Search Images Maps Play YouTube News Gmail Drive More »
Sign in
Screen reader users: click this link for accessible mode. Accessible mode has the same essential features but works better with your reader.

Patents

  1. Advanced Patent Search
Publication numberUS3816855 A
Publication typeGrant
Publication dateJun 18, 1974
Filing dateMay 30, 1972
Priority dateJun 1, 1971
Also published asDE2226541A1, DE2226541C2
Publication numberUS 3816855 A, US 3816855A, US-A-3816855, US3816855 A, US3816855A
InventorsB Saleh
Original AssigneeNat Res Dev
Export CitationBiBTeX, EndNote, RefMan
External Links: USPTO, USPTO Assignment, Espacenet
Knee joint prosthesis
US 3816855 A
Abstract
A prosthetic knee joint device comprises a femoral component in the form of a shell member having two condylar portions with major convex bearing surfaces areas, which portions are bridged at one end by a portion defining a trough between the convex areas. An associated tibial component has similar portions in a platform bearing member defining major concave bearing surface areas and a ridge therebetween. The convex bearing areas are longer than the concave bearing areas and generally U-shaped longitudinally to simulate the corresponding shaping in the natural joint from which the shell member can in fact be derived. The concave bearing areas however simulate the menisci of the natural joint different phases of rotation to provide an optimized congruity between the bearing surfaces during rotation of the predetermined geometry of the prosthesis as compared to the variable geometry in the natural joint.
Images(4)
Previous page
Next page
Claims  available in
Description  (OCR text may contain errors)

United States Patent [191 Saleh 1 June 18, 1974 KNEE JOINT PROSTHESIS [75] Inventor: Bahaa Botros Seedhom Saleh,

Leeds, England [30] Foreign Application Priority Data June 1, 1971 Great Britain 18278/71 [52] U.S. Cl 1. 3/1, 128/92 C, 264/222,

264/D1G. 30 [51] Int. Cl. A6lf l/24 [58] Field of Search..... 3/1; 128/92 C, 92 CA, 92 R [56] References Cited UNITED STATES PATENTS 2,668,531 2/1954 Haboush 128/92 CA FOREIGN PATENTS OR APPLICATIONS 1,047,640 7/1953 France l28/92C OTHER PUBLICATIONS M.G.H. Femoral Condyle Replacements (NO. 6662), Vitallium Surgical Appliances Catalog, Austenal Company, New York, N.Y., page 62, 1964.

Acrylic Prosthesis Replacing Lower End of the Fcmur For Benign Giant-Cell Tumor by G. L. Kraft et al., Journal of Bone & Joint Surgery, Vol. 36-A,

No. 2, Apr. 1954, pages 368374.

Developments In Total Hip Joint Replacement by G. K. McKee, Proceedings of the Institution of Mechanical Engineers, Vol. 181, part 31, 1966-1967, pages 8589.

Primary Examiner-Richard A. Gaudet Assistant Examiner-Ronald L. Frinks Attorney, Agent, or Firm-Cushman, Darby & Cushman 57 ABSTRACT A prosthetic knee joint device comprises a femoral component in the form of a shell member having two condylar portions with major convex bearing surfaces areas, which portions are bridged at one end by a portion defining a trough between the convex areas. An associated tibial component has similar portions in a platform bearing member defining major concave bearing surface areas and a ridge therebetween. The convex bearing areas are longer than the concave bearing areas and generally U-shaped longitudinally to simulate the corresponding shaping in the natural joint from which the shell member can in fact be derived. The concave bearing areas however simulate the menisci of the natural joint different phases of rotation to provide an optimized congruity between the bearing surfaces during rotation of the predetermined geometry of the prosthesis as compared to the variable geometry in the natural joint.

9 Claims, 23 Drawing Figures WWW 18 mm (1816 856 SHEET 1 UF PATENTEB l I 8 i974 SHEET 2 BF 4 PATENTEUJUM 1 a new SHEET 3 BF 4 1 KNEE JOINT PROSTHESIS Various proposals have been made for knee joint prostheses in the past with varying degrees of success in practice. The more successful proposals, in terms of alleviation of pain and long term provision of a useful range of flexion, have involved hinge devices. However, these last devices are not fully satisfactory in that they invariably involve the removal of the natural ligaments and the patella, and, while such devices have their place when the ligaments have deteriorated beyond possible preservation, it is frequently only the condition of the cartilage and the adjacent underlying bone layers which give rise to the need for surgery.

An object of the present invention is to alleviate this situation.

According to one aspect of the present invention, there is provided a prosthetic knee joint device comprising:

a femoral component including a shell bearing member having two first elongate portions and a first bridge portion,

said first elongate portions each being of generally U-shaped form in the longitudinal direction, and generally dished form in the lateral direction, and the curvatures of such forms being of the same sense to provide a major surface of overall convex curvature for each of said first elongate portions,

said first elongate portions being disposed in spaced side-by-side longitudinal relation,

and said first bridge portion integrating said first elongate portions in continuous manner partway along the U-bases and along one pair of corresponding U- arms thereof;

and a tibial component including a platform bearing member having two second elongate portions and a second bridge portion,

said second elongate portions each having a major surface of generally dished form in both the longitudinal and lateral directions to provide overall concave curvature,

said second elongate portions being disposed in spaced side-by-side longitudinal relation,

and said second bridge portion integrating said second elongate portions in continuous manner partway therealong from one pair of corresponding ends;

and wherein the major surfaces of said components opposite to said convex and concave surfaces are adapted for respective fixation to the femur and tibia.

In use of the proposed device, the femoral component replaces the bearing area of the femoral condyles, on the one hand, and the tibial component replaces the lateral and medial menisci together with an area of the tibial condyles, on the other hand. For this purpose the menisci and appropriate parts of the femoral and tibial condyles are removed, and the respective components secured to dispose the same in mutual bearing relationship with their bridge portions generally superposed in the anterior aspect and their non-bridged elongate portion convex and concave surfaces engaged for mutual sliding and rotation along the longitudinal directions thereof.

Regarding the more particular geometry of the de- 6 vice: the convex bearing surfaces of the femoral component simulates the femoral condyles and, in fact, it is preferred that such surfaces closely follow the natural shaping of the condyles. Similarly, it is preferred that the corresponding surface of the associated bridge portion should define a trough between the convex bearing surfaces to simulate, and again preferably follow, the natural form of the inter-condylar trough which receives and guides the patella and associated tendon.

The concave bearing surfaces of the tibial component, on the other hand, do not follow the natural form of the tibial condyles since the latter are not markedly concave in the natural joint, but rather the medial one tends to a flat form and the lateral one to a convex form. Thus, very high stresses would result from direct engagement between natural condyle shaping for each of the engaging surfaces of the prosthesis, with inevitable failure in use. In the present device, the bearing surface form of the tibial component largely follows that of the menisci which are concave and engage the femoral condyles in the natural joint. Even then, the shaping of the menisci varies with the degree of flexion in the natural joint, and to simulate one phase of the menisci with a prosthetic part of fixed shaping would also give rise to undesirably high stresses when the femoral component was in a position corresponding to a degree of flexion other than that for which the menisci shaping had been simulated. For this reason, in a preferred form of the invention, the concave bearing surfaces of the tibial component follow shapings developed from thatof the menisci in different phases to provide enhanced congruity and reduce stress between it and the associated femoral part when in use together.

More specifically, according to another aspect of the invention there is provided a method of making a prosthetic knee joint device including a femoral component and a tibial component having respective bearing surfaces for mutual sliding and rotational bearing engagement, which method comprises:

making a first former with two side-by-side spaced elongate convex bearing surface areas respectively closely conforming to the surface shapes of the femoral condyles of a natural knee joint; making a second former with two side-by-side spaced elongate concave bearing surface areas respectively closely conforming to shapes developed from the menisci of said joint in different phases of rotation thereof, with one pair of corresponding end portions of said concave areas respectively closely conforming to the surface shapes of the anterior aspect of said menisci when said joint is in a rotational phase of relatively full extension, the other pair of corresponding ends of said concave areas similarly conforming to the surface shapes of the posterior aspect of said menisci when said joint is in a rotational phase of relatively full flexion, and intermediate portions of said concave areas being developed to smoothly bridge said ends portions;

smoothing said convex and concave bearing surface areas to provide optimised congruity therebetween in said bearing engagement;

making from said first and second formers respective moulds for said femoral and tibial components; and

casting said components in said moulds.

In order that the invention may be more fully understood, the same will now be described by way of example with reference to the accompanying drawings. in which:

FIGS. 1 and 2 diagrammatically illustrate, in one side view, femoral and tibial components of the natural knee joint in extension and flexion, respectively,

FIGS. 3 and 4 similarly illustrate the same components in the opposite side view,

FIG. 5 diagrammatically illustrates tibial components in a superior view associated with FIGS. 1 and 2,

FIGS. 6 to II illustrate the femoral component of one embodiment of the present invention in respective plan (inferior) view, inverted plan (superior) view, one side (medial) view, the other side (lateral) view, front (anterior) view, and rear (posterior) view, the bracketed terms indicating the sense of these views in medical terminology relative to the leg,

FIGS. 12 to 1'7 similarly illustrate the associated tibial component of the same embodiment, except that in this instance the plan and inverted plan views respectively represent the superior and inferior views, and

FIGS. 18 to 23 respectively illustrate the tibial component in cross-sectional views taken at II to VI--VI.

Referring to the drawings more particularly: FIGS. 1 and 2 are schematic views in the lateral aspect and show the femoral condyles at 1, the tibial condyles at 2, and the lateral meniscus at 3. These views show the joint in different phases of rotation, in which the joint is in maximum extension and maximum flexion, respectively, and clearly indicate the large excursion (normally of the order of 10 mm) of the lateral meniscus and associated change of superior form which occurs between these positions.

FIGS. 3 and 4 illustrate corresponding rotational phase views in the medial aspect direction to indicate the corresponding, but smaller (normally of the order of 2mm), excursion and associated change in superior form of the medial meniscus 4.

FIG. 5 indicates these excursions in the menisci after notionally fixing the anterior aspects of the menisci at maximum extension and the posterior aspects at maximum flexion, with resultant gaps in the menisci being indicated at 3a and 4a. FIG. 5 also indicates the anterior and posterior cruciate ligaments at 5 and 6.

The femoral component of FIGS. 6 to 11 comprises a shell bearing member 10 having two elongate portions 11 and 12 and a bridge portion 13. The elongate portions I1 and 12 are each of generally U-shaped form in the longitudinal direction and generally dished form in the lateral direction to provide a major surface of overall convex curvature. These major surfaces of the portions 11 and I2 serve as bearing surfaces to respectively replace the corresponding function of the femoral, lateral and medial condyles. For this purpose the portions l1 and 12 are disposed in spaced side-byside relation. The portions 11 and 12 are held in such relationship by the bridge portion 13 which integrates the same in continuous manner partway along the U- bases and one pair of corresponding U-arms.

The pair of U-arms in question are those which represent the anterior end portions of the femoral condylar bearing surfaces, and the bridge portion is shaped to define a trough between the portions 1 1 and 12 relative to their convex curvature. This trough also serves as a bearing surface to replace the corresponding function of the similar trough in the natural joint which guides the patella and associated tendon.

In its preferred form, as illustrated, the bearing surfaces of the shell member of the femoral component closely conform to the natural shapings of the corresponding parts of the knee joint and these shapings are such that the member will be normally most conveniently produced by casting. A mould for this purpose can be developed from a former in which the relevant surfaces are derived by direct moulding from the femur of a natural joint.

The remaining parts of the illustrated femoral component are those concerned with its fixation. This is intended to be by use of acrylic resin or other gap-filling agents or cements such as used with bone joint prostheses and, in this connection, the concave surface areas of the elongate portions 11 and 12, and the associated rear surface of the bridge portion 13, are formed with a plurality of relatively short studs 14. These studs serve to space the main body component from the cancellous bone of a suitably prepared femur to allow flow of resin therebetween over a sufficient area and to an adequate thickness to afford good securement. Also, the studs enhance the securement by providing a key between the component and the cement.

The associated tibial component of FIGS. 12 to 23 comprises a platform bearing member 20 which also has two elongate portions 21 and 22, and a bridge portion 23. The portions 21 and 22 each have a major surface of generally dished form in both the longitudinal and lateral directions to provide overall concave curvature. These major surfaces serve as bearing surfaces to respectively replace the corresponding function of the lateral and medial menisci and tibial condyles, and to co-operate with the convex bearing surfaces of the illustrated femoral component. Accordingly, the portions 21 and 22 are held in spaced side-by-side relation by the bridge portion 23 which integrates the same in continuous manner partway therealong from one pair of corresponding ends. The corresponding ends in question represent the anterior part of the component and the bridge portion is shaped to define a ridge between the concave dished surfaces, which ridge extends into the trough of the associated femoral component when the two components are engaged in bearing relation in a position representing maximum extension. This position can be envisaged from the four pairs of FIGS. 8 and 14, 9 and l5, l0 and 16 and 11 and 17, which show the components in their respective dispositions for this position, but separated in the longitudinal direction of the relevant leg.

Also, it is to be noted that the bridge portion 23 does not depend below the bearing surface areas of the tibial component to the same extent as the elongate portions 21 and 22, but is relieved to provide a cavity 24 therebelow.

Regarding fixation of the tibial component:

This also involves use of a resin or cement as used for the femoral component, although in this instance it is preferred to afford spacing and keying by the provision of grooves 25 over the non-concave major surfaces of the elongate portions 21 and 22. These grooves are preferably of dovetail cross-sectional form to provide an enhanced key, and are also preferably aligned with both the longitudinal and lateral directions of their respective elongate portions to provide a crosshatched effect.

In addition, a central part of each grooved area extends further than the remainder of such area to provide a plateau 26. This has a similar spacing function to the studs 14 of the femoral component in ensuring an adequate layer of resin or cement below the tibial component as well as entry of such material into the grooves.

In its preferred form, as illustrated, the bearing surfaces of the tibial component closely conform to those of the menisci in FIG. 3 with the gaps 3a and 4a effectively reconstructed. Thus, one pair of corresponding ends of the concave bearing surface areas respectively closely conform to the surface shapes of the anterior portions of the menisci of the natural joint when the joint is in a rotational phase of relatively small flexion angle, the other pair of corresponding ends of such areas similarly conform to the surface shapes of the menisci when the joint is in a rotational phase of relatively large fiexion angle, and intermediate portions of such areas conform to developments smoothly bridging said anterior and posterior portions. As with the femoral component, such shaping in the tibial component will be normally best achieved by use of casting techniques. A suitable former from which the desired shaping can be obtained has been produced from a natural joint on which a menisectomy was first carried out, leaving all of the ligaments intact. Then a wax was poured into the joint space with the joint at full extension. After at least peripheral setting, the wax was heated at the rear and side regions of the joint, and the joint flexed to generate a fixed surface which had the maximum effective congruence with the femoral condyles throughout the range of flexion.

While the femoral and tibial components can be cast from moulds produced, as described above, from formers which are directly moulded from a natural joint, it is preferred that the bearing surface areas of the moulds, and so of the cast components, be idealized. Thus all undulations resulting from the presence of cartilage should be smoothed, the indentations of the menisci on the natural femoral condyles are not reproduced, and a mutual lapping operation in production of the relevant moulds is effected to provide an optimized fit. Also, it will be normally appropriate to extend the bridge portion of the femoral component to ensure the provision of a bearing surface for the patella in the final degrees of extension.

Features of the final shaping which can be appreciated from the drawings are that the condylar bearing surfaces of the femoral component follow smooth generally spiral curves in their longitudinal directions with increasing radius of curvature from back to front, while the corresponding curvatures of the tibial component are more uniform. More particularly, the components have greater congruity at the front than the rear when engaged in bearing relation in the position corresponding to full extension. Indeed the components are highly congruous, both longitudinally and laterally, in this position in their front parts and bridge portions. This reduces stresses when standing and also assists positioning of the tibial component relative to the femoral component during implantation.

Also, the longitudinal directions of the elongate portions of the femoral component, and those of the tibial component similarly, diverge from their bridged ends by an angle of about as do the natural condyles. This enhances antero-posterior stability.

The invention is, of course, not intended to be limited to the form which has been more particularly described with reference to the drawings, but can be varied within the scope of the appendant claims. For example, either of the femoral and tibial components can be provided with suitably located grooves or ribbed formations, studs, spikes, stems, or other fixation formations or members. Indeed, in a presently proposed modification, the majority of the studs of the femoral component are to be replaced by a pair of intracondylar webs extending partway along the longitudinal directions of the respective elongate portions, generally centrally of the bridged parts thereof, while retaining one or two studs at the other ends thereof.

Also, the components can be made in any materials suited to the purpose, although the present preference is for a metal/plastics material combination for the respective components. More particularly, the present preference is that the femoral component be of a metal such as chrome/cobalt alloy, and that the tibial component be of a plastics material such as high density polyethylene.

Lastly, it is useful to mention practical advantages of the device of the invention. Since the bearing surfaces closely simulate those of the natural joint, the former can afford a range of fiexion and extension closely approximating that of the latter. The use of shell and platform bearing members does not involve removal of large amounts of bone from the natural joint as is commonly the case with hinged forms of knee joint prostheses. Also, the proposed device need not involve the use of long intramedullary stems or like members for the purposes of fixation, and so obviates the need for lengthy excursions of foreign material into and along the medullary canals. These last two points mean that the device can, if the need arises, be removed without undue difficulty after implantation and, more important, still afford the possibility of alternative remedial action such as use of another form of joint prosthesis (including a hinge device), or arthrodesis. These possibilities are significantly reduced if large amounts of bone are removed in an initial remedial action.

Further factors of advantage are that all of the natural ligaments, and also the patella, can be retained.

I claim:

1. A prosthetic knee joint device comprising:

a femoral component including a shell bearing member having two first elongate portions and a first bridge portion, said first elongate portions each being of generally U-shaped form in the longitudinal direction and generally dished form in the late ral direction, and the curvatures of such forms being of the same sense to provide a smooth major surface of overall convex curvature for each of said first elongate portions, said first elongate portions being disposed in spaced side-by-side longitudinal relation, said first bridge portion integrating said first elongate portions in continuous manner partway along the U-bases and along one pair of cone sponding U-arms thereof, and said major convex surfaces follow a generally spiral curvature in their longitudinal directions with increasing radius of curvature towards their non-bridged ends,

and a tibial component including a platform bearing member having two second elongate portions and a'second bridge portion,

said second elongate portions each having a major surface of generally dished form in both the longitudinal and lateral directions to provide smooth overall concave curvature,

said second elongate portions being disposed in spaced side-by-side longitudinal relation;

said second bridge portion integrating said second elongate portions in continuous manner partway therealong from one pair of corresponding ends,

and said major concave surfaces follow a more uniform curvature in their longitudinal directions than do said major convex surfaces, with said major concave surfaces being more congruous with the bridged ends of said major convex surfaces,

said femoral and tibial components being disposed in mutual bearing relationship with their respective bridge portions generally superposed and their respective non-bridged elongate portion convex and concave surfaces engaged for mutual sliding and rotation along the longitudinal directions thereof;

and wherein the major surfaces of said components opposite to said convex and concave surfaces are adapted by the provision of shallow configurations thereon for respective fixation to the femur and tibia by a gap-filling agent.

2. A device according to claim 1 wherein said first bridge portions defines a first trough, relative to said convex curvature, between said first elongate portions integrated thereby; and said second bridge portion defines a ridge relative to said concave curvature, between said second elongate portions integrated thereby.

3. A device according to claim 1 wherein said convex surfaces are generally divergent in their longitudinal directions from their bridged ends, and said concave areas are similarly divergent.

4. A device according to claim 1 wherein said femoral component is adapted for fixation to the femur with a gap-filling agent by the provision of a plurality of relatively short members projecting from the major surface thereof opposite to said convex surfaces.

5. A device according to claim 1 wherein said tibial component is adapted for fixation to the tibia with a gap-filling agent by the provision of a grooved formation on the major surface thereof opposite to said concave surfaces.

6. A device according to claim 5 wherein each groove of said grooved formation has a dovetail crosssectional form.

7. A device according to claim 5 wherein said grooved formations define generally central regions of the respective surfaces of said second elongate portions which central regions extend further than the remainder of such surfaces to define plateaus.

8. A device according to claim 1 wherein said femoral and tibial components are respectively made of metal and plastics material.

9. A prosthetic knee joint device, comprising a femoral component and a tibial component;

the femoral component being a shell having two laterally spaced convex bearing surfaces respectively closely conforming to the surface shapes and spatial orientation of the femoral condyles of the natural knee joint, and having a trough portion bridging between the two bearing surfaces adjacent their respective convergent ends for receiving and guiding the patella and associated tendon should these be retained;

the tibial component being a platform having two laterally spaced concave bearing surfaces closely conforming to shapes developed from menisci of the natural knee joint in a plurality of different phases of rotation thereof, with one pair of corresponding end portions of said concave bearing surfaces respectfully closely conforming to the surface shapes of the anterior aspect of said menisci when said natural knee joint is in a rotational phase of relatively full extension, the other pair of corresponding ends of said concave bearing surfaces similarly conforming to the surface shapes of the posterior aspect of said menisci when said natural knee joint is in a phase of relatively full flexion, and intermediate portions of said concave bearing surfaces between the respective ends smoothly bridging therebetween, said concave bearing surfaces being dished both longitudinally and laterally, the corresponding anterior end portions of said platform being held in spaced, side-by-side relation by a bridge portion which forms a ridge between the concave dished surfaces and extends into the trough of said femoral component when these two components are engaged in a bearing relation representing maximum extension;

the convex bearing areas being longer than the concave bearing areas and being generally U-shaped longitudinally and low relief protuberance and recess means formed on the reverses of the two components from the bearing surfaces, for keying, spacing and permitting resin fixation of the compo nents without need for removal of so large amounts of bone from the natural knee joint of the patient as is generally the case with hinged forms of knee joint prostheses and without lengthy excursions of foreign material along the medullary canals.

Patent Citations
Cited PatentFiling datePublication dateApplicantTitle
US2668531 *Feb 15, 1952Feb 9, 1954Haboush Edward JProsthesis for hip joint
FR1047640A * Title not available
Non-Patent Citations
Reference
1 *Acrylic Prosthesis Replacing Lower End of the Femur For Benign Giant Cell Tumor by G. L. Kraft et al., Journal of Bone & Joint Surgery, Vol. 36 A, No. 2, Apr. 1954, pages 368 374.
2 *Developments In Total Hip Joint Replacement by G. K. McKee, Proceedings of the Institution of Mechanical Engineers, Vol. 181, part 3J, 1966 1967, pages 85 89.
3 *M.G.H. Femoral Condyle Replacements (NO. 6662), Vitallium Surgical Appliances Catalog, Austenal Company, New York, N.Y., page 62, 1964.
Referenced by
Citing PatentFiling datePublication dateApplicantTitle
US3964106 *Mar 3, 1975Jun 22, 1976Physical Systems, Inc.Three-part total knee prosthesis
US4081866 *Feb 2, 1977Apr 4, 1978Howmedica, Inc.Total anatomical knee prosthesis
US4094017 *Feb 16, 1977Jun 13, 1978Larry Stanford MatthewsKnee joint prosthesis with patellar-femoral contact
US4178641 *Dec 1, 1977Dec 18, 1979Schutt and Grundei O.H.G.Knee-joint-endoprothese
US4207627 *Jan 18, 1979Jun 17, 1980Cloutier Jean MarieKnee prosthesis
US4215439 *Oct 16, 1978Aug 5, 1980Zimmer, USASemi-restraining knee prosthesis
US4344193 *Nov 28, 1980Aug 17, 1982Kenny Charles HMeniscus prosthesis
US4353135 *May 9, 1980Oct 12, 1982Minnesota Mining And Manufacturing CompanyPatellar flange and femoral knee-joint prosthesis
US4353136 *Nov 5, 1980Oct 12, 1982Polyzoides Apostolos JEndoprosthetic knee joint
US4470158 *Mar 9, 1979Sep 11, 1984Biomedical Engineering Corp.Joint endoprosthesis
US4714473 *Jul 25, 1985Dec 22, 1987Harrington Arthritis Research CenterKnee prosthesis
US4964868 *Aug 27, 1987Oct 23, 1990Harrington Arthritis Research CenterKnee prosthesis
US4979957 *Sep 11, 1989Dec 25, 1990Zimmer, Inc.Textured prosthetic implant
US5219362 *Feb 6, 1992Jun 15, 1993Finsbury (Instruments) LimitedKnee prosthesis
US5370699 *Jan 21, 1993Dec 6, 1994Orthomet, Inc.Modular knee joint prosthesis
US5413604 *Dec 24, 1992May 9, 1995Osteonics Corp.Prosthetic knee implant for an anterior cruciate ligament deficient total knee replacement
US5509934 *Dec 7, 1994Apr 23, 1996Osteonics Corp.Prosthetic knee tibial component constructed of synthetic polymeric material
US5639279 *Feb 9, 1995Jun 17, 1997Intermedics Orthopedics, Inc.Posteriorly-stabilized prosthetic knee
US5738686 *Feb 16, 1994Apr 14, 1998Joachim TheusnerArtificial joint to replace the human patella
US5755803 *May 17, 1996May 26, 1998Hudson Surgical DesignProsthetic implant
US5876460 *Sep 6, 1996Mar 2, 1999Bloebaum; Roy D.Cemented prosthetic component and placement method
US5879354 *Jul 14, 1997Mar 9, 1999Hudson Surgical Design, Inc.Prosthetic implant
US6197064 *Mar 3, 1999Mar 6, 2001Hudson Surgical Design, Inc.Prosthetic implant
US6355067Jul 27, 1998Mar 12, 2002Aaron. A. HofmannCemented prosthetic component and placement method
US6364911 *Apr 22, 1998Apr 2, 2002Plus Endoprothetik AgFemoral sled prosthesis
US6893467 *Jul 25, 2000May 17, 2005Michel BercovyKnee prosthesis
US6942475 *Mar 13, 2003Sep 13, 2005Ortho Development CorporationDisposable knee mold
US7258701Jan 12, 2005Aug 21, 2007Depuy Products, Inc.Systems and methods for compartmental replacement in a knee
US7261740Oct 29, 2003Aug 28, 2007Wright Medical Technology, Inc.Tibial knee prosthesis
US7306609Jul 9, 2003Dec 11, 2007Plus Orthopedics AgFemoral slideway
US7326252Dec 22, 2003Feb 5, 2008Smith & Nephew, Inc.High performance knee prostheses
US7344541Jan 13, 2004Mar 18, 2008Hudson Surgical Design, Inc.Methods and apparatus for femoral and tibial resection
US7537664Nov 7, 2003May 26, 2009Howmedica Osteonics Corp.Laser-produced porous surface
US7544209 *Feb 6, 2004Jun 9, 2009Lotke Paul APatello-femoral prosthesis
US7544210 *Feb 25, 2005Jun 9, 2009Roberto SchaeferMedial and lateral femoral implants for single-compartment knee prosthesis
US7695520May 31, 2006Apr 13, 2010Biomet Manufacturing Corp.Prosthesis and implementation system
US7753960 *Feb 25, 2005Jul 13, 2010Omni Life Science, Inc.Modular knee prosthesis
US7815645Jan 14, 2005Oct 19, 2010Hudson Surgical Design, Inc.Methods and apparatus for pinplasty bone resection
US7857814Mar 8, 2005Dec 28, 2010Hudson Surgical Design, Inc.Methods and apparatus for minimally invasive arthroplasty
US7922771Jan 31, 2008Apr 12, 2011Smith & Nephew, Inc.High performance knee prostheses
US7935151Apr 9, 2010May 3, 2011Hudson Surgical Design, Inc.Femoral prosthetic implant
US7967822Oct 29, 2004Jun 28, 2011Hudson Surgical Design, Inc.Methods and apparatus for orthopedic implants
US8002840Jun 30, 2005Aug 23, 2011Depuy Products, Inc.Systems and methods for compartmental replacement in a knee
US8021368Mar 8, 2005Sep 20, 2011Hudson Surgical Design, Inc.Methods and apparatus for improved cutting tools for resection
US8062377Oct 31, 2007Nov 22, 2011Hudson Surgical Design, Inc.Methods and apparatus for knee arthroplasty
US8077950Aug 10, 2010Dec 13, 2011Conformis, Inc.Methods for determining meniscal size and shape and for devising treatment
US8088167Dec 15, 2009Jan 3, 2012Hudson Surgical Design, Inc.Femoral prosthetic implant
US8112142Jun 27, 2007Feb 7, 2012The Board Of Trustees Of The Leland Stanford Junior UniversityAssessing the condition of a joint and devising treatment
US8114083Mar 8, 2005Feb 14, 2012Hudson Surgical Design, Inc.Methods and apparatus for improved drilling and milling tools for resection
US8142886Jul 24, 2008Mar 27, 2012Howmedica Osteonics Corp.Porous laser sintered articles
US8147861Aug 15, 2006Apr 3, 2012Howmedica Osteonics Corp.Antimicrobial implant
US8234097Feb 24, 2010Jul 31, 2012Conformis, Inc.Automated systems for manufacturing patient-specific orthopedic implants and instrumentation
US8265730Jun 15, 2001Sep 11, 2012The Board Of Trustees Of The Leland Stanford Junior UniversityAssessing the condition of a joint and preventing damage
US8268099Apr 22, 2009Sep 18, 2012Howmedica Osteonics Corp.Laser-produced porous surface
US8268100Jul 26, 2010Sep 18, 2012Howmedica Osteonics Corp.Laser-produced porous surface
US8277513Jun 22, 2010Oct 2, 2012Omni Life Science, Inc.Modular knee prosthesis
US8287545Mar 8, 2005Oct 16, 2012Hudson Surgical Design, Inc.Methods and apparatus for enhanced retention of prosthetic implants
US8292965 *Feb 11, 2008Oct 23, 2012New York UniversityKnee joint with a ramp
US8298238Aug 6, 2008Oct 30, 2012Hudson Surgical Design, Inc.Methods and apparatus for pivotable guide surfaces for arthroplasty
US8306601Aug 13, 2011Nov 6, 2012The Board Of Trustees Of The Leland Stanford Junior UniversityAssessing the condition of a joint and devising treatment
US8337507Dec 22, 2008Dec 25, 2012Conformis, Inc.Methods and compositions for articular repair
US8343218Dec 22, 2008Jan 1, 2013Conformis, Inc.Methods and compositions for articular repair
US8350186Dec 29, 2006Jan 8, 2013Howmedica Osteonics Corp.Laser-produced implants
US8353914Jul 9, 2007Jan 15, 2013Hudson Surgical Design, Inc.Methods and apparatus for improved profile based resection
US8357111Sep 30, 2007Jan 22, 2013Depuy Products, Inc.Method and system for designing patient-specific orthopaedic surgical instruments
US8361076Sep 29, 2008Jan 29, 2013Depuy Products, Inc.Patient-customizable device and system for performing an orthopaedic surgical procedure
US8369926Jan 31, 2011Feb 5, 2013The Board Of Trustees Of The Leland Stanford Junior UniversityAssessing the condition of a joint and devising treatment
US8377068Sep 29, 2008Feb 19, 2013DePuy Synthes Products, LLC.Customized patient-specific instrumentation for use in orthopaedic surgical procedures
US8394147Nov 23, 2010Mar 12, 2013Smith & Nephew, Inc.High performance femoral knee prostheses
US8394148Nov 23, 2010Mar 12, 2013Smith & Nephew, Inc.Tibial component of high performance knee prosthesis
US8398715Oct 20, 2009Mar 19, 2013Smith & Nephew, Inc.High performance knee prostheses with converging anterior and posterior portions
US8398716Nov 23, 2010Mar 19, 2013Smith & Nephew, Inc.High performance knee prostheses with posterior cam
US8403992Nov 23, 2010Mar 26, 2013Smith & Nephew, Inc.High performance knee prostheses
US8414286Dec 4, 2008Apr 9, 2013Zimmer Orthopaedic Surgical Products, Inc.Spacer molds with releasable securement
US8419740Sep 29, 2008Apr 16, 2013DePuy Synthes Products, LLC.Customized patient-specific bone cutting instrumentation
US8425523Sep 29, 2008Apr 23, 2013DePuy Synthes Products, LLCCustomized patient-specific instrumentation for use in orthopaedic surgical procedures
US8425524Sep 29, 2008Apr 23, 2013DePuy Synthes Products, LLCCustomized patient-specific multi-cutting blocks
US8425617Nov 23, 2010Apr 23, 2013Smith & Nephew, Inc.Knee prostheses with convex slope on portion of tibial articular surface
US8430932Dec 6, 2011Apr 30, 2013Puget Bio Ventures LLCFemoral prosthetic implant
US8449618Nov 23, 2010May 28, 2013Smith & Nephew, Inc.High performance knee prostheses
US8480389Jul 9, 2010Jul 9, 2013Zimmer Orthopedic Surgical Products, Inc.Spacer mold and methods therefor
US8480754Feb 25, 2010Jul 9, 2013Conformis, Inc.Patient-adapted and improved articular implants, designs and related guide tools
US8535383Jun 30, 2005Sep 17, 2013DePuy Synthes Products, LLCSystems and methods for compartmental replacement in a knee
US8545569Jan 5, 2004Oct 1, 2013Conformis, Inc.Patient selectable knee arthroplasty devices
US8556981Sep 18, 2009Oct 15, 2013Howmedica Osteonics Corp.Laser-produced porous surface
US8556983Mar 9, 2011Oct 15, 2013Conformis, Inc.Patient-adapted and improved orthopedic implants, designs and related tools
US8594395Sep 29, 2008Nov 26, 2013DePuy Synthes Products, LLCSystem and method for fabricating a customized patient-specific surgical instrument
US8603095Nov 8, 2011Dec 10, 2013Puget Bio Ventures LLCApparatuses for femoral and tibial resection
US8603178Nov 23, 2010Dec 10, 2013Smith & Nephew, Inc.Knee prostheses with convex portion on tibial lateral articular surface
US8617242Feb 14, 2008Dec 31, 2013Conformis, Inc.Implant device and method for manufacture
US8634617Dec 6, 2011Jan 21, 2014Conformis, Inc.Methods for determining meniscal size and shape and for devising treatment
US8641721Jun 30, 2011Feb 4, 2014DePuy Synthes Products, LLCCustomized patient-specific orthopaedic pin guides
US8647389Dec 17, 2010Feb 11, 2014Smith & Nephew, Inc.High performance knee prostheses
US8652210 *Nov 23, 2010Feb 18, 2014Smith & Nephew, Inc.Femoral prostheses with lateral buttress for patella
US8682052Mar 5, 2009Mar 25, 2014Conformis, Inc.Implants for altering wear patterns of articular surfaces
US8690945May 11, 2010Apr 8, 2014Conformis, Inc.Patient selectable knee arthroplasty devices
US8709089May 3, 2010Apr 29, 2014Conformis, Inc.Minimally invasive joint implant with 3-dimensional geometry matching the articular surfaces
US8728086 *May 28, 2010May 20, 2014Smith & Nephew, Inc.Methods and apparatus for performing knee arthroplasty
US8728167Jan 10, 2011May 20, 2014Howmedica Osteonics Corp.Bicruciate retaining tibial baseplate design and method of implantation
US8728387Dec 6, 2005May 20, 2014Howmedica Osteonics Corp.Laser-produced porous surface
US8735773Jun 10, 2011May 27, 2014Conformis, Inc.Implant device and method for manufacture
US8740906Jul 11, 2008Jun 3, 2014Hudson Surgical Design, Inc.Method and apparatus for wireplasty bone resection
US8768028May 11, 2010Jul 1, 2014Conformis, Inc.Methods and compositions for articular repair
US8771365Jun 23, 2010Jul 8, 2014Conformis, Inc.Patient-adapted and improved orthopedic implants, designs, and related tools
US8801983Jun 11, 2013Aug 12, 2014Zimmer Orthopaedic Surgical Products, Inc.Spacer mold and methods therefor
US20100331848 *May 28, 2010Dec 30, 2010Richard Michael SmithMethods and Apparatus for Performing Knee Arthroplasty
US20110130843 *Nov 23, 2010Jun 2, 2011Otto Jason KHigh performance knee prostheses
US20120101587 *Jul 12, 2010Apr 26, 2012Milux Holding SaKnee joint device and method
US20120197411 *Jul 12, 2010Aug 2, 2012Milux Holding SaKnee joint device and method
USRE43282Aug 19, 2008Mar 27, 2012The Board Of Trustees Of The Leland Stanford Junior UniversityAssessing the condition of a joint and devising treatment
CN1874738BOct 25, 2004Dec 15, 2010瑞特医疗技术公司Tibial knee prosthesis
DE2703059A1 *Jan 26, 1977Jul 27, 1978Schuett & Grundei SanitaetKniegelenk-endoprothese
DE2919803A1 *May 16, 1979Dec 6, 1979New York SocietyKniegelenkprothese
EP1738720A2Jun 14, 2006Jan 3, 2007DePuy Products, Inc.Systems for use in knee replacement surgery
EP2305182A1Jun 14, 2006Apr 6, 2011Depuy ProductsSystems for use in Knee Replacement Surgery
WO1979000739A1 *Mar 9, 1979Oct 4, 1979Biomedical Eng CorpImproved joint endoprosthesis
WO2005044150A1 *Oct 25, 2004May 19, 2005Robert M FenclTibial knee prosthesis
WO2005067521A2Jan 12, 2005Jul 28, 2005Depuy Products IncSystems and methods for compartmental replacement in a knee
WO2005069809A2 *Jan 12, 2005Aug 4, 2005Paul A LotkePatello-femoral prosthesis
WO2009158318A1 *Jun 23, 2009Dec 30, 2009Zimmer, Inc.Acl accommodating tibial design
WO2013007747A1 *Jul 11, 2012Jan 17, 2013Zimmer GmbhFemoral knee prosthesis with diverging lateral condyle
Classifications
U.S. Classification623/20.31, 264/DIG.300, 264/222
International ClassificationA61F2/38
Cooperative ClassificationY10S264/30, A61F2/38
European ClassificationA61F2/38