WO2000032125A1 - Schraube - Google Patents
Schraube Download PDFInfo
- Publication number
- WO2000032125A1 WO2000032125A1 PCT/CH1998/000504 CH9800504W WO0032125A1 WO 2000032125 A1 WO2000032125 A1 WO 2000032125A1 CH 9800504 W CH9800504 W CH 9800504W WO 0032125 A1 WO0032125 A1 WO 0032125A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- thread
- screw according
- core
- section
- screw
- Prior art date
Links
- 230000007704 transition Effects 0.000 claims description 11
- 210000000988 bone and bone Anatomy 0.000 abstract description 36
- 238000005452 bending Methods 0.000 abstract description 4
- 238000004873 anchoring Methods 0.000 description 5
- 230000000694 effects Effects 0.000 description 4
- 230000035515 penetration Effects 0.000 description 3
- 238000011161 development Methods 0.000 description 2
- 230000018109 developmental process Effects 0.000 description 2
- 239000002360 explosive Substances 0.000 description 2
- 230000007774 longterm Effects 0.000 description 2
- 230000008719 thickening Effects 0.000 description 2
- 208000010392 Bone Fractures Diseases 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 210000002449 bone cell Anatomy 0.000 description 1
- 210000000078 claw Anatomy 0.000 description 1
- 230000001427 coherent effect Effects 0.000 description 1
- 238000006073 displacement reaction Methods 0.000 description 1
- 238000005553 drilling Methods 0.000 description 1
- 230000003993 interaction Effects 0.000 description 1
- 230000000284 resting effect Effects 0.000 description 1
- 210000004872 soft tissue Anatomy 0.000 description 1
- 230000008093 supporting effect Effects 0.000 description 1
- 230000000472 traumatic effect Effects 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/84—Fasteners therefor or fasteners being internal fixation devices
- A61B17/86—Pins or screws or threaded wires; nuts therefor
- A61B17/8625—Shanks, i.e. parts contacting bone tissue
- A61B17/8635—Tips of screws
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/84—Fasteners therefor or fasteners being internal fixation devices
- A61B17/86—Pins or screws or threaded wires; nuts therefor
- A61B17/8625—Shanks, i.e. parts contacting bone tissue
- A61B17/863—Shanks, i.e. parts contacting bone tissue with thread interrupted or changing its form along shank, other than constant taper
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/70—Spinal positioners or stabilisers ; Bone stabilisers comprising fluid filler in an implant
- A61B17/7001—Screws or hooks combined with longitudinal elements which do not contact vertebrae
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
- F16B—DEVICES FOR FASTENING OR SECURING CONSTRUCTIONAL ELEMENTS OR MACHINE PARTS TOGETHER, e.g. NAILS, BOLTS, CIRCLIPS, CLAMPS, CLIPS OR WEDGES; JOINTS OR JOINTING
- F16B25/00—Screws that cut thread in the body into which they are screwed, e.g. wood screws
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
- F16B—DEVICES FOR FASTENING OR SECURING CONSTRUCTIONAL ELEMENTS OR MACHINE PARTS TOGETHER, e.g. NAILS, BOLTS, CIRCLIPS, CLAMPS, CLIPS OR WEDGES; JOINTS OR JOINTING
- F16B33/00—Features common to bolt and nut
- F16B33/02—Shape of thread; Special thread-forms
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
- F16B—DEVICES FOR FASTENING OR SECURING CONSTRUCTIONAL ELEMENTS OR MACHINE PARTS TOGETHER, e.g. NAILS, BOLTS, CIRCLIPS, CLAMPS, CLIPS OR WEDGES; JOINTS OR JOINTING
- F16B35/00—Screw-bolts; Stay-bolts; Screw-threaded studs; Screws; Set screws
- F16B35/04—Screw-bolts; Stay-bolts; Screw-threaded studs; Screws; Set screws with specially-shaped head or shaft in order to fix the bolt on or in an object
- F16B35/041—Specially-shaped shafts
Definitions
- the invention relates to a screw according to the preamble of patent claim 1.
- Such screws are used in particular in rod or plate systems for the dorsal fixation of instabilities in the spine.
- These systems generally consist of a side member and anchoring elements that can be attached to it.
- the anchoring elements are either hooks or screws passed through the pedicles, so-called pedicle screws.
- pedicle screws The advantage of pedicle screws over hooks is their intrinsic stability in the bone.
- a pedicle screw can be differentiated between an upper part (head) used for connection to the longitudinal beam and a lower part (shaft) to be anchored in the bone.
- the formation of the lower part anchored in the bone plays a very important role with regard to the short-term and long-term stability of the fixation.
- the short-term stability is of a purely mechanical nature, while the long-term stability is strongly influenced by the interaction of mechanics and biology at the interface (interface) between bone and screw and the fatigue strength of the pedicle screw itself.
- Pedicle screws are mainly subjected to bending and tension. Excessive bending stress can lead to a "traumatic" or “biological” cutting of the pedicle screw in the bone and / or breaking of the pedicle screw itself. Breaking a pedicle screw is always a mechanical failure due to fatigue. Excessive tensile loads only endanger the bone / screw interface and not the screw itself.
- both the core and the thread are circular cylindrical.
- this shape has the highest pull-out strength.
- the pull-out strength is hardly influenced.
- this form has the following disadvantages compared to the other screw types:
- both the core and the thread are conical.
- the advantage of this type of screw is that it grips and tightens in the bone.
- a disadvantage of this type is the potential for cutting through the relatively soft, cancellous bone of the vertebral body. Furthermore, the screw must not be turned back without risking loosening.
- screws of the 1st type which have two circular cylindrical shank sections with different core and outside diameters, which are connected by a conical transition part.
- the front part is threadless.
- a disadvantage of this known bone screw is that the screw, due to the thread-free front part, does not fit well into the bone without good pre-drilling and high axial pressure. In the case of brittle, skierotic bone, it can even happen that the screwing resistance becomes so great that the screw thread is torn out when trying to drive the screw through the skierotic zone.
- the invention seeks to remedy this.
- the invention has for its object to provide a screw which has an improved pull-out, cutting and bending strength and also a good, more or less independent of the bone quality gripping in the bone.
- the invention solves the problem with a screw having the features of claim 1.
- the constant outer diameter of the threaded shaft of the screw results in an optimal pull-out strength, which is of particular clinical relevance especially when used as a bone screw, in particular as a pedicle screw.
- the threaded front part of the screw which tapers towards the tip, has the following advantages over the prior art:
- the threaded front part drives the screw forward without additional axial pressure, even in brittle, skierotic bones, with minimal risk of the bone thread being torn out due to excessive screwing resistance and with minimal risk of bone fracture;
- the threaded, tapered front part centers and guides the screw in a spinal application in the pedicle and thus minimizes the risk of lateral penetration of the screw in the pedicle.
- the combination of the section having a smaller constant core diameter with the section of the central part of the screw which has a larger, also constant core diameter has the following advantages: the widening of the entry point caused by "screwing in” the screw is made larger by the enlarged core diameter of the one , constant core diameter section compensated; the good anchoring in the area of the entry point combined with a good anchoring in the area of the screw tip offers an optimal resistance to cutting through of the screw in the bone; thanks to the circular cylindrical design of the two sections with constant core diameter, the pull-out and Cutting resistance of the screw in the bone is more or less independent of turning the screw back within approx.
- the thickness of the thread tips in a larger, constant core diameter section is constant over the entire length of the section and depends on the difference in the core diameters of the two circular cylindrical sections; the greater the difference, the thicker the thread tips in the circular cylindrical section with the larger core diameter;
- the section with a conical core lying between the two cylindrical sections minimizes the explosive effect when changing from the smaller to the larger core diameter.
- This section causes an additional wedging of the screw in the bone. The wedging is drastically reduced every time the screw is turned back.
- the length of the section with a conical core is so short in Compared to the length of the two circular cylindrical sections, the influence of this section on the pull-out and cutting resistance of the screw in the bone is negligible.
- the front part tapering towards the tip is linear-conical or cambered (e.g. square, parabolic profile).
- the advantages lie in the good grasping of the thread, in the centering and guidance in the pedicle, and in a reduced risk of the bone exploding.
- a further preferred embodiment consists in that the front part has at its tip a threadless guide nose running in the direction of the central axis.
- the guide nose preferably has the same diameter as the hole to be drilled in the bone and guides the screw along the hole in the bone, so that the risk of lateral penetration of the pedicle is reduced.
- the guide lug is preferably of circular cylindrical design.
- the thread is designed as a two-start thread.
- This provides the advantage that, with the same holding force in the bone tissue, the pedicle screw performs an x-fold axial displacement along the screw axis per revolution and can therefore be screwed into the bone more quickly, as is possible with single-screw screws according to the prior art.
- the two-course Threads also have less potential for cutting through in the vertebral body because the thread flanks have a supporting effect due to the large pitch. Finally, the centering in the threaded hole is also improved.
- Fig. 2 is an enlarged partial section of the thread of the screw of FIG. 1 in the region of the tapered section of the central part.
- the screw shown in FIGS. 1 and 2 has a central axis 1, a head part 2, a central part 3 provided with a thread 6 and a front part 4 with a tip 5.
- the middle part 3 has three different sections 31, 32 and 33, the core of the section 33 being circular-cylindrical and connected to the front part 4, the core of the section 31 adjoining the head part 2 being circular-cylindrical and having a larger diameter than the core of section 33 and the core of section 32 lies between the two sections 31 and 33 and tapers towards the tip 5.
- the sections 31, 32 and 33 of the middle part 3 are continuously provided with the thread 6 and the middle part 3 carrying the continuous thread 6 has an essentially constant outside diameter D.
- the front part 4 tapers towards its tip 5 and is provided with a thread 8.
- the tip 5 has a threadless guide nose 7 running in the direction of the central axis 1 and having a circular cylindrical shape.
- the head part 2 is partially spherical in order to be able to insert the screw polyaxially.
- the head part can have usual depressions, e.g. Identify hexagonal shape to accommodate a corresponding screwing tool.
- the diameter of the screw in the transition area 9 from the central part 3 to the head part 2 increases in the direction of the head part 2, but can also be circular cylindrical.
- a thread 10 is provided in the transition area 9 from the central part 3 to the head part 2.
- the core and outer diameter of the thread 10 in the transition region 9 widens conically from the central part 3 to the head part 2.
- the thread 10 in the transition area 9 from the middle part 3 to the head part 2 and the thread 6 of the middle part 3 are coherent and have the same pitch.
- the thread 6 can be designed as a two-start thread with a pitch angle between 10 ° and 22 °, preferably between 14 ° and 18 °.
- the thread pitch is 3 to 5 mm, preferably 3.5 to 4.5 mm.
- the thread pitch and number of thread turns define the optimal size of the thread gaps, which result in a mechanically protected resting area for bone cells, which leads to improved biological anchoring.
- the thread 6 can also be designed to be catchy.
- the pitch angle of the thread 6 is between 5 ° and 18 °, preferably between 8 ° and 14 ° and the thread pitch is between 1.5 mm and 4.0 mm, preferably between 1.75 mm and 3.50 mm.
- the depth of the thread 6 in the region of the section 31 is greater than 0.2 mm and is typically 0.4 mm to 0.6 mm, preferably 0.5 mm. In an alternative embodiment, the depth of the thread 6 in the region of the section 31 is greater than 0.5 mm and is typically 0.6 to 1.0 mm, preferably 0.85 mm.
- the thread 6 of the middle part 3 continues in the front part 4.
- the front part 4 tapers advantageously towards the tip 5 in a convex (or also conical) manner.
- the convex taper runs tangentially into the core of the middle part 3 and has a radius of between 30 and 50 mm, preferably in profile between 38 and 42 mm.
- the convex taper can run tangentially into the core of the middle part 3 and be parabolic in profile.
- the thread 8 of the front part 4 and the thread 6 of the middle part 3 have the same pitch and the same number of thread turns.
- the thread 6 of the middle part 3 merges continuously into the thread 8 of the front part 4, which tapers convexly or conically towards the tip 5 (however, it can also be circular-cylindrical).
- the taper of the thread 8 of the front part 4 has a radius between 20 mm and 40 mm in profile. It can also be parabolic.
- the front part 4 expediently ends in a spherical radius between 0.5 and 3.0 mm, preferably between 1.5 and 2.0 mm.
- the core of section 32 tapers conically with a half cone angle in the range from 3 ° to 7 °.
- the core of section 31 is 15-35% larger than the core of section 33.
- the tips 11 of the thread 6 are thicker in the area of the section 31 than in the area of the section 33.
- the difference between the core diameter of the section 33 and the section 31 is designed such that the tips 11 of the thread 6 in the area of section 31 have a width B between 0.3 and 0.5 mm.
- the section 33 can in turn comprise three further sections (not shown in the drawing), which in their
- the pedicle is opened with a suitable tool, such as an awl or a drill.
- a suitable tool such as an awl or a drill.
- the diameter of the bore should be smaller than the smallest core diameter of the screw, ie section 33.
- the cambered front part 4 expands the borehole in the cancellous bone with a minimal explosive effect on the core diameter of section 33.
- the displaced cancellous bone becomes compressed in the area of the thread 6.
- the screwing in of the screw is often hindered by the soft parts.
- the lateral pressure of the soft parts can lead to an "egg" screwing in of the screw at the beginning and widen the threaded hole in the area of the entry point. As the depth of penetration increases, however, the screw stabilizes more and more.
- the sequence of the two circular cylindrical sections 33 and 31 is now coordinated with one another in such a way that the section 31 having a larger core diameter does not penetrate into the bone until the screw has been completely stabilized.
- the section 32 having a conical core expands the core diameter of the threaded hole to the core diameter of section 31. With increasing core diameter, the thickness of the threaded tip 11 increases evenly up to the area of section 31, where it is constant again.
- the section 31 is so long that it extends into the pedicle and can optimally claw in the compressed edge zone of the pedicle.
- the length of section 31 is between 10 and 30 mm, preferably 15 mm for screws up to a thread length of 45 mm and 20 mm for screws with a thread length greater than 45 mm.
- the thickness of the thread tip in the region of section 31 depends on the difference between the two core diameters of sections 33 and 31.
- the two core diameters are matched to one another such that the thickness of the thread tip is between 0.2 and 0.5 mm, preferably between 0.3 and 0.4 mm.
- the actual length compensation of the screw only takes place in section 33.
Abstract
Description
Claims
Priority Applications (12)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE59812947T DE59812947D1 (de) | 1998-11-26 | 1998-11-26 | Schraube |
EP98954103A EP1133263B1 (de) | 1998-11-26 | 1998-11-26 | Schraube |
CA002352185A CA2352185C (en) | 1998-11-26 | 1998-11-26 | Bone screw having a constant diameter thread |
JP2000584827A JP4488625B2 (ja) | 1998-11-26 | 1998-11-26 | ねじ |
ES98954103T ES2245047T3 (es) | 1998-11-26 | 1998-11-26 | Tornillo para huesos. |
DK98954103T DK1133263T3 (da) | 1998-11-26 | 1998-11-26 | Skrue |
AT98954103T ATE299672T1 (de) | 1998-11-26 | 1998-11-26 | Schraube |
AU11396/99A AU742502B2 (en) | 1998-11-26 | 1998-11-26 | Screw |
PCT/CH1998/000504 WO2000032125A1 (de) | 1998-11-26 | 1998-11-26 | Schraube |
ZA9907344A ZA997344B (en) | 1998-11-26 | 1999-11-26 | Screw. |
US09/864,449 US6585740B2 (en) | 1998-11-26 | 2001-05-25 | Bone screw |
HK01107843A HK1036920A1 (en) | 1998-11-26 | 2001-11-08 | Screw. |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
PCT/CH1998/000504 WO2000032125A1 (de) | 1998-11-26 | 1998-11-26 | Schraube |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/864,449 Continuation US6585740B2 (en) | 1998-11-26 | 2001-05-25 | Bone screw |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2000032125A1 true WO2000032125A1 (de) | 2000-06-08 |
Family
ID=4551374
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/CH1998/000504 WO2000032125A1 (de) | 1998-11-26 | 1998-11-26 | Schraube |
Country Status (11)
Country | Link |
---|---|
US (1) | US6585740B2 (de) |
EP (1) | EP1133263B1 (de) |
JP (1) | JP4488625B2 (de) |
AT (1) | ATE299672T1 (de) |
AU (1) | AU742502B2 (de) |
CA (1) | CA2352185C (de) |
DE (1) | DE59812947D1 (de) |
ES (1) | ES2245047T3 (de) |
HK (1) | HK1036920A1 (de) |
WO (1) | WO2000032125A1 (de) |
ZA (1) | ZA997344B (de) |
Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2001015613A1 (en) * | 1999-08-26 | 2001-03-08 | Australian Surgical Design And Manufacture Pty Limited | Surgical screw and guidewire |
FR2860139A1 (fr) * | 2003-09-26 | 2005-04-01 | Numedic | Dispositif de solidarisation d'une piece sur un support, en particulier d'une plaque d'osteosynthese sur un os |
WO2008146199A2 (en) * | 2007-05-29 | 2008-12-04 | Small Bone Innovations International | Bone screw, in particular for osteosynthesis |
DE102010040228A1 (de) | 2010-09-03 | 2012-03-08 | Aces Gmbh | Knochenverankerungs- oder Verbindungseinrichtung die einen Dehnungsreiz induziert |
DE102013107170A1 (de) * | 2013-07-08 | 2015-01-22 | Aesculap Ag | Knochenschraube |
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US20050143734A1 (en) * | 1996-11-12 | 2005-06-30 | Cachia Victor V. | Bone fixation system with radially extendable anchor |
US6648890B2 (en) * | 1996-11-12 | 2003-11-18 | Triage Medical, Inc. | Bone fixation system with radially extendable anchor |
US6632224B2 (en) * | 1996-11-12 | 2003-10-14 | Triage Medical, Inc. | Bone fixation system |
US6306138B1 (en) * | 1997-09-24 | 2001-10-23 | Ethicon, Inc. | ACL fixation pin and method |
AU755551B2 (en) * | 1999-10-06 | 2002-12-12 | Astra-Tech Aktiebolag | Femur fixture and set of femur fixtures |
ATE285207T1 (de) * | 1999-10-22 | 2005-01-15 | Archus Orthopedics Inc | Facettenarthroplastiegeräte |
US8187303B2 (en) | 2004-04-22 | 2012-05-29 | Gmedelaware 2 Llc | Anti-rotation fixation element for spinal prostheses |
US7674293B2 (en) | 2004-04-22 | 2010-03-09 | Facet Solutions, Inc. | Crossbar spinal prosthesis having a modular design and related implantation methods |
US6974478B2 (en) * | 1999-10-22 | 2005-12-13 | Archus Orthopedics, Inc. | Prostheses, systems and methods for replacement of natural facet joints with artificial facet joint surfaces |
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US6726689B2 (en) | 2002-09-06 | 2004-04-27 | Roger P. Jackson | Helical interlocking mating guide and advancement structure |
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DE10107801A1 (de) * | 2001-02-19 | 2002-09-05 | Hilti Ag | Betonschraube |
US7686807B2 (en) * | 2001-03-22 | 2010-03-30 | Interventional Spine, Inc. | Tool for bone fixation device |
US6511481B2 (en) * | 2001-03-30 | 2003-01-28 | Triage Medical, Inc. | Method and apparatus for fixation of proximal femoral fractures |
US6887243B2 (en) | 2001-03-30 | 2005-05-03 | Triage Medical, Inc. | Method and apparatus for bone fixation with secondary compression |
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US6685706B2 (en) * | 2001-11-19 | 2004-02-03 | Triage Medical, Inc. | Proximal anchors for bone fixation system |
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US7879075B2 (en) | 2002-02-13 | 2011-02-01 | Zimmer Spine, Inc. | Methods for connecting a longitudinal member to a bone portion |
US7066937B2 (en) | 2002-02-13 | 2006-06-27 | Endius Incorporated | Apparatus for connecting a longitudinal member to a bone portion |
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US6793678B2 (en) | 2002-06-27 | 2004-09-21 | Depuy Acromed, Inc. | Prosthetic intervertebral motion disc having dampening |
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US8257402B2 (en) | 2002-09-06 | 2012-09-04 | Jackson Roger P | Closure for rod receiving orthopedic implant having left handed thread removal |
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US8257398B2 (en) * | 2003-06-18 | 2012-09-04 | Jackson Roger P | Polyaxial bone screw with cam capture |
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US8398682B2 (en) | 2003-06-18 | 2013-03-19 | Roger P. Jackson | Polyaxial bone screw assembly |
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US6592587B1 (en) | 1999-08-26 | 2003-07-15 | Australian Surgical Design And Manufacture Pty Limited | Surgical screw and guidewire |
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FR2860139A1 (fr) * | 2003-09-26 | 2005-04-01 | Numedic | Dispositif de solidarisation d'une piece sur un support, en particulier d'une plaque d'osteosynthese sur un os |
US8303634B2 (en) | 2007-05-29 | 2012-11-06 | Small Bone Innovations International | Bone screw, in particular for osteosynthesis |
WO2008146199A2 (en) * | 2007-05-29 | 2008-12-04 | Small Bone Innovations International | Bone screw, in particular for osteosynthesis |
FR2916624A1 (fr) * | 2007-05-29 | 2008-12-05 | Small Bone Innovations Interna | Vis a os, notamment d'osteosynthese |
WO2008146199A3 (en) * | 2007-05-29 | 2009-04-30 | Small Bone Innovations Interna | Bone screw, in particular for osteosynthesis |
JP2010527726A (ja) * | 2007-05-29 | 2010-08-19 | スモール・ボーン・イノベーションズ・インターナショナル | 骨接合術用の骨ねじ |
US8668726B2 (en) | 2007-05-29 | 2014-03-11 | Small Bone Innovations International | Bone screw, in particular for osteosynthesis |
WO2012045307A1 (de) | 2010-09-03 | 2012-04-12 | Aces Gmbh | Knochenverankerungs- oder verbindungseinrichtung die einen dehnungsreiz induziert |
DE102010040228A1 (de) | 2010-09-03 | 2012-03-08 | Aces Gmbh | Knochenverankerungs- oder Verbindungseinrichtung die einen Dehnungsreiz induziert |
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DE102013107170A1 (de) * | 2013-07-08 | 2015-01-22 | Aesculap Ag | Knochenschraube |
EP3019102A1 (de) * | 2013-07-08 | 2016-05-18 | Aesculap AG | Knochenschraube |
US9956018B2 (en) | 2013-07-08 | 2018-05-01 | Aesculap Ag | Bone screw |
EP3019102B1 (de) * | 2013-07-08 | 2022-08-31 | Aesculap AG | Knochenschraube |
Also Published As
Publication number | Publication date |
---|---|
ES2245047T3 (es) | 2005-12-16 |
EP1133263A1 (de) | 2001-09-19 |
AU742502B2 (en) | 2002-01-03 |
DE59812947D1 (de) | 2005-08-25 |
JP2002531163A (ja) | 2002-09-24 |
ATE299672T1 (de) | 2005-08-15 |
AU1139699A (en) | 2000-06-19 |
ZA997344B (en) | 2000-06-22 |
HK1036920A1 (en) | 2002-01-25 |
CA2352185A1 (en) | 2000-06-08 |
JP4488625B2 (ja) | 2010-06-23 |
US6585740B2 (en) | 2003-07-01 |
CA2352185C (en) | 2008-04-15 |
EP1133263B1 (de) | 2005-07-20 |
US20020016594A1 (en) | 2002-02-07 |
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