HK1221893B - Spine stabilization device - Google Patents

Description

FIELD OF THE INVENTION

The invention relates to a spine stabilization device used in spinal surgery as a spacer in place of a degenerated or injured intervertebral disc between two adjacent vertebral bodies for permanent fusion of two vertebrae. The invention further relates to kits of instruments for implantation of the spine stabilization device, and to methods of implanting the device.

BACKGROUND OF THE INVENTION

In the prior art, such implant systems which function as spacers between adjacent vertebral bodies to be fused and replace injured or degenerated intervertebral discs are known:

• US 7,077,864 describes an example of a vertebral interbody cage that can be implanted from an anterior, posterior, anteriolateral or lateral position. A cage is an example of a vertebral interbody spacer and spine stabilizer. The cage is filled with bone graft or bone growth promoting material, which promotes the fusion of the vertebrae for long term stability. Advantageously, three screws are used for fixation of the cage, wherein one screw projects at one angle up or down and the other two screws are angled so as to splay in opposite directions. Preferably, the screws are to be inserted through the anterior wall of the cage and through the endplates of hard cortical bone into the softer, more cancellous portion of the bone of the adjacent upper and lower vertebral body to fix the relative position of the cage and vertebral bodies. Furthermore, precautions are necessary to fix the screws in the anterior wall of the spacer or cage in such a way that the screw heads do not protrude outwards of the anterior wall of the cage and that the screws cannot loosen to avoid damaging the major blood vessels that run along the anterior portion of the spine.

Similarly, US 7,232,464 teaches an intervertebral spacer implant with a three-dimensional structure with several boreholes designed to receive screws or other elongate affixation means which can be rigidly connected to the intervertebral implant and are anchored in the adjacent vertebral bodies through penetration of either the inferior or the superior or both of the endplates. The affixation means are typically guided at an angle deviating more than 25°, preferably 35°-55° from the median plane. Such an arrangement of the affixation means ensures anchoring in the compact cortical bone of the endplates of the adjacent vertebral bodies. Again special measures are taken such that the affixation means neither loosen nor protrude, in order to avoid damaging of the major blood vessels.

The fixation of these and other interbody spacers to the vertebral bodies relies on the penetration of the cortical bone of the endplate. Thus the exact placement and angular guiding of the screws is critical. Driving the fixation means through the endplates may weaken the cortical bone of the endplates, compromising the stability of the vertebral bodies. This may be problematic if the bone quality is already weakened by degenerative osteoporosis or traumatic injury or if multiple attempts for the fixation are required during the surgical procedure. Furthermore, during spine surgery access to apply instruments is often limited and it may be difficult to drive affixation means into the vertebral bodies at such pronounced angles required to drive the fixation means from the frontal or a lateral side wall of the intervertebral spacer implant through the endplates of the vertebral bodies.

US 7,255,698 discloses devices for stabilizing vertebral bodies, which devices include an interbody spinal fusion implant and spinal fixation devices secured by a screw to the interbody spinal fusion implant so that loosening of the device is prevented. The spinal fixation devices have a length exceeding the distance between the two adjacent vertebral bodies and are engaged in both vertebral bodies by means of screws or ratchet like structures.

Also in this system, measures have to be taken so that the screw heads do not protrude outwards of the anterior wall of the cage and that the screws cannot loosen to avoid damaging the major blood vessels that run along the anterior portion of the spine. A further potential problem lies in the engagement between the spinal fixation devices and the vertebral bodies. Especially in the case of already weakened bone the fastening primarily relies on a mechanic engagement between a screw or staple with ratcheted structures on the one hand and a relatively thin layer of anterior cortical bone on the other hand. Constant mechanical wear may damage the bone tissue in a vicinity of the screw or staple projection, and this may result in a loosening of the screw or staple.

DE 103 23 363 , US 2006/0178745 , US 7,060,079 and US 2006/0136061 all disclose intervertebral disk implants that are designed for maintaining and improving the mobility of the spinal column. The implants are secured to the intervertebral bodies by means of elements that are pushed into grooves along the cranial and caudal end surfaces of the implants.

SUMMARY OF THE INVENTION

It is the objective of the invention to overcome the disadvantages of intervertebral implants according to the state of the art.

This object is achieved by the invention as defined in the claims.

The upper and lower vertebra may be neighboring vertebra. Then, the interbody spacer may replace the intervertebral disc and may serve as spinal fusion implant or may serve as intervertabral disc prosthesis restoring the function of an intervertebral disc. The concepts of the invention are also suited for multi-segment fusion, i.e. the replacement of a plurality of intervertebral discs. Most embodiments of the invention feature the advantage of a small constructional height, and this makes them especially suited for multi-segment fusion.

Alternatively, a vertebra may be at least partially removed, together with the adjacent intervertebral discs. Then, the interbody spacer replaces the vertebral body of the at least partially removed vertebra as well as the removed intervertebral discs, and the upper and lower vertebra are not initially neighboring vertebra but vertebra neighboring the removed vertebra.

Also, the fixation device for the interbody spacer (or the anchoring devices) may be the only fixation device(s) or may be adjuvant fixation devices used in addition to other fixation devices, for example according to the state of the art. Such other fixation devices may for example be pedicle screws to be introduced from a posterior side.

In this text, often the dorsal and ventral directions are referred to as posterior and anterior directions following the convention that is applicable for humans; this does not exclude the application of the devices and methods taught herein also for veterinary purposes; in this case "anterior" is generally to be replaced by "ventral", "posterior" by "dorsal". Also, terms like "upper", "lower", "above", "below", "top", "bottom" are used in this text, and this does not exclude the application of the devices and methods for spine segments that are, in a normal position, not vertical. Generally, "upper" and "above" etc. refer to more cranial positions, "below" or "lower" to more caudal positions.

The interbody spacer is a three dimensional body with a top surface to be oriented towards - and for example contacting - the lower endplate of the vertebral body above and with a bottom surface to be oriented towards - and for example contacting - the upper endplate of the vertebral body below the spacer, and with a circumferential surface that may comprise a front, back and side walls in anterior, posterior and lateral orientations to the spinal column. The top and the bottom surface of the spacer may be essentially parallel. In other embodiments, they are tilted slightly towards each other such that the dorsal portion of the circumferential surface is less high than the ventral wall portion of the circumferential surface, and the spacer forms a flat wedge imitating the anatomical form of an intervertebral disc (or of a vertebral body with intervertebral discs).

While in most embodiments, especially for anterior or anteriolateral or lateral implantation, the interbody spacer is of one piece, it may in special embodiments also comprise a plurality of pieces, especially for implantation from a dorsal side.

The median plane of the implanted intervertebral spacer runs approximately (not accounting for the optional slight taper) parallel to the adjacent endplates of the vertebral bodies above and below. In the context of this application the orientation of the median plane is sometimes referred to as "horizontal" while "vertical" always refers to an orientation essentially parallel with respect to the longitudinal (craniocaudal) extension of the spine in the region of the spine where two vertebral bodies need to be fused in a particular case.

For example, the interbody spacer is made from a plastic material such as PEEK (Polyetheretherketone) or of Titanium, but other biocompatible materials are possible also, including other plastics, other metals, and ceramics. In some embodiments a surface coating of Hydroxilapatite (HA) is applied enhancing the osseointegrative properties of the interbody spacer and therefore promote longterm stability.

The interbody spacer may furthermore be shaped to comprise further structural elements such as recesses, bores, indentations, bulges and other three dimensional structures, which modify the properties of the spacer and/or which accommodate corresponding structures of the at least one fixation device or anchoring device. Furthermore the material of the interbody spacer does not have to be uniform: it may be composed of more than one material components, and/or it may contain filler materials like stabilizing fibers etc.

Referring to the anchoring devices, each of the first and second securing portions may protrude, on the distal side, further than the bridge portion. The first and optionally the second securing portions may comprise material liquefiable by thermal energy (e.g. friction heat created by mechanical oscillation or absorption heat created by absorption of electromagnetic radiation preferably of the visible or infrared frequency range), so that the first securing portion is equipped for being anchored in bone tissue with the aid of e.g. mechanical oscillation or electromagnetic radiation, and optionally the second securing portion is equipped for being anchored in the same manner in the structures.

The device according to the invention is an improvement over the device shown in Figures 26-29 of WO 2008/034 276 . More concretely, the first and second securing portions each function as an anchor anchored in the bone tissue and in the interbody spacer, respectively. The anchoring in these two elements takes place simultaneously by the joint action of e.g. mechanical vibration or electromagnetic radiation coupled into the anchoring device and a pressing force pressing it towards the distal direction (corresponding to the posterior direction). Due to the bridge portion, the anchoring device then forms a solid connection between the bone tissue and the interbody spacer.

Preferably, a total of four anchoring devices are provided, two for the top surface and two for the bottom surface.

Mechanical vibration or oscillation suitable for a method of implanting a device according to embodiments of the invention that include liquefaction of a polymer by friction heat created through the mechanical vibration has preferably a frequency between 2 and 200 kHz (even more preferably between 10 and 100 kHz, or between 20 and 40 kHz) and a vibration energy of 0.2 to 40 W, especially 0.2 to 20 W or 10 W to 35 W for special applications (for example if the fastener comprises a tube element and a thermoplastic anchoring material element) per square millimeter of active surface. The vibrating element is e.g. designed such that its contact face oscillates predominantly in the direction of the element axis (longitudinal vibration) and with an amplitude of between 1 and 100 µm, preferably around 10 to 30 µm or around 20 to 40 µm for applications with a tube element. Rotative or radial oscillation is possible also.

For specific embodiments of the spine stabilization device it is possible also to use, instead of mechanical vibration, a rotational movement for creating the named friction heat needed for the liquefaction of the anchoring material. Such rotational movement has preferably a speed in the range of 10'000 to 100'000 rpm. A further way for producing the thermal energy for the desired liquefaction comprises coupling electromagnetic radiation into one of the device parts to be implanted and designing one of the device parts to be capable of absorbing the electromagnetic radiation, wherein such absorption preferably takes place within the anchoring material to be liquefied or in the immediate vicinity thereof. Preferably electromagnetic radiation in the visible or infrared frequency range is used, wherein the preferred radiation source is a corresponding laser. Electric heating of one of the device parts may also be possible.

While the principles of the invention are primarily described referring to a spine stabilization device with an interbody spacer and a fixation device, where the interbody spacer is assumed to be dimensionally stable, the approach of the first, second, and third aspects as well as advantageous features and embodiments thereof can also be used for other configurations.

A group of such alternative configurations are configurations with an interspineous spacer. Such an interspineous spacer is inserted between the posterior spineous processes. Interspinous spacers are known in the art. The concept of the second group of alternative configurations proposes to use the fastening technology with one or more fixation devices to the spinal column, especially the spinal processi.

In this group of such alternative configurations, the teaching relating to an 'interbody spacer' in the above-discussed and hereinafter further described embodiments is to be replaced by yet an other kind of implant, namely an interspineous spacer, and instead of in the vertebral bodies, anchoring occurs preferably in the spinal processi.

In this text the expression "thermoplastic material being liquefiable e.g. by mechanical vibration" or in short "liquefiable thermoplastic material" or "liquefiable material" is used for describing a material comprising at least one thermoplastic component, which material becomes liquid or flowable when heated, in particular when heated through friction i.e. when arranged at one of a pair of surfaces (contact faces) being in contact with each other and vibrationally or rotationally moved relative to each other, wherein the frequency of the vibration is between 2 kHz and 200 kHz, preferably 20 to 40 kHz and the amplitude between 1 µm and 100 µm, preferably around 10 to 30 µm (or around 20 to 40 µm). Such vibrations are e.g. produced by ultrasonic devices as e.g. known for dental applications. For being able to constitute a load-bearing connection to the tissue, the material has an elasticity coefficient of more than 0.5 GPa, preferably more than 1 GPa and a plastification temperature of up to 200°C, of between 200°C and 300°C or of even more than 300°C. In applications where the anchoring material is provided in a supporting, load bearing structure, especially a tube element of the hereinbefore-discussed kind, the elasticity coefficient (especially Young's Modulus) may also be lower than 0.5 GPa, for example 0.08 GPa or more, especially at least 0.1 GPa, for example between 0.1 GPa and 2 GPa. In such applications, the where the anchoring material is provided in a supporting, load bearing structure, the anchoring material may optionally be entirely liquefied during the anchoring process (and not only in regions close to the surface) and thus does not necessarily have to transmit vibrations to the periphery. An example of an anchoring material suitable for such applications are thermoplastic elastomers. A specific example is a thermoplastic polyurethane elastiomers, for example pellethane® by Dow Chemicals.

Depending on the application, the liquefiable thermoplastic material may or may not be resorbable.Suitable resorbable polymers are e.g. based on lactic acid and/or glycolic acid (PLA, PLLA, PGA, PLGA etc.) or polyhydroxyalkanoates (PHA), polycaprolactones (PCL), polysaccharides, polydioxanones (PD), polyanhydrides, polypeptides or corresponding copolymers or blended polymers or composite materials containing the mentioned polymers as components are suitable as resorbable liquefiable materials. Thermoplastics such as for example polyolefins, polyacrylates, polymetacrylates, polycarbonates, polyamides, polyesters, polyurethanes, polysulphones, polyaryl ketones, polyimides, polyphenyl sulphides or liquid crystal polymers (LCPS), polyacetals, halogenated polymers, in particular halogenated polyoelefins, polyphenylene sulphides, polysulphones, polyethers, polypropylene (PP), or corresponding copolymers or blended polymers or composite materials containing the mentioned polymers as components are suitable as non-resorbable polymers.

Specific embodiments of degradable materials are Polylactides like LR706 PLDLLA 70/30, R208 PLDLA 50/50, L210S, and PLLA 100% L, all of Böhringer. A list of suitable degradable polymer materials can also be found in: Erich Wintermantel und Suk-Woo Haa, "Medizinaltechnik mit biokompatiblen Materialien und Verfahren", 3. Auflage, Springer, Berlin 2002 (in the following referred to as "Wintermantel"), page 200; for information on PGA and PLA see pages 202 ff., on PCL see page 207, on PHB/PHV copolymers page 206; on polydioxanone PDS page 209. Discussion of a further bioresorbable material can for example be found in CA Bailey et al., J Hand Surg [Br] 2006 Apr;31(2):208-12.

Specific embodiments of non-degradable materials are: Polyetherketone (PEEK Optima, Grades 450 and 150, Invibio Ltd), Polyetherimide, Polyamide 12, Polyamide 11, Polyamide 6, Polyamide 66, Polycarbonate, Polymethylmethacrylate, Polyoxymethylene. An overview table of polymers and applications is listed in Wintermantel, page 150; specific examples can be found in Wintermantel page 161 ff. (PE, Hostalen Gur 812, Höchst AG), pages 164 ff. (PET) 169ff. (PA, namely PA 6 and PA 66), 171 ff. (PTFE), 173 ff. (PMMA), 180 (PUR, see table), 186 ff. (PEEK), 189 ff. (PSU), 191 ff. (POM - Polyacetal, tradenames Delrin, Tenac, has also been used in endoprostheses by Protec).

Examples of suited thermoplastic material include polylactides such as any one of the products LR708 (amorphous Poly-L-DL lactide 70/30), L209 or L210S by Böhringer Ingelheim or polycarbonates.

The liquefiable material having thermoplastic properties may contain foreign phases or compounds serving further functions. In particular, the thermoplastic material may be strengthened by admixed fillers, for example particulate fillers that may have a therapeutic or other desired effect. The thermoplastic material may also contain components which expand or dissolve (create pores) in situ (e.g. polyesters, polysaccharides, hydrogels, sodium phosphates) or compounds to be released in situ and having a therapeutic effect, e.g. promotion of healing and regeneration (e.g. growth factors, antibiotics, inflammation inhibitors or buffers such as sodium phosphate or calcium carbonate against adverse effects of acidic decomposition). If the thermoplastic material is resorbable, release of such compounds is delayed.

If the liquefiable material is to be liquefied not with the aid of vibrational energy but with the aid of electromagnetic radiation, it may locally contain compounds (particlulate or molecular) which are capable of absorbing such radiation of a specific frequency range (in particular of the visible or infrared frequency range), e.g. calcium phosphates, calcium carbonates, sodium phosphates, titanium oxide, mica, saturated fatty acids, polysaccharides, glucose or mixtures thereof.

Fillers used may include degradable, osseostimulative fillers to be used in degradable polymers, including: β-Tricalciumphosphate (TCP), Hydroxyapatite (HA, < 90% crystallinity; or mixtures of TCP, HA, DHCP, Bioglasses (see Wintermantel). Osseo-integration stimulating fillers that are only partially or hardly degradable, for non degradable polymers include: Bioglasses, Hydroxyapatite (>90% cristallinity), HAPEX® , see SM Rea et al., J Mater Sci Mater Med. 2004 Sept;15(9):997-1005; for hydroxyapatite see also L. Fang et al., Biomaterials 2006 Jul; 27(20):3701-7, M. Huang et al., J Mater Sci Mater Med 2003 Jul;14(7):655-60, and W. Bonfield and E. Tanner, Materials World 1997 Jan; 5 no. 1:18-20. Embodiments of bioactive fillers and their discussion can for example be found in X. Huang and X. Miao, J Biomater App. 2007 Apr; 21(4):351-74), JA Juhasz et al. Biomaterials, 2004 Mar; 25(6):949-55. Particulate filler types include: coarse type: 5-20µm (contents, preferentially 10-25% by volume), sub-micron (nanofillers as from precipitation, preferentially plate like aspect ratio > 10, 10-50 nm, contents 0.5 to 5% by volume).

More generally liquefaction in these embodiments is achieved by using materials with thermoplastic properties having a melting temperature of up to about 350°C. If a liquefaction interface or one of a plurality of liquefaction interfaces is situated between a device part comprising the liquefiable material and a counter element, the modulus of elasticity of the liquefiable material should be at least 0.5 GPa so that the liquefiable material is capable of transmitting the ultrasonic oscillation with such little damping that inner liquefaction and thus destabilization of the named device part does not occur, i.e. liquefaction occurs only where the liquefiable material is at the liquefaction interface. If only the interface to the oscillation tool serves as the liquefaction interface, the material may in principle also have a lower modulus of elasticity. However, for some applications, due to the load bearing function the material has, also in this situation, a preferred modulus of elasticity of at least 0.5 GPa. As discussed hereinbefore, the modulus of elasticity may be lower than 0.5 GPa if the applications where the anchoring material is provided with an additioinal supporting, load bearing structure, such as a tube structure.

The teaching of the present text also concerns method of implanting a spine stabilization device, and kits of parts that include a spine stabilization device and further includes instruments for their implantation, as described in more detail referring to some of the drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

In the following, embodiments of the invention are described with reference to drawings. The drawings are all schematic and not to scale. In the drawings, same reference numerals denote same or analogous elements. The drawings show:

• Figs. 1-3 an embodiment of the invention;
• Fig. 4 the principle of guiding the anchoring material element by means of e.g. a sonotrode;
• Fig. 5 an alternative embodiment of an anchoring device for a device according to the third aspect of the invention.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

Figures 1-3 show embodiments of the invention. The embodiments of Figures 1-3 include anchoring devices e.g. of the kind described in WO 2008/034 276 . In addition to the embodiments described in WO 2008/034 276 , the anchoring devices of this aspect of the invention, however, comprises a first and a second securing portion each approximately pin-shaped in the depicted embodiment, and the two securing portions connected by a bridge portion that protrudes, on the distal side, less far than the securing portions.

The teaching that holds for devices of the kind illustrated in Figures 1-3 may be used for example for fixing respective upper and lower plate elements (retaining elements) of an intervertebral disc prosthesis.

Figure 1 depicts an embodiment of a spine stabilization device according this aspect inserted in a human spine. Fig. 1 shows an upper vertebra 1 and a lower vertebra 2, between which the intervertebral disc has been at least partly removed. The device of the embodiment described here also comprises an interbody spacer 3, serving as a distance holder, between the vertebral body of the upper vertebra and the lower vertebra. The interbody spacer after the surgical insertion between the vertebral bodies is held in place by a plurality of anchoring devices 121.

Figure 2 shows the interbody spacer 3. The interbody spacer 3 may again be made of any suitable material including PEEK, potentially coated by Hydroxylapatite (HA). It may alternatively be made of a different biocompatible material suitable for an intervetebral, such as an other plastics, a ceramics, or Titanium, also potentially coated.

The interbody spacer 3 comprises a top surface 11 and an opposite bottom surface for being in contact with the lower endplate of the upper vertebral body and the upper endplate of the lower vertebral body, respectively. The interbody spacer further comprises a longitudinal (relating to the spine axis) through opening 12 permitting bone growth between the upper and lower vertebral bodies and optionally being filled, when inserted surgically, by bone graft and/or bone growth promoting material.

In the depicted configuration, the interbody spacer comprises one through opening that is centrally located with respect to the sagittal plane. However, other numbers and arrangements of openings are possible. For example, it would also be possible to have two or more, possibly smaller, central through openings, or one opening or a plurality of openings more on a lateral position, or no opening at all etc.

Further, the interbody spacer 3 may be shaped according to the surgeon's needs and comprise retention structures and/or bone ingrowth macroscopic and/or microscopic structures such as the holes 13 perpendicular to the longitudinal axis depicted in the figure, channels etc.

The interbody spacer comprises four channel-like recesses 123 that are open both, to the ventral side, as well as to the upper or lower side. At least in vicinity to the recesses, the interbody spacer further comprises an open porous structure, with preferably macroscopic pores, that may be interpenetrated by anchoring material in a liquid state. This results in a macro form fit connection. Instead of an open porous structure, also a structure with a single cavity (or very few cavities) with an undercut may be present, so that the resulting macro form fit connection is a rivet-kind connection.

The anchoring device as depicted in Figure 3 consists of a thermoplastic material liquefiable e.g. by the joint action of mechanical oscillation and a pressing force, such as a polylactic acid (PLA). It comprises an upper and a lower securing portion 127 as well as a bridge portion 128 between the anchoring portions. The securing portions 127 are pin-shaped with energy directors 129. Each securing portion has a tip piece 125 protruding, on the distal side, preferably further than the bridge portion.

In the anchoring process, one of the securing portions 127 is inserted into a recess 123 of the interbody spacer 3, while the other securing portion is inserted into a pre-drilled recess in the vertebral body adjacent to the recess 123. To that end, both, the recess 123 in the interbody spacer 3 and the recess in the bone tissue are configured to have a diameter that is smaller than an outer diameter of the respective securing portion 127. When being inserted into the space comprising the recesses 123 in the interbody spacer and in the vertebral body, the thermoplastic material of the securing portions due to the effect of e.g. the mechanical vibrations coupled into the anchoring device starts being liquefied and interpenetrates the open porous structure of the interbody spacer and the tissue of the vertebral body, respectively. The bridge portion after the anchoring process couples, due to the arising positive-fit connections of the securing portions with the open porous structure and with the bone tissue, the interbody spacer and the vertebral body to each other. If the anchoring devices 121 are chosen to be of a resorbable material, after resorption there will be ingrowth of bone tissue into the recess 123 in the interbody spacer and into the open porous structure 124.

As previously mentioned for other embodiments of the spinal stabilization device according to the invention it is possible for the embodiment as illustrated in Figs. 25 to 27 also to achieve liquefaction of the anchoring material comprised by the securing portions 127 by coupling electromagnetic radiation preferably of the visible or infrared frequency range into the securing portions 127 and to absorb the radiation in the vicinity of surfaces of the securing portions which are in contact with the bone tissue of the vertebral body or with the interbody spacer to there produce the thermal energy needed for the desired liquefaction.

Figure 5 shows an embodiment of an anchoring device that is of a hybrid kind, i.e. that comprises, in addition to the portions of liquefiable material, also portions of non-liquefiable material. More concretely, the anchoring device 121 comprises a metallic core 161 constituting the bridge portion 128 and a core of the two securing portions 127, and, for each securing portion, an outer part 162 consisting of liquefiable material.

Figure 4 illustrates an anchoring material element 31 for embodiments not according to the claimed invention, mounted on a sonotrode 67 having a sonotrode tip 151. The sonotrode tip is provided with retaining structures (such as a thread) for a fixed coupling with the anchoring material element; it is also possible that the anchoring material element is held just by frictional force. In embodiments where the anchoring structure includes an elongate cavity accessible from anterior, the length of the sonotrode tip 151 is preferably less than the length of the elongate cavity, so that the proximal end of the sontorode tip also defines a stop for the anchoring process.

The sonotrode tip 151 has a guiding effect on the anchoring material element, and this has shown to provide advantageous results in many configurations.

An analog guiding mechanism with a double sonotrode tip (not shown) may be used for embodiments of the invention.

Various further embodiments may be envisaged without departing form the scope and spirit of the invention. For example, while the figures for illustration purposes generally show lumbar vertebrae, the invention may also be applied to all other vertebrae, especially including cervical, and thoracic vertebrae.

The anchoring process in the embodiments in which liquefaction of polymeric material is included may be done manually, or at least partially automated. For the latter, the skilled person is for example referred to the teaching of US2009 018471 or WO 2011/054123 .

While all figures that show the spine stabilization device in a state inserted in the spine relate to a spinal fusion implant replacing an intervertebral disc, the teaching of all figures may also be used for the situation where an entire vertebra and the adjacent vertebral disc is replaced. Further, embodiments of the invention that do not require a dimensionally stiff interbody spacer may be used also for intervertebral disc prostheses.

Claims (10)

1. A spine stabilization device, comprising:

   - An interbody spacer (3) shaped to be inserted between a vertebral body (1) of an upper vertebra and a vertebral body (2) of a lower vertebra, and comprising a top surface (11) oriented towards the lower endplate of the vertebral body of the upper vertebra and a bottom surface oriented towards the upper endplate of the vertebral body of the lower vertebra;

   - the interbody spacer comprising at least one channel-like recess (123) reaching to an end in the top surface and at least one channel-like recess (123) reaching to an end in the bottom surface, and comprising in a region of these recesses a structure (124) that includes an undercut, whereby it is suitable for making a positive-fit connection together with an anchoring device (121),

   - for every channel-like recess an anchoring device (121), the anchoring devices comprising a proximal end and a distal end, a first securing portion (127), a second securing portion (127) and a bridge portion (128) between the first and second securing portions

   characterized in that the interbody spacer (3) comprises a through opening (12) arranged longitudinally relating to a spine axis.
2. The spine stabilization device according to claim 1, wherein the end in the top surface and the end in the bottom surface are anterior ends.
3. The spine stabilization device according to claim 1 or 2, wherein each of the first and second securing portions (127) protrudes, on the distal side further than the bridge portion (128).
4. The spine stabilization device according to any one of claims 1-3, wherein the first securing portion (127) comprises a liquefiable, whereby the first securing portion is equipped for being anchored in bone tissue by the liquefiable material being liquefied, made to penetrate into and re-solidify in the bone tissue.
5. The spine stabilization device according to claim 4, wherein both, the first and second securing portions (127) comprise liquefiable material, whereby the second securing portion is equipped for being anchored in the structure, for making the positive-fit connection, by the liquefiable material being liquefied, made to penetrate into and re-solidify in the structure (124).
6. The spine stabilization device according to any one of claims 1-5, comprising a total of four anchoring devices (121) and an according number of channel-like recesses (123), two in the top surface and two in the bottom surface.
7. The spine stabilization device according to any one of claims 1-6, wherein the interbody spacer (3) is made of PEEK.
8. The spine stabilization device according to any one of claims 1-7, wherein the interbody spacer (3) comprises retention structures.
9. The spine stabilization device according to any one of claims 1-8, wherein the structure (124) comprises an open porous structure at least in a vicinity of the channel-like recesses (123).
10. The spine stabilization device according to any one of claims 1-8, wherein the channel-like recesses (123) form a single cavity with an undercut.