CA1326739C - Anchoring element for supporting a joint mechanism of a finger or other reconstructed joint - Google Patents
Anchoring element for supporting a joint mechanism of a finger or other reconstructed jointInfo
- Publication number
- CA1326739C CA1326739C CA000613216A CA613216A CA1326739C CA 1326739 C CA1326739 C CA 1326739C CA 000613216 A CA000613216 A CA 000613216A CA 613216 A CA613216 A CA 613216A CA 1326739 C CA1326739 C CA 1326739C
- Authority
- CA
- Canada
- Prior art keywords
- anchoring element
- joint
- bone
- joint mechanism
- sleeve
- Prior art date
- Legal status (The legal status 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 status listed.)
- Expired - Fee Related
Links
Classifications
-
- A—HUMAN NECESSITIES
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
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- A61F2/42—Joints for wrists or ankles; for hands, e.g. fingers; for feet, e.g. toes
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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- A61F2/36—Femoral heads ; Femoral endoprostheses
- A61F2/3662—Femoral shafts
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- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
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- 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
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
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- A61F2002/30535—Special structural features of bone or joint prostheses not otherwise provided for
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- Health & Medical Sciences (AREA)
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Abstract
ABSTRACT OF THE DISCLOSURE
An anchoring element for supporting a joint mechanism.
The anchoring element is substantially rotationally symmetrical, at least partially hollow, and includes a material which is compatible with the tissue of a bone. The anchoring element has a surface which can be at least partially osseo-integrated with the tissue to achieve permanent endosteal anchorage in the longitudinal axis of the bone. The anchoring element is applied within the bone by:
cutting the bone close to its joint to expose the marrow cavity of the bone; forming a space in the marrow cavity close to the joint; applying a guide sleeve in the space; and screwing the anchoring element into the marrow cavity while using the guide sleeve to center the anchoring element.
An anchoring element for supporting a joint mechanism.
The anchoring element is substantially rotationally symmetrical, at least partially hollow, and includes a material which is compatible with the tissue of a bone. The anchoring element has a surface which can be at least partially osseo-integrated with the tissue to achieve permanent endosteal anchorage in the longitudinal axis of the bone. The anchoring element is applied within the bone by:
cutting the bone close to its joint to expose the marrow cavity of the bone; forming a space in the marrow cavity close to the joint; applying a guide sleeve in the space; and screwing the anchoring element into the marrow cavity while using the guide sleeve to center the anchoring element.
Description
The present invention relates to an anchoring element for supporting a joint mechanism, a method of applying an anchoring element within a bone, and a reconstructed joint.
A preferred embodiment of the invention will be deæcribed in detail in the following with reference to the reconstruction of a finger joint. However, the invention is not limited thereto. The invention can be used for other similar joints, such as toe joints, elbow joints, and so on.
~he invention can also be used in reconstructions after amputation or other defects.
Finger-joint reconstructions, entailing prostheses, are primarily carried out on MCP joints which have become rheumatically changed. Prostheses known for this purpose include Swanson Silastic finger joints. Such joints consist of a material similar to silicon, are elongate in shape, and have ends with substantially circular cross sections. The ends can be substantially circular cross sections. The ends can be fitted and anchored into the marrow cavity of each bone. The central portion o~ the prosthesis is elastically deformable and thus constitutes the actual joint mechanism.
The St. George prosthesis, a cemented prosthesis, is 2~ also known for finger-joint reconstructions.
A problem with these conventional prostheses is that the anchoring element supporting the actual prosthesis mechanism ~ 3~b739 loosens (mainly due to bone resorption) with undesired displacement of the prosthesis in the direction of the load.
Attempts have therefore been made in recent years to use titanium fixtures anchored in the marrow cavity of the bone with the object of becoming osseo-integrated as described by Hagert et al. "Metacarpophalangal Joint Replacement with Osseo-integrated Endoprostheses" in Scand. J. Plast.
Reconstr. Surg. 20, pages 207-218, 1986. It is already known to permanently anchor oral and extraoral prostheses in bone tissue. This dental osseo-integration technique has been developed over the last 25 years by professor Branemark and his colleagues, with excellent results in applying fixtures in the jawbone to hold teeth or arch attachments. However, the experiments performed by Hagert to apply this technique to the reconstruction of finger joints has not fulfilled expectations. The unacceptable results are evidently due to the entirely different conditions encountered when using this "dental technique" in the prosthetic reconstruction of finger-joints. For example, in the known techniques, the fixture is anchored at right angles to the longitudinal axis of the bone. In the finger joint, the fixture is placed along the axis of the bone. Of course, this creates totally di~ferent loads and stresses on the anchoring elements.
Today, the main problem is orthopedic prosthesis surgery is still loosening of the bone anchoring unit. However, with a success rate for dental implants of more than 90~ over a 20 1 32673~
year period, a number of other problems arise which, so far, it has been unnecessary to take into account. One of the major problems is increased wear on the joint mechanism. A
different type of prosthesis design from that used hitherto 5 i8 re~uired if the osseo-integration method is to be applied.
To enable the joint mechanism to be replaced without disturbing the bone anchorage, the prosthesis system must be divided into components where the joint-mechanism element can be separated from the actual bone-anchoring element.
~urther, if the two-stage method is to be-used, it must be possible to connect the joint mechanism in the second stage if the patient, or at least the patient's reconstructed joint i8 not to be kept immobilized. Two factors must therefore be taken into account: First, the joint mechanism is subject to wear and tharefore must be replaceable. Second, to use the two stage method, the joint mechanism must be replac~able.
It has now surprisingly been found that the problems and drawbacks of the techniques described above can be eliminated or at least mitigated by the present invention.
The invention is based on ext~nsive experimental biological analysis of the structure and function of ~oints in the course of a disease or in defective state after wear or inflammatory decomposition of bone tissue and extensive studies of the vascular supply to the bone marrow. It has been established that, in the synthetic replacement of destroyad articular cartilage and ligament, bone and marrow i - 3 tissue must be treated as a structural and functional unit.
It is absolutely necessary to account for the cooperation between the bone and marrow tissue, particularly over a long period of time, if the hard tissue is to function as a support element.
The invention is thus based on the realization that, when anchoring a prosthetic replacement for a joint surface and ligament parts of the skeleton close to a joint, the interaction between bone marrow and bone tissue must be respectedO This means that an attachment element in the marrow cavity of a long bone must be anchored by mechanical elements which will permi~ communication between marrow and bone tissue along, as far as technically possible, the entire length of the anchoring element, paying particular attention to the boundary layer betwaen marrow and compact bone in the wall of the marrow cavity.
Thus, the invention is directed to an anchoring element for supporting a joint mechanism, wherein the anchoring element is substantially rotationally symmetrical, at least partially hollow, and includes a material which is compatible with the tissue of a bone. The anchoring element has a surface which can be at least partially osseo-integrated with the tissue to achieve permanent endosteal anchorage in the longitudinal axis of the bone. The invention is also directed to a reconstructed joint.
X
The invention is also directed to a method of applying .
an anchoring element with a bone, comprising: cutting the bone close to its joint to expose the marrow cavity of the bone; forming a æpace in the marrow cavity o~ the bone;
forming a space in the marrow cavity close to the ~oint;
applying a guide sleeve in the space; and screwing the anchoring element into the marrow cavity wh anchoring element guide sleeve to center the anchoring element.
Other features and advantages o~ the invention will become apparent from the following description of a preferred embodiment of the invention, with reference to the accompanying drawings.
Fig. 1 is a partial cross-sectional view of a rezonstructed finger joint with an anchoring elemenk in accordance with the invention;
Fig. 2 shows a fully reconstructed ~inger joint;
2~
Fig. 3 illustrates how the anchoring element is located in the long bone;
Fig. 4 is a perspective view of the anchoring element;
~5 Fig. 5 is a cross-sectional view along the line 5-5 of Fig. 4;
Fig. 6 is a partial cross-sectional view along the line 6-6 of Fig. 4, and illustrates a portion of the joint mechanism in accordance with the invention; and Fig. 7 illustrates the assembly of the joint mechanism to anchoring elements in accordance with the invention.
In Fig. l, the parts of a long bone on each side of a finger joint mechanism 1 are designated 2 and 3, respectively.
A rotationally symmetrical anchoring element 4 is formed of ~ hollow, substantially sleeve-like body 5 with external threading 6 and decreasing wall thickness. The open insertion end 7 of the body 5 tapers and is provided with slits 8 and 9 initiating from the open end 7.
The end 13 (Fig. 6) of the anchoring element 4 closest to the joint mechanism 1 i5 located in a guide sleeve 11.
~0 The quide sleeve 11 surrounds the joint end 13. The joint end 13 of the ~ody 5 is thus locked by a wedge effect against the inner surface 14 of the guide sleeve ll when the body 5 has been screwed sufficiently far into the bone tissue. The joint end 13 detachably receives connection parts 15 of the joint mech~nism 1. The connection parts 15 may be centered dowels (Fig. 7) protruding from the joint mechanism l. Such dowels cooperate with corresponding recesses 16 in the anchoring element 4 or a connection piece (not illustrated) arranged suitably between the guide sleeve 11 and the joint mechanism 1.
one or more holes may be directly connected with the radially outer surface of the anchoring element 4 r with the ~dges of the holes toward the surface forming cutting edges.
Self-tapping is thus achieved when the body 5 is screwed into the bone 2. The rPmoved bone tissue 17 is taken up inside the anchoring element 4 as illustrated in Fig. 5.
Since the thickness of the wall of the anchoring element 4 gradually decreases toward the insertion end 7 and/or since the element 4 has the longitudinal slits 8 and 9, the requirement for good deformation is fulfilled, thus greatly reducing the risk of concentrated stress which causes particular problems in prior art designs. The arrows B-B in Fig. l denote the flexibil~ty of the open end 7, i.e. its ability to adjust to the surrounding tissue. ~he same ~pplies to the arrows A-A.
The slits 8 and 9 may suitably be provided with cutting edges and, since the hollow cavity takes up tha shavings 17, as illustrated in Fig. 5, the anchoring element 4 is, in itself, its own preparation tool. ~t the same time, optimum conditions for normal anatomical and physiological situations are ensured such that disturbance of the remaining biological tissue, i.e. marrow and bone tissue, is minimized.
Fig. 2 shows the joint reconstruction achieved with the anchoring element 4 in place.
Fig. 3 illustrates how the anchoring element 4 is positioned in the bone 2. When in use, the anchoring element 4 is positioned in the boundary zone between marrow and bone tissue. The wall thickness of the sleeve-like body 5 decreases toward the slit insertion end 7, finishing in a cutting tapered edge 12. The edges of the longitudinal slits 8 may also be in the form of cutting edges. The shavings 17 produced when the anchoring element 4 is screwed into the marrow cavity are thus transferred to the hollow space inside the body 5 as illustrated in Fig. 5.
In operation, the part of the long bone 2 close to the joint is cut, thus exposing the marxow cavity. A probe ~not illustrated) is then inserted into the marrow cavity to localize a suitable longitudinal axis for insertion of the anchoring element 4. The probe is used as a direction finder to center the anchoring element 4 as desired. A recess for the guide sleeve 11 is then carefully drilled in the exposed cavity. After application of the guida-sleeve 11, the sleeve-like body 5 is screwed down into the marrow cavity through the guide sleeve 11. The probe has of course been previously removed. The joint end 13 of the anchoring element 4 widens somewhat outwardly and upwardly as illustrated at 18 such that its diameter is slightly larger than the lower opening of the guide sleeve 11. Thus, a wedga effect will finally occur between the joint end 13 and the 1 32673q guide sleeve 11 (when the sleeve 1~ is moved to the position.
illustrated in dotted lines in Fig. 6), so that both guide sleev~ 11 and sleeve-like body 5 are positioned as desixed.
The anchoring element 4 and the guide sleeve 11 consist of or axe manufactured of titanium or are coated with titanium. The structure of the titanium ~urface is such that, at least over part of the relevant surface, integration is promoted. Advantageously, the surface may have irregularities consisting of micro-pitting, as described in Swedish Patent No. 7902035-0, with pitting diameters of between 10 and 1000 nm, preferably 10-200 nm. Alternatively, the chemical composition of the titanium sur~ace layer may be given certain positive tissue reactions, as described in Swedish Patent No. 8505158-9, for instance.
~' ~b. _ ~ _
A preferred embodiment of the invention will be deæcribed in detail in the following with reference to the reconstruction of a finger joint. However, the invention is not limited thereto. The invention can be used for other similar joints, such as toe joints, elbow joints, and so on.
~he invention can also be used in reconstructions after amputation or other defects.
Finger-joint reconstructions, entailing prostheses, are primarily carried out on MCP joints which have become rheumatically changed. Prostheses known for this purpose include Swanson Silastic finger joints. Such joints consist of a material similar to silicon, are elongate in shape, and have ends with substantially circular cross sections. The ends can be substantially circular cross sections. The ends can be fitted and anchored into the marrow cavity of each bone. The central portion o~ the prosthesis is elastically deformable and thus constitutes the actual joint mechanism.
The St. George prosthesis, a cemented prosthesis, is 2~ also known for finger-joint reconstructions.
A problem with these conventional prostheses is that the anchoring element supporting the actual prosthesis mechanism ~ 3~b739 loosens (mainly due to bone resorption) with undesired displacement of the prosthesis in the direction of the load.
Attempts have therefore been made in recent years to use titanium fixtures anchored in the marrow cavity of the bone with the object of becoming osseo-integrated as described by Hagert et al. "Metacarpophalangal Joint Replacement with Osseo-integrated Endoprostheses" in Scand. J. Plast.
Reconstr. Surg. 20, pages 207-218, 1986. It is already known to permanently anchor oral and extraoral prostheses in bone tissue. This dental osseo-integration technique has been developed over the last 25 years by professor Branemark and his colleagues, with excellent results in applying fixtures in the jawbone to hold teeth or arch attachments. However, the experiments performed by Hagert to apply this technique to the reconstruction of finger joints has not fulfilled expectations. The unacceptable results are evidently due to the entirely different conditions encountered when using this "dental technique" in the prosthetic reconstruction of finger-joints. For example, in the known techniques, the fixture is anchored at right angles to the longitudinal axis of the bone. In the finger joint, the fixture is placed along the axis of the bone. Of course, this creates totally di~ferent loads and stresses on the anchoring elements.
Today, the main problem is orthopedic prosthesis surgery is still loosening of the bone anchoring unit. However, with a success rate for dental implants of more than 90~ over a 20 1 32673~
year period, a number of other problems arise which, so far, it has been unnecessary to take into account. One of the major problems is increased wear on the joint mechanism. A
different type of prosthesis design from that used hitherto 5 i8 re~uired if the osseo-integration method is to be applied.
To enable the joint mechanism to be replaced without disturbing the bone anchorage, the prosthesis system must be divided into components where the joint-mechanism element can be separated from the actual bone-anchoring element.
~urther, if the two-stage method is to be-used, it must be possible to connect the joint mechanism in the second stage if the patient, or at least the patient's reconstructed joint i8 not to be kept immobilized. Two factors must therefore be taken into account: First, the joint mechanism is subject to wear and tharefore must be replaceable. Second, to use the two stage method, the joint mechanism must be replac~able.
It has now surprisingly been found that the problems and drawbacks of the techniques described above can be eliminated or at least mitigated by the present invention.
The invention is based on ext~nsive experimental biological analysis of the structure and function of ~oints in the course of a disease or in defective state after wear or inflammatory decomposition of bone tissue and extensive studies of the vascular supply to the bone marrow. It has been established that, in the synthetic replacement of destroyad articular cartilage and ligament, bone and marrow i - 3 tissue must be treated as a structural and functional unit.
It is absolutely necessary to account for the cooperation between the bone and marrow tissue, particularly over a long period of time, if the hard tissue is to function as a support element.
The invention is thus based on the realization that, when anchoring a prosthetic replacement for a joint surface and ligament parts of the skeleton close to a joint, the interaction between bone marrow and bone tissue must be respectedO This means that an attachment element in the marrow cavity of a long bone must be anchored by mechanical elements which will permi~ communication between marrow and bone tissue along, as far as technically possible, the entire length of the anchoring element, paying particular attention to the boundary layer betwaen marrow and compact bone in the wall of the marrow cavity.
Thus, the invention is directed to an anchoring element for supporting a joint mechanism, wherein the anchoring element is substantially rotationally symmetrical, at least partially hollow, and includes a material which is compatible with the tissue of a bone. The anchoring element has a surface which can be at least partially osseo-integrated with the tissue to achieve permanent endosteal anchorage in the longitudinal axis of the bone. The invention is also directed to a reconstructed joint.
X
The invention is also directed to a method of applying .
an anchoring element with a bone, comprising: cutting the bone close to its joint to expose the marrow cavity of the bone; forming a æpace in the marrow cavity o~ the bone;
forming a space in the marrow cavity close to the ~oint;
applying a guide sleeve in the space; and screwing the anchoring element into the marrow cavity wh anchoring element guide sleeve to center the anchoring element.
Other features and advantages o~ the invention will become apparent from the following description of a preferred embodiment of the invention, with reference to the accompanying drawings.
Fig. 1 is a partial cross-sectional view of a rezonstructed finger joint with an anchoring elemenk in accordance with the invention;
Fig. 2 shows a fully reconstructed ~inger joint;
2~
Fig. 3 illustrates how the anchoring element is located in the long bone;
Fig. 4 is a perspective view of the anchoring element;
~5 Fig. 5 is a cross-sectional view along the line 5-5 of Fig. 4;
Fig. 6 is a partial cross-sectional view along the line 6-6 of Fig. 4, and illustrates a portion of the joint mechanism in accordance with the invention; and Fig. 7 illustrates the assembly of the joint mechanism to anchoring elements in accordance with the invention.
In Fig. l, the parts of a long bone on each side of a finger joint mechanism 1 are designated 2 and 3, respectively.
A rotationally symmetrical anchoring element 4 is formed of ~ hollow, substantially sleeve-like body 5 with external threading 6 and decreasing wall thickness. The open insertion end 7 of the body 5 tapers and is provided with slits 8 and 9 initiating from the open end 7.
The end 13 (Fig. 6) of the anchoring element 4 closest to the joint mechanism 1 i5 located in a guide sleeve 11.
~0 The quide sleeve 11 surrounds the joint end 13. The joint end 13 of the ~ody 5 is thus locked by a wedge effect against the inner surface 14 of the guide sleeve ll when the body 5 has been screwed sufficiently far into the bone tissue. The joint end 13 detachably receives connection parts 15 of the joint mech~nism 1. The connection parts 15 may be centered dowels (Fig. 7) protruding from the joint mechanism l. Such dowels cooperate with corresponding recesses 16 in the anchoring element 4 or a connection piece (not illustrated) arranged suitably between the guide sleeve 11 and the joint mechanism 1.
one or more holes may be directly connected with the radially outer surface of the anchoring element 4 r with the ~dges of the holes toward the surface forming cutting edges.
Self-tapping is thus achieved when the body 5 is screwed into the bone 2. The rPmoved bone tissue 17 is taken up inside the anchoring element 4 as illustrated in Fig. 5.
Since the thickness of the wall of the anchoring element 4 gradually decreases toward the insertion end 7 and/or since the element 4 has the longitudinal slits 8 and 9, the requirement for good deformation is fulfilled, thus greatly reducing the risk of concentrated stress which causes particular problems in prior art designs. The arrows B-B in Fig. l denote the flexibil~ty of the open end 7, i.e. its ability to adjust to the surrounding tissue. ~he same ~pplies to the arrows A-A.
The slits 8 and 9 may suitably be provided with cutting edges and, since the hollow cavity takes up tha shavings 17, as illustrated in Fig. 5, the anchoring element 4 is, in itself, its own preparation tool. ~t the same time, optimum conditions for normal anatomical and physiological situations are ensured such that disturbance of the remaining biological tissue, i.e. marrow and bone tissue, is minimized.
Fig. 2 shows the joint reconstruction achieved with the anchoring element 4 in place.
Fig. 3 illustrates how the anchoring element 4 is positioned in the bone 2. When in use, the anchoring element 4 is positioned in the boundary zone between marrow and bone tissue. The wall thickness of the sleeve-like body 5 decreases toward the slit insertion end 7, finishing in a cutting tapered edge 12. The edges of the longitudinal slits 8 may also be in the form of cutting edges. The shavings 17 produced when the anchoring element 4 is screwed into the marrow cavity are thus transferred to the hollow space inside the body 5 as illustrated in Fig. 5.
In operation, the part of the long bone 2 close to the joint is cut, thus exposing the marxow cavity. A probe ~not illustrated) is then inserted into the marrow cavity to localize a suitable longitudinal axis for insertion of the anchoring element 4. The probe is used as a direction finder to center the anchoring element 4 as desired. A recess for the guide sleeve 11 is then carefully drilled in the exposed cavity. After application of the guida-sleeve 11, the sleeve-like body 5 is screwed down into the marrow cavity through the guide sleeve 11. The probe has of course been previously removed. The joint end 13 of the anchoring element 4 widens somewhat outwardly and upwardly as illustrated at 18 such that its diameter is slightly larger than the lower opening of the guide sleeve 11. Thus, a wedga effect will finally occur between the joint end 13 and the 1 32673q guide sleeve 11 (when the sleeve 1~ is moved to the position.
illustrated in dotted lines in Fig. 6), so that both guide sleev~ 11 and sleeve-like body 5 are positioned as desixed.
The anchoring element 4 and the guide sleeve 11 consist of or axe manufactured of titanium or are coated with titanium. The structure of the titanium ~urface is such that, at least over part of the relevant surface, integration is promoted. Advantageously, the surface may have irregularities consisting of micro-pitting, as described in Swedish Patent No. 7902035-0, with pitting diameters of between 10 and 1000 nm, preferably 10-200 nm. Alternatively, the chemical composition of the titanium sur~ace layer may be given certain positive tissue reactions, as described in Swedish Patent No. 8505158-9, for instance.
~' ~b. _ ~ _
Claims (11)
1. A substantially rotationally symmetrical and at least partially hollow anchoring element for supporting a joint mechanism, comprising a sleeve-like body with a radial outer surface with external threads for screwing said element into a bone, said element comprising a material compatible with bone tissue to achieve permanent endosteal anchorange in a longitudinal axis of the bone, said element at its end proximal to said joint mechanism comprising a radially extending flange, wherein said element is arranged to be insertable with its distal end into a guide sleeve until abutment of said flange with said guide sleeve.
2. The anchoring element of claim 1, wherein abutment is between a distal face of said flange and a radially extending face of said guide sleeve.
3. The anchoring element of claim 1, wherein a joint between a distal face of said flange and the outer surface of said sleeve-like body is rounded and arranged for wedge-like cooperation with said guide sleeve.
4. The anchoring element of claim 1, wherein a wall thickness of said sleeve-like body decreases towards its distal end.
5. The anchoring element according to claim 4, further comprising, at its insertion end distal to said joint mecha-nism, slits proximally extending from said end.
6. The anchoring element according to claim 5, wherein said slits have cutting edges.
7. The anchoring element according to claim 1, further comprising holes directly connected to said radial outer surface, said holes having cutting edges at said radial outer surface.
8. The anchoring element according to claim 1, wherein said sleeve-like body is deformable.
9. The anchoring element according to claim 1, wherein the proximal end of said element to said joint mechanism is open in an axial direction for receiving a connecting portion of said joint mechanism for detachably applying said joint mechanism to said anchoring element.
10. The anchoring element of any one of claims 1 to 9, wherein said material is titanium.
11. Use of an anchoring element of any one of claims 1 to 9, in osteo-surgery.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CA000616791A CA1334884C (en) | 1989-04-25 | 1994-01-10 | Anchoring element for supporting a joint mechanism of a finger or other reconstructed joint |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
SE8901508A SE466936B (en) | 1989-04-25 | 1989-04-25 | ANCHORING ELEMENT FOR PROCESSING |
SE8901508-5 | 1989-04-25 |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA000616791A Division CA1334884C (en) | 1989-04-25 | 1994-01-10 | Anchoring element for supporting a joint mechanism of a finger or other reconstructed joint |
Publications (1)
Publication Number | Publication Date |
---|---|
CA1326739C true CA1326739C (en) | 1994-02-08 |
Family
ID=20375795
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA000613216A Expired - Fee Related CA1326739C (en) | 1989-04-25 | 1989-09-26 | Anchoring element for supporting a joint mechanism of a finger or other reconstructed joint |
CA000616791A Expired - Fee Related CA1334884C (en) | 1989-04-25 | 1994-01-10 | Anchoring element for supporting a joint mechanism of a finger or other reconstructed joint |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA000616791A Expired - Fee Related CA1334884C (en) | 1989-04-25 | 1994-01-10 | Anchoring element for supporting a joint mechanism of a finger or other reconstructed joint |
Country Status (6)
Country | Link |
---|---|
US (1) | US5062851A (en) |
KR (1) | KR970007086B1 (en) |
CA (2) | CA1326739C (en) |
MX (1) | MX173835B (en) |
SE (1) | SE466936B (en) |
ZA (1) | ZA903084B (en) |
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-
1989
- 1989-04-25 SE SE8901508A patent/SE466936B/en not_active IP Right Cessation
- 1989-09-13 US US07/406,586 patent/US5062851A/en not_active Expired - Fee Related
- 1989-09-26 CA CA000613216A patent/CA1326739C/en not_active Expired - Fee Related
-
1990
- 1990-04-24 ZA ZA903084A patent/ZA903084B/en unknown
- 1990-04-24 MX MX2043390A patent/MX173835B/en unknown
- 1990-04-25 KR KR1019900005835A patent/KR970007086B1/en not_active IP Right Cessation
-
1994
- 1994-01-10 CA CA000616791A patent/CA1334884C/en not_active Expired - Fee Related
Also Published As
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ZA903084B (en) | 1991-02-27 |
SE466936B (en) | 1992-05-04 |
SE8901508D0 (en) | 1989-04-25 |
KR970007086B1 (en) | 1997-05-02 |
SE8901508A (en) | 1990-10-26 |
US5062851A (en) | 1991-11-05 |
CA1334884C (en) | 1995-03-28 |
MX173835B (en) | 1994-03-30 |
KR900015695A (en) | 1990-11-10 |
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