WO1989004150A1 - Implant for osteosynthesis - Google Patents

Implant for osteosynthesis Download PDF

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Publication number
WO1989004150A1
WO1989004150A1 PCT/EP1987/000663 EP8700663W WO8904150A1 WO 1989004150 A1 WO1989004150 A1 WO 1989004150A1 EP 8700663 W EP8700663 W EP 8700663W WO 8904150 A1 WO8904150 A1 WO 8904150A1
Authority
WO
WIPO (PCT)
Prior art keywords
bone
implant according
plate
screws
contact surface
Prior art date
Application number
PCT/EP1987/000663
Other languages
French (fr)
Inventor
Stephan M. Perren
Fritz Straumann
Franz Sutter
Slobodan Tepic
Original Assignee
Synthes Ag
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=25672379&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=WO1989004150(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Priority to DE3789876T priority Critical patent/DE3789876T2/en
Priority to MX013546A priority patent/MX170527B/en
Priority to PCT/EP1987/000663 priority patent/WO1989004150A1/en
Priority to EP88900013A priority patent/EP0340223A1/en
Priority to JP63500377A priority patent/JP2564183B2/en
Application filed by Synthes Ag filed Critical Synthes Ag
Priority to BR8707937A priority patent/BR8707937A/en
Priority to AR88312349A priority patent/AR241572A1/en
Priority to CA000588337A priority patent/CA1329525C/en
Publication of WO1989004150A1 publication Critical patent/WO1989004150A1/en
Priority to US07/492,403 priority patent/US5053036A/en
Priority to US07/662,634 priority patent/US5151103A/en

Links

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
    • A61B17/80—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates
    • A61B17/8052—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates immobilised relative to screws by interlocking form of the heads and plate holes, e.g. conical or threaded
    • 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
    • A61B17/80—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates
    • A61B17/8028—Cushions, i.e. elements forming interface between bone plate and bone
    • 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
    • A61B17/80—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates
    • A61B17/8033—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates having indirect contact with screw heads, or having contact with screw heads maintained with the aid of additional components, e.g. nuts, wedges or head covers
    • A61B17/8047—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates having indirect contact with screw heads, or having contact with screw heads maintained with the aid of additional components, e.g. nuts, wedges or head covers wherein the additional element surrounds the screw head in the plate hole
    • 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
    • A61B17/80—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates
    • A61B17/809—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates with bone-penetrating elements, e.g. blades or prongs

Definitions

  • This invention relates to an implant for osteosynthesis, comprising a device connectable with a bone with at least two clearance holes and screws with a head for fastening said device rigidly to said bone.
  • a plate is applied to fractured bone bridging the fracture.
  • the plate is fixed to the bone by means of a number of screws which are tightened in the bone producing compressive stresses between the plate and the bone. Transmission of functional load from the bone to the plate and back to the bone is achieved mostly by means of friction corresponding to the compressive stresses.
  • Both the near and the far wall of the bone cortex are usually engaged by the screws.
  • Bone cortex is supplied by blood from periostal, or outer side, and from endosteal, or inner side. Compression between the plate and bone impedes the blood perfusion of the cortex region under the plate. This is believed to increase the chances of infection - a major complication of operative fracture treatment.
  • Dead bone under the plate is in due course remodelled and revascularized. Porosity within the remodelling bone persists for a long time and reduces bone strength, particularly in fatigue. This requires keeping the plate on bone longer than needed for the fracture to heal.
  • the use of long screws running first through the near cortex, then through the medullary canal, and through the far cortex may further compromise blood supply of the fractured bone by cutting through larger blood vessels.
  • the invention as claimed is intended to remedy these drawbacks. It solves the problem of how to design an implant for osteosynthesis that allows operative treatment of bone fractures with minimal vascular damage to the treated bone.
  • Fig. 1 is a schematic view of a fractured bone with a conventional bone plate.
  • Fig. 2 is a cross section of the plate according to Figure 1.
  • Fig. 3 is a transverse cross section of a bone plate according to the invention with short screws.
  • Fig. 4 is a longitudinal cross section of a bone plate according to Figure 3.
  • Fig. 5 is a cross section of a bone plate according to the invention with resorbable buds at the plate undersurface.
  • Fig. 6 is a cross section of a bone plate according to the invention with an expandable spherical insert.
  • Fig. 7 is a cross section of a bone plate according to the invention with an expandable conical insert.
  • Fig. 8 is a cross section of a bone plate according to the invention with removable clip-on springs.
  • Fig. 1 represents a conventional bone plate 1 for the treatment of bone fractures fixed to the bone 2 by means of a number of screws 4. Screws 4 are tightened in the bone 2 producing compressive stresses 5 between the plate 1 and the bone 2. As shown in Fig. 2 transmission of functional load from the bone 2 to the conventional plate 1 and back to the bone 2 is achieved mostly by means of friction corresponding to the compressive stresses 5. Both the near and the far wall of the bone cortex 2 are usually engaged by the screws 4. Bone cortex 2 is supplied by blood from periostal, or outer side 6 , and from endosteal, or inner side 7. Compression 5 between the conventional plate 1 and bone 2 impedes the blood perfusion of the cortex region 8 under the conventional plate 1.
  • Dead bone within region 8 is in due course remodelled and revascularized, whereby remodelling activity starts at periphery 9 of unperfused bone and proceeds towards the plate 1.
  • Porosity within the remodelling bone persists for a long time and reduces bone strength, particularly in fatigue. This requires keeping the conventional plate 1 on bone longer than needed for the fracture to heal. Long screws 4 in running first through the near cortex 10, then through the medullary canal 11, and through the far cortex 12 may further compromise blood supply of the fractured bone by cutting through larger blood vessels.
  • the plate 21 according to the invention is applied to the bone 2 by means of short screws 22.
  • the plate undersurface is shaped so as to permit only point contact to the bone at very small areas 23. This may be achieved by arching the underside of the plate 24 at a curvature larger than that of the bone outer contour 25.
  • the plate underside is also shaped with multiple arches 26 spanning the distance between the screws 22. This leaves the possibility of contact only at small areas 23.
  • the screw 22 is provided with a conical head 27 which upon insertion locks safely in the conical hole 28 of the plate 21.
  • the angle of the conus on the screw head 27 is smaller than friction angle.
  • Preferred taper of the conus is between 1:5 and 1:20.
  • short screws 22 in place of conventional long ones is made possible by locking the screw 22 in the plate 21. This prevents tilting of the screw 22 within the cortex 2. Loads between the bone 2 and the plate 21 are transferred directly through the screws 22, which now act as pegs (under shear) rather than anchors (under tension). In addition to reducing damage to bone 2 and in particular to the intramedullary vascular system, short screws 22 can be made self-tapping without compromises necessary with long self-tapping screws.
  • the described undercutting of the plate 21 with arches 24 in transverse and arches 26 in longitudinal direction may be used to other advantages in addition to reducing the plate-bone contact to point-like areas 23.
  • Conventional plate strength is lowest at the screw hole sections and so is the plate stiffness. Overall plate strength is limited by the weakest section. Keeping the outer dimensions similar to the normal plate, the plate design according to the invention allows for doubling the strength. This is mostly due to the reduced screw hole size. Variation of strength along the plate is much smaller than in conventional plates. The same is true for stiffness. This facilitates plate adaptation to curved bone surfaces.
  • Figure 5 shows another way to reduce the contact between the plate 21 and the bone 2 to point-like areas 23.
  • Small buds 29 are added to the plate undersurface.
  • These may be made from a material which is resorbable, or even dissoluble in body (e.g. polysaccharides), since they need to support the plate 21 only during screw insertion and locking into the plate 21.
  • Figure 6 shows a plate 21 according to the invention combined with a long screw 32 which may be locked into the plate 21 via the spherical insert 30 with substantial freedom of angular placement 31.
  • the conical head 27 of the screw 32 expands the slotted sphere 30, locking itself and the sphere 30 in the plate 21.
  • Taper on the conus is again smaller than friction angle, preferably between 1:5 and 1:20.
  • Figure 7 shows another embodiment of the invention where the locking of the screw 34 in the plate 21 is achieved by the conical insert 35 which expands the slotted screw head 33 thereby forming a rigid connection at the cylindrical interface 36.
  • Figure 8 shows a further embodiment of the invention where the minimal plate contact to the bone 2 is achieved through removable clip-on springs 27 providing bud-like extensions 38 on the undersurface of plate 21.
  • Springs 37 may be removed following insertion and locking of screw 22 in the plate 21.
  • Hooks 39 facilitate removal following screw tightening.

Abstract

The implant for osteosynthesis according to the invention comprises a plate-like device (21) connectable with a bone (2) with at least two clearance holes (28) and screws (22) with a head (27) for fastening said device (21) rigidly to said bone (2), whereby the contact surface (23) of said device (21) to said bone (2) is reduced to the level necessary only for initially locking said screws (22) to said device (21) at the time of insertion. It allows operative treatment of bone fractures with minimal vascular damage to the treated bone.

Description

IMPLANT FOR OSTEOSYNTHESIS
Background of the Invention
This invention relates to an implant for osteosynthesis, comprising a device connectable with a bone with at least two clearance holes and screws with a head for fastening said device rigidly to said bone.
In conventional operative treatment of bone fractures a plate is applied to fractured bone bridging the fracture. The plate is fixed to the bone by means of a number of screws which are tightened in the bone producing compressive stresses between the plate and the bone. Transmission of functional load from the bone to the plate and back to the bone is achieved mostly by means of friction corresponding to the compressive stresses. Both the near and the far wall of the bone cortex are usually engaged by the screws. Bone cortex is supplied by blood from periostal, or outer side, and from endosteal, or inner side. Compression between the plate and bone impedes the blood perfusion of the cortex region under the plate. This is believed to increase the chances of infection - a major complication of operative fracture treatment. Dead bone under the plate is in due course remodelled and revascularized. Porosity within the remodelling bone persists for a long time and reduces bone strength, particularly in fatigue. This requires keeping the plate on bone longer than needed for the fracture to heal. The use of long screws running first through the near cortex, then through the medullary canal, and through the far cortex may further compromise blood supply of the fractured bone by cutting through larger blood vessels.
Summary of the Invention
The invention as claimed is intended to remedy these drawbacks. It solves the problem of how to design an implant for osteosynthesis that allows operative treatment of bone fractures with minimal vascular damage to the treated bone.
Further advantages offered by the invention are - besides the reduced damage to bone and in particular to the intramedullary vascular system - the possibility to use short screws which can be made self-tapping without compromises necessary with long self-tapping screws. Furthermore the plate design according to the invention allows for doubling the strength of the bone plate due to the reduced screw hole size. Variation of strength along the bone plate according to the invention is much smaller than in conventional plates. The same is true for stiffness. This facilitates plate adaptation to curved bone surfaces. The various features of novelty which characterize the invention are pointed out with particularity in the claims annexed to and forming part of this disclosure. For the better understanding of the invention, its operating advantages and specific objects attained by its use, reference should be had to the accompanying drawings and descriptive matter in which are illustrated and described preferred embodiments of the invention.
Brief Description of the Drawings
In the drawings:
Fig. 1 is a schematic view of a fractured bone with a conventional bone plate.
Fig. 2 is a cross section of the plate according to Figure 1.
Fig. 3 is a transverse cross section of a bone plate according to the invention with short screws.
Fig. 4 is a longitudinal cross section of a bone plate according to Figure 3.
Fig. 5 is a cross section of a bone plate according to the invention with resorbable buds at the plate undersurface. Fig. 6 is a cross section of a bone plate according to the invention with an expandable spherical insert.
Fig. 7 is a cross section of a bone plate according to the invention with an expandable conical insert.
Fig. 8 is a cross section of a bone plate according to the invention with removable clip-on springs.
Description of the Preferred Embodiments
Fig. 1 represents a conventional bone plate 1 for the treatment of bone fractures fixed to the bone 2 by means of a number of screws 4. Screws 4 are tightened in the bone 2 producing compressive stresses 5 between the plate 1 and the bone 2. As shown in Fig. 2 transmission of functional load from the bone 2 to the conventional plate 1 and back to the bone 2 is achieved mostly by means of friction corresponding to the compressive stresses 5. Both the near and the far wall of the bone cortex 2 are usually engaged by the screws 4. Bone cortex 2 is supplied by blood from periostal, or outer side 6 , and from endosteal, or inner side 7. Compression 5 between the conventional plate 1 and bone 2 impedes the blood perfusion of the cortex region 8 under the conventional plate 1. This is believed to increase the chances of infection - a major complication of operative fracture treatment. Dead bone within region 8 is in due course remodelled and revascularized, whereby remodelling activity starts at periphery 9 of unperfused bone and proceeds towards the plate 1. Porosity within the remodelling bone persists for a long time and reduces bone strength, particularly in fatigue. This requires keeping the conventional plate 1 on bone longer than needed for the fracture to heal. Long screws 4 in running first through the near cortex 10, then through the medullary canal 11, and through the far cortex 12 may further compromise blood supply of the fractured bone by cutting through larger blood vessels.
In Figure 3 the plate 21 according to the invention is applied to the bone 2 by means of short screws 22. The plate undersurface is shaped so as to permit only point contact to the bone at very small areas 23. This may be achieved by arching the underside of the plate 24 at a curvature larger than that of the bone outer contour 25. In the longitudinal direction (Figure 4), the plate underside is also shaped with multiple arches 26 spanning the distance between the screws 22. This leaves the possibility of contact only at small areas 23. As shown in Figure 3 the screw 22 is provided with a conical head 27 which upon insertion locks safely in the conical hole 28 of the plate 21. The angle of the conus on the screw head 27 is smaller than friction angle. Preferred taper of the conus is between 1:5 and 1:20. Using short screws 22 in place of conventional long ones is made possible by locking the screw 22 in the plate 21. This prevents tilting of the screw 22 within the cortex 2. Loads between the bone 2 and the plate 21 are transferred directly through the screws 22, which now act as pegs (under shear) rather than anchors (under tension). In addition to reducing damage to bone 2 and in particular to the intramedullary vascular system, short screws 22 can be made self-tapping without compromises necessary with long self-tapping screws.
The described undercutting of the plate 21 with arches 24 in transverse and arches 26 in longitudinal direction may be used to other advantages in addition to reducing the plate-bone contact to point-like areas 23. Conventional plate strength is lowest at the screw hole sections and so is the plate stiffness. Overall plate strength is limited by the weakest section. Keeping the outer dimensions similar to the normal plate, the plate design according to the invention allows for doubling the strength. This is mostly due to the reduced screw hole size. Variation of strength along the plate is much smaller than in conventional plates. The same is true for stiffness. This facilitates plate adaptation to curved bone surfaces.
Figure 5 shows another way to reduce the contact between the plate 21 and the bone 2 to point-like areas 23. Small buds 29 are added to the plate undersurface. These may be made from a material which is resorbable, or even dissoluble in body (e.g. polysaccharides), since they need to support the plate 21 only during screw insertion and locking into the plate 21.
Figure 6 shows a plate 21 according to the invention combined with a long screw 32 which may be locked into the plate 21 via the spherical insert 30 with substantial freedom of angular placement 31. The conical head 27 of the screw 32 expands the slotted sphere 30, locking itself and the sphere 30 in the plate 21. Taper on the conus is again smaller than friction angle, preferably between 1:5 and 1:20.
Figure 7 shows another embodiment of the invention where the locking of the screw 34 in the plate 21 is achieved by the conical insert 35 which expands the slotted screw head 33 thereby forming a rigid connection at the cylindrical interface 36.
Figure 8 shows a further embodiment of the invention where the minimal plate contact to the bone 2 is achieved through removable clip-on springs 27 providing bud-like extensions 38 on the undersurface of plate 21. Springs 37 may be removed following insertion and locking of screw 22 in the plate 21. Hooks 39 facilitate removal following screw tightening.

Claims

Claims
1. An implant for osteosynthesis, comprising a device (21) connectable with a bone (2) with at least two clearance holes (28) and screws (22) with a head (27) for fastening said device (21) rigidly to said bone (2), characterized in that the contact surface (23) of said device (21) to said bone (2) is reduced to the level necessary only for initially locking said screws (22) to said device (21) at the time of insertion.
2. Implant according to claim 1, characterized in that the contact surface of the underside (24) of said device (21) to said bone (2) is reduced to point-like areas (23).
3. Implant according to claim 1 or 2, characterized in that the contact surface of the underside (24) of said device (21) to said bone (2) is less than 5%, preferably less than 2% of the full undersurface area (24) of said device (21).
4. Implant according to one of the claims 1 to 3 characterized in that the contact surface of the underside (24) of said device (21) to said bone (2) consists of contact buds (29) made of a material which is resorbable or dissoluble in body fluids, preferably in the form of resorbable or dissoluble buds (29)applied on the normal unstructured bone contact surface of said device (21).
5. Implant according to one of the claims 1 to 4, characterized in that additional clip-on springs (37) are provided for mounting on said device (21) which form bud-like extensions (38) on the undersurface (24) of said device (21).
6. Implant according to one of the claims 1 to 5, characterized in that said clearance holes (28) have the shape of a cone for receiving a correspondingly shaped screw head (27), with a cone angle being smaller than the resulting friction angle, preferably in the range of 1:5 to 1:20.
7. Implant according to one of the claims 1 to 6, characterized in that at least one of said clearance holes (28) is designed as self compressing hole.
8. Implant according to one of the claims 1 to 7, characterized in that only one of said clearance holes (28) is designed as self compressing hole.
9. Implant according to one of the claims 1 to 8, characterized in that said screw heads (27) are expandable by means of a third body (35) insertable into said head (27).
10. Implant according to one of the claims 1 to 9, characterized in that a third body (30) is provided fitting in said clearance hole (28) which is expandable by the conical screw head (27) having a cone angle being smaller than the resulting friction angle, preferably in the range of 1:5 to 1:20.
11. Implant according to one of the claims 1 to 10, characterized in that said screws (22) have a reduced length for engagement only with one cortex of said bone (2).
12. Implant according to one of the claims 1 to 11, characterized in that said device (21) is of plate-like form.
PCT/EP1987/000663 1987-11-03 1987-11-03 Implant for osteosynthesis WO1989004150A1 (en)

Priority Applications (10)

Application Number Priority Date Filing Date Title
BR8707937A BR8707937A (en) 1987-11-03 1987-11-03 PROSTHESIS FOR OSTEOSYNTHESIS
MX013546A MX170527B (en) 1987-11-03 1987-11-03 IMPLEMENTATION FOR OSTEOSYNTHESIS
PCT/EP1987/000663 WO1989004150A1 (en) 1987-11-03 1987-11-03 Implant for osteosynthesis
EP88900013A EP0340223A1 (en) 1987-11-03 1987-11-03 Implant for osteosynthesis
JP63500377A JP2564183B2 (en) 1987-11-03 1987-11-03 Bone graft
DE3789876T DE3789876T2 (en) 1987-11-03 1987-11-03 Bone plate with conical holes.
AR88312349A AR241572A1 (en) 1987-11-03 1988-11-01 Ostheosynthesis implant.
CA000588337A CA1329525C (en) 1987-11-03 1989-01-16 Point contact bone compression plate
US07/492,403 US5053036A (en) 1987-11-03 1990-03-08 Point contact bone compression plate
US07/662,634 US5151103A (en) 1987-11-03 1991-02-28 Point contact bone compression plate

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
PCT/EP1987/000663 WO1989004150A1 (en) 1987-11-03 1987-11-03 Implant for osteosynthesis
CA000588337A CA1329525C (en) 1987-11-03 1989-01-16 Point contact bone compression plate

Publications (1)

Publication Number Publication Date
WO1989004150A1 true WO1989004150A1 (en) 1989-05-18

Family

ID=25672379

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/EP1987/000663 WO1989004150A1 (en) 1987-11-03 1987-11-03 Implant for osteosynthesis

Country Status (8)

Country Link
US (1) US5053036A (en)
EP (1) EP0340223A1 (en)
JP (1) JP2564183B2 (en)
BR (1) BR8707937A (en)
CA (1) CA1329525C (en)
DE (1) DE3789876T2 (en)
MX (1) MX170527B (en)
WO (1) WO1989004150A1 (en)

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DE3743638A1 (en) * 1987-12-22 1989-07-06 Johannes Franz Dr Med Hoenig Osteosynthesis or reconstruction plates
EP0382256A1 (en) * 1989-02-10 1990-08-16 Pasquale Mario Calderale Osteosynthesis means for the connection of bone fracture segments
EP0436885A2 (en) * 1989-12-21 1991-07-17 Anton Prof. Dr. Härle Auxiliary osteosynthesis screw
US5810823A (en) * 1994-09-12 1998-09-22 Synthes (U.S.A.) Osteosynthetic bone plate and lock washer
DE4343117C2 (en) * 1993-12-17 1999-11-04 Dietmar Wolter Bone fixation system
WO2001030251A1 (en) * 1999-10-27 2001-05-03 Sepitec Foundation Implant for osteosyntheses
US6322562B1 (en) 1998-12-19 2001-11-27 Dietmar Wolter Fixation system for bones
EP1738702A1 (en) * 2005-07-02 2007-01-03 Greater Glasgow Health Board Supra mucosal bone fixation
US8197523B2 (en) 2005-02-15 2012-06-12 Apex Biomedical Company, Llc Bone screw for positive locking but flexible engagement to a bone
US8287538B2 (en) 2008-01-14 2012-10-16 Conventus Orthopaedics, Inc. Apparatus and methods for fracture repair
US8398690B2 (en) 2007-02-07 2013-03-19 Apex Biomedical Company, Llc Rotationally asymmetric bone screw
US8696721B2 (en) 2005-03-17 2014-04-15 Spinal Elements, Inc. Orthopedic expansion fastener
US8740955B2 (en) 2005-02-15 2014-06-03 Zimmer, Inc. Bone screw with multiple thread profiles for far cortical locking and flexible engagement to a bone
US8790378B2 (en) 2012-02-02 2014-07-29 Biomet C.V. Distal radius fracture fixation plate with integrated and adjustable volar ulnar facet support
US8888824B2 (en) 2005-07-25 2014-11-18 Smith & Nephew, Inc. Systems and methods for using polyaxial plates
US8906022B2 (en) 2010-03-08 2014-12-09 Conventus Orthopaedics, Inc. Apparatus and methods for securing a bone implant
US8940028B2 (en) 2005-07-25 2015-01-27 Smith & Nephew, Inc. Systems and methods for using polyaxial plates
US8961518B2 (en) 2010-01-20 2015-02-24 Conventus Orthopaedics, Inc. Apparatus and methods for bone access and cavity preparation
US8992581B2 (en) 2003-09-29 2015-03-31 Smith & Nephew, Inc. Bone plate and bone plate assemblies including polyaxial fasteners
US9220547B2 (en) 2009-03-27 2015-12-29 Spinal Elements, Inc. Flanged interbody fusion device
US9730686B2 (en) 2014-09-03 2017-08-15 Biomet C.V. System and method of soft tissue anchoring to metaphyseal bone plate
US9730739B2 (en) 2010-01-15 2017-08-15 Conventus Orthopaedics, Inc. Rotary-rigid orthopaedic rod
US10022132B2 (en) 2013-12-12 2018-07-17 Conventus Orthopaedics, Inc. Tissue displacement tools and methods
US10390866B2 (en) 2011-06-15 2019-08-27 Smith & Nephew, Inc. Variable angle locking implant
US10758361B2 (en) 2015-01-27 2020-09-01 Spinal Elements, Inc. Facet joint implant
US10918426B2 (en) 2017-07-04 2021-02-16 Conventus Orthopaedics, Inc. Apparatus and methods for treatment of a bone
US10993750B2 (en) 2015-09-18 2021-05-04 Smith & Nephew, Inc. Bone plate
US11382769B2 (en) 2018-09-20 2022-07-12 Spinal Elements, Inc. Spinal implant device
US11911284B2 (en) 2020-11-19 2024-02-27 Spinal Elements, Inc. Curved expandable interbody devices and deployment tools

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US5360452A (en) * 1991-05-20 1994-11-01 Depuy Inc. Enhanced fixation system for a prosthetic implant
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US5505736A (en) * 1992-02-14 1996-04-09 American Cyanamid Company Surgical fastener with selectively coated ridges
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DE3789876D1 (en) 1994-06-23
CA1329525C (en) 1994-05-17
EP0340223A1 (en) 1989-11-08
JP2564183B2 (en) 1996-12-18
JPH03500487A (en) 1991-02-07
MX170527B (en) 1993-08-30
BR8707937A (en) 1990-02-13
DE3789876T2 (en) 1994-11-03
US5053036A (en) 1991-10-01

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