WO2004043278A1 - Articular facet interference screw - Google Patents

Articular facet interference screw Download PDF

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Publication number
WO2004043278A1
WO2004043278A1 PCT/CH2002/000608 CH0200608W WO2004043278A1 WO 2004043278 A1 WO2004043278 A1 WO 2004043278A1 CH 0200608 W CH0200608 W CH 0200608W WO 2004043278 A1 WO2004043278 A1 WO 2004043278A1
Authority
WO
WIPO (PCT)
Prior art keywords
bone screw
screw
screw head
bone
head
Prior art date
Application number
PCT/CH2002/000608
Other languages
French (fr)
Inventor
Paul Pavlov
Robert Frigg
Beat Lechmann
Original Assignee
Synthes Ag Chur
Synthes (U.S.A.)
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
Priority to EP02774232A priority Critical patent/EP1585449B8/en
Priority to DE60214908T priority patent/DE60214908T2/en
Priority to JP2004550592A priority patent/JP4307387B2/en
Priority to AU2002340694A priority patent/AU2002340694B2/en
Priority to PCT/CH2002/000608 priority patent/WO2004043278A1/en
Priority to BRPI0215923-6A priority patent/BR0215923B1/en
Priority to CA2505850A priority patent/CA2505850C/en
Priority to ES02774232T priority patent/ES2274099T3/en
Application filed by Synthes Ag Chur, Synthes (U.S.A.) filed Critical Synthes Ag Chur
Priority to TW092127407A priority patent/TWI296194B/en
Priority to MYPI20033915A priority patent/MY134584A/en
Publication of WO2004043278A1 publication Critical patent/WO2004043278A1/en
Priority to US11/126,976 priority patent/US7699878B2/en
Priority to US12/716,631 priority patent/US8317839B2/en
Priority to US13/675,511 priority patent/US8668722B2/en

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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
    • A61B17/88—Osteosynthesis instruments; Methods or means for implanting or extracting internal or external fixation devices
    • 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
    • A61B17/7062—Devices acting on, attached to, or simulating the effect of, vertebral processes, vertebral facets or ribs ; Tools for such devices
    • A61B17/7064—Devices acting on, attached to, or simulating the effect of, vertebral facets; Tools therefor
    • 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
    • A61B17/8605—Heads, i.e. proximal ends projecting from bone
    • A61B17/861—Heads, i.e. proximal ends projecting from bone specially shaped for gripping driver
    • A61B17/8615—Heads, i.e. proximal ends projecting from bone specially shaped for gripping driver at the central region of the screw head
    • 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
    • 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
    • A61B17/685—Elements to be fitted on the end of screws or wires, e.g. protective caps
    • 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
    • A61B17/864—Pins or screws or threaded wires; nuts therefor hollow, e.g. with socket or cannulated
    • 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
    • A61B17/88—Osteosynthesis instruments; Methods or means for implanting or extracting internal or external fixation devices
    • A61B17/8875—Screwdrivers, spanners or wrenches
    • 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
    • A61B2017/8655—Pins or screws or threaded wires; nuts therefor with special features for locking in the bone

Definitions

  • This invention concerns a bone screw, in particular for locking an articular facet between the superior and inferior articular processes of two vertebral bodies, in accordance with the pre-characterising portion of Claim 1.
  • the anterior and the posterior columns must be treated.
  • the goal of the treatment is the restoration of the lordotic curve and the anatomically correct disc space.
  • the posterior vertebral column, where the articular facet is located, should be locked as well.
  • State-of-the-art techniques consider translaminar screws or transpedical instrumentation which, however, are not satisfactory.
  • Translaminar screws have certain disadvantages, like a) the screw insertion point is difficult to localize; the localization is done under full view, i.e. a separate posterior incision is performed medially whereas muscles must be separated from spinal and laminar processes. Most morbidity results from medial incision; b) the surgeon's view is two-dimensional due to the small incision which may result in interference of the second screw with the first one; and c) aiming devices or navigation tools did not improve insertion technique or precision of screw placement.
  • the invention as claimed aims at solving the above described problems .
  • the present invention provides a bone screw as defined in Claim 1 and a method for locking an articular facet of a vertebral body as defined in Claim 24.
  • the interference screw according to the invention allows a new surgical technique to lock the articular facets of vertebral bodies .
  • the natural functional spine unit (FSU) contains two articular facets.
  • the function of the screw according to the invention is the interference in the sense of obstruction or fixation of said articular facets. Since the core diameter of the screw is significantly larger than the gap in the articular facet, the device is hindering the natural articulation.
  • the function of the screw thread is the insertion by rotation. After insertion the screw thread protects the screw from axial migration and the anti-rotation device protects the screw from migration by rotation.
  • the locking screws are inserted through two percutaneous approaches in the trajectories parallel to the articular surface of the articular facet.
  • Aiming wires guarantee the correct positioning.
  • An anti-rotation element keeps the bone screw in position and hinders the screws from turning out if micro-motion is applied to the screws.
  • This technique is applicable if the anterior vertebral column (i.e. the intervertebral space of the related segment) is stabilised with a spacer such as an intervertebral cage.
  • the grooves on the periphery of the screw head are running essentially parallel to the central axis.
  • Such an angulation in a radial plane and measured relative to the central axis might be in the order of up to 60°, but preferably less than 20°.
  • the possible angulation in a tangential plane and measured relative to the central axis might be in the order of maximum 20 °, preferably less than 10°.
  • the bone screw is provided with at least one pair of diametrally opposed grooves on the periphery of said screw head which enhances stability of the implant.
  • the screw head may be provided with a central cavity coaxially arranged with respect to said central axis, e.g. with a polygonal profile, preferably a hexagonal profile for receiving a screw-driver having a corresponding profile.
  • the grooves on the periphery of the screw head may be juxtaposed to the polygonal planes of said central cavity.
  • an anti-rotation element is insertable in said groove or said pair of grooves on the periphery of said screw head, whereby said anti-rotation element in its inserted position projects radially out of the periphery of said screw head.
  • the anti-rotation element is preferably a U-shaped staple with two legs and a central portion bridging said two legs and designed for insertion into said groove or said pair of grooves of said screw head.
  • the anti-rotation element has preferably a diameter which is larger than said screw head.
  • the anti-rotation element in form of a U-shaped staple may be provided with a guiding element attached to said central portion and running essentially parallel to said legs.
  • the guiding element may be in the form of a plate, a circular cylinder or a prism designed for insertion into said central cavity of said screw head.
  • the cylindrical shape of the guiding element has the advantage of a more accurate gliding.
  • the central portion of the anti-rotation element may be provided with at least one perforation for removal of the screw.
  • the threaded shaft of the bone screw has preferably a thread with a high angle of pressure, e.g. in the range of 4° to 70°.
  • the flank of said thread can be symmetrically or asymmetrically oriented.
  • the asymmetrically oriented thread is compressing particularly cancellous bone. This increases initial fixation stability.
  • the bone screw may be self-tapping, preferably by means of a cutting edge.
  • the core of the screw shaft may be either cylindrical or tapering away from the screw head.
  • the shaft In the case of a conical shape of the core the shaft is compressing the surrounding bone. This increases the initial stability of the implant.
  • the envelope of the threaded shaft may be cylindrical allowing also a constant insertion torque.
  • the envelope of the threaded shaft preferably tapers away from the screw head so that the purchase of the thread in the bone is increasing by turning the screw in.
  • the bone screw may be self-drilling, preferably by means of a chucking groove .
  • the new ' method for locking an articular facet between the superior and inferior articular processes of two vertebral bodies consists in the insertion of the threaded shaft of a bone screw in the gap of said articular facet .
  • the bone screw is preferably cannulated and insertion is performed by means of an aiming wire .
  • the bone screw has preferably a screw head with a larger diameter than said threaded shaft and said threaded shaft is inserted in said gap of said articular facet until said screw head touches the bone.
  • an anti-rotation element may be applied to said screw head such that rotation of said bone screw is prevented.
  • Fig. 1 is a perspective view of the bone screw according to the invention together with an anti-rotation element to be used with the screw;
  • Fig. 2a is a longitudinal section through the central axis of the screw and the anti-rotation element according to Fig. 1;
  • Fig. 2b is a top view of the bone screw according to Fig. 1 with the anti-rotation element inserted into the screw head;
  • Fig. 3 is a perspective view of a trocar for bringing an aiming wire into the gap between the articular facet
  • Fig. 4. is a perspective view of a drill bit, the aiming wires being temporarily fixed in the gaps of the articular facets;
  • Fig. 5 is a perspective view of the bone screw being inserted by means of a screw-driver into the gap of the articular facet by using the temporarily fixed guiding wire;
  • Fig. 6 is a perspective view of the anti-rotation element being put over the screw head into its grooves closest to the joint gap;
  • Fig. 7 is a perspective view of the inserted bone screw to which the anti-rotation element has been attached.
  • the bone screw 1 as represented in Figs. 1, 2a and 2b is used in particular for locking an articular facet between the superior and inferior articular processes of two vertebral bodies. It has a threaded shaft 2, a screw head 3 and a central axis 4.
  • the screw head 3 is provided with six grooves 5 regularly disposed on the periphery of the screw head 3 running essentially parallel to the central axis 4.
  • the screw head 3 is further provided with a central cavity 6 coaxially arranged with respect to the central axis 4 and having a hexagonal shape.
  • the anti-rotation element 10 is provided with a U-shaped staple having two legs 11 and a central portion 13 bridging said two legs 11.
  • the U-shaped staple is provided with a guiding element 12 - having the shape of a circular cylinder - attached to the central portion 13 and running essentially parallel to the legs 11.
  • the anti-rotation element 10 may be connected to the bone screw 1 by moving it along the central axis 4 whereby its central portion 13 enters the central cavity 6 of the screw head 3 and the two legs 11 are inserted into one of the three pairs of grooves 5 of the screw head 3 as shown in Fig. 2b.
  • the free ends of the two legs 11 are provided with an protrusion 15 oriented radially inwards to the central axis 4 so that when the legs 11 are gliding along the grooves 5 the protrusions 15 will click under the lower edge 16 of the screw head 3 thereby securing the anti-rotation element 10 against withdrawal in the opposite axial direction.
  • the central portion 13 of the U-shaped staple is further provided with at a perforation 14 facilitating removal of the bone screw 1.
  • Useful materials for the bone screw 1 as well as for the anti-rotation element 10 are titanium, titanium alloys or fibre-reinforced plastic materials. They may be coated with ceramic .
  • Bilateral skin incisions are performed in the direction of the articular facets.
  • a trocar 17 or similar instrument is used to bring an aiming wire 18 into the ga 19 between the articular facets (Fig. 3) .
  • Positional control is indicated using an image intensifier.
  • aiming wires 18 are temporarily fixed in the gaps 19 of the articular facets by means of the drill bit 20 ("screw head reamer” or “counter sink”) .
  • a cannulated and self-tapping bone screw 1 is inserted by means of a screw-driver 21 into the gap 19 by using the temporarily fixed guiding wires 18 until the screw heads 3 of the bone screws 1 are touching the bone .
  • the method of operation as described can be performed on one side of the vertebral column only but is preferably performed simultaneously on the right and left side, as shown in Figs. 3 to 7, which has biomechanical advantages.

Abstract

The bone screw (1) is used for locking an articular facet between the superior and inferior articular processes of two vertebral bodies and is provided with a threaded shaft (2), a screw head (3) and a central axis (4). The screw head (3) is further provided with a number of grooves (5) on the periphery of the screw head (3) which run essentially parallel to said central axis (4).

Description

Articular Facet Interference Screw
This invention concerns a bone screw, in particular for locking an articular facet between the superior and inferior articular processes of two vertebral bodies, in accordance with the pre-characterising portion of Claim 1.
To achieve a circumferential arthrodesis (fusion) the anterior and the posterior columns must be treated. The goal of the treatment is the restoration of the lordotic curve and the anatomically correct disc space. Anteriorly, i.e. in the intervertebral space, implants like cages are inserted after disc removal. The posterior vertebral column, where the articular facet is located, should be locked as well. State-of-the-art techniques consider translaminar screws or transpedical instrumentation which, however, are not satisfactory.
Translaminar screws have certain disadvantages, like a) the screw insertion point is difficult to localize; the localization is done under full view, i.e. a separate posterior incision is performed medially whereas muscles must be separated from spinal and laminar processes. Most morbidity results from medial incision; b) the surgeon's view is two-dimensional due to the small incision which may result in interference of the second screw with the first one; and c) aiming devices or navigation tools did not improve insertion technique or precision of screw placement.
The invention as claimed aims at solving the above described problems .
The present invention provides a bone screw as defined in Claim 1 and a method for locking an articular facet of a vertebral body as defined in Claim 24.
The advantages of said method and the use of said bone screw are the following:
percutaneous approach which results in reduced morbidity; low implant cost due to simple design, in particular in comparison to transpedicular fixation; lower risk with regard to screw positioning compared to translaminar screws; and easy removal of the screws .
The interference screw according to the invention allows a new surgical technique to lock the articular facets of vertebral bodies . The natural functional spine unit (FSU) contains two articular facets. The function of the screw according to the invention is the interference in the sense of obstruction or fixation of said articular facets. Since the core diameter of the screw is significantly larger than the gap in the articular facet, the device is hindering the natural articulation. The function of the screw thread is the insertion by rotation. After insertion the screw thread protects the screw from axial migration and the anti-rotation device protects the screw from migration by rotation.
According to the new surgical method the locking screws are inserted through two percutaneous approaches in the trajectories parallel to the articular surface of the articular facet. Aiming wires guarantee the correct positioning. An anti-rotation element keeps the bone screw in position and hinders the screws from turning out if micro-motion is applied to the screws. This technique is applicable if the anterior vertebral column (i.e. the intervertebral space of the related segment) is stabilised with a spacer such as an intervertebral cage.
According to a special embodiment the grooves on the periphery of the screw head are running essentially parallel to the central axis. This shall be interpreted in such a way that minor angulation with regard to the central axis either towards radially the latter or tangentially to it would still be functional . Such an angulation in a radial plane and measured relative to the central axis might be in the order of up to 60°, but preferably less than 20°. The possible angulation in a tangential plane and measured relative to the central axis might be in the order of maximum 20 °, preferably less than 10°.
In a particular embodiment the bone screw is provided with at least one pair of diametrally opposed grooves on the periphery of said screw head which enhances stability of the implant.
The screw head may be provided with a central cavity coaxially arranged with respect to said central axis, e.g. with a polygonal profile, preferably a hexagonal profile for receiving a screw-driver having a corresponding profile.
The grooves on the periphery of the screw head may be juxtaposed to the polygonal planes of said central cavity. By this measure a higher mechanical strength can be achieved.
In a further embodiment an anti-rotation element is insertable in said groove or said pair of grooves on the periphery of said screw head, whereby said anti-rotation element in its inserted position projects radially out of the periphery of said screw head. The anti-rotation element is preferably a U-shaped staple with two legs and a central portion bridging said two legs and designed for insertion into said groove or said pair of grooves of said screw head. The anti-rotation element has preferably a diameter which is larger than said screw head. The anti-rotation element in form of a U-shaped staple may be provided with a guiding element attached to said central portion and running essentially parallel to said legs. The guiding element may be in the form of a plate, a circular cylinder or a prism designed for insertion into said central cavity of said screw head. The cylindrical shape of the guiding element has the advantage of a more accurate gliding.
The central portion of the anti-rotation element may be provided with at least one perforation for removal of the screw.
The threaded shaft of the bone screw has preferably a thread with a high angle of pressure, e.g. in the range of 4° to 70°. The flank of said thread can be symmetrically or asymmetrically oriented. The asymmetrically oriented thread is compressing particularly cancellous bone. This increases initial fixation stability.
The bone screw may be self-tapping, preferably by means of a cutting edge.
The core of the screw shaft may be either cylindrical or tapering away from the screw head.
In the case of cylindrical core of the screw shaft various advantages can be achieved, namely: a continuous bending strength along the screw shaft; the application of a constant insertion torque while turning the screw in the articular facet; and due to the constant shaft diameter the screw does not become loose if the device is turned back slightly after insertion. This could appear if the surgeon brings the grooves for the anti-rotation element in congruent direction like the articular facet gap.
In the case of a conical shape of the core the shaft is compressing the surrounding bone. This increases the initial stability of the implant.
The envelope of the threaded shaft may be cylindrical allowing also a constant insertion torque. However, the envelope of the threaded shaft preferably tapers away from the screw head so that the purchase of the thread in the bone is increasing by turning the screw in.
The bone screw may be self-drilling, preferably by means of a chucking groove .
The new' method for locking an articular facet between the superior and inferior articular processes of two vertebral bodies consists in the insertion of the threaded shaft of a bone screw in the gap of said articular facet . To that purpose the bone screw is preferably cannulated and insertion is performed by means of an aiming wire . The bone screw has preferably a screw head with a larger diameter than said threaded shaft and said threaded shaft is inserted in said gap of said articular facet until said screw head touches the bone. Upon insertion of said bone screw an anti-rotation element may be applied to said screw head such that rotation of said bone screw is prevented.
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, examples and descriptive matter in which are illustrated and described preferred embodiments of the invention.
In the drawings :
Fig. 1 is a perspective view of the bone screw according to the invention together with an anti-rotation element to be used with the screw;
Fig. 2a is a longitudinal section through the central axis of the screw and the anti-rotation element according to Fig. 1;
Fig. 2b is a top view of the bone screw according to Fig. 1 with the anti-rotation element inserted into the screw head;
Fig. 3 is a perspective view of a trocar for bringing an aiming wire into the gap between the articular facet; Fig. 4. is a perspective view of a drill bit, the aiming wires being temporarily fixed in the gaps of the articular facets;
Fig. 5 is a perspective view of the bone screw being inserted by means of a screw-driver into the gap of the articular facet by using the temporarily fixed guiding wire;
Fig. 6 is a perspective view of the anti-rotation element being put over the screw head into its grooves closest to the joint gap; and
Fig. 7 is a perspective view of the inserted bone screw to which the anti-rotation element has been attached.
The bone screw 1 as represented in Figs. 1, 2a and 2b is used in particular for locking an articular facet between the superior and inferior articular processes of two vertebral bodies. It has a threaded shaft 2, a screw head 3 and a central axis 4. The screw head 3 is provided with six grooves 5 regularly disposed on the periphery of the screw head 3 running essentially parallel to the central axis 4. The screw head 3 is further provided with a central cavity 6 coaxially arranged with respect to the central axis 4 and having a hexagonal shape.
The anti-rotation element 10 is provided with a U-shaped staple having two legs 11 and a central portion 13 bridging said two legs 11. The U-shaped staple is provided with a guiding element 12 - having the shape of a circular cylinder - attached to the central portion 13 and running essentially parallel to the legs 11. As can be seen in Figs. 1 and 2a the anti-rotation element 10 may be connected to the bone screw 1 by moving it along the central axis 4 whereby its central portion 13 enters the central cavity 6 of the screw head 3 and the two legs 11 are inserted into one of the three pairs of grooves 5 of the screw head 3 as shown in Fig. 2b.
The free ends of the two legs 11 are provided with an protrusion 15 oriented radially inwards to the central axis 4 so that when the legs 11 are gliding along the grooves 5 the protrusions 15 will click under the lower edge 16 of the screw head 3 thereby securing the anti-rotation element 10 against withdrawal in the opposite axial direction.
The central portion 13 of the U-shaped staple is further provided with at a perforation 14 facilitating removal of the bone screw 1.
Useful materials for the bone screw 1 as well as for the anti-rotation element 10 are titanium, titanium alloys or fibre-reinforced plastic materials. They may be coated with ceramic .
A detailed method of operation follows for the better understanding of the invention: 1. Both positions in extension of the articulating planes of the articular facet concerned are identified and marked accordingly on the skin. To this purpose an image intensifier is used to control position and direction.
2. Bilateral skin incisions are performed in the direction of the articular facets.
3. Depending on the surgeon's preference, a trocar 17 or similar instrument is used to bring an aiming wire 18 into the ga 19 between the articular facets (Fig. 3) . Positional control is indicated using an image intensifier.
4. As shown in Fig. 4 the aiming wires 18 are temporarily fixed in the gaps 19 of the articular facets by means of the drill bit 20 ("screw head reamer" or "counter sink") .
5. As shown in Fig. 5 a cannulated and self-tapping bone screw 1 is inserted by means of a screw-driver 21 into the gap 19 by using the temporarily fixed guiding wires 18 until the screw heads 3 of the bone screws 1 are touching the bone .
6. As shown in Fig. 6 an anti-rotations element 10 is put over the screw head 3 in the grooves 5 (notches) closest to the joint gap 19. Eventually the bone screw 1 must be turned back by some degrees in order to match the grooves 5 (notches) in the screw head 3 with the joint gap 19 (Fig. 7) . 7. All instruments are removed.
8. The placement of the bone screws 1 is verified by using an image identifier and the wound is closed.
The method of operation as described can be performed on one side of the vertebral column only but is preferably performed simultaneously on the right and left side, as shown in Figs. 3 to 7, which has biomechanical advantages.

Claims

Claims
1. Bone screw (1), in particular for locking an articular facet between the superior and inferior articular processes of two vertebral bodies, having a threaded shaft (2), a screw head (3) and a central axis (4) , characterized in that said screw head (3) is provided with at least one axial groove
(5) on the periphery of said screw head (3) .
2. Bone screw (1) according to claim 1, characterized in that the at least one axial groove (5) is running essentially parallel to said central axis (4) .
3. Bone screw (1) according to claim 1, characterized in that the at least one axial groove (5) has an angulation in a radial plane and measured relatively to said the central axis (4) in the order of less than 60° and preferably less than 20°.
4. Bone screw (1) according to claim 1, characterized in that the at least one axial groove (5) has an angulation in a tangential plane and measured relatively to said central axis (4) in the order of less than 20°, preferably less than 10°.
5. Bone screw (1) according to one of the claims 1 - 4, characterized in that is provided with at least one pair of diametrally opposed grooves (5) on the periphery of said screw head (3) .
6. Bone screw (1) according to one of the claims 1 - 5, characterized in that said screw head (3) is provided with a central cavity (6) coaxially arranged with respect to said central axis (4) .
7. Bone screw (1) according to one of the claims 1 to 6, characterized by a anti-rotation element (10) insertable in said groove (5) or pair of grooves (5) , whereby said anti-rotation element (10) in its inserted position projects radially out of the periphery of said screw head (3) .
8. Bone screw (1) according to claim 7, characterized in said that
A) said anti-rotation element (10) is a U-shaped staple with two legs (11) and a central portion (13) bridging said two legs (11) ; and
B) said anti-rotation element (10) is designed for insertion into said groove (5) or pair of grooves (5) of said screw head (3) .
9. Bone screw (1) according to claim 7 or 8 , characterized in that said anti-rotation element (10) has a diameter which is larger than said screw head (3) .
10. Bone screw (1) according to claim 8 or 9 , characterized in that said U-shaped staple is provided with a guiding element (12) attached to said central portion (13) and running essentially parallel to said legs (11) .
11. Bone screw (1) according to claim 10, characterized in that said guiding element (12) is in the form of a plate, a cii-cular cylinder or a prism designed for insertion into said central cavity (6) of said screw head (3) .
12. Bone screw (1) according to one of the claims 8 to 11, characterized in that said central portion (13) is provided with at least one perforation (14) .
13. Bone screw (1) according to one of the claims 1 to 12, characterized in that said threaded shaft (2) has a thread (7) with a high angle of pressure, preferably in the range of 4° to 70° .
14. Bone screw (1) according to claim 13, characterized in that the flank of said thread (7) is symmetrically oriented.
15. Bone screw (1) according to claim 13, characterized in that the flank of said thread (7) is asymmetrically oriented.
16. Bone screw (1) according to one of the claims 1 to 15, characterized in that it is self-tapping, preferably by means of a cutting edge.
17. Bone screw (1) according to one of the claims 6 to 16, characterized in that said central cavity (6) has a polygonal profile, preferably a hexagonal profile.
18. Bone screw (1) according to claim 17, characterized in that said grooves (5) on the periphery of said screw head (3) are juxtaposed to the polygonal planes of said central cavity (6) .
19. Bone screw (1) according to one of the claims, 1 to 18, characterized in that the core of said shaft (2) is cylindrical.
20. Bone screw (1) according to one of the claims 1 to 18, characterized in that the core of said shaft (2) tapering away from said screw head (3) .
21. Bone screw (1) according to one of the claims 1 to 20, characterized in that the envelope of said threaded shaft (2) is cylindrical .
22. Bone screw (1) according to one of the claims 1 to 20, characterized in that the envelope of said threaded shaft (2) tapers away from said screw head (3) .
23. Bone screw (1) according to one of the claims 1 to 22, characterized in that it is self-drilling, preferably by means of a chucking groove .
2 . Method for locking an articular facet between the superior and inferior articular processes of two vertebral bodies, characterized in that, the threaded shaft (2) of a bone screw (1) is inserted in the gap of said articular facet.
25. Method according to claim 24, characterized in that said bone screw (1) is cannulated and insertion is performed by means of an aiming wire .
26. Method according to claim 24 or 25, characterized in that
A) said bone screw (1) has a screw head (3) with a larger diameter than said threaded shaft (2) ; and
B) said threaded shaft (2) is inserted in said gap of said articular facet until said screw head (3) touches the bone.
27. Method according to one of the claims 24 to 26, characterized in that upon insertion of said bone screw (1) an anti-rotation element (10) is applied to said screw head (3) such that rotation of said bone screw (1) is prevented.
28. Method according to one of the claims 24 to 27, characterized in that it is performed simultaneously on the right and left side of the vertebral column.
PCT/CH2002/000608 2002-11-13 2002-11-13 Articular facet interference screw WO2004043278A1 (en)

Priority Applications (13)

Application Number Priority Date Filing Date Title
CA2505850A CA2505850C (en) 2002-11-13 2002-11-13 Articular facet interference screw
JP2004550592A JP4307387B2 (en) 2002-11-13 2002-11-13 Small joint surface interference screw
AU2002340694A AU2002340694B2 (en) 2002-11-13 2002-11-13 Articular facet interference screw
PCT/CH2002/000608 WO2004043278A1 (en) 2002-11-13 2002-11-13 Articular facet interference screw
BRPI0215923-6A BR0215923B1 (en) 2002-11-13 2002-11-13 articular facet interference screw.
EP02774232A EP1585449B8 (en) 2002-11-13 2002-11-13 Articular facet interference screw
ES02774232T ES2274099T3 (en) 2002-11-13 2002-11-13 CIRCULAR FACET INTERFERENCE SCREW.
DE60214908T DE60214908T2 (en) 2002-11-13 2002-11-13 JOINT FORT SET-INTERFERENCE SCREW
TW092127407A TWI296194B (en) 2002-11-13 2003-10-03 Articular facet interference screw
MYPI20033915A MY134584A (en) 2002-11-13 2003-10-14 Articular facet interference screw
US11/126,976 US7699878B2 (en) 2002-11-13 2005-05-10 Method for locking an artificial facet between two vertebral bodies
US12/716,631 US8317839B2 (en) 2002-11-13 2010-03-03 Method for locking an artificial facet between two vertebral bodies
US13/675,511 US8668722B2 (en) 2002-11-13 2012-11-13 Method for locking an artificial facet between two vertebral bodies

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CH2002/000608 WO2004043278A1 (en) 2002-11-13 2002-11-13 Articular facet interference screw

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US11/126,976 Continuation US7699878B2 (en) 2002-11-13 2005-05-10 Method for locking an artificial facet between two vertebral bodies

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US (3) US7699878B2 (en)
EP (1) EP1585449B8 (en)
JP (1) JP4307387B2 (en)
AU (1) AU2002340694B2 (en)
BR (1) BR0215923B1 (en)
CA (1) CA2505850C (en)
DE (1) DE60214908T2 (en)
ES (1) ES2274099T3 (en)
MY (1) MY134584A (en)
TW (1) TWI296194B (en)
WO (1) WO2004043278A1 (en)

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AU2002340694B2 (en) 2006-09-21
AU2002340694A1 (en) 2004-06-03
DE60214908D1 (en) 2006-11-02
EP1585449A1 (en) 2005-10-19
US8317839B2 (en) 2012-11-27
ES2274099T3 (en) 2007-05-16
EP1585449B8 (en) 2007-04-18
CA2505850C (en) 2011-01-04
BR0215923A (en) 2005-08-09
CA2505850A1 (en) 2004-05-27
US20130116732A1 (en) 2013-05-09
TW200414890A (en) 2004-08-16
US7699878B2 (en) 2010-04-20
US8668722B2 (en) 2014-03-11
BR0215923B1 (en) 2013-01-22
JP4307387B2 (en) 2009-08-05
JP2006506113A (en) 2006-02-23
EP1585449B1 (en) 2006-09-20
US20100179598A1 (en) 2010-07-15
US20060064099A1 (en) 2006-03-23
TWI296194B (en) 2008-05-01
DE60214908T2 (en) 2007-03-01
MY134584A (en) 2007-12-31

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