and periods of relaxation when the compression decreases. In the preferred embodiment shown, the forming zone 22 is positioned at the top of the implant 1. Therefore, after the implant 1 is inserted, the forming zone 22 will stay in the top area of the patient's jaw, which is characterized by relatively hard bone tissue. After insertion, this forming profile characterized by a local minimum will produce an area of low bone stress near the minimum, thereby allowing enhanced regeneration of bone material and significantly minimizing the negative effects of excessive compression on blood vessels. Thus, by providing a local minimum of the shaped area 22 in the area of the critical bone structure, the regeneration of bone material and osseointegration are significantly improved, and it is considered very beneficial to provide these effects for at least 2.5 mm or even better at least 3 mm of the top plate for the purpose of osseointegration. Therefore, as seen in the longitudinal direction of the implant, the first shaped area 22 has a length of at least 2.5 mm in the embodiment shown.

Thirdly, the core 2 of the implant 1 comprises a transition zone 26, which is positioned between the circular zone 20 and the core shaped zone 22, as seen in the longitudinal direction of the implant 1. In order to allow a smooth and advantageous transition between the zones 20, 22, the transition zone 26 is provided with a transient cross-section that changes (as seen in the longitudinal direction) from a circular cross-section that matches the cross-section of the core circular zone 20 in the region close to the core circular zone 20 to a non-circular, leaf-shaped cross-section that matches the cross-section of the core circular zone 20 in the region close to the shaped zone 22. Due to this transition zone 26, direct and abrupt changes in geometry, shearing effects on bone tissue, and other damaging effects on bone tissue can be avoided.

FIG2 shows an alternative embodiment of the invention. This embodiment can be used alone or in combination with the embodiment of FIG1 . In this alternative embodiment, similar to the embodiment of FIG1 , the dental implant 1 ′ is also equipped with a core 2 comprising a core circular zone 20 and a core forming zone 22. However, instead of or in addition to the transition zone 26, the dental implant 1 ′ comprises a second core forming zone 26 ′ in which—as in the first core forming zone 22—the cross section of the core 2 has a plurality of main directions in which the radius measuring the distance between the center of the cross section and its outer contour takes a relative maximum and therefore a higher value than in adjacent orientations. As seen in the longitudinal direction of the implant 1, the second core forming zone 26 ′ is positioned between the zones 20, 22. In order to allow the desired smooth and advantageous transition between the zones 20, 22, in this embodiment the core eccentricity parameter, defined as the ratio of the maximum radius of the cross section of the core 2 to its minimum radius, is greater in the first core forming zone 22 than in the second core forming zone 26′. Obviously, as another alternative, this second forming zone 26′ could also itself consist of a series or a plurality of individual forming zones of this type having different eccentricities.

Figure 3 shows a schematic view of the implant 1 of Figure 1 and the implant 1' of Figure 2, wherein the zones 20, 22, 26, 26' are distinguishably identifiable. In the example shown, the transition zone 26 begins at a distance of approximately 2 to 3 mm from the apex 4 of the implant 1 as seen in the longitudinal direction.

The design concept of the core 2 (i.e. providing three zones 20, 22 and 26 or 20, 22 and 26', respectively) is considered to be a first group of possible embodiments of the concept of the present invention. Alternatively, a second independent group of embodiments of the concept of the present invention, which can be used independently or in combination with the first group of embodiments, can be achieved with beneficial cutting properties and similar or equivalent effects of bone treatment by a design of the outer profile of the thread 12 similar to the design for the core 2 described above. In Figure 4, an embodiment of the implant 1 is shown, which is characterized in that these two groups of alternative embodiments of the present invention are combined, but they can also be used independently. In order to better explain the design of the outer profile of the thread 12, it will be referred to as the "outer volume" or envelope volume 28 defined by the outer profile of the thread 12, as clearly shown in the longitudinal cross-sectional view according to Figure 4.

In the combined embodiment shown, the thread 12 of the implant 1 further comprises a first or profiled thread zone 30, wherein the cross-section of the outer volume 28 enclosing the thread 12 has a plurality of principal directions in which the radius, measuring the distance between the center of the cross-section and its outer contour, takes a relative maximum and therefore a higher value than in adjacent orientations. Furthermore, in this embodiment, the thread 12 comprises a thread circular zone 32, which in the preferred embodiment shown is also located near the apex 4 of the implant 1, wherein the cross-section of the outer envelope volume 28 is substantially circular, and, as seen in the longitudinal direction of the implant, a thread transition zone 34, located between the first, profiled zone 30 and the second, profiled zone 32 (wherein the geometry of the cross-section of the outer volume 28 enclosing the thread 12) changes from a substantially circular shape near the profiled zone 32 to a shape in which the cross-section of the envelope volume 28 corresponds to the shape of the cross-section in the first or profiled zone 30, in particular with respect to the general geometry of the cross-section and/or the values of its characteristic parameters.

FIG5 shows an alternative embodiment of this set of embodiments of the present invention. This embodiment can be used alone or in combination with the embodiment of FIG4 . In this alternative embodiment, similar to the embodiment of FIG4 , the dental implant 1′ also features an envelope volume 28 of the thread 12 comprising a thread circular zone 32 and a thread forming zone 30 . However, instead of or in addition to the thread transition zone 34 , the dental implant 1′ includes a second thread forming zone 34 ′ in which—as in the first thread forming zone 30 —the cross section of the outer volume 28 has a plurality of principal directions in which the radius measuring the distance between the center of the cross section and its outer contour takes on a relative maximum value and therefore has a higher value than in adjacent orientations. As seen in the longitudinal direction of the implant 1 , the second thread forming zone 34 ′ is positioned between the zones 30 , 32 . In order to allow the desired smooth and advantageous transition between the zones 30, 32, in this embodiment, the thread eccentricity parameter, defined as the ratio of the maximum radius of the cross section of the outer volume 28 to its minimum radius, is greater in the first thread forming zone 30 than in the second thread forming zone 34'. Obviously, as another alternative, this second forming zone 34' itself can also consist of a series or a plurality of separate forming zones of this type having different eccentricities.

Due to its transition zones 26, 26', 34, 34', the implants 1, 1' are specifically designed to achieve a smooth and beneficial transition (during the screwing process) between the first engagement of the thread 12 in the bone tissue (in the core circular zone 20 and/or the thread circular zone 32) and the shaping and direct processing of the bone tissue by varying compression (in the shaping zones 22, 30). To further improve the smooth transition between these zones, the core 2 in the transition zone 26 is conical or tapered, in particular with a cone angle/taper angle between 1° and 12°, preferably between 4° and 8°.

The cross-section of the core 2 can be characterized by an eccentricity parameter, defined as the ratio of the maximum radius of the cross-section to its minimum radius. This eccentricity parameter, which takes a circular value of 1, characterizes the deviation of the corresponding cross-section from a circular shape. To provide a particularly smooth transition between the core circular region 20 with a circular cross-section and the core-forming region 22 with a non-circular cross-section, this eccentricity parameter in the transition region 26 has a linear dependence on the coordinate parameters of the implant 1 in the longitudinal direction. In the example shown, the eccentricity value of the core 2 in its core-forming region 22 is approximately 1.1. The same concept can be applied to the eccentricity parameters of the transition region 34 of the thread 12 and the outer volume 28 in the thread-forming region 30.

In the following, various considerations concerning individual elements and components of the implant 1, 1' and their geometrical parameters are discussed with reference to several groups of embodiments according to the implant 1. Obviously, they also apply to several groups of embodiments according to the implant 1' or combinations of these groups of embodiments.

The positions and boundaries of the individual core regions 20, 22, 26 (or 26', respectively) and the individual threaded regions 30, 32, 34 (or 34', respectively) in the longitudinal direction of the implant 1 may be different in different embodiments, seven of which are shown as general examples in Figures 6a to 9e. In each of these representations, Figures 6a, 7a, 8a, 9a show perspective views of the respective implant 1, Figures 6b, 7b, 8b, 9b show longitudinal cross-sectional views of the respective implant 1, and Figures 6c to 6e, 7c to 7e, 8c to 8e, and 9c to 9e show cross-sections of the outer contour of the core 2 and the outer contour of the envelope volume 28.

In the embodiment of Figures 6a to 6e, the core 2 and envelope volume 28 are triangular-oval in their cross-section from the top-middle portion to the coronal end 6 in order to augment the cheek bone and aid in bone normalization.

In the embodiment of Figures 7a to 7e, by contrast, the cross-section of the core 2 is circular in the top region 42 above the transition line 4 (as shown in Figure 7c), while the outer contour of the envelope volume 28 is triangular-oval. This is done to improve torque and initial stability during insertion and the strength of the implant, while maintaining the outer triangular-oval shape to achieve a bone normalization effect and increased cheek bone.

In the embodiment shown in FIGS. 8 a to 8 e , the cross section of the core 2 is circular over the entire length of the implant 1 , and only the outer contour of the envelope volume 28 changes from circular near the apical end 4 to triangular oval near the coronal end 6 .

9a to 9e show an embodiment in which the cross section of the core 2 is circular in the middle portion of the implant 1 ( FIG. 9d ) and triangular-oval in the apical region 42. In the middle range, as shown in FIG. 9d , the circular cross-sectional area of the core 2 overlaps the triangular-oval cross-sectional area of the envelope volume 28.

Figures 10a to 10f show, by way of example, embodiments of the implant 1 and possible input data for CNC machining of the corresponding shapes. In Figure 10a, the implant 1 is shown in a longitudinal section, while Figure 10b shows the implant 1 in a side view. Figure 10c is a longitudinal section through the threaded outer volume 28 of an embodiment of the implant 1, wherein the implant is on the side of the smallest radius. The outer shape of the outer volume 28 can be obtained by CNC machining, wherein the outer shape of the mold matches at least one of the lines shown in Figure 10c. After the raw material has been machined into this form, the thread 12 is machined by engraving a thread groove, the depth of which is given by the outer shape shown in Figure 10d. This results in the final shape of the core 2 as described above.

The triangular ovality of the design of the implant 1 can be obtained by CNC machining, the circular pattern of which is shown in Figure 10f. As can be seen from Figure 10f, the differential ovality parameter e for a typical diameter of about 4 mm is preferably selected to be about 0.23 mm, said differential ovality parameter e being an alternative definition of the shape of the core 2/external volume 28 and being defined by the difference between the maximum radius of the cross section and its minimum radius.

Figure 10c also shows multiple ordinates/points Y01 to Y05 along axis y (longitudinal axis of the implant), which define multiple zones along the axis y. Y01 is a point with a coordinate of 0 mm. In the embodiment shown in Figure 10c, the value of the oval parameter e varies according to the coordinate y along the axis. For example, in the first zone Y01-Y02, the oval parameter e can have a constant value including/selected between 0.10 mm and 0.50 mm, and more preferably between 0.20 mm and 0.25 mm. In addition, the zone Y1-Y2 (external zone 1 or first external zone) can be a zone with a constant eccentricity. In the zone Y1-Y2, the maximum diameter of the outer volume 28 can be a constant and have a value of 4 mm. In the zone Y2-Y3 (external zone 2 or second external zone), the oval parameter e can have a value varying from a value including/selected between 0.20 mm and 0.30 mm at point Y2 to a value of 0 mm at point Y03. In the zone Y02-Y03, the maximum diameter of the outer volume 28 can vary between 4 mm and 3.54 mm. The variation of the ovality parameter and/or the variation of the eccentricity defined above can be linear in the zone Y2-Y3. Finally, the ovality parameter e can have a value of 0 mm between points Y03 and Y05. As a non-limiting example, the outer volume 28 can have a conical shape between points Y03 and Y04 (outer zone 3 or third outer zone), whose diameter varies between 3.54 mm and 3.40 mm. The outer volume 28 can also have a conical shape between points Y04 and Y05 (outer zone 4 or fourth outer zone), whose diameter varies between 3.40 mm and 1.80 mm.

Obviously, the length of each zone depends on the total length of the implant, but as a non-limiting example of an implant with a total length of 13 mm, Y2 may be located 2.30 mm from Y1, Y3 may be located 5 mm from Y1, Y4 may be located 11.70 mm from Y1 and Y5 may be located 13 mm from Y1.

Figure 10d shows a longitudinal cross-section of the core 2 of the implant 1 of Figure 10a. Figure 10d also shows a plurality of longitudinal coordinates/points Y6 to Y09 located along the axis y. The points also define a plurality of zones along the axis y. Y1 is a point with a coordinate of 0 mm. In the embodiment shown in Figure 10d, the value of the oval parameter e varies according to the coordinate y along the axis. For example, in the first zone Y1-Y6, the oval parameter e may have a constant value comprised between 0.10 mm and 0.50 mm. In the first zone, the maximum core diameter may vary between 4 mm and 3.60 mm along the longitudinal axis. The zones Y1-Y6 (core zone 1 or the first core zone) may have a constant eccentricity. In the zones Y6-Y7 (core zone 2 or the second core zone), the oval parameter e may have a value varying from a constant value comprised between 0.10 mm and 0.50 mm at point Y6 to a value of 0 mm at point Y7. The variation of the ovality parameter can be linear in the zone Y6-Y7. In the zone Y6-Y7, the maximum core diameter can vary between 3.30 mm and 2.70 mm. Finally, the ovality parameter e can have a value of 0 mm between points Y07 and Y09. As a non-limiting example, the core 2 can have a conical shape between points Y07 and Y08 (core zone 3 or the third core zone), with a diameter varying between 2.70 mm and 2.2 mm, and can have a conical shape between points Y08 and Y09 (core zone 4 or the fourth core zone), with a diameter varying between 2.2 mm and 1.6 mm.

Obviously, the length of each zone depends on the total length of the implant, but as a non-limiting example of an implant with a total length of 13 mm, Y6 may be located 2.30 mm from Y1, Y7 may be located 5 mm from Y1, Y8 may be located 11.70 mm from Y1, and Y9 may be located 13 mm from Y1.

Another alternative embodiment of the present invention is shown in Figure 11. This embodiment can be used alone or in combination with the embodiments of Figures 1 and/or 2. In this alternative embodiment as shown in Figure 11, the dental implant 1" similar to the embodiment of Figures 1 and/or 2 is also equipped with a core 2, which includes a core circular area 20, a core forming area 22, a circular thread area 32, and a thread forming area 30, however, this alternative embodiment can also be used without one or more of these areas. In this alternative embodiment, the thread 12 in the coronal section is superimposed with an additional groove 38 defined on the outer width or outside of the thread 12. This additional groove promotes bone attachment to the implant. This groove 38 defines a bottom height at its bottom according to its groove depth. In order to better explain the design of the alternative embodiment, it is referred to as the "bottom volume" defined by the bottom height of the groove 38 in the thread 12. In other words, this "bottom" volume (also called "groove core volume") is the volume through all the innermost points of the groove or through all points of the groove closest to the longitudinal axis of the implant 1". In a combined embodiment as shown in Figure 11, the groove 38 in the thread 12 of the implant 1 also includes a first or molded groove area 40, wherein the cross-section of the bottom volume in the thread 12 has multiple main directions, in which the radius measuring the distance between the center of the cross-section and its outer contour takes a relatively maximum value, and therefore takes a higher value than in adjacent orientations.

10a to 10f, FIG12a to FIG12j show by way of example possible input data for CNC machining of the corresponding shape of the implant 1 ″. Specifically, FIG12a shows a right side view of the outer volume 28, FIG12b shows the outer shape of the outer volume 28, and FIG12c shows a left side view of the outer volume 28. FIG12d shows a right side view of the core 2, FIG12e shows the outer shape of the core 2, FIG12f shows a left side view of the core 2, FIG12g shows a right side view of the bottom volume, and FIG12h shows The bottom volume is shown in FIG12i , which shows a left side view of the bottom volume, and FIG12j shows a circular pattern for CNC machining. As can be seen from FIG12j , the differential ovality parameter e for a typical maximum diameter of about 4.20 mm is selected between 0.10 mm and 0.50 mm, and may more preferably be about 0.23 mm. The differential ovality parameter e is an alternative definition of the shape of the core 2 / outer volume 28 / bottom volume and is defined by the difference between the maximum radius of the cross section and the minimum radius of the cross section.

In the embodiment of Figures 12a to 12j, the variation of the ovality parameter e of the core 2/external volume 28/bottom volume along the longitudinal axis y of the implant, and thus the variation of the eccentricity parameter, is similar to that already explained with respect to Figures 10a to 10f, to which reference is made. The main difference between the embodiment of Figures 10a to 10f and that of Figures 12a to 12j lies in the length of the implant and the presence of grooves in the embodiment of Figures 12a to 12j. As a non-limiting example, the implant of Figures 12a to 12j may have a total length of 9 mm and have a point with the following coordinates, starting from Y01:

- For the outer volume 28 (see FIG. 12 b ): Y02 at 2.30 mm, Y03 at 4.5 mm, Y04 at 8.10 mm and Y05 at 9 mm

- For core: Y07 at 2.30mm, Y08 at 5mm, Y09 at 7mm and Y10 at 9mm

- For the "bottom" volume or "groove core volume": Y11 at 0.75 mm, Y12 at 2.30 mm, Y13 at 4.50 mm, and Y14 at 7.90 mm

As non-limiting examples, between points Y01 and Y02, the implant may have a maximum outer diameter of 4.20 mm, between points Y02 and Y03, the implant may have a maximum outer diameter varying between 4.20 mm and 3.80 mm, between points Y03 and Y04, the implant may have a conical shape with an outer diameter varying between 3.80 mm and 3.57 mm, and between points Y04 and Y05, the implant may have an outer diameter varying between 3.57 mm and 1.90 mm.

Furthermore, as a non-limiting example, between points Y01 and Y07, the implant may have a maximum core diameter ranging between 4.20 mm and 3.78 mm. Between points Y07 and Y08, the implant may have a maximum core diameter ranging between 3.78 mm and 2.84 mm. Between points Y08 and Y09, the implant may have an outer diameter ranging between 2.84 mm and 2.31 mm, and between points Y09 and Y10, the implant may have an outer diameter ranging between 2.31 mm and 1.68 mm.

Furthermore, the "bottom" volume or "groove core volume" may have a differential ovality parameter e that varies along the y-axis. As a non-limiting example, the ovality parameter e may have a constant value or a varying value comprised/selected between 0.10 mm and 0.50 mm. In one embodiment, the "bottom" volume or "groove core volume" may have the following varying parameters:

- from Y1 to Y11 (first bottom volume), the differential ovalness parameter e may have a constant value, for example comprised between 0.10 mm and 0.50 mm, and the eccentricity may be constant,

from Y11 to Y12 (second bottom volume), e can vary from a starting value selected between 0.20 mm and 0.30 mm and a final value of 0 mm, said variation can be linear, and the eccentricity can also vary linearly,

- from Y12 to Y13 (third bottom volume zone), e may have a value of 0 mm and the “bottom” volume or “groove core volume” may have a conical shape that tapers towards the axis y,

- From Y13 to Y14 (fourth bottom volume zone), e may have a value of 0 mm and the "bottom" volume or "groove core volume" may have a conical shape.

It must be noted that in a given cross-section, the differential ovality parameter e (and therefore the eccentricity value) may be different for each of the core 2, the outer volume 28, and/or the bottom volume. The ovality parameter e may have a value comprised/selected between 0.10 mm and 0.50 mm. In some embodiments, the ovality parameter e may have a value of 0.15 mm, 0.20 mm, 0.23 mm, or 0.30 mm.

Thus, an implant according to the invention may comprise an envelope volume 21 and/or a core 2 and/or a groove core volume having:

- at least one coronal region (also referred to as a first shaped region) or portion extending along the longitudinal axis y of the implant, having a maximum (e.g., constant) eccentricity. The maximum eccentricity may be comprised between 1.05 and 1.2 and may extend over, for example, 0 and 80% of the total length of the implant. In some embodiments, the coronal region extends over approximately 30%, 45%, 60%, or 70% of the total length of the implant;

at least one transition zone or portion extending along the longitudinal axis y of the implant, having an eccentricity that varies between said maximum eccentricity and said minimum eccentricity, said variation being linear, and

- at least one apical zone (also called circular zone) or portion extending along the longitudinal axis y of the implant, which has said minimum constant eccentricity.

Thus, an implant according to the invention may comprise an envelope volume 21 and/or a core 2 and/or a groove core volume having:

- at least one coronal region (also called first shaped region) or portion extending along the longitudinal axis y of the implant, which has a maximum (e.g. constant) eccentricity. The maximum eccentricity may be comprised between 1.05 and 1.2. The coronal region may extend over at least 10%, at least 15%, at least 20% or at least 25% of the total length of the implant,

at least one transition zone or portion extending along the longitudinal axis y of the implant, having an eccentricity that varies between said maximum eccentricity and said minimum eccentricity, said variation being linear, said transition zone extending over at least 10%, at least 15%, at least 20% or at least 25% of the total length of the implant,

and at least one apical region (also called circular region) or portion extending along the longitudinal axis y of the implant, which has said minimum constant eccentricity. The apical region may extend over at least 30%, at least 35%, at least 40%, at least 45%, or at least 50% of the total length of the implant.

The table below gives different, non-limiting possible values for the length of each zone of the implant depending on the overall length of the implant.

Figure 35 is a graph showing different values (variations or evolutions) of the eccentricity of the core 2 and/or the thread envelope volume 28 and/or the groove forming area 40 depending on the position along the longitudinal axis of the implant in some embodiments. As can be seen in Figure 35, the top region of the core 2 and/or the thread envelope volume 28 and/or the groove forming area 40 may have a constant minimum eccentricity equal to 1 between points A and B. The core 2 and/or the thread envelope volume 28 and/or the groove forming area 40 may also have a transition region starting at point B, where the eccentricity changes from the constant minimum eccentricity to a maximum eccentricity value at point C. After point C, the core 2 and/or the thread envelope volume 28 and/or the groove forming area 40 may have a coronal region where the eccentricity has a constant maximum value. As previously mentioned, the constant maximum eccentricity value may be included between 1.05 and 1.2.

In some embodiments, and specifically for the core 2 and/or for the thread envelope volume 28, point A may represent the apex of the implant, and point D may represent the coronal end of the implant. Points A, B, C, and D do not always have the same coordinates for the core 2, thread envelope volume 28, or groove forming area 40. Point A should be understood as the highest point of the core 2, thread envelope volume 28, or groove forming area 40. As can be seen in FIG. 35 , the shape of the eccentricity curve has no sharp corners; it is a continuous line with only one tangent at each point.

In addition to the geometrical design of the core 2 and/or thread 12 as described above, in preferred alternative embodiments, the details of which are also considered to be independent inventions, additional means may be provided to support a reliable engagement with bone tissue at a high primary stability. To this end, in the embodiments shown in Figures 13 to 18, cutting grooves 46 are provided in the threaded portion of the implant 1, 1', 1". Figures 13 to 18 each show a perspective view of the corresponding implant, in which the various core/thread zones 20, 22, 26, 30, 32, 34 are indicated by changes in the section lines. In these embodiments, in selected sections or the entire core 2 and thread 12, a plurality of cutting grooves 46 (preferably equal to the number in the main direction of the core 2 and/or thread 12) may be provided in the transition zone 26 and/or in the other zones 20, 22 of the implant 1. These cutting grooves 46 are each provided with a cutting groove. A cutting edge 48 is featured (see FIG. 19 ), which removes bone material when the implant 1 is screwed in, thereby allowing an enhanced cutting ability of the implant 1 during the screwing-in process. Obviously, although the groove 38 is not shown in the embodiments of FIG. 13 to FIG. 18 , in another alternative embodiment, any of these shown may also be equipped with a groove 38. With regard to construction and/or design, the cutting groove 46 has specific features that are considered to be independent inventions and can be used as shown in combination with the features of the implant 1 and/or implant 1′ and/or implant 1″ explained above, or with other conventional implants or screw systems.

13 to 15 show embodiments of the implant 1 of FIG. 1 , in which the position and/or length of the cutting grooves are preferably varied according to the specific requirements of the individual implant design. These embodiments form a variant with a plurality of cutting grooves 46 extending in the longitudinal direction along the parts of the transition zones 28 , 34 and the parts of the forming zones 22 , 30 .

In the embodiment shown in FIG13 , the core 2 and the external thread are configured to have matching outer profiles, i.e., the core circular area 20 and the thread circular area 32 are both located near the apex 4. Adjacent thereto, the core transition area 26 and the thread transition area 34 are both located in an overlapping manner. Near the coronal end 6, the core forming area 22 and the thread forming area 30 are located together, and in this embodiment, both have a triangular oval cross-section.

In contrast, FIG14 illustrates an embodiment in which zones of different types and cross-sections partially overlap. Specifically, both the core circular zone 20 and the thread circular zone 32 are positioned near the apex 4, each beginning at the apex 4. As indicated by the deformation in the crosshatching, for the core 2—as viewed in the longitudinal direction—the transition from the core circular zone 20 to the core transition zone 26 is located at an intersection 43, while the thread 12 remains within its circular zone 32. At intersection 43a, the core transition zone 26 ends and the core forming zone 22 begins, and at a certain point within the core forming zone 22, the thread circular zone 32 crosses into the thread transition zone 34. At a certain point closer to the crown 10, at intersection 43b, the core forming zone 22 ends again and transitions into another transition zone 26. At the same intersection 43b, the thread transition zone 34 transitions into the thread forming zone 30. Thus, in this embodiment, the various zones of the core and thread partially overlap in various combinations.

FIG15 again shows an embodiment in which the core 2 and the external thread 12 are configured to have matching outer profiles, i.e., the core circular area 20 and the thread circular area 32 are both located near the apex 4. Adjacent thereto, the core transition area 26 and the thread transition area 34 are both located in an overlapping manner. Near the coronal end 10, the core forming area 22 is located together with the thread forming area 30, and in this embodiment, both have a triangular oval cross-section.

As shown in the examples according to Figures 16 to 18, the cutting groove 46 can have various orientations, such as being substantially parallel to the longitudinal axis of the implant 1 (the example of Figure 16), being inclined with respect to the longitudinal axis of the implant 1 (as in Figure 17) or being curved and wrapped around the outer surface 8 of the core 2 as shown in Figure 18.

Another preferred embodiment based on the basic implant design of the implant 1″ is shown in FIG. 19 . FIG. 19 shows a side view of the top or coronal section of the implant 1″. Obviously, with regard to the number and position of the cutting grooves 46, the concept shown can also be used for any other preferred implant concept, or even for conventional implant/screw designs. In the embodiment shown in FIG. 19 , which is also to be considered an independent invention in itself, the cutting grooves 46 are positioned in the threaded area of the implant 1″. With regard to their position in the “z-direction”, i.e. in the longitudinal direction of the implant 1″, they are positioned with a certain displacement relative to their adjacent cutting grooves 46, so that in their position the cutting grooves 46 follow the spacing of the threads 12. By means of this design, it is ensured that when the implant 1″ is screwed into the bone tissue, the individual threads 12 engaging the bone material will provide a cutting effect on the same bone area via the continuous cutting edges 46.

FIG20 shows a variation of the implant 1 of FIG1 having a plurality of cutting grooves 46 extending longitudinally along portions of the transition zones 28, 34 and portions of the forming zones 22, 30. FIG21 (schematically) shows a cross-section of the implant 1 of FIG20 in the position indicated in FIG20. As can be seen from FIG21, the cross-section of the core 2 and its outer surface 8 have a triangular oval shape. In other words, in its core forming zone 22, the cross-section of the core 2 (and the cross-section of the envelope volume 28 of the thread 12) has multiple (i.e., three) principal directions in which the radius, measuring the distance between the center 50 of the cross-section and its outer contour, reaches a relative maximum ("maximum radius"), thus taking a higher value than in adjacent orientations. In the diagram of FIG21, one of these principal directions is oriented parallel to the vertically upward direction indicated by line 52. The radius of the outer contour of the core 2 in this principal direction reaches a local maximum at point 54. Due to the symmetrical positioning of the main directions about the center 50 , the other two main directions make an angle of 120° with respect to the line 52 .

In this example, the cutting grooves 46 are also positioned symmetrically around the center 50, that is, the angle between two adjacent cutting grooves is also 120 °. Taking into account the relaxation effect in the bone tissue after the local maximum of the radius has passed during the screwing process, the cutting grooves 46 are appropriately positioned in the rotational orientation so as to maximize the cutting efficiency in the bone material. For this reason, as seen on the orientation direction around the center 50 or the central longitudinal axis of the core 2, each cutting groove 46 is positioned at a rotational offset given from the adjacent main direction. In Figure 21, the core 2 is shown from a top view (so that when inserted, the core will rotate in the right-hand direction (or clockwise), and the rotational offset is represented by the angle α, which is between the leading maximum represented by line 52 and the next trailing cutting groove 46 represented by dotted line 56, and the dotted line 56 points to the corresponding cutting edge 48 of the cutting groove 46.

In the embodiment shown, this angle α is selected according to a selection criterion, which is itself considered an independent invention. According to this selection criterion, the cutting edge 48 should be positioned so that the cutting edge radius defined by the intersection of the dotted line 56 and the outer surface 8 (i.e., the outer limit of the radial extension of the cutting edge 48 from the center 50) is 20 μm to 75 μm smaller than the maximum radius. This criterion takes into account the characteristic elastic properties of bone, which, depending on its density, rebounds or relaxes by approximately this amount after compression. In the embodiment shown, the cutting edge radius is selected to be approximately 35 μm smaller than the maximum radius, which, according to the remaining geometric parameters of the core 2, translates into a preferred angle of approximately 106°.

This preferred offset angle can also vary depending on the value of the maximum radius in order to reliably take into account the elastic properties of the bone material. Due to the preferred conical design of the core 2 and/or the outer volume 28, this maximum radius can vary depending on the longitudinal coordinate of the implant 1, thereby also making the preferred offset angle dependent on this longitudinal coordinate. The resulting cutting groove 46 can thus be wound around the core 2 of the implant 1.

In general, the thread 12 can have any convenient thread profile, specifically a flat thread. Depending on the corresponding position in the longitudinal direction of the implant 1, the free width 58 of the thread 12 increases continuously with the increase of the distance from the top 4. In this design, the thread 12 in the area near the top 4 can be characterized by a relatively sharp small outer width, thereby providing high cutting power when the thread 12 enters the bone tissue. As the implant 1 is further screwed in (that is, the implant further enters the bone tissue), at a given position in the bone tissue, the width 58 of the thread 12 increases continuously, thereby continuously widening the corresponding local gap in the bone tissue and constantly increasing the contact area between the bone tissue and the implant.

In the embodiment of the invention shown in the accompanying drawings, the thread 12 is designed to have a specific tooth shape in order to interact advantageously with the core 2 and/or the non-circular cross-section of the thread 12. In this variant, which is also considered to be inventive in itself and, in particular, an independent invention, as can be seen from the enlarged representations of Figures 22 and 23, the thread 12 has a tooth shape with a top surface 60 and a coronal surface 62, wherein the top surface 60 is oriented substantially perpendicular to the longitudinal axis 64 of the implant 1, i.e., the plane normal of the top surface 60 is oriented substantially parallel to the longitudinal axis 64 of the implant 1. In addition, the coronal surface 62 is oriented at an angle of approximately 60° relative to the longitudinal axis 64, i.e., the plane normal of the coronal surface 62 is oriented at an angle of approximately 30° relative to the longitudinal axis 64 of the implant 1. This angle is represented by the line 66. In other words, the thread 12 as a whole forms a so-called buttress thread.

Due to this specific choice of orientation of the top surface 60, which is considered an independent invention in itself, it is possible to compensate for the potential effects of a non-circular (e.g. triangular oval) shape. This effect is the oscillation of the bone with which the thread 12 contacts during insertion. This means that when the implant 1 is inserted, the thread 12 will only contact the bone at certain intervals.

By aligning the top side of the thread 12 at 90° relative to the longitudinal axis, the contact of the top surface over the entire thread length is improved after insertion. This is shown in the enlarged section according to FIG24 . FIG24 shows a section of the implant 1 in longitudinal section after insertion into the bone material 70.

In the preferred embodiment shown (which is also considered an independent invention in its own right), the depth of the threads 12 at their top surface 60 is selected with a view to enhancing primary stability after insertion. To this end, this preferred embodiment takes into account that, in the core forming zone 22 and/or the thread forming zone 30 and/or in the core transition zone 26 and/or the thread transition zone 34, after insertion, in order to absorb masticatory forces, the top surface 60 of the threads should ideally be in the greatest possible physical contact with the bone material 70. In this regard, the region of minimum radius in the forming/transition zone will adopt a final position after insertion that has passed the aforementioned maximum value, thereby creating a void 72 through which the bone tissue is pushed out. However, in order to provide a reliable platform 74 in the bone material, in which the top surface 60 of the threads can rest on a portion of the bone material 70, the depth of the threads 12 at their top surface 60 is selected to be greater, preferably at least twice the difference between the maximum and minimum radii of the outer contour of the envelope volume 28.

In a further preferred embodiment, which is also to be considered an independent invention in itself, the implant 1 (as well as the implants 1′, 1″) is provided with an advanced connection system 80 for mechanically connecting the implant 1 and the associated abutment to one another. In the following, various embodiments for the advanced connection system 80 are described based on the implant 1. Obviously, all embodiments can also be advantageously used for any other implant type according to, for example, the implants 1″, 1″′ described above.

The connection system 80 includes a receiving channel 10 into which a corresponding connecting pin of the abutment can be inserted. Figures 25a and 25b show views of the implant 1 from the direction indicated by arrow 82 in Figure 4. As can be seen in Figures 25a and 25b, the cross-section or outer contour of the non-circular regions 22 and 30 of the implant 1 is triangular-oval, thereby providing three main directions in the transition regions 26 and 34 and the forming regions 22 and 30, respectively. These main directions are positioned symmetrically about the central longitudinal axis of the core 2, and the corresponding radii of the cross-section in these main directions have local maxima. As is also apparent from the representations in Figures 25a and 25b, the outer contour of the implant 1, defined by the outer contour of the thread 12, matches or "conforms" to the outer contour of the core 2. Therefore, in those orientations where the radius of the core 2 has a local maximum, the outer contour of the thread 12 also adopts a local maximum. Furthermore, due to the conical or tapered geometry of the core 2 in the transition region 26 , the smallest radius of the core 2 in the forming region 22 is greater than the radius of the outer contour of the thread 12 in the circular region 20 .

Furthermore, the receiving channel 10 has an outer profile or contour that matches or "conforms" to both the outer contour of the threads 12 of the implant 1 and the outer contour of the core 2. Therefore, in those orientations where the radius of the core 2 and the outer contour of the threads 12 reach local maxima, the contour of the receiving channel 10 also adopts a local maximum, i.e., a triangular oval shape. Furthermore, the receiving channel 10 is tapered, its cross-section narrowing as it approaches its bottom end 84. Due to this shape, the receiving channel 10, together with its associated connecting pins for the abutment, provides a so-called indexing structure that ensures correct rotational alignment of the abutment during insertion. As shown in Figures 25a and 25b, and also in the longitudinal cross-sections of the implant 1 according to Figures 26 and 27, the receiving channel 10 is provided with an indexing profile 86 at its lower or bottom end 84 to ensure proper assembly of the abutment. This "second indexing" can be used to transmit the torque required for implant insertion by inserting an appropriate tool, which, in the preferred embodiment shown in Figures 26 and 27, has a quincunx-shaped cross-section. Due to the graduated profile 86 , this torque can be applied without affecting the graduated profile of the actual receiving channel 10 .

In an alternative embodiment of an implant 1''' with a second indexing, as shown in FIG. 28 , the second indexing profile may be integrated in its non-circular cross-section with the first indexing profile provided by the receiving channel 10. According to the embodiment shown, this is achieved by a plurality of slots 88 cut in the tapered side walls of the receiving channel 10. In order to apply the torque necessary to insert the implant 1''' into the bone material, a corresponding tool in the form of a screwdriver may be applied to engage with the slots 88, thereby ensuring that the inner surface of the receiving channel 10 is unloaded and therefore not damaged during insertion. With regard to the triangular-oval cross-section of the receiving channel 10 in the embodiment shown, the slots 88 may be positioned so as to "match" said cross-section, i.e. they may be positioned in a main direction characterized by a local maximum of the radius, or they may be positioned with a certain offset with respect to the main direction.

As shown in Figures 26 to 28, in all preferred embodiments, the implant 1, 1', 1", 1"' is equipped with an additional highly beneficial feature, which by itself or in combination with any number of the features disclosed above is also considered to be an independent invention. According to this feature, the implant 1, 1', 1", 1"' as part of its internal connection system 80 includes a feedback structure 90, which provides feedback to the user after the connecting pin or the like of the associated second implant component (e.g., the abutment) has been properly and completely inserted into the receiving channel of the implant 1, 1', 1". In order to provide such feedback, the feedback system 90 includes a narrow groove or groove 92 positioned on the inner surface of the receiving channel, and in the embodiment shown at its bottom end 84, circularly surrounds the receiving channel 10. This circular groove 92 One or more corresponding protrusions of a dental accessory (such as the one described in patent application EP16151231.4) and/or a protrusion of a retaining element (such as the one described in patent application EP15178180.4 by the same applicant), both of which are incorporated herein by reference, can be engaged or received. Once the connecting pin has been fully and correctly inserted into the receiving channel 10, these protrusions snap into the groove 92 with an audible "click" sound, thereby confirming to the user that the correct insertion of the contact pin into the receiving channel 10 has been completed.

In another alternative embodiment of the implant 1″″ as shown in Figures 29, 30 and 31 (side views), the coronal end 6 has a unique, molded design. This feature (which is also considered an independent invention by itself or in combination with any number of the features disclosed above) provides improved positioning orientation of the implant 1″″ during insertion, as well as improved overall system strength. This is achieved by the fact that the width of the top/upper or coronal surface 100 of the implant 1″″, i.e. the wall width of the implant 1″″, varies due to the inverted taper and peaks and valleys, with a larger width at the valley and a smaller width at the peaks, as shown in Figures 29 and 30.

Specifically, the coronal surface 100 of the implant 1"" has an undulating, wavy or sinusoidal profile, and the highest and lowest parts of the coronal surface 100, that is, the maximum and minimum values of the height in the longitudinal direction of the implant 1"" are arranged alternately along the circumference of the coronal end 6 of the implant 1"". At the highest parts of the coronal surface 100, and preferably also near these highest parts, the coronal end 6 of the implant 1"" has a conical shape or configuration, that is, a post-conical shape or configuration, so that the lateral dimension or extension of the cross-section of the coronal end 6 perpendicular to the longitudinal direction of the implant 1"" decreases along the direction from the top 4 of the implant 1"" toward the coronal end 6 of the implant 1"" (see Figures 29 and 30).

Due to this undulating, wavy or sinusoidal profile and the posterior tapered shape or configuration of the implant 1″″, the wall width of the implant 1″″, i.e., the width of the wall of the implant 1″″, also varies at the coronal end 6. Specifically, the wall width is larger at the lowest part of the coronal surface 100 and smaller at the highest part of the coronal surface 100.

The above-identified features of the coronal surface 100 are considered to be independent inventions on their own or in combination with any number of features disclosed further above. These features allow a particularly reliable and simple identification of the orientation of the implant.

In the embodiment shown in FIG. 29 , the implant 1″″ has a triangular-oval cross-section in its core-forming zone 22 and - due to the preferred design of the “matching profile” - also in its thread-forming zone 30 , i.e. the respective cross-section is characterized by three main directions in which the radius has local maxima. In sync with this cross-sectional shape, the coronal end 6 also has a local maximum in positions matching these main directions, as seen in a direction parallel to the longitudinal axis of the implant 1″″. In other words: the coronal surface 100 of the implant 1″″ is not a flat surface, but has a wavy, sinusoidal structure, the highest points of which are located in the main directions defined by the forming zones 22 , 30 , as already described in detail above.

In another preferred embodiment of the implant 1 ''', in particular with regard to the external thread 12 in this section, the tip or apex 4 can be specifically designed to facilitate insertion into the bone material. To this end, at least one top side portion of the thread 12 is serrated, as can be seen in FIG. 32 . In this embodiment, a plurality of grooves 102 having at least one cutting edge can be defined in the top and/or coronal surface of the thread 12.

Figure 33 shows an embodiment of an implant according to the present invention, which has at least one discontinuous top side cutting groove 104, which can be defined (or milled or cut) at least in the top side half of the thread 12. As seen in Figure 33, the cutting groove does not extend in the core of the implant. The implant according to this embodiment can also have two or more such cutting grooves. And in this embodiment, the thread can be considered as a buttress thread.

The buttress threads help insert the implant into the hole when used in a patient's extraction socket. Because the angle of the socket wall is not perpendicular to the axis of the implant, one side of the wall will contact the implant first and affect the implant's positioning. To help reduce this effect, the buttress threads cut into the bone on the side of the implant.

These features, either alone or in combination with any number of the features disclosed above, are also considered to be independent inventions.

The overall length of the implant 1, 1', 1", 1"', 1"", 1""' or any combination thereof in any of the embodiments described above is preferably designed according to the specific requirements given by the individual treatment of the patient. In the embodiments shown in the above figures, a typical "standard" value for the overall length of the corresponding implant may be about 13 mm. In other embodiments, the implant may be designed as a "short version" with an overall length of (for example) about 7 mm. An example of this embodiment is shown in Figure 34.

36a to 36c show an insertion tool 200 according to a first embodiment of the present invention.

Insertion tool 200 is an insertion tool for inserting a dental implant into a patient's bone tissue. Insertion tool 200 includes a proximal portion 202 and a distal portion 204, as shown in FIG36 a. Distal portion 204 is configured to cooperate with an implant to screw the implant into the bone tissue.

The distal portion 204 has a retaining element 206. The retaining element 206 includes an attachment portion 208 for attaching the insertion tool 200 to a dental implant. The retaining element 206 is elastically deformable at least in all directions perpendicular to the longitudinal direction of the insertion tool 200, that is, along all transverse directions of the retaining element 206. The attachment portion 208 includes a protrusion 210 (see FIG. 36 b ) that extends in multiple directions substantially perpendicular to the longitudinal direction of the insertion tool 200, that is, along multiple transverse directions of the retaining element 206.

The retaining element 206 is formed integrally with one of the two components of the insertion tool 200 (i.e., the proximal component) (see Figures 37a and 37b). Specifically, the retaining element 206 is formed integrally with the proximal component of the insertion tool 200 by two coupling portions 212 arranged between the retaining element 206 and the proximal component in the longitudinal direction of the retaining element 206 (see Figures 36c and 37a). The coupling portions 212 each extend only along a portion of the retaining element 206 in the circumferential direction of the retaining element 206, as schematically shown in (for example) Figures 37a and 37b. The coupling portions 212 are arranged substantially opposite to each other in the radial direction of the retaining element 206.

The retaining element 206 has a substantially cylindrical shape with a substantially circular cross-section perpendicular to the longitudinal direction of the retaining element 206 (see FIG. 37 a). The retaining element 206 is formed into a hollow, tubular body. The retaining element 206 has a closed ring shape or annular shape, i.e., a ring shape with no openings in its circumference. The retaining element 206 is elastically deformable in all transverse directions by appropriately selecting the material and wall thickness of the retaining element 206.

The retaining element 206 may be made of, for example, a metal, such as titanium, a titanium alloy, or stainless steel, a polymer, or a composite material.

When the insertion tool 200 is attached to the dental implant, the retaining element 206 may be elastically compressed in its lateral direction (eg, FIG. 37 d and FIG. 39 ).

The protrusion 210 of the attachment portion 208 allows the insertion tool 200 to be attached to the dental implant by snap-fitting, as will be explained in detail below with reference to Figs. 37d and 39 .

As shown in Fig. 37a, the protrusion 210 of the attachment portion 208 is arranged between the two coupling portions 212. In this way, a particularly reliable and effective snap-fit of the attachment portion 208 to the dental implant can be ensured.

The distal portion 204 of the insertion tool 200 has a transmission region 214 (see, for example, Figures 36a to 38f). In the transmission region 214, a cross section of the distal portion 204 perpendicular to the longitudinal direction of the insertion tool 200 has a plurality of main directions in which the radius measuring the distance between the center of the cross section and its outer contour takes a relative maximum and therefore a higher value than in adjacent orientations (see Figure 38d).

The drive region 214 of the distal portion 204 of the insertion tool 200 engages the implant. The drive region 214 constitutes an anti-rotation structure. The drive region 214 is configured to prevent relative rotation between the insertion tool 200 and the implant about the longitudinal axis of the tool 200 when the tool 200 and the implant are engaged with each other, for example, by partially introducing the distal portion 204 of the tool 200 into the implant socket.

The transmission region 214 is configured to cooperate with a corresponding anti-rotation structure (ie, a transmission portion) of the implant (see Figures 37d and 39a-39c), as will be explained in further detail below.

The main directions in the transmission region 214 of the insertion tool 200 are positioned axially symmetrically about the central longitudinal axis of the insertion tool 200, and the corresponding radius of the cross section in each of these main directions has a local maximum (see FIG38 d ). The number of main directions in the transmission region 214 is three, i.e., the transmission region 214 has a triangular oval cross section, as shown in FIG38 d . Combined with the symmetrical positioning of the main directions about the longitudinal direction of the insertion tool 200, this triangular oval shape results in a rotational offset angle of 120° between two adjacent main directions.

The transmission region 214 has a tapered configuration such that in the transmission region 214, the lateral dimension or extension of the cross-section of the distal portion 204 perpendicular to the longitudinal direction of the insertion tool 200 decreases in a direction from the proximal end of the insertion tool 200 toward the distal end of the insertion tool 200 (see Figures 36a to 36c, Figures 37a to 37d and Figures 38a to 38f).

The transmission region 214 is arranged in the vicinity of the retaining element 206 .

The cross-sectional shape of the transmission region 214 allows rotational forces applied to the insertion tool 200 about its longitudinal axis to be effectively, reliably, and uniformly transmitted to the implant.

In a variation of the first embodiment of the insertion tool 200 shown in Figure 38e, the tool 200 does not have a transmission area. Instead, as depicted in Figure 38e, a cross section taken along line A-A in Figure 38c has a circular shape.

The distal portion 204 of the insertion tool 200 also has a transmission section 216. In the transmission section 216, a cross section of the distal portion 204 perpendicular to the longitudinal axis of the insertion tool 200 has a plurality of radially convex portions 218 and a plurality of radially concave portions 220, which are arranged alternately along the circumference of the cross section (see FIG. 38f). Each of the radially outermost points 222, 224 of the radially convex portions 218 is located on a corresponding circle around the center of the cross section, as shown in FIG. 38f.

The cross section of the distal portion 204 of the insertion tool 200 in the transmission section 216 has the same number of radially convex portions 218 and radially concave portions 220 , namely six each.

The radially raised portion 218 includes a first radially raised portion and a second radially raised portion, wherein the radially outermost points 222 of the first radially raised portion are all located on a single first circle around the center of the cross section, and the radially outermost points 224 of the second radially raised portion are all located on a single second circle around the center of the cross section. The radius of the second circle is smaller than the radius of the first circle (see FIG. 38 f). The first radially raised portion and the second radially raised portion are alternately arranged along the circumference of the cross section, with corresponding radially recessed portions 220 provided between them. The number of first radially raised portions is the same as the number of second radially raised portions.

The radially convex portion 218 and the radially concave portion 220 of the cross section of the transmission section 216 each have a curved shape, eg, at least partially circular, at least partially elliptical, at least partially oval, etc. The radially convex portion 218 and the radially concave portion 220 are arranged directly adjacent to each other.

The radially innermost points 226 of the radially concave portions 220 lie on a single circle 228 about the center of the cross section. Thus, all radially innermost points 226 of the radially concave portions 220 lie on the same circle 228 about the center of the cross section.

The transmission section 216 may have a length in the longitudinal direction of the insertion tool in the range of 0.5 mm to 1.2 mm.

The drive section 216 of the distal portion 204 of the insertion tool 200 engages the implant. The drive section 216 constitutes an anti-rotation feature. The drive section 216 is configured to prevent relative rotation between the insertion tool 200 and the implant about the longitudinal axis of the tool 200 when the tool 200 and the implant are engaged with each other, for example, by at least partially introducing the distal portion 204 of the tool 200 into the implant socket.

The drive section 216 is configured to cooperate with a corresponding anti-rotation structure (ie, a drive zone) of the implant (see Figures 37d and 39a-39c), as will be explained in further detail below.

Thus, the distal portion 204 of the insertion tool 200 according to the first embodiment of the present invention has a transmission region 214 and a transmission section 216. The transmission region 214 is arranged in the vicinity of the transmission section 216 (see Figures 36a to 38f).

Because there are two anti-rotation structures (i.e., the transmission area 214 and the transmission section 216) on the distal portion 204 of the insertion tool 200, which can cooperate with two corresponding anti-rotation structures on the implant (i.e., the transmission portion and the transmission area), the rotational force or load applied to the implant when the implant is inserted into the bone tissue can be shared by the two structures. Therefore, any damage to either of the two structures in the implant can be minimized. Therefore, after the implant is inserted into the bone tissue, one or both of these structures in the implant can be reliably and effectively used as an indicator for an abutment, scanning post, impression post, etc.

The transmission area 214 and the transmission section 216 also help to accurately position the insertion tool 200 relative to the implant. Due to the cross-sectional shape of these elements, only three relative rotational positions between the tool 200 and the implant are possible.

The distal portion 204 of the insertion tool 200 also has a retaining element 206 , as already described in detail above. The transmission section 216 , the retaining element 206 and the transmission region 214 are arranged in this order in the direction from the distal end of the insertion tool 200 towards the proximal end of the insertion tool 200 .

The insertion tool 200 is composed of two separate components, namely a distal component 230 and a proximal component 232 that are attached to each other, as shown in Figures 37a to 37c.

The distal component 230 of the insertion tool has a protrusion that fits into a corresponding recess in the proximal component 232 of the insertion tool 200 (see Figures 37c and 37d). The distal component 230 and the proximal component 232 are attached to each other by inserting the protrusion into the recess. The protrusion is held in place within the recess by a friction fit using a press-fit shoulder 234 of the distal component 230, located distal to the protrusion (see Figure 37b). The press-fit shoulder 234 also provides a sealing function against liquids.

The protrusion and the recess have corresponding anti-rotation structures to prevent any rotation of the distal component 230 and the proximal component 232 relative to each other about the longitudinal axis of the insertion tool 200. The anti-rotation structure of the distal component 230 has a cross-section perpendicular to the longitudinal direction of the insertion tool 200, that is, the outer cross-section of the protrusion, which is non-circular, that is, generally square (see Figure 37a). The anti-rotation structure of the distal component 230 of the insertion tool 200 can cooperate with the corresponding anti-rotation structure of the proximal component 232 of the insertion tool 200. The anti-rotation structure of the proximal component 232 of the insertion tool 200 has a cross-section perpendicular to the longitudinal direction of the insertion tool 200, that is, the inner cross-section of the recess, which is non-circular, that is, generally square. The cross-sections of the anti-rotation structures of the distal component 230 and the proximal component 232 are substantially the same.

The distal part 230 comprises the transmission section 216 and the proximal part 232 comprises the retaining element 206 and the transmission region 214. In this way, the production of the insertion tool 200, in particular of the retaining element 206, can be significantly simplified.

The retaining element 206 is integrally formed with the proximal component 232 .

37d and 39a to 39c show a combination of the insertion tool 200 according to the first embodiment of the present invention and the dental implant 201 according to the embodiment of the present invention, with a portion of the distal portion 204 of the insertion tool 200 inserted into the implant 201. In the state shown in these figures, the insertion tool 200 is fully engaged with the implant 201.

The dental implant 201 is made of metal, for example, titanium, titanium alloy or stainless steel.

The dental implant 201 is for insertion into a patient's bone tissue. The dental implant 201 comprises a core 205 having an apical end 207 and a coronal end 209, as shown in FIG39a.

The dental implant 201 has a socket or channel 236 (see FIG. 37 d and FIG. 39 b ) formed at the coronal portion of the implant 201 to receive a portion of the distal portion 204 of the insertion tool 200 including the retaining element 206. The core 205 includes the channel 236. The channel 236 opens into the coronal end 209 and extends from the coronal end 209 toward the apex 207 along the longitudinal direction of the implant 201 (see FIG. 39 a and b ).

The coronal portion of the implant 201 is formed with an annular cavity 238 (see Figures 37d and 39b) for receiving the protrusion 210 of the attachment portion 208 of the retaining element 206. Therefore, the attachment portion 208 of the retaining element 206 can be firmly retained in the coronal portion of the implant 201 by snap fit.

Furthermore, the dental implant 201 has an external threaded portion 203 in order to screw the implant 201 into the jawbone tissue of the patient (see Figs. 39a and 39b).

When attaching the insertion tool 200 to the dental implant 201, part of the distal portion 204 of the insertion tool 200 is inserted into the channel 236 of the implant 201, so that the protrusion 210 of the attachment portion 208 of the retaining element 206 is received in the annular cavity 238 formed in the coronal portion of the implant 201. Therefore, the retaining element 206 is firmly retained in this coronal portion by a snap fit, thereby reliably attaching the insertion tool 200 to the implant 201.

During the process of attaching the insertion tool 200 to the implant 201, when the retaining element 206 is inserted into the channel 236, the retaining element 206 first undergoes elastic deformation in its lateral direction, i.e., elastic compression, and then returns to its original shape once the protrusion 210 is received in the annular cavity 238. This "clicking" process of the protrusion 210 provides audible and tactile feedback to the user of the insertion tool 200 (such as, for example, a clinician or technician in a dental laboratory) to indicate that the insertion tool is correctly positioned in the implant 201 (see Figures 37d and 39a to 39c).

In this fully engaged state of the insertion tool 200, the insertion tool 200 can be used to pick up the implant 201 and transfer it to the implantation site where it will be inserted into the bone tissue. Due to the reliable engagement of the tool 200 with the implant 201, any risk of the implant 201 falling off the insertion tool 200 before reaching the desired position can be reliably avoided.

Furthermore, in this fully engaged state of the insertion tool 200, the transmission region 214 and the transmission section 216 of the distal portion 204 of the insertion tool 200 engage with the transmission portion 240 and the transmission zone 242 of the implant 201, respectively, as shown in Figures 39b and 39c. The core 205 of the implant 201 has a transmission portion 240 and a transmission zone 242. The transmission zone 242 is arranged on top of the transmission portion 240, as shown in Figure 39b.

In the transmission portion 240 of the implant 201, a cross section of the channel 236 of the implant 201 perpendicular to the longitudinal direction of the implant 201 (i.e., an inner cross section) has a plurality of principal directions in which the radius measuring the distance between the center of the cross section and its outer contour takes a relative maximum value and therefore takes a higher value than in adjacent orientations. The cross sections of the transmission region 214 of the insertion tool 200 and the transmission portion 240 of the implant 201 are substantially identical.

The transmission portion 240 has a tapered configuration such that in the transmission portion 240 , the lateral dimension of the cross section of the channel 236 perpendicular to the longitudinal direction of the implant 201 decreases in the direction from the coronal end 209 toward the apical end 207 , as shown in FIG. 39 b .

In the transmission area 242 of the implant 201, the cross-section of the implant 201 (i.e., the inner cross-section) of the channel 236 perpendicular to the longitudinal direction of the implant 201 has a plurality of radial protrusions and may have a plurality of radial recessed portions, which are alternately arranged along the circumference of the cross-section, wherein each of the radially outermost points of the radial protrusions is on a corresponding circle around the center of the cross-section, as shown in FIG39c.

The cross section of the channel 236 of the implant 201 in the transmission zone 242 has the same number of radially convex portions and radially concave portions, namely six each (see FIG. 39 c ).

The radially protruding portions of transmission region 242 include a first radially protruding portion and a second radially protruding portion. The radially outermost points of the first radially protruding portions all lie on a single first circle about the center of the cross section, and the radially outermost points of the second radially protruding portions all lie on a single second circle about the center of the cross section. The radius of the second circle is smaller than the radius of the first circle. The first and second radially protruding portions are alternately arranged along the circumference of the cross section of transmission region 242, with corresponding radially recessed portions disposed therebetween. The number of first radially protruding portions is the same as the number of second radially protruding portions.

The radially convex and concave portions of the cross section of the transmission region 242 each have a curved shape, eg, at least partially circular, at least partially elliptical, at least partially oval, etc. The radially convex and concave portions are arranged directly adjacent to each other.

The radially innermost points of the radially concave portions lie on a single circle around the centre of the cross section. Thus, all radially innermost points of the radially concave portions lie on the same circle around the centre of the cross section.

The transmission region 242 may have a length in the longitudinal direction of the dental implant 201 in the range of 0.5 mm to 1.2 mm.

The cross sections of the transmission section 216 of the insertion tool 200 and the transmission region 242 of the implant 201 are substantially identical.

Therefore, the implant 201 can be screwed into the bone tissue by the cooperation or interaction between the transmission area 214 and the transmission section 216 of the distal portion 204 of the insertion tool 200 and the transmission portion 240 and the transmission area 242 of the implant 201. As already mentioned above, due to the presence of the transmission area 214 and the transmission section 216 that can cooperate with the transmission portion 240 and the transmission area 242, the rotational force or load applied to the implant 201 when the implant 201 is inserted into the bone tissue can be shared by the two structures, thereby minimizing the risk of damage to the implant 201.

Figures 40a and 40b illustrate an insertion tool 300 according to a second embodiment of the present invention. In particular, the insertion tool 300 according to the second embodiment differs from the insertion tool 200 according to the second embodiment in that the insertion tool 300 is formed from a single piece of material. Thus, all components of the insertion tool 300 are integrally formed with one another.

The general structure and function of the insertion tool 300 are substantially the same as those of the insertion tool 200. Specifically, the insertion tool 300 includes a proximal portion (not shown) and a distal portion 304. The distal portion 304 includes a transmission section 316, a retaining element 306, and a transmission region 314, which are arranged in this order from the distal end of the insertion tool 300 toward the proximal end of the insertion tool 300, as shown in Figures 40a and 40b. In addition, the insertion tool 300 includes a cutout portion 320 at the transmission section 316, which facilitates the production of the insertion tool 300, specifically, with reference to the manufacture of the retaining element 306.

41a to 41c and 42a to 42d illustrate a dental implant 401 according to an embodiment of the present invention.

The dental implant 401 is a self-cutting dental implant for insertion into a patient's jawbone or bone tissue. The dental implant 401 comprises a core 402 having a top 404, a coronal end 406, and an outer surface 408 extending between the top 404 and the coronal end 406 along the longitudinal direction of the implant 401, as shown in FIG41a.

The dental implant 401 is made of metal, for example, titanium, titanium alloy or stainless steel.

The implant 401 further comprises threads 412 (see Figures 41a and 41c and Figures 42a and 42b) extending outwardly from the core 402. The threads 412 have a thread angle of approximately 10°.

The thread 412 has a top surface 414 facing toward the top end 404 of the core 402, and a coronal surface 416 facing toward the coronal end 406 of the core 402. The thread 412 has a first groove 418 formed therein, i.e., a first cutting groove 418 (see 41a and FIG. 41b and FIG. 42b). The first groove 418 extends from the top end of the thread 412 toward the coronal end of the thread 412. As shown in FIG. 42b, the first groove 418 extends over the first three complete turns of the thread 412.

The thread 412 has a recessed portion 420 formed in its coronal surface 416 at its top portion. The recessed portion 420 extends along a portion of the thickness of the thread 412 in a direction from the coronal surface 416 toward the top surface 414. The recessed portion 420 leads to the first groove 418, as shown in Figures 41a and 42b. The recessed portion 420 is located adjacent to, i.e., directly adjacent to, the first groove 418. The recessed portion 420 has a cutting function, i.e., a function of cutting bone tissue.

The thread 412 also has a second groove 418' and a third groove 418" (see Figures 41a and 42b and Figures 42a and 42d). The first to third grooves 418, 418', 418" are arranged to be staggered or shifted along the length of the thread 412 and along the circumference of the thread 412. Specifically, the second groove 418' is staggered or shifted relative to the first groove 418 along the length and circumference of the thread 412, as shown in Figure 41a. The third groove 418" is arranged opposite to the first groove 418 in the radial direction of the implant 401 and is set at substantially the same height or length position of the thread 412 (see Figure 41b and Figures 42a and 42b). The first to third grooves 418, 418', 418" and the recess 420 make the implant 401 self-cutting.

The first groove 418 and the third groove 418" extend in a direction that is inclined or skewed with respect to the longitudinal direction of the implant 401 (see Figures 42a and 42b). The second groove 418' extends in a direction that is substantially parallel to the longitudinal direction of the implant 401 (see Figure 41a).

In the width direction of the groove, the first to third grooves 418, 418', 418" extend along a portion of the circumference of the core 402.

The recess 420 extends from the coronal surface 416 toward the top surface 414, that is, the depth of the recess 420 varies along a direction parallel to the coronal surface 416 (see FIG. 41c and FIG. 42b and FIG. 42c ). Specifically, the depth of the recess 420 decreases in a circumferential direction away from the first groove 418, as shown in FIG. 42b . In this manner, a particularly effective cutting function of the recess 420 is achieved.

Therefore, the maximum depth of the recessed portion 420 exists at a portion of the recessed portion 420 that is arranged directly adjacent to the first groove 418 .

In particular, the recess 420 has the general shape of a quarter sphere, as indicated in Figures 41c and 42b and 42c. This shape of the recess 420 allows the recess 420 and the implant 401 to be manufactured in a particularly simple and cost-effective manner.

The recessed portion 420 is arranged on the upstream side of the first groove 418 in the rotation direction of the implant 401 (see FIG. 42 b ).

A recess 420 is formed in the coronal surface 416 of the thread 412 at the first complete turn (i.e., the topmost complete turn) of the thread 412, as shown in Figures 41a, 42c, and 42b. This arrangement of the recess 420 allows the implant 401 to engage the jawbone or bone tissue in a particularly stable and robust manner.

The recess 420 helps to effectively cut and remove bone material and further convey the removed bone material toward the coronal end 406 of the core 402 .

The implant 401 of this embodiment allows to be inserted into the bone tissue with less force and high precision. In this way, a particularly stable and robust connection or engagement of the implant 401 with the bone tissue, ie high implant stability, can be achieved.

Due to the arrangement of the recess 420 in the coronal surface 416 of the threads 412 , these beneficial effects are achieved for substantially all implant thread angles, particularly for small implant thread angles, such as thread angles of approximately 10° for the threads 412 .

43a to 43c illustrate a dental implant 501 according to an embodiment of the present invention.

Dental implant 501 is a self-cutting dental implant for insertion into a patient's jawbone or bone tissue. Dental implant 501 includes a core 502 having a top end 504, a coronal end 506, and an outer surface 508 extending between the top end 504 and the coronal end 506 along the longitudinal direction of the implant 501, as shown in FIG43a. Implant 501 also includes threads 512 extending outward from core 502 (see FIG43a and FIG43b).

The dental implant 501 is made of metal, for example, titanium, titanium alloy or stainless steel.

The external configuration of the dental implant 501 may be substantially the same as any of the dental implants disclosed above, such as, for example, the dental implant 1 shown in Figures 1, 3, 6a-6e, and 7a-7e.

Specifically, the dental implant 501 may have a first core forming region, wherein the cross section of the core 502 has a plurality of main directions in which the radius measuring the distance between the center of the cross section and its outer contour takes a relative maximum value and therefore takes a higher value than in adjacent orientations. Specifically, the core 502 in the first core forming region may have a triangular oval cross section (see FIG. 43 c).

The dental implant 501 may have a core circular region, wherein the cross section of the core 502 is substantially circular.

The dental implant 501 may include a core transition region positioned between the core forming region and the core circular region. The geometry of the cross section of the core 502 in the core transition region continuously changes from a substantially circular shape near the core circular region to a shape corresponding to the cross section in the first core forming region, based on parameter characteristics of the coordinates in the longitudinal direction. Specifically, the core 502 in the core transition region may have a triangular oval cross section.

The dental implant 501 has a socket or channel 510 (see Figures 43a to 43c) formed at the coronal portion of the implant 501. The channel 510 opens into the coronal end 506 of the implant 501 and extends along the longitudinal direction of the implant 501 from the coronal end 506 toward the apex 504 thereof.

The core 502 has hexagonal interlocking recesses 515 , wherein a cross section of the channel 510 perpendicular to the longitudinal direction of the implant 501 has a substantially hexagonal shape.

The channel 510 includes a conical portion 514, a hexagonal interlocking recess 515, and an internal threaded portion 516 (see Figures 43b and 43c), which are arranged in this order in a direction from the coronal end 506 of the implant 501 toward the apex 504 of the implant 501. The conical portion 514 and the hexagonal interlocking recess 515 are configured to receive the tip portions of the abutment and the insertion tool 200, 300, and the internal threaded portion 516 is configured to receive a connecting screw for fixing the abutment to the dental implant 501.

The conical portion 514 has sidewalls that taper inwardly with respect to the longitudinal axis of the dental implant 501 to provide a wider initial opening for the channel 510 at the coronal end 506 of the implant 501. The specific geometry of the conical portion 514 defines a cone half-angle with respect to the longitudinal axis of the dental implant 501. This cone half-angle may be between about 10° and about 20°. That is, the angle between the inner wall of the conical portion 514 and the longitudinal center axis of the dental implant 501 may be between about 10° and about 20°. In one embodiment, the cone half-angle is about 12°.

The ratio of the length of the conical portion 514 in the longitudinal direction of the implant 501 to the length of the hexagonal interlocking recess 515 in the longitudinal direction of the implant 501 can be approximately 1:1. The length of the conical portion 514 can be at least approximately 1 mm, and the length of the hexagonal interlocking recess 515 can be at least approximately 1 mm. The length of the conical portion 514 is the distance measured in the vertical direction from the top surface of the implant 501 to the portion of the channel 510 where the conical surface of the conical portion 514 terminates. The length of the hexagonal interlocking recess 515 is measured in the vertical direction from the end of the conical portion 514 to the end of the hexagonal interlocking recess 515.

The proportions and lengths of the conical portion 514 and the hexagonal interlocking recess 515 advantageously combine the advantages of a sufficiently long conical connection to provide an effective seal and a sufficiently long hexagonal interlocking recess 515 so that sufficient transmission torque can be transmitted to the implant 501 when the implant 501 is pushed into the patient's jaw.

The features of all embodiments of the dental implant of the present invention described above may be combined with each other or separated from each other.The features of all embodiments of the insertion tool of the present invention described above may be combined with each other or separated from each other.

List of Figure Numbers

1, 1′, 1″,

1″′、1″″、

201, 401,

501 Dental Implants

2, 205,

402, 502 core

4, 207,

404, 504 top

6, 209,

406, 506 crown end

8, 408,

508 outer surface

10, 236,

510 receiving channel

12, 203,

412, 512 threads

20 Core circular area

22 Core forming area

24 Top platform area

26 Core transition zone

26′ Second core forming area

28 Envelope Volume

30 Thread forming area

32 thread circular area

34 Thread transition zone

34′ Second thread forming area

38 grooves

40 Groove forming area

42 Top Area

43 cross position

44 Transition Line

46 Cutting grooves

48 cutting edges

50 Center of the cross section

52 lines

54 points

56 dotted line

58 free width

60 top surface

62 crown

64 longitudinal axis

Line 66

70 bone tissue

72 Gap

74 Platform

80 connection system

82 Arrow

84 bottom

86 indexing profile

88 slots

90 Feedback Structure

92 Grooves

100 crown side surface

102 Grooves

104 Top side cutting groove

200, 300 insertion tools

202 proximal part

204, 304 distal part

206, 306 retaining elements

208 Attachment

210 protrusion

212 connection part

214, 314 transmission area

216, 316 transmission sections

218 radial protrusion

220 radial recess

222, 224 The radially outermost point of the radially raised portion

226 The radially innermost point of the radially concave portion

228 Circle around the center of the cross section

230 distal component

232 proximal component

234 Pressure Fit Shoulder

238 Ring Cavity

240 transmission part

242 Transmission Area

320 cutout

414 Top side thread surface

416 coronal thread surface

418, 418’,

418” groove

420 Depression

514 conical part

515 Hexagonal interlocking recess

516 internal thread part

Claims (34)

1. A dental implant (1) for insertion into a patient's bone tissue, said dental implant (1) comprising: - Core (2) having a top end (4), a crown end (6) and an outer surface (8) extending longitudinally between the top end (4) and the crown end (6); - At least one thread (12) extending outward from the core (2), and - A characteristic implant volume, which is defined by the core (2) or by an external thread volume (28) as defined by the thread (12), wherein for each value of the parameter characteristic of the longitudinal direction of the dental implant, the cross section of the characteristic implant volume is characterized by an eccentricity parameter, which is defined as the ratio of the maximum distance of the profile of this cross section from its center to the minimum distance of the profile of this cross section from its center; The characteristic implant volume includes - At least one coronal lateral region, in which the eccentricity parameter has a constant maximum value, the coronal lateral region extending along the longitudinal axis of the dental implant for at least 10% of the total length of the dental implant; - At least one top-side region, in which the eccentricity parameter has a constant minimum value, and - At least one transition zone is located between the coronal lateral zone and the apical lateral zone, in which the eccentricity parameter continuously varies from a minimum near the apical lateral zone to a maximum near the coronal lateral zone according to the parameter characteristics of the coordinates in the longitudinal direction, and the transition zone extends along the longitudinal axis of the dental implant for at least 10% of the total length of the dental implant. 2. The dental implant of claim 1, wherein the apical region extends along the longitudinal axis of the dental implant for at least 30% of the total length of the dental implant. 3. The dental implant (1) according to claim 1, wherein in the top side region, the cross-section of the characteristic implant volume has a substantially circular shape. 4. The dental implant (1) according to claim 1, wherein in the coronal region and/or the transition region, the cross section of the characteristic implant volume has a plurality of principal directions, wherein the radius defined as the distance between the center of the cross section and its outer contour in the plurality of principal directions takes a relative maximum value, and thus takes a higher value compared to adjacent orientations. 5. The dental implant (1) according to claim 1, wherein for each value of the parameter characteristic of the coordinate in the longitudinal direction, the cross section of the core (2) is characterized by a core eccentricity parameter, which is defined as the ratio of the maximum radius of the cross section to its minimum radius. 6. The dental implant (1) according to claim 1, wherein in the at least one transition zone, the eccentricity parameter changes linearly from a minimum near the top side zone to a maximum near the coronal side zone, based on the parameter characteristics of the coordinates in the longitudinal direction. 7. The dental implant (1) according to claim 1, wherein for each value of the parameter characteristic of the coordinate in the longitudinal direction, the outer cross section of the threaded outer volume (28) is characterized by a thread eccentricity parameter, which is defined as the ratio of the maximum radius of the outer cross section to its minimum radius. 8. The dental implant (1) according to claim 1, wherein the coronal side region is the top plateau region (24) near the coronal end (6). 9. The dental implant (1) according to claim 4, wherein the principal direction is symmetrically positioned about the central longitudinal axis (64) of the core (2). 10. The dental implant (1) according to claim 1, wherein the outer contour of the threaded outer volume (28) matches the outer contour of the core (2) with respect to the longitudinal central axis of the core (2) and with respect to the highest or lowest part of the core (2). 11. The dental implant (1) according to claim 1, wherein the core (2) has a triangular oval cross section in the coronal region and/or in at least a portion of the transition region (26). 12. The dental implant (1) according to claim 1, wherein the core (2) is conical in the transition zone (26). 13. The dental implant (1) according to claim 1, wherein, as seen in the longitudinal direction, the transition zone (26) begins at a distance of 2 mm to 4 mm from the apex (4). 14. The dental implant (1) according to claim 1, wherein the thread (12) is a flat thread. 15. The dental implant (1) according to claim 14, wherein the free width (58) of the flat thread increases continuously with increasing distance from the top end (4) of the core (2) according to the coordinate parameters in the longitudinal direction. 16. The dental implant (1) according to claim 4, wherein a plurality of cutting grooves (46) are provided in at least the transition region (26). 17. The dental implant (1) according to claim 16, wherein the number of cutting grooves (46) is equal to the number in the main direction. 18. The dental implant (1) according to claim 16 or 17, wherein the cutting groove (46) is symmetrically positioned about the central longitudinal axis of the core (2). 19. The dental implant (1) according to claim 16, wherein each cutting groove (46) is positioned at a rotational offset given from the adjacent principal direction, as seen in the orientation direction around the central longitudinal axis of the core (2). 20. The dental implant (1) according to claim 1, wherein the core (2) includes a channel (10) leading to the coronal end (6) and extending along the longitudinal direction of the dental implant (1) from the coronal end (6) toward the apex (4), and The core (2) has a transmission zone in which the channel (10) has a cross section perpendicular to the longitudinal direction of the dental implant (1) with a plurality of radially protruding portions arranged along the circumference of the cross section, wherein each of the radially outermost points of the radially protruding portions is located on a corresponding circle around the center (50) of the cross section, and at least two of these circles have different radii from each other. 21. The dental implant according to claim 1, wherein... The coronal surface (100) of the dental implant has a wavy profile, wherein the highest and lowest portions of the coronal surface (100) are arranged alternately along the circumference of the coronal end (6) of the dental implant, and At the highest point of the crown-side surface (100), the crown tip (6) of the dental implant has a tapered configuration such that the lateral dimension of the cross section of the crown tip (6) perpendicular to the longitudinal direction of the dental implant decreases along the direction from the top tip (4) of the dental implant toward the crown tip (6) of the dental implant. 22. The dental implant of claim 1, wherein the core (502) includes a channel (510) leading to the crown end (506) and extending from the crown end (506) toward the apex (504) along the longitudinal direction of the dental implant, and the channel (510) includes a conical portion (514). 23. The dental implant (1) according to claim 12, wherein in the transition zone (26), the core (2) has a cone angle in the range of 1° to 12°. 24. An insertion tool (200) for inserting a dental implant, specifically for inserting a dental implant according to any one of the preceding claims into the bone tissue of a patient, wherein... The insertion tool (200) includes a proximal portion (202) and a distal portion (204), the distal portion (204) being used to mate with the dental implant. The distal portion (204) has a retaining element (206). The retaining element (206) includes an attachment portion (208) for attaching the insertion tool (200) to the dental implant. The retaining element (206) is elastically deformable in at least all directions perpendicular to the longitudinal direction of the insertion tool (200), and The attachment portion (208) includes at least one protrusion (210) that extends in one or more directions substantially perpendicular to the longitudinal direction of the insertion tool (200). 25. The insertion tool (200) according to claim 24, wherein The distal portion (204) also has a transmission region (214) in which the cross section of the distal portion (204) perpendicular to the longitudinal direction of the insertion tool (200) has multiple principal directions in which the radius of the distance between the center of the cross section and its outer contour is measured in the multiple principal directions, and therefore takes a higher value than in adjacent orientations. 26. The insertion tool (200) according to claim 25, wherein the transmission region (214) has a tapered configuration such that in the transmission region (214), the lateral dimension of the cross section of the distal portion (204) perpendicular to the longitudinal direction of the insertion tool (200) decreases along a direction from the proximal end of the insertion tool (200) toward the distal end of the insertion tool (200). 27. The insertion tool (200) according to claim 25, wherein the number of the main directions is three or more. 28. The insertion tool (200) according to claim 25, wherein The distal portion (204) also has a transmission section (216) in which the cross section of the distal portion (204) perpendicular to the longitudinal direction of the insertion tool (200) has a plurality of radially raised curved portions (218) arranged along the circumference of the cross section, wherein each of the radially outermost points (222, 224) of the plurality of radially raised curved portions (218) is located on a corresponding circle around the center of the cross section, and at least two of these circles have different radii from each other. 29. The insertion tool (200) according to claim 28, wherein the transmission section (216), the retaining element (206) and the transmission region (214) are arranged in such an order in a direction from the distal end of the insertion tool (200) toward the proximal end of the insertion tool (200). 30. The insertion tool (200) according to any one of claims 24 to 29, wherein The insertion tool (200) consists of two separate parts attached to each other. 31. The insertion tool (200) according to claim 30 when dependent on claim 28, wherein one of the two separate components (230) includes the transmission section (216), and the other of the two separate components (232) includes the retaining element (206) and the transmission area (214). 32. The insertion tool (200) according to claim 24, wherein the retaining element (206) has at least one cut portion extending from the distal end of the retaining element (206) toward the proximal end of the retaining element (206). 33. The insertion tool (200) according to claim 32, wherein the retaining element (206) is a hollow body, and the at least one cut portion penetrates the outer wall of the retaining element (206). 34. The insertion tool (200) according to claim 30, wherein the two separate components are releasably attached to each other.