CN1870952B - elastic implant - Google Patents

Abstract

Implant for temporary or permanent implantation in the human or animal body, made of at least one biocompatible material having a shape adapted to perform one or more of its primary functions, characterized in that said shape has one or more areas (1, 18) with elasticity or mobility as secondary function, said implant having in this or these areas a material recess (7, 19) for locally reducing the stiffness of the implant and retaining the shape required for the primary function.

Description

elastic implant

technical field

The invention relates to an implant according to the preamble of claim 1 or claim 3 and a method of manufacturing an implant according to the preamble of claim 19 . the

Background technique

In modern medicine, implants are used to compensate or minimize the effects of defects in the human or animal body. For example, spacer supports for vertebrae or intervertebral discs can be used in place of vertebral bodies or intervertebral discs. As another example, the spinal reinforcement or stabilization system can be fixed to the vertebrae with pedicle screws and connected to each other through connecting rods, so that the distance and arrangement of the vertebrae can be adjusted and fixed. the

For all implants it is important that the implant material is compatible with the human or animal organism, that is to say does not cause rejection or burden the organism due to degradation phenomena. Therefore, the choice of materials for implants is substantially limited. the

In addition, it is preferable to make the implant as simple as possible, especially with few parts, because the combination of parts requires an increase in the surgical cost of inserting the implant, and on the other hand, it is more difficult where the various parts are connected to each other. Error prone and thus more likely to fail. Therefore, it is particularly recommended to make an integral implant. the

Contrary to this, however, the implant has to fulfill multiple functions, which in turn makes it desirable to use different materials and/or to compose the implant from different parts. For example, for the spacers, it is hoped that they not only fulfill the function of filling the space and maintaining a certain distance between adjacent vertebrae, but also facilitate a certain mutual movement between the vertebrae, that is, they act like joints within a certain narrow range. effect. For this purpose, a spacer support can be used, for example according to DE 10056977 C2, wherein between the supports adjacent to the vertebral body, there is arranged a spacer made of a dense woven or braided material between the implants. A bellows-shaped pipe that is stretchable in the longitudinal direction. But this brings with it the aforementioned disadvantage of requiring the use of several different materials that must be joined together, which increases the possibility of error. Moreover, although there are already implants whose advantages are certain elasticity, specifically stretchability, compressibility and bendability, due to the above-mentioned problems related to connection technology or material selection, so far So far it has not been considered. the

Such a stabilizing device for stabilizing adjacent vertebrae is known from EP0669109B1: it consists of 2 uniaxial pedicle screws and a ribbon, which is respectively fixed by a fastening screw at the receiving end of the pedicle screw. position, the device also includes several supporting elements, which are pressure-resistant bodies that are sheathed on the belt. However, in addition to the disadvantage of having a large number of various parts, this stabilizing device has the problem that it is no longer elastic when the support element is put on. The use of uniaxial pedicle screws further limits the application of this stabilization device. Another similar stabilization device is known from EP1188416A1, in which polyaxial pedicle screws are used instead of monoaxial pedicle screws. the

Such a dynamic vertebral stabilization device is known from US2003/0109880A1: the device comprises a first screw and a second screw anchored on the vertebrae, each screw has a receiving part for inserting a spring connecting the screws and One such spring. The spring itself is formed as a whole in the form of a tension spring in the shape of a helical spring with closely adjacent coils and fixed at the receiving site by fastening screws. However, this device also carries the risk of loosening the fixation between the bone screw and the spring due to the elastic yielding of the spring to the pressure of the fastening screw. the

Contents of the invention

It is therefore an object of the present invention to provide an implant consisting of as simple as possible parts, in particular of one piece or of several pieces easily connected; and wherein, among other functions, it is ensured that the implant or some of its Regions have a certain degree of elasticity and activity. Among other things, the device should be easy to manufacture, implant, safe to use, durable and versatile. the

The above object is achieved by the following implant. the

The present invention provides a spinal stabilization device comprising a first bone anchoring element for anchoring into a vertebra, the first bone anchoring element having a first end seat; a second bone anchoring element for anchoring into a vertebra, The second bone anchoring element has a second end seat; and a connecting member configured to connect the first end seat by being received in the first end seat and the second end seat. A bone anchoring element is connected to the second bone anchoring element, the connecting part comprising: a first rigid portion having a first rigid tubular body configured to be connected to the first bone anchoring an element; a second rigid portion having a second rigid tubular body configured to be connected to the second bone anchoring element; and an elastic portion having an elastic tubular body with helical depressions, the an elastic tubular body is disposed between the first rigid portion and the second rigid portion, wherein the spinal stabilization device further comprises a spacer supporter for displacing an intervertebral disc or vertebra adjacent to the connecting member, The spacer support has a tubular body with a resilient section with helical depressions. the

The invention is based on the recognition that, with respect to implants for the human and animal body, the shape is essentially chosen according to the function or functions it fulfills for the implant in the body. These functions may also include a certain degree of mobility or elasticity of the implant. In other cases, however, mobility or elasticity within the implant is not essentially necessary, but may be desirable or advantageous. In this regard, in the following description, the mobility and resilience functions will be referred to as secondary functions, while all remaining functions will be referred to as primary functions. the

In the first group of cases, prior art mobility or elasticity is achieved through additional components and/or different types of materials. This invention takes an alternative approach where mobility or elasticity is achieved not through additional material or additional separate components, but through the design of recesses in the material in an integrally formed implant or implant component Provisions are made to achieve areas of resilience or mobility. the

In the second group of cases, mobility or elasticity is not an absolutely necessary function, which is also achieved according to the invention by the additional provision of corresponding material depressions in the corresponding regions on the shape prescribed by the desired function. the

In this way, the elasticity and mobility of the implant or its parts can be obtained in a simple manner without the use of additional elastic material and corresponding connection parts or additional separate parts. In this respect, the elasticity or mobility function can be provided in addition to or as a component of the necessary function of the implant. In particular, this makes it possible to produce compression and/or tension zones and, within certain limits, to form bending joints or torsion elements etc. in a simple and reliable manner, especially in integrally formed implants or parts thereof. the

Correspondingly, for implants which are preferably formed in one piece, stable, hard, and especially under specific application conditions, rigid, preferably elastic, rigid materials such as titanium, titanium alloys, plastics, etc., can be used. In general, all biocompatible materials that do not cause rejection or disintegrate that burden the body can be candidates. the

The material depressions are preferably groove-like depressions or openings formed in the wall of the implant or implant component. The shape, number and arrangement of the material depressions can be adjusted on a case-by-case basis to meet the load requirements. the

As a universal shape that meets many requirements, the material depression is particularly suitable for forming a helix that extends around the implant body, thereby forming in particular a helical spring type shape, and is particularly suitable for forming in the helical spring element through the material depression Free spaces are formed between adjacent spiral strips. In addition to easier production and a wider choice of relevant materials, it also facilitates greater flexibility. the

It is particularly advantageous if the two material depressions can be formed in parallel in pairs or in the shape of a double-flying helix. In this way, in particular two helical springs arranged nestedly in one another can be formed. If the height of such helical depressed regions is the same, double pitched double helical depressions can replace low pitch single helical depressions. the

Resilient implants are particularly suitable, and particularly well suited, for use together as a system of spacer supports for vertebrae and/or intervertebral discs and connecting rods for pedicle screw arrangements to keep the patient's spine relatively stable while There is also moderate activity. the

The space support and gravity transmission functions are the primary functions of the vertebral and/or intervertebral space support, while the damping effect and mobility are additional functions as secondary functions. the

The supporting and connecting functions are the primary functions for connecting rods. the

For implants or spacer supports or connecting rods, it has proven to be best to form them as tubular bodies with a central tubular body and connecting elements at the ends, and the material depressions for obtaining elasticity are best formed tubular In the form of one or two helical holes in the body, so that the part basically forms the shape of one or two helical springs embedded in each other. The connecting elements of the spacer support preferably have means for connecting adjacent body parts such as vertebrae, such as hook-like protrusions at the ends and/or depressions, grooves and openings in the outer surface, so that the spacer support can grow into the tissue and intertwined with it. But in this regard, do not confuse the holes or recesses of the connecting element with the material recesses in the tubular body used to obtain the elasticity and mobility of the spacer support. Since the connecting elements are completely interwoven with adjacent body parts such as vertebrae, they do not contribute to the elasticity or mobility of the vertebrae. the

The means for connecting the tubular body to the adjacent body part may be arranged either integrally with the tubular body, in particular by means of extension at the end of the tubular body, or detachable at the end, for example capable of being screwed into the end of the tubular body on the end plate. the

When using such a separable end plate or an end plate integrally connected with the tubular body, preferably at least one sleeve of elastic material is provided around the tubular body with material depressions to To achieve elasticity or mobility; or to provide at least one elastic core within the tubular body. Such an elastic core or sleeve, preferably made of elastomer, has the advantage of being able to precisely adjust the elasticity or rigidity of the tubular body or spacer support. Through the modular arrangement of the tubular body and the core and/or the sleeve with corresponding depressions, an implant of exactly defined stiffness in terms of damping can be obtained in a simple manner using different components of different stiffness. Here, the combination of an implant part with material depressions which can be made elastic with an implant part consisting of a piece of elastic material which can be adjusted to a defined stiffness is a very basic object of the invention. To obtain a modified stiffness, it is only necessary to change the combination of parts, ie for example just use another core or another sleeve of different stiffness with the elastic tubular body. Although it is conceivable that both the sleeve and the core could be used with the elastic tubular body, for simplicity only one combination of the tubular body and the core or the tubular body and the sleeve is usually used. Here, the sleeve also has the advantage of protecting the tubular body with the preferably helical depression from external influences, whereas in contrast to this, when using a core, the core is protected by the tubular body. the

Preferably both the core and the sleeve can be fixed by arranging end plates at the ends of the tubular body, in the case of sleeves the end plates preferably protrude from the tubular body and thus form a larger diameter than the tubular body. The end plate can be integrated at least partially, ie on one side, with the tubular body so that it forms a beaker here. Furthermore, the end plate can also be detachably connected to the tubular body at one or both ends, for example by screws or threads. Here, the external thread can be provided both on the end plate and on the tubular body. the

Preferably, the implant or tubular body with material depressions for elasticity and mobility is stretchable or compressible in the longitudinal direction by 0.5% to 20%, in particular 1% to 15% along the longitudinal axis of the spacer support. %, and can be bent about a radial axis perpendicular to the longitudinal axis of the spacer support so that adjacent body parts can deflect about 0.5 to 10 degrees, particularly 1 to 6 degrees, relative to the longitudinal axis. Furthermore, in a preferred embodiment, twisting is possible by 0.5 to 2.5 degrees about the longitudinal axis. the

In yet another advantageous application of elastic implants, the connecting rods between uniaxial or polyaxial pedicle screw devices in the region between the pedicle screw devices can be provided with a certain degree of rigidity by arranging corresponding material recesses. Elasticity and mobility, which in turn can be enhanced in particular by the fact that at least part of the connecting rod is formed as a hollow body. Rod elements are especially suitable for Stabilization and mobility limitation of adjacent vertebrae in various degrees of disc defect. These properties are obtained in a simple manner by changing the dimensions of the rod-shaped element during the manufacturing process. the

For example, such an implant can be made from an object in a simple manner by having one or more material depressions formed in the object by mechanical or chemical machining, electrical discharge machining (EDM), laser treatment or any other means. on the wall. In particular one or preferably two material depressions can be arranged helically around the object or along the wall. the

When the body is a solid body, such as a solid cylinder, a bore can be formed in a preceding or subsequent auxiliary step, in particular coaxially with the material depression, so that preferably a helical spring is formed in the elastic region. When using pipe material, it is not necessary to drill the center section. the

Ideally, the material depressions are made by laser processing of the tubular body, since in that case both depressions can be formed in the same processing step. By means of a laser, the bores are formed simultaneously on both sides by drilling through the tubular body (for example, also a square tube). Simultaneously rotate and propel the tubular body to form a double fly helix. the

In another aspect, the present invention relates to a rod-shaped element for connecting at least two bone-anchoring elements, each bone-anchoring element having an anchoring section for anchoring into a bone and for connecting with the rod-shaped element. The receiving part of the part connection, and the rod-shaped element is wrapped with at least one rigid section and an elastic section formed from one piece of material, and the elastic section is especially formed as a helical spring, and/or wherein the elastic section and A second rigid section adjoins the resilient section at the other end adjacent to the rigid section, and/or wherein the outer diameter of the resilient section differs from the outer diameter of the rigid section in at least one location, and/or wherein the resilient section At least some portion of the section has a smaller outer diameter in one direction perpendicular to the axis of the rod than in another direction, and/or wherein the outer diameter of the elastic section varies, and/or wherein the elastic section has A core, and/or wherein a coaxial bore is provided through the rod-shaped element. the

And, in another aspect, the invention relates to a bone stabilization device comprising at least two bone anchoring elements and a rod-shaped element as described above for connecting the bone anchoring elements, each bone anchoring element having a bone for anchoring into the bone. The anchoring section and the receiving section, in particular the bone anchoring element, can be uniaxial or polyaxial bone screws. the

Furthermore, the invention relates to a method of manufacturing a rod-shaped element comprising the steps of:

Prepare a rigid rod;

Preferably, the helical spring section is formed on at least one longitudinal section within a predetermined distance from the free end of the rod by removing material, and its central part can be drilled or left in the axial direction, and/or in the elastic section. A defined area of material is removed longitudinally to produce a non-circular cross-section in at least one area of the elastic section, and/or the rigid section is made smaller in diameter relative to the elastic section. the

In particular, the invention relates to a resilient member for use in bone or vertebral stabilization devices, which is generally a cylinder having a first end and a second opposite end, each of the opposite ends of the cylinder having a coaxial hole and the At least one of the ends contains an internal thread for connection to the nut and/or screw of the bone screw or for connection to a rod section or plate, wherein in particular both ends each have an internal thread. the

The invention also relates to an elastic element for use in bone and vertebral stabilization devices, which is generally a cylinder having a first end and an opposite second end, said cylinder first end having a cylindrical protrusion with an external thread material for connection to the nut or shank of a bone screw, for connection to a stem section, or for connection to a plate. the

The second end of the cylinder contains an externally threaded cylindrical protrusion for connection to the nut or shank of a bone screw, for connection to a stem section or for connection to a plate. the

According to yet another preferred embodiment, said elastic element comprises a coaxial bore adjacent to the second end and/or at least in the section of the coaxial bore adjacent to the second end, an internal thread is provided. For connection to a nut or shank of a bone screw, for connection to a rod section, or for connection to a plate. the

According to yet another preferred embodiment, the elastic element is characterized by a bore running through its entire length, and/or the cylinder is tubular with a continuous coaxial bore and has a helical shape in the direction of the axis of the cylinder. An extended in-wall recess, wherein the recess terminates radially at the bore. the

According to yet another preferred embodiment, the elastic element is characterized in that a core is arranged in the bore and/or the elastic element is formed as a helical spring. the

According to another preferred embodiment, the elastic element is made of biocompatible material, especially Is made of titanium. the

The invention particularly relates to a bone anchoring element with an elastic element as described above, comprising a bone threaded screw rod connected to one end of the elastic element and a bone screw end piece preferably a nut connected to the other end of the elastic element. the

The invention relates in particular to a rod-shaped element for connecting two bone anchoring elements, the rod-shaped element having an elastic element and a first rigid rod section connected to one end of the elastic element, in particular a second rigid rod section Connect to the other end of the elastic element. the

The invention relates in particular to a plate having, at least at one end thereof, a cylindrical protrusion with an external thread or a bore with an internal thread for the attachment of the above-mentioned flexible or elastic element. the

The invention relates in particular to a stabilization device for the dynamic stabilization of bones, bone parts or the spine with at least two bone anchoring elements interconnected by a rod-shaped element as described above. the

This invention particularly relates to a kind of manufacturing method of elastic element, comprises the following several steps:

(a) Prepare a tubular body or

(b) prepare a cylindrical object;

(c) forming helical depressions by metal-cutting material removal in a helical form coaxial with the major axis of the cylindrical or tubular body from the outside in the direction of extension;

(d) forming a bore along the major axis of the cylinder;

(e) forming an internal thread in one of the two end sections of the tubular body or bore;

wherein the inner diameter of the bore in step (d) is selected such that the helical depression on the outer wall of the cylinder formed by metal cutting in step (c) ends radially in the bore, particularly at the other end of the bore Internal threads are formed in the upper section. the

This invention particularly relates to a kind of manufacturing method of elastic element, comprises the following several steps:

(a) prepare a cylinder;

(b) forming a cylindrical protrusion with external threads at each of the two ends of the cylinder by metal rotary cutting;

(c) Metal through a helical shape coaxial with the main axis of the cylinder along the direction of extension from the outside The method of removing material by cutting forms a helical depression;

(d) forming a bore along the major axis of the cylinder, in particular including the steps of:

(f) finishing the tail of the helical depression by grinding after forming the bore to remove sharp edges on the inside of the bore; and

(g) Deburring the elastic member thus produced. the

This invention particularly relates to a kind of manufacturing method of elastic element, comprises the following several steps:

(a) preparing a tubular body with first and second ends;

(b) preparing a cylinder with first and second ends and forming a bore coaxial with the major axis of the cylinder, said bore being adjacent at least the first end of the cylinder;

(c) The helix coaxial with the main axis of the cylinder along the extension direction is cut out by wire-cut electric discharge machining, laser treatment or water jet treatment;

(d) or form a cylindrical protrusion with a diameter smaller than the predetermined outer diameter of the tubular body in step (a) or the predetermined outer diameter of the cylinder in step (b) by metal rotary cutting at the first end of the cylinder, and externally threaded on the surface, or internally threaded in a bore adjacent to the first end section of the cylindrical or tubular body, wherein in particular the bore formed in step (b) extends from the first end to the second end of the cylindrical body . the

According to a further preferred embodiment, the method further comprises the step of forming an internal thread in the bore adjacent the second end section of the cylindrical body. the

According to yet another preferred embodiment, the above method further comprises the following steps: at the second end of the cylinder or the tubular body, forming a second cylindrical protrusion with a diameter smaller than the predetermined outer diameter of the cylinder or the tubular body by metal rotary cutting, And an external thread is formed on the surface of the second cylindrical protrusion. the

This invention particularly relates to a kind of manufacturing method of elastic element, comprises the following several steps:

(a) preparing a cylindrical or tubular body with a first end and a second end;

(b) At the first end and the second end of the cylinder, a cylindrical protrusion having a diameter smaller than the predetermined outer diameter of the cylinder or tubular body in step (a) is formed by metal rotary cutting, and the cylindrical protrusion external threads formed on the surface of the object; and

(c) The helix coaxial with the main axis of the cylinder along the direction of extension, the depressions are cut by wire-cut electric discharge machining, laser treatment or water jet treatment, especially the two sides of the helical depressions The tail is in the form of a 1/4 circle. the

Description of drawings

Further advantages, features and features of the present invention will become more apparent through the following detailed description of two specific embodiments in conjunction with the accompanying drawings. The drawings shown are purely schematic. the

Figure 1 Three-dimensional view of the spacer supporter of the vertebra or intervertebral disc;

A side view of the spacer support in Figure 2 Figure 1;

Figure 3 is a detailed side view of the spacer support in Figures 1 and 2;

Fig. 4a)-c) the view of another kind of spacer supporter;

Fig. 5a)-c) the view of the third spacer support;

Figure 6a)-c) stages of manufacture of objects of the invention;

Figure 7. Three-dimensional view of two pedicle screw devices and spacer support with a connecting rod;

Figure 8 is a three-dimensional view of adjacent vertebrae with spacer supports arranged therebetween and laterally fixed by a pedicle screw device with elastic connecting rods;

Fig. 9 is a three-dimensional schematic diagram of a stabilizing device with rod-shaped parts in the present invention;

The three-dimensional diagram of rod-shaped part in Fig. 10 Fig. 9;

A side view of the rod-shaped part in Fig. 11a Fig. 9;

The cross-sectional view of the rod-shaped part in Fig. 11b Fig. 9;

A three-dimensional view of the connection between the rod-shaped part and the bone anchoring part of Fig. 12a;

The cross-sectional view of the connection between the rod-shaped part and the bone anchoring part of Fig. 12b;

The side view of the rod-shaped part in another kind of embodiment of Fig. 13;

The side view of the rod-shaped part in another embodiment of Fig. 14;

The side view of the rod-shaped element rotated 90 degrees in Fig. 15 and Fig. 14;

A three-dimensional view of the rod-shaped element in another embodiment of Fig. 16;

The side view of the rod-shaped part in Fig. 17 Fig. 16;

Figure 18 is also a cross-sectional view of the rod-shaped part in an embodiment;

Use of a stabilizing device with a rod-shaped part among Fig. 19 the present invention;

The side view of the rod-shaped part in Fig. 20 Fig. 19;

Another use state of the stabilizing device with a rod-shaped part among Fig. 21 Fig. 19 3D view of state;

The side view of the rod-shaped part in Fig. 22 Fig. 21;

Another application of the stabilizing device in Figure 23;

Another application example of Fig. 24 stabilizing device;

A side view of another embodiment of the elastic rod-shaped part of Fig. 25a;

The cross-sectional view of the elastic rod-shaped part in Fig. 25b Fig. 25a;

The first application example of the elastic rod-shaped part of Fig. 26a;

Modification of the rod-shaped part in Fig. 26b Fig. 26a;

Fig. 27 has the bone anchoring part of elastic rod-shaped part in Fig. 25a and 25b;

Figure 28 A stabilization device consisting of two three-piece bone anchoring components and a rod-like component, each of which includes an elastic component;

A side view of another embodiment of the elastic rod-shaped part of Fig. 29;

A side view of another embodiment of the elastic rod-shaped part of Fig. 30;

The side view of another embodiment of Fig. 31a elastic rod-shaped part;

The side view of the elastic rod-shaped part rotated 90 degrees in Fig. 31b Fig. 31a;

The sectional view of Fig. 32 elastic rod-shaped part;

The elastic rod-shaped part in another embodiment of the present invention in Fig. 33;

The elastic rod-shaped part in another embodiment of the present invention in Fig. 34;

Figure 35a comprises an exploded view of a rod-shaped part, an elastic part of the present invention and a combination part of a plate;

Figure 35b is a cross-sectional view of the plate along the A-A line in Figure 35a;

Figure 36 Example of application of the plate in Figures 35a and 35b, wherein the plate and the rod-shaped part connected to the plate by elastic means are anchored to the vertebrae by means of bone anchoring means. the

The application of the elastic rod-shaped part of the present invention in the dynamic stabilization device for the hip bone of Fig. 37a;

Figure 37b is applied to the cross-sectional view of the bone anchoring component on the stabilizing device in Figure 37a;

Fig. 38 is a spring component made by wire-cut electrical discharge machining, laser treatment or water jet treatment in the present invention. the

Detailed ways

Figure 1 shows a three-dimensional representation of a first embodiment of the implant of the present invention as a spacer support for a vertebra or intervertebral disc. The spacer support 10 has a cylinder 1 and two connecting parts 2 positioned at the ends of the cylinder 1, the connection parts are used to connect the spacer support 10 to its adjacent body parts, such as bones or cartilage. the

The connecting parts 2 arranged at the respective ends of the cylinder 1 have the same shape in the illustrated exemplary embodiment, but may also be of different shapes. On each free end of the end part, the connecting part 2 has a serrated protrusion 3 which is able to engage adjacent body tissue at the implantation site. the

The saw-toothed protrusions 3 at both ends of the spacer support 10 are formed by triangular recesses 5, so that the trapezoidal saw-toothed protrusions 3 can be fitted and fixed in adjacent body tissues. the

Furthermore, the connection part 2 has diamond-shaped cutouts 4 (see FIG. 2 ) and are arranged so that they are adjacent to each other over the entire cylindrical outer surface of the connection part 2 . As a result, each connecting part is itself formed by a plurality of rhombus-shaped interconnected bars 6 , and the ends of the rhombus formed by the bars 6 are cut away to form trapezoidal serrations 3 . the

In the illustrated embodiment, the tubular body 1 between the connecting parts 2 at the ends of the cylinder has a helical material recess 7, so that the wall 11 (see Fig. 3) itself is formed in a helical shape. Since the spacer support 10 is formed as a hollow cylinder as a whole, even if the spacer support 10 itself is made of an inherently rigid material such as titanium or a titanium alloy, the tubular body 1 with the material recess 7 between the connecting parts 2 Become an elastic area or activity area. The spacer support 10 achieves a design-related elasticity in the area of the tubular body 1 by means of the material recesses 7, so that it is possible to achieve a separate elasticity or mobility without using a separate elastic material in this area. In particular, this avoids having to manufacture the spacer support in several parts that need to be assembled together. the

The extensibility and compressibility of the tubular body 1 along the longitudinal axis 9 of the spacer support 10 and around the longitudinal axis 9 perpendicular to the major axis 9 as indicated by the axis 8 ( FIG. 2 ) is conveniently obtained by means of the helical material depression 7 Bendability on the axis of rotation of . Here, in particular, the helical shape of the material depression 7 plays a role, which facilitates a smooth and even surface in as many directions as possible. Balanced elasticity or mobility. However, other shapes of material depressions and different numbers and arrangements of such material depressions are naturally conceivable and can also be used depending on the individual solution or possible load situations. the

Sub-figures a) to c) of Fig. 4 are three different figures, i.e. three-dimensional exploded views (a), (c) and three-dimensional cross-sectional views (b) of the second embodiment of the spacer 100 with the tubular body 101 ), the tubular body 101 is sealed at the lower side with an end plate 125 integrally connected with the tubular body 101, thereby forming a beaker shape. the

The tubular body 101 has on its wall 111 helical depressions 107 which, according to the invention, impart a certain elasticity to the tubular body 101 . the

In order to be able to precisely adjust the stiffness of the spacer support 100, inside the tubular body 101 there is provided a replaceable core part 130 made of elastic material, which is fixed from the bottom by the end plate 125 and from the top by the end plate 126 In the tubular body 101 . the

The end plate 126 on the upper side of the spacer has an external thread 127, through which it can be screwed into the internal thread 128 of the tubular body 101 at the inner upper end of the tubular body 101. The end plate 126 has a shoulder to make it tightly cover the wall. 111 on. Serrations 103 are provided over the entire circumference of the ends of wall 111 and extend through end plates 125 and 126 to engage adjacent tissue to securely position the spacer support there. the

The end plate 126 has connection holes 129 so that the end plate 126 can be screwed into the tubular body 101 . the

Figure 5 shows a third embodiment of a spacer support in sub-figures a) to c); where sub-figures a) and c) are three-dimensional exploded views, and sub-figure b) a three-dimensional cross-sectional view. In the embodiment of FIG. 5 , the tubular body 201 also has a helical depression 207 on the wall 211 . the

The tubular body 201 is also closed at the underside by an integrally formed end plate 225, which in turn forms the tubular body 201 in a beaker. Admittedly, the outer diameter of the end plate 225 is made larger than that of the tubular body 201 in which the helical material recess 207 is provided. A shoulder is thus formed, giving an end seat to the tubular sleeve 230 made of elastic material. The elastic sleeve 230 fits on the tubular body 201 and completely surrounds it. At the upper end, an end plate 226 is screwed onto the tubular body 201 by means of a screw connection. Here, the external thread 227 of the end plate 226 is engaged with the internal thread 228 of the tubular body 201 , so that the sleeve 230 is tightly fixed between the end plate 225 and the end plate 226 . set The sleeve 230 is also used to adjust the overall rigidity, wherein the overall rigidity of the implants 100 and 200 is simply changed by simply replacing the sleeve 230 in a manner similar to replacing the core 130 (see FIG. 4 ). the

The end plates 225 and 226 are provided with pyramid-shaped serrations 203 for fitting with surrounding tissues and firmly anchoring the spacer support. the

The cover 226 also has attachment holes 229 for screwing the end plate 226 onto the tubular body 201 . the

Figure 6 shows an example of how a laser beam 331 can easily create material depressions 307 and 337 in a tube 301 by laser processing. the

It can be seen from the sub-figure a) of Fig. 6, and it is particularly obvious from the plan view that at first the laser beam 331 is used to drill through the pipe 301 to form two openings 332 and 333; then, as shown in Fig. Simultaneously advancing in the direction of the arrow, the depression 307 starting from the opening 332 and the depression 337 starting from the opening 333 can be formed. The result is two parallel indentations of the material, thereby forming helical springs or helical spring regions arranged in nested, parallel pairs, double pitch. the

Fig. 7 shows another embodiment of the elastic implant of the present invention. Two pedicle screw arrangements 12 and 14 with corresponding pedicle screws 13 , 15 are shown in three-dimensional view in FIG. 7 , connected to each other by a connecting rod 20 . The connecting rod 20, more precisely at the elastic or mobile region 18 located between the fixation regions 16, 17, is designed as an elastic implant in which the connecting rod is supported by means of a pedicle screw arrangement. the

In the elastic region 18 of the connecting rod 20 there is provided a helical material recess 19 which extends around the longitudinal axis 21 of the connecting rod 20 . the

Since the connecting rod 20 is designed as a hollow cylinder, the elastic region 18 is actually also helical. the

In order to make the connecting rod of the present invention as shown in Fig. 7, a solid cylindrical or rod shape made of a biocompatible material such as a titanium alloy can be used. The first step is to create a material recess 19 in this solid rod by machining or chemical etching or by laser treatment in a specific area, namely the elastic area 18 . This connecting rod will have bigger in elastic area 18 flexibility and can be used in this way. the

The elasticity or mobility of the region 18 can be further enhanced by mechanically or chemically forming a bore in the longitudinal axis 21 of the connecting rod 20 and forming the connecting rod 20 into a hollow cylindrical or tubular shape. the

If the diameter of the bore is selected so that the thickness of the wall left by the connecting rod is less than the depth of the material depression 19 formed originally, then in the elastic region 18 it is not a groove-like depression but an opening, which is actually a spiral shape. Although this last-mentioned shape is a preferred embodiment, the previously mentioned shapes with only material depressions, ie groove-like depressions of hollow bodies or other structures are also possible as an alternative. the

Figure 8 shows the application of these two embodiment examples, namely the placement of a spacer support 10 between two vertebrae 22, 23 and the provision of an elastic connecting rod between pedicle screw arrangements 12, 14 on the human spine 20. From this figure it can be easily seen that, especially in the case of combined application, the elastic structure of the implant allows a certain mobility in the corresponding area of the spine, which will significantly increase the comfort of the patient. the

Figures 19 to 38 show further embodiments and areas of application of elastic implants, especially connecting rods in spinal stabilization devices. the

As can be seen in Figure 9, this stabilization device in the application shown comprises a rod-shaped member 401 and two pedicle screws 402, 403 interconnected by the rod-shaped member. The pedicle screws 402, 403 are anchored in the pedicles of two adjacent vertebrae 404, 405 between which the intervertebral disc 406 is damaged. the

The rod member 401 in the present invention is integrally formed. According to a first embodiment as shown in Figures 10, 11a and 11b, it comprises a first rigid section 407 of predetermined length starting from a first end of the rod-shaped part and having a length starting from a second end of the rod-shaped part. A second rigid section 408 of predetermined length, and an elastic section 409 of predetermined length between the rigid sections 407, 408, and the outer diameters of all sections are the same. In addition, a coaxial bore 410 having a predetermined diameter penetrates the rod member. The elastic section 409 is formed as a helical spring with a thread 411 of a predetermined pitch. The height of the thread 411 of the elastic section 409 along the longitudinal axis A of the rod-shaped component, the diameter of the coaxial bore 410 and the thread pitch that determine the radial thickness of the thread 411 The selection is such that the rod-shaped member 411 has the required rigidity when subjected to axial force, bending force, and torque force. the

As can be seen from Figures 9, 12a and 12b, the pedicle screws 402, 403 of the stabilizing device have, as known, a screw rod 412 with a bone thread and a U-shaped recess 415 with a rod-shaped part, basically The upper end seat 413 is cylindrical. Built-in screws 414 screwed into the end blocks are provided to secure the rigid sections 407, 408 to the end blocks 413 as known. Pedicle screws are preferably made as polyaxial screws. The axial length and diameter of the rigid sections 407 , 408 of the rod member 401 are dimensioned such that the rod member 401 with the rigid sections 407 , 408 can be attached to the pedicle screws 402 , 403 . The length of the rigid sections 407, 408 therefore corresponds at least approximately to the diameter of the built-in screw 414 used to fix the rod-shaped part. For the end seat 413' of the pedicle screw 420, since the rod-shaped part is not inserted from the top but is pushed in laterally at the opening 421, the length of the rigid section also has to be the same as that at the end seat 413 to fix the rod-shaped part. The built-in screws 414 are at least approximately equal in diameter. the

In the example of the stabilizing device shown in Figure 9, the length of the elastic section 409 of the rod-shaped member 401 is selected to be approximately equal to the distance between the pedicle screws 402, 403 in the unloaded state of the intervertebral disc 406, but the elastic section 409 It can also be longer or shorter. the

The rod member 401 is made of a biocompatible material, such as titanium or biocompatible plastic, however such materials have little or no elasticity. the

During the procedure, the pedicle screws 402, 403, 420 are first screwed into the vertebra adjacent to the pedicle, and then the rod member 401 and its rigid sections 407, 408 are inserted into the pedicle screws 402, 403, respectively. , 420 in one of the end seats (receiving parts) 413, 413'. After determining the relative positions of the vertebrae 404, 405 and adjusting the relative positions of the pedicle screws 402, 403, 420 and the rod member, the rigid sections 407, 408 are fixed in the end seats 413, 413'. The relative positions of the vertebrae 404, 405 are determined such that the elastic section 409 of the rod member 401 is in a relaxed state when the intervertebral disc 406 is unloaded. When loaded, forces are applied to the intervertebral disc 406 via the vertebral and intervertebral disc assembly. The rod-shaped part 401 limits the multiaxial movement of the vertebrae relative to each other via the elastic section 409 , thereby avoiding excessive stress on the intervertebral disc. This prevents mildly or moderately defective discs from deteriorating. As an alternative, pre-set vertebral alignment can be implemented with stabilization devices as needed in an unloaded state of the spine traction to relieve the load on the intervertebral disc in this way. As a further option, bone screws can also be directly anchored laterally into the vertebrae as desired. the

In the embodiment shown in FIG. 13, as in the previous embodiments, a rod member 500 comprises rigid sections 507, 508 and an integral elastic section 590 in the form of a helical spring, wherein the elastic section Segment 590 is between rigid sections 507 , 508 . It differs from the first embodiment in that the elastic section 590 has a larger diameter than the rigid sections 507 , 508 . In this way, the rigidity obtained is also greater than that of the rod-shaped member in the first embodiment. The surgical procedure was as described in the first example. the

Figures 14 and 15 show a rod member 501 in yet another embodiment. Unlike the rod members 401, 500 of the previous embodiments, the elastic section 591 disposed between the rigid sections 507, 508 has two regions 592 which are offset by 180 degrees from each other and concave towards the rod axis. The length L of the region 592 in the direction of the rod axis is at most the length of the elastic section 592, and the radius of curvature is set so that the thread of the coil spring will not be interrupted. As a result of this configuration, the elastic section 591 forms a narrower waist in the axial direction B perpendicular to the rod axis A and is less rigid in this direction. The result is a directional rigidity which is advantageous for some applications. the

The surgical procedure is as in the case of the previous embodiment, the only difference being that the rod member 501 can be connected in a circumferentially oriented manner within the pedicle screw. The required stiffness can be precisely selected and set by selecting the size of the elastic section. the

In yet another embodiment shown in Figures 16 and 17, the rod-shaped member 502 has a coaxial cylindrical core 511 extending through its elastic section 593, said core having a certain bending elasticity. The diameter of the core 511 is set such that the core can be properly snapped into place after being pushed into the bore 510 . The core is preferably of the same material as the rod-shaped part, but elastic plastics can also be used. the

In a design variant, the core 511 is integral with the threaded connection of the helical springs to the rigid sections 507 , 508 and to the elastic section 593 . the

The core 511 imparts greater bending stiffness to the rod member 502 compared to the previous embodiments. Therefore, in this embodiment, similar rigidity to that of the rod member 500 having a larger diameter of the elastic section can be obtained. Can be further tuned by choice of core diameter and/or material whole bending stiffness. the

The surgical procedure was carried out as in the case of the previous example. However, different from the previous embodiments, the elastic section 593 is smaller in size in terms of axial compression or extension and torque. In particular only bending movements are allowed, which is advantageous for certain applications. the

In another embodiment shown in FIG. 18, the rod member 503 has rigid sections 507, 508 and a resilient section 590 as in the previous embodiment. In the coaxial bore 510 is provided a stretchable member 512 such as a wire which is fixed in tension on the rigid sections 507 , 508 by means of a fixing member such as a clamping screw 513 . During surgery, this can prestress the elastic section 590 . the

The technical features of the various embodiments can be combined with each other. For example, the rod member 501 can also have a core and/or a specially shaped section for directional rigidity. In a design variant of embodiment 502, the elastic section forms a uniformly narrow waist at one location or provides several uniformly spaced concave regions on the circumference to obtain a certain rigidity in a defined direction. the

In another embodiment, the rod member has several rigid sections corresponding to several elastic sections, and each elastic section is located between the rigid sections, so that many pedicle screws can The partially rigid sections are elastically interconnected. the

In yet another embodiment, the resilient section is surrounded by a covering or protective sheath of biocompatible material to prevent tissue, blood vessels, or other bodily material from being trapped in the threads and causing injury or stem member function. damage. the

In yet another embodiment, a uniaxial screw is used instead of a polyaxial screw, or a combination of a uniaxial screw and a polyaxial screw or a combination of several of these screws are used in the stabilization device. It is also conceivable to use hooks instead of bone screws. In yet another embodiment, the rigid section and/or the elastic section is curved. the

Figures 19 to 24 show several preferred applications of the stabilizing device with rod-like elements. In the stabilizing device of FIGS. 19 to 22, a rod-shaped member 502 with a core 511 is used. This stabilizing device is used, for example, when a mildly or moderately defective intervertebral disc 506 needs support and it is desired to avoid harmful forces acting on the intervertebral disc by restricting the movement of the vertebrae. Rod Member 502 is axially rigid, allowing neither elongation nor compression in the axial direction. However, bending movements at an angle α to the shaft axis, for example a maximum of 8 degrees, are possible. the

Figure 23 shows the application of a stabilization device with a rod-shaped part in the case of connecting two vertebrae 404, 405 with a rigid part 450 such as a titanium cylinder after removal of the native intervertebral disc. Here, the rod needs to be more rigid in order to obtain sufficient motion restriction. However, slight relative motion between the vertebrae is beneficial compared to a fully rigid connection; because increased circulatory local loading stimulates bone growth and accelerates the ossification process. the

Shown in FIG. 24 is the application of a dynamic stabilization device as an elastic end of an extended connection, several of which in the illustrated example are 3 vertebrae 405, 405′, 405″ interconnected by a rigid member 450 and subsequently by a rigid rod 460. connection. Here, the native intervertebral disc 406 adjacent to the last vertebra 405 and the next vertebra 404 of the connecting chain is subjected to a disproportionate load resulting in increased wear of the intervertebral disc 406. In order to protect this adjacent part from abnormal movement and thus Incremental loads, stabilizers are used to limit movement. In this illustrated embodiment, the rod member 460 has a rigid section sized to enable three pedicle screws 402, 402', 402" to be connected thereto. 458. A resilient section 459 is disposed adjacent thereto and in turn adjoins at the end a rigid section 457 for attachment to the pedicle screw 403 . the

In the method of manufacturing a rod-shaped member of the present invention, a rigid rod of a desired diameter is prepared in a body-compatible material such as titanium. A resilient section 409 in the form of a helical spring is then machined in the section between the ends of the rod-shaped part. The core 410 is drilled through the spring member to form the rod member 401, if necessary. the

When the rod-shaped part 502 is manufactured, the core 511 is left or a separate core is inserted later. the

When manufacturing the rod-shaped part 500, prepare a rod whose diameter meets the diameter requirement of the elastic section 590 as a raw material, then adopt a method such as milling to make a coil spring, and then turn the rigid end sections 507, 508 into required diameters . the

To produce the rod-shaped part 501 , material is removed in a region of the elastic sections at positions offset from each other by 180° in the circumferential direction in order thereby to form the oriented waist. the

The elastic member 601 shown in Figures 25a and 25b comprises a cylindrical tube with a continuous coaxial bore 602 and a spiral with a predetermined pitch. In the form of a recess 603 that extends a predetermined length on the wall along the axis of the cylinder and terminates in the hole 602 in the radial direction. A helical spring is thus formed. The length of the helical depression in the axial direction of the cylinder, the height of the depression, the pitch of the helix and the diameter of the coaxial bore are selected to make the helical spring have the desired properties with respect to the axial force, bending force and torsional force acting on the spring member. required strength. The elastic member 601 has internal threads 604 and 604' of a predetermined length near each free end thereof. The outer diameter of the elastic member is selected according to the respective application. the

In the first application example shown in FIG. 26 , the spring member 601 is an integral part of the elastic rod member 630 . The elastic rod member 630 includes an elastic member 601 and two cylindrical rod sections 631, 631', each of which has a cylindrical protrusion 632, 632' at its end, and the two protrusions There are external threads 633, 633' which can cooperate with the internal threads 604, 604' on the elastic member 601 respectively. In this embodiment, the rod member and the elastic member have substantially the same diameter. The lengths of the rod members 631, 631' and the spring member 601 can be independently selected according to the desired application. For example, a rod-like component is used to attach pedicle screws on the spine. Due to the elasticity of the spring member 601, the rod-shaped member 630 thus formed absorbs compression force, tension force, bending force, and torsion force to a predetermined degree. the

The elastic rod member 680 shown in Figure 26b differs from the elastic rod member 630 in that its first rigid rod section 681 has a larger outer diameter than the elastic member 601 and the second rigid rod section The outer diameter of 681' is smaller than that of elastic member 601. Alternatively, the diameter of both rod sections may be larger or smaller than the spring member. the

FIG. 27 shows the second application example of the elastic member 601 . It can be seen from the figure that the elastic member 601 is an integral part of the bone anchoring member 610 configured in the form of a polyaxial bone screw. The polyaxial bone screw comprises a screw part 611 consisting of a spring part 601 , a screw shaft 612 with a tip not shown here and a nut 613 . the

There are bone threads 624 and cylindrical protrusions 625 on the screw rod 612 , wherein the bone threads 624 are used to screw into the bone, and the external threads on the cylindrical protrusions 625 cooperate with the internal threads 604 on the elastic component 601 . the

Nut 613 includes cylindrical protrusion 627 and its adjacent cylindrical protrusion 626 , similar to the screw 612 , the cylindrical protrusion 626 has an external thread that cooperates with the internal thread 604 ′ on the elastic member 601 . the

The screw part 611 is nested in the receiving portion 614 and can rotate under no load. The receiving part 614 is substantially cylindrical in shape, and has a first bore 615 arranged in an axis-symmetrical direction at one end thereof, and the diameter of the bore is larger than that of the screw rod 612 but smaller than that of the nut 613 . In addition, the receiving portion 614 also has a coaxial second bore 616 at the opposite end from the first bore 615, the diameter of which is designed to allow the screw member to pass through the open end and pass through the first bore together with its screw rod. The hole 615 reaches the nut 613 and abuts against the edge of the first bore 615 . The receiving portion 614 has a T-shaped recess 614 ′, which extends from its free end in the direction of the first bore 615 and forms two free legs 617 , 618 . In the vicinity of their free ends, the legs 617 , 618 have internal threads which can be used together with the external threads of the built-in screw 619 to fix the rod 620 . the

In addition, there is also a pressure member 621 in the receiving portion 614 for fixing the nut 613. The pressure member 621 is designed to have a spherical depression 622 on the side facing the nut 613. The radius of the spherical depression 622 is approximately equal to that of the nut. 613 the radius of the billiard section. The outer diameter of the pressure part 621 is selected such that the pressure part 621 can be inserted into the receptacle 614 in the direction of the nut 613 . In addition, there is a coaxial bore 623 on the pressure member 621, so that a screw-in tool can be inserted to engage with a recess (not shown) on the nut 613 . the

During the operation, the screw rod 612 is screwed into the internal thread 604 of the elastic member 601 through its cylindrical protrusion 625, and the nut 613 is screwed into the internal thread 604' through its cylindrical protrusion 626, thus forming the screw part 611 . With the screw rod 612 facing forward, the screw part 611 made in this way is inserted through the second opening into the receiving portion 614 until the edge of the nut 613 and the first bore 615 abuts. Then, the pressure member 621 enters the receiving site 614 through the second bore 616 forwardly in a spherical depression. The screw member 611 is then screwed into the bone or vertebrae. Finally, the rod 620 is placed at the receiving site 614 between the two legs 617 , 618 , the angular position of the receiving site relative to the screw part is adjusted and fixed with built-in screws 619 . The elastic section allows limited movement around the relaxed position. the

The polyaxial screw is not limited to the embodiments described above, but may be any other polyaxial screw with the three-segment screw components described above. Correspondingly, if the elastic part is 601 and the screw rod 612 are screwed into the nut 613 before the nut 613 enters the receiving part 614 through the second bore 616 forward with the cylindrical projection 626, then the first bore 615 in the embodiment shown in Figure 27 The diameter may be smaller than that of the screw 612. In this case, it is sufficient that the diameter of the first bore 615 is larger than that of the cylindrical protrusion 626 and the cylindrical section 627 . Alternatively, the screw cap 613 can also have no cylindrical section 627 . In this case, the diameter of the first bore only needs to be large enough to allow the protrusion 626 to pass through. the

However, the receptacle can also be designed so that the screw part is inserted from below and the screw part is clamped in the receptacle by a pressure part. In this case, the diameter of the bore 615 shown in FIG. 27 should be larger than the diameter of the nut 613 . the

Fixing of the rod is not limited to internal screws as shown in Fig. 27, but additional external nuts or any other known type of rod fixing methods may be used. the

If the elastic member 601 can protrude at least partially over the bone surface, then the elastic member 601 can absorb bending forces as well as tension and compression. When the spring member does not protrude above the surface of the bone, the screw member 611 can still react in a certain way to the movement of the bone or vertebrae. This prevents the development of unfavorable tension. the

What Fig. 28 shows is the stabilizing device 690 of the spine, which comprises two bone anchoring parts 691, 691' with screw parts 693 and an elastic rod part 692 for connecting the two bone anchoring parts, these elastic rod parts 692 has the elastic member 601 of the present invention. This multi-piece design of the elastic rod part and the screw part allows to obtain a stabilization device 690 with various properties with the combination of only a few basic parts. The stabilizing device also does not necessarily have to comprise a bone anchoring element with an elastic element and a rod-shaped element with an elastic element. Depending on the field of application, it is also possible to comprise only a rod-shaped part with a spring part and a bone-anchored part with a rigid screw part. the

Figure 29 shows the elastic component 640. The difference between the elastic component 640 and the elastic component 601 is that the internal thread 641 running through the entire length of the elastic component replaces the two internal threads 604, 604'. the

Shown in FIG. 30 is an elastic member 650 . What differs from the previous embodiments is that the part includes rigid end portions 651 and 651' and fewer helical turns than the previous embodiments number. This makes it possible to design the elasticity of the spring element independently of the length of the spring element. the

Figures 31a and 31b show a spring member 660 which, unlike the previous embodiments, comprises two regions 661 which are offset by 180 degrees from each other and which are both concave towards the central axis. The length L' of the region 661 in the direction of the central axis is not greater than the length L of the helix, and the radius of curvature of the region 661 is set so as not to interrupt the coils of the coil spring. Due to this design, the spring element has a narrower waist shape perpendicular to the central axis and is therefore less rigid in this direction. This allows the stiffness of the elastic member to be directional to suit the needs of certain applications. the

The elastic member 672 shown in FIG. 32 includes a rod-shaped core 671 inserted into the hole. On the one hand, this core can act as a stopper when the elastic member 672 is under pressure. On the other hand, the core 671 may enhance the rigidity of the elastic member 672 against bending force. the

The spring member 760 shown in Figure 33 comprises an externally threaded cylindrical protrusion 761 at one end thereof rather than an internally threaded bore as in the previous embodiment. Correspondingly, the part connected to this end of the spring part has a bore with a corresponding internal thread. At the other end of the spring member is a pocket bore 762 with internal threads 763 adjacent the end of the spring member as in the previous embodiments. the

Shown in Figure 34 is a spring member 770 having an externally threaded cylindrical protrusion 771, 772 at each end. the

As a modification of the previous embodiment, the resilient member does not contain a continuous bore. the

As yet another application example of the elastic member 601 of the present invention, the exploded view shown in FIG. 35 a is a connecting member 700 , which includes a rod-shaped member 631 , an elastic member 601 and a plate 701 . The rod member 631 has a cylindrical protrusion 632 with an external thread 633 for screwing into an internal thread 604 near one end of the elastic member 601 . The plate 701 also includes a cylindrical protrusion 702 with an external thread 703 for screwing into an internal thread 604' located near the other end of the resilient member 601 . The plate comprises two segments 704 and 704 ′, circular in plan view and connected to each other by fins 705 . The width B of the fin 705 is smaller than the diameter D of the circular segments 704, 704'. Two through-plate bores 706, 706' for placement of countersunk screws are arranged coaxially with the circular section. Figure 35b As shown, the first face 707 of the plate has a convex curvature and the second face 708 of the plate has a concave curvature, the concave curvature being used to abut this face against the bone. The different radii of curvature of the two faces 707 , 708 of the plate 701 result in a gradual thinning of the plate 701 towards the sides 709 . This makes the board both stable and space-saving. As shown in Figure 35b, the bores 706, 706' each include a bore 706a, a tapered first section 706b, and a second section 706c; wherein the bore 706a is adjacent to the second face 708 of the plate, the tapered first section 706b Adjacent to the hole, the second section 706c is adjacent to the first section and the first face 707 of the plate. Their shape is such that bores 706 and 706' are adapted to accept countersunk screws. Bores 706 and 706' may be shaped differently than described above so long as they are adapted to accept countersunk screws. the

Figure 36 shows an application example of the connection part in Figure 35a. Wherein the plate 701 is fixed to the two vertebrae 711 located in the cervical spine from the rear side by two bone screws 710, and the rod-shaped part 631 connected to the plate 701 by the elastic member 601 is anchored to the chest by three bone anchoring screw parts 715. on the vertebra 712 of the segmental spine. the

Fig. 37a shows another application example in which the spring component 601 of the present invention is used in a dynamic pelvic stabilization device 730. The dynamic pelvic stabilization device includes bone anchoring members 728, 728' and 728" interconnected by rod members 631, 631' and 631" and spring members 601 and 601".

Like the other two bone anchoring parts 728' and 728", the bone anchoring part 728 includes two halves 725 and 731, which are connected to each other by a screw 727, the screw 727 is connected to the first half 725 The thread 734 in and the thread 735 engagement in the second half 731. The top view in Fig. 37a shows only the upper half 725. The rod-shaped member 631 is sandwiched between the two halves 725, 731 mentioned above , and in the recess 732 on the first half 725 and in the recess 733 on the second half 731, so that the bone anchoring member 728 is firmly connected to the rod member 631. In addition, the two halves 725 , 731 have bores 736, 737 respectively, and these two bores are arranged coaxially under the assembled state. The spherical depression 738 near the bore 736 and the spherical depression 739 near the bore 737 are used to accommodate the bone screw 726. The bone screw 726 includes a rod-shaped section 751 and a ball-shaped nut section 753, wherein the rod-shaped section 751 has an external thread 752 for screwing into the bone, and the radius of the ball-shaped nut 753 is compatible with spherical depressions 738 and 739 The radii are basically equal.

Similar to the bone anchoring member, the connecting member 724 also has two halves 722, only one of which is visible in the top view of FIG. 37a. By entering the recess, the rod-shaped part 631 is sandwiched between the aforementioned two halves 722 , so that the connection part 724 is securely attached to the rod-shaped part 631 . the

The stem part 721 includes a spherical head section 721b and a stem section 721a. The head section 721b is clamped by a not shown recess between the two halves 722 so as to be connected to the two halves 722 so that it is fixed in a pivotal position. At the other end opposite the head 721b is a rod member 721a, which includes a cylindrical protrusion (not shown) with an external thread that can be screwed into an internal thread in the elastic member 601' (not shown in the figure). the

The elastic part can be produced by the method of milling. The raw material used is a cylinder made of a biocompatible material such as titanium with a predetermined outer diameter, and then a sheet milling cutter is used along a line whose main axis is the same as the main axis of the cylinder. The helical line mills out the depression. Subsequently, a bore is formed along the major axis of the cylinder, which runs the full length of the cylinder and terminates the helical depression in the bore. In order to ensure the stability of the elastic element, the helix end of the transition between the helical part and the end section of the elastic element is important. It is therefore necessary to trim the helix tail with an end mill at both ends of the helix to remove the sharp edges inside the bore. To achieve this, the helix tail is milled tangentially to the helix profile using an end mill. Subsequently, the entire assembly is deburred inside and outside. Finally, an internal thread is produced in each of the two end sections of the bore. the

In addition to milling techniques, elastic member 800 may also be machined from a cylinder using wire-cut electrical discharge machining, laser processing, or water jet processing. As shown in FIG. 38, machining can also start from a cylinder having a predetermined outer diameter D', and in a subsequent step a bore 801 is formed along the main axis A of the cylinder and runs through the entire length of the cylinder. Then, one of the above-mentioned processing methods is selected according to the thickness of the wall, and the wall of the hollow cylinder thus produced is cut along the spiral 802 . The tail 803 of the helix 802 is formed in the shape of a 1/4 circle, thereby making it unnecessary to complete the tail 803 through an additional process relative to the milling process. Also, there is no need for deburring during these operations. The shape of the tail does not have to be 1/4 circle, it can be any other shape such as the shape of another section of the circle, as long as the material is used in these shapes The maximum load in the process can be kept at a low level. the

Finally, as with the milling process, an internal thread is formed in each end section of the bore. the

In a refinement, the method described above can be modified to replace at least one internal thread by turning a cylindrical protrusion with an external thread on a lathe at the beginning of the process. In this case, the diameter of the bore must be smaller than the diameter of the cylindrical protrusion. the

In yet another modified fabrication process, the spring member is fabricated without a continuous bore. the

Claims (29)

1. A spinal stabilization device comprising: a first bone anchoring element for anchoring into a vertebra, the first bone anchoring element having a first end seat; a second bone anchoring element for anchoring into a vertebra, the second bone anchoring element having a second end seat; and a connecting member configured to connect the first bone anchoring element to the second bone anchoring element by being received in the first and second end seats, the connecting member, The connecting parts include: a first rigid portion having a first rigid tubular body configured to connect to the first bone anchoring element; a second rigid portion having a second rigid tubular body configured to connect to the second bone anchoring element; and an elastic portion having an elastic tubular body with helical depressions arranged between the first rigid portion and the second rigid portion, wherein, The spinal stabilization device also includes a spacer support for replacing an intervertebral disc or vertebra adjacent to the connecting member, the spacer support having a tubular body with a resilient section with helical depressions. 2. The spinal stabilization device according to claim 1, wherein at least a part of said spinal stabilization device is integrally made of one material. 3. Spinal stabilization device according to claim 1 or 2, characterized in that the area forming the helical depression acts as a compression or tension zone, a torsion zone and/or as a connecting joint. 4. The spinal stabilization device according to claim 3, wherein the area forming the spiral depression is integrally connected with other areas of the spinal stabilization device. 5. The spinal stabilization device according to claim 1 or 2, characterized in that said spinal stabilization device comprises at least one biocompatible material, said biocompatible material being rigid. 6. The spinal stabilization device according to claim 5, wherein the biocompatible material is a material with bending rigidity under specific application conditions. 7. The spinal stabilization device according to claim 5, wherein the biocompatible material is selected from the group consisting of titanium and its alloys, and plastic. 8. The spinal stabilization device according to claim 1 or 2, characterized in that the helical depression is formed as an opening in the wall and/or as a groove-like depression. 9. The spinal stabilization device according to claim 1 or 2, wherein the two helical depressions are formed as groove-shaped depressions and/or openings that are embedded in each other and arranged in parallel in pairs . 10. The spinal stabilization device according to claim 1 or 2, characterized in that the spinal stabilization device comprises a part made of elastic material, which is used together with a part with helical depressions to obtain elasticity, so that the whole The final stiffness or mobility of the spinal stabilization device is determined. 11. The spinal stabilization device according to claim 10, wherein the elastic material is an elastomer. 12. The spinal stabilization device according to claim 1 or 2, characterized in that the spacer support (10) has spacer support and weight transfer functions as primary functions, and/or the connecting part has support and connection functions as the primary function. 13. The spinal stabilization device according to claim 1 or 2, characterized in that, the end of the tubular body has a connecting device (2) for connecting with an adjacent body part or other spinal stabilization device parts, and the The helical depressions on the tubular body make the spinal stabilization device axially compressible and stretchable and for the end connection means (2) bendable around a radial axis of rotation (13) and twistable around an axial axis of rotation . 14. Spinal stabilization device according to claim 13, characterized in that the tubular body is surrounded by a sleeve made of a biocompatible elastic material and/or has a core made of a biocompatible elastic material . 15. The spinal stabilization device according to claim 14, characterized in that the sleeve and/or core are fixed by end plates integrally or detachably arranged on the tubular body. 16. The spinal stabilization device according to claim 15, wherein the sleeve and/or core are fixed by end plates detachably connected to the tubular body by screws or threads. 17. The spinal stabilization device according to claim 14 or 15, wherein the elastic material is an elastomer. 18. The spinal stabilization device according to claim 1 or 2, characterized in that, the spacer support and/or the connecting member, in terms of its longitudinal direction, can be elastically stretched or elastically compressed by 0.5% to 20% . 19. The spinal stabilization device according to claim 18, characterized in that, the spacer support and/or the connecting part can be elastically stretched or elastically compressed by 1% to 15% with respect to its longitudinal direction. 20. The spinal stabilization device according to claim 1 or 2, wherein the tubular body is elastically stretchable or elastically compressible by 0.5% to 20% in its longitudinal direction. 21. The spinal stabilization device according to claim 20, wherein the tubular body is elastically stretchable or elastically compressible by 1% to 15% in its longitudinal direction. 22. The spinal stabilization device according to claim 1 or 2, characterized in that, the spacer support and/or the connecting part can be elastically bent on the radial axis, so that the end of the tubular body for The connection means (2) to the adjacent body part or other spinal stabilization device part can be deflected by 0.5° to 10° relative to the longitudinal axis (12) of the tubular body. 23. The spinal stabilization device according to claim 22, characterized in that, the spacer support and/or the connecting part can be elastically bent on the radial axis, so that the end part of the tubular body is used to communicate with the corresponding The connection means (2) to which adjacent body parts or other spinal stabilization device parts are connected can be deflected by 1° to 6° relative to the longitudinal axis (12) of the tubular body. 24. The spinal stabilization device according to claim 1 or 2, characterized in that the tubular body can be elastically bent on the radial axis, so that the end of the tubular body is used to communicate with adjacent body parts or other The connection means (2) to which the spinal stabilization device parts are connected can be deflected by 0.5° to 10° relative to the longitudinal axis (12) of the tubular body. 25. The spinal stabilization device according to claim 24, wherein the tubular body can be elastically bent on the radial axis, so that the end of the tubular body is used for stabilizing the adjacent body part or other spine. The connection means (2) to which the device parts are connected can be deflected by 1° to 6° relative to the longitudinal axis (12) of the tubular body. 26. The spinal stabilization device according to claim 1 or 2, characterized in that the spacer support and/or the connecting part can be twisted around its axial axis by 0.5° to 10°. 27. The spinal stabilization device according to claim 26, characterized in that the spacer support and/or the connection part can be twisted about its axial axis by 1° to 6°. 28. The spinal stabilization device according to claim 1 or 2, wherein the tubular body can be twisted about its axial axis by 0.5° to 10°. 29. The spinal stabilization device according to claim 28, wherein the tubular body is rotatable about its axial axis by 1° to 6°.

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