US20120179265A1 - Knee prosthesis - Google Patents

Knee prosthesis Download PDF

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Publication number
US20120179265A1
US20120179265A1 US13/389,950 US201013389950A US2012179265A1 US 20120179265 A1 US20120179265 A1 US 20120179265A1 US 201013389950 A US201013389950 A US 201013389950A US 2012179265 A1 US2012179265 A1 US 2012179265A1
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United States
Prior art keywords
trace
line
knee prosthesis
contact point
radius
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Abandoned
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US13/389,950
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English (en)
Inventor
Urs Wyss
Shahram Amiri
Theodore Derek Vernon Cooke
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
ORTHOPAEDIC INNOVATION CENTRE Inc
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Urs Wyss
Shahram Amiri
Theodore Derek Vernon Cooke
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Application filed by Urs Wyss, Shahram Amiri, Theodore Derek Vernon Cooke filed Critical Urs Wyss
Publication of US20120179265A1 publication Critical patent/US20120179265A1/en
Assigned to ORTHOPAEDIC INNOVATION CENTRE INC. reassignment ORTHOPAEDIC INNOVATION CENTRE INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: AMIRI, SHAHRAM, COOKE, THEODORE DEREK VERNON, WYSS, URS
Abandoned legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • 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
    • A61F2/30—Joints
    • A61F2/38—Joints for elbows or knees
    • A61F2/3836—Special connection between upper and lower leg, e.g. constrained
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • 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
    • A61F2/30—Joints
    • A61F2/38—Joints for elbows or knees
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • 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
    • A61F2/30—Joints
    • A61F2/38—Joints for elbows or knees
    • A61F2/3859—Femoral components
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • 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
    • A61F2/30—Joints
    • A61F2/38—Joints for elbows or knees
    • A61F2/389—Tibial components
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • 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
    • A61F2/30—Joints
    • A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30316—The prosthesis having different structural features at different locations within the same prosthesis; Connections between prosthetic parts; Special structural features of bone or joint prostheses not otherwise provided for
    • A61F2002/30317—The prosthesis having different structural features at different locations within the same prosthesis
    • A61F2002/30327—The prosthesis having different structural features at different locations within the same prosthesis differing in diameter
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0063—Three-dimensional shapes
    • A61F2230/0093—Umbrella-shaped, e.g. mushroom-shaped
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0063—Three-dimensional shapes
    • A61F2230/0095—Saddle-shaped
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
    • A61F2250/0039—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in diameter

Definitions

  • the invention covers a knee prosthesis for a knee joint of a width “w” with a ball-like femoral condyle and a corresponding tibial cavity on the medial side, the ball and cavity having a centre “Mb”, a radius “Rb”, a spherical surface “Sb” and defining a Cartesian coordinate system X, Y, Z attached to the Tibia with its origin “O” at the centre “Mb”.
  • the invention has the advantage that there is a clear guidance for pivoting the tibia about the medial side of the femur as a function of the flexion angle ⁇ as long as there is joint compression applied due to muscle forces, weight, and ligament tensions to enforce contact.
  • a very important feature of the invention is that to satisfy the kinematic degrees of freedom and the geometric constraints required for proper guiding, the geometries of the medial and lateral sides are designed in harmony with the characteristics of the expected kinematics. It can be shown that proper guiding can only take place by considering certain relationships between the characteristics of the expected kinematics and the geometries of the ball-shape medial compartment and guiding surfaces of the lateral compartment.
  • the locations of contact on the guiding surfaces do not interfere with the locations of cruciate ligaments and with the location of the patellar groove on the femur. Therefore, there can be options for preserving the cruciate ligaments and for having anatomical shape for the trochlear groove on the femur, which enhances natural articulation of the patella for the full range of motion from full extension to deep flexion.
  • Another advantage of the invention is that it clearly defines the complete geometric relationships required to generate the complex 3D geometries of the guiding surfaces, which facilitates the production of components through numerically controlled machine tools for instance. Since geometric relationships are defined dimensionless as functions of the width of the knee joint, they can be used to generate any size of the prosthesis, when the width is known.
  • the dependent claims 2 to 12 show improvements of the invention. If the guiding curves “Bi” and “Be” are arcs geometries of which are defined based on mathematical functions, programming of the guiding surface becomes easier. These arcs can be parts of the circles tangent at the common contact point Pt 1 /Pt 2 to the line “T 2 ” in plane E 1 which is drawn from the common contact point to the surface “Sb” of the ball.
  • Another object of the invention is to generate a three-dimensional trace-line “Lt 1 ” according to measurements on cadaveric specimen but with a simple generator. This is achieved by defining a generator in a sagittal plane and by projecting it orthogonally from the sagittal plane to the spherical surface “Sc 1 ” of the tibia component.
  • Another object of the invention is to have clearly defined relative movements between the tibia and femur as rotation about a 3D axis passing through the centre of the medial ball. This is achieved in that at each flexion angle ⁇ a tangent line T 1 to the trace of tibial contact points Lt 1 at the contact point Pt 1 is also the tangent to the trace line Lt 2 on the spherical surface “Sc 2 ” of the femur, and in that a momentary rotational axis for the movement between the two spheres Sc 1 /Sc 2 is therefore located on a plane E 1 , which is perpendicular to the common tangent T 1 .
  • the input kinematics in this process can be taken from cadavers or living subjects. However, the input kinematics should be processed to first meet the geometric constraints of the ball and socket configuration with minimum deviation from its original form. Second the processed kinematics should be able to generate a trace of contact points in proximity to the surface of the cartilage in the normal knee joint, so that as a further advantage minimum bone resection would be required during implantation.
  • a thesis of the inventor Shahran Amiri (not yet public; Title: Conceptual Design for a Surface - Guided Total Knee Replacement with Normal Kinematics; 2009, Queen's University, guitarist, Canada) shows how optimization methods can be used to process the input kinematics and generate corresponding articular surfaces. It further shows, that the certain geometric compatibility should be maintained between the design of the medial and lateral compartment.
  • the suggested guiding features have the advantage of not interfering with the geometric locations of the patellofemoral articulation and also the location of the cruciates and their attachments. This offers the options for bi-cruciate or PCL-retaining designs as well as a design with a more normal patellofemoral articulation throughout the full range of motion.
  • a lateral monocompartmental prosthesis can also be developed based on the introduced concept.
  • Another solution can be a prosthesis with two monocompartmental parts, a ball-like medial compartment and a lateral compartment which incorporates the introduced guiding features.
  • the invention offers a method for constructing a knee prosthesis for a knee joint of a width “w” with a ball-like femoral condyle and a corresponding tibia cavity on the medial side, the ball and the cavity having a centre “Mb”, a radius “Rb”, a spherical surface “Sb” and defining a Cartesian coordinate system X, Y, Z attached to the tibia with its origin “O” at the centre “Mb”,
  • the predetermined curve may be generated by interference on the spherical surface “Sc” with a the surface of a cylinder, which stands orthogonal to a sagittal plane and which is constructed by a continuous curve “Lc” located on the sagittal plane:
  • a tangent T 1 to the trace-line Lt 1 at the contact point Pt 1 is also the tangent for the trace-line Lt 2 on the spherical surface “Sc 2 ” of the femur and that at each flexion angle the location of a momentary rotation axis is on a plane E 1 , which passes through the centre Mb of the medial ball and is perpendicular to the tangent T 1 of the three-dimensional trace-line Lt 1 at contact point Pt 1 for the tibia.
  • the guiding curves “Bi” and “Be” may progressively change their shapes in opposite directions by change of flexion angle ⁇ , for generating an enforced gliding and rolling movement in both flexion and extension directions.
  • conical surfaces can be added on the interior side of the trace-lines Lt 1 and Lt 2 for additional support, which have their centres at the centre Mb of the medial ball and which have the trace-lines Lt 1 , Lt 2 as generator for the cones.
  • the guiding curves “Be” and “Bi” may be arcs, which start from common contact points Pt 1 /Pt 2 .
  • the guiding curves “Be” and “Bi” at the contact points Pt 1 /Pt 2 may be tangent to a line “T 2 ” on the plane E 1 , which is drawn from the common contact point Pt 1 /Pt 2 to the surface “Sb” on the ball, whereby the plane E 1 is orthogonal to a tangent “T 1 ” of the trace-line Lt 1 at the common contact point Pt 1 /Pt 2 .
  • the guiding curves “Be” and “Bi” may be circular arcs with radii “Re” and “Ri” and the curves for the tibial component may be less congruent to the corresponding guiding curves of the femoral component in the middle range of flexion angle ⁇ , than for the end positions full extension and full flexion.
  • FIG. 1 shows schematically a posterior view of a knee joint prosthesis with a coordinate System X; Y; Z;
  • FIG. 2 a shows schematically a vertical cut of a tibia component along the YZ-plane
  • FIG. 2 b shows schematically a view from lateral of FIG. 2 a with a cut along a trace-line La on a spherical surface Sc 1 , as well as a generating curve Lc in a sagittal plane 4 ;
  • FIG. 2 c shows schematically a top view of the tibia component of FIGS. 2 b and 2 c with a trace-line Lt 1 ;
  • FIG. 3 shows graphically for the lateral sagittal plane the angular location of contact points Pt 1 with the angle ⁇ as a function of the flexion angle ⁇ and also some values for the angular relationship in a table;
  • FIG. 4 shows a schematic view of the tibia component 2 with plane E 1 , which passes through a the centre O, and the contact point Pt 1 , perpendicular to the tangent of the trace-line Lt 1 at the point Pt 1 ;
  • FIG. 5 shows graphically the pivot angle ⁇ of the femur with reference to the tibia as a function of the flexion angle ⁇ , and also some values for the angular relationship in a table;
  • FIG. 6 shows schematically from posterior a plane E 1 with the geometrical relationship between the lateral guiding curves Be and Bi and the medial spherical surface Sb;
  • FIG. 7 shows a table with the dimensions of the radii for the lateral guiding curves and their corresponding flexion angles ⁇ ;
  • FIG. 8 a shows schematically a view from posterior for an extended position
  • FIG. 8 b shows schematically the changes in the shape of the guiding curves for different flexion angles ⁇ ;
  • FIG. 9 shows schematically for femur and tibia a graph with the interior radius Ri as a fraction of the width w depending on the flexion angle ⁇ ;
  • FIG. 10 shows schematically for femur and tibia a graph with the exterior radius Re as a fraction of the width w depending on the flexion angle ⁇ ;
  • FIG. 11 shows schematically a femur prosthesis part from distal with an additional conical surface
  • FIG. 12 shows schematically from a posterior angle a knee prosthesis with the additional conical surfaces
  • FIG. 13 shows schematically a cut through a tibial part along a plane E 1 at full extension with the bearing surfaces
  • FIG. 14 shows schematically a cut through the tibial part of FIG. 13 along a plane E 1 for a large flexion angle with the bearing surfaces.
  • femur 3 and tibia bone 5 are shown with their prosthetic parts in extension position.
  • the parameter “w” defines the width of the component 2 in the mediolateral direction.
  • the medial and lateral sagittal planes 4 are defined parallel to the sagittal plane of the tibia 5 and passing through the medial and lateral centre of the tibia plateau 2 at a distance of 0.25w from the midpoint 6 (see FIG. 2 a ) of the width w.
  • a coordinate system X, Y, Z has its centre O on the medial sagittal plane.
  • the X, Y, and Z axes in this coordinates system point to the anterior, proximal, and lateral directions respectively.
  • FIGS. 2 a , 2 b and 2 c the position and the shape of a lateral cavity 8 are illustrated.
  • a reference coordinate system is defined having its origin “O” by 0.25w in medial direction, by 0.32w in proximal direction and by 0.07w in posterior direction. From origin “O” the X-axis points towards anterior, the Y-axis points towards proximal and the Z-axis points towards lateral.
  • the shapes of the lateral condyles are generated by first defining the trace-lines Lt 1 , Lt 2 of contact points Pt 1 , Pt 2 on the lateral compartment.
  • Two identical spherical surfaces are defined, one “Sc 1 ” attached to the tibia and one “Sc 2 ” attached to the femur. These spheres are defined concentric with the medial ball when the joint is at full extension and with their radii Rc 1 and Rc 2 equal to 0.65w.
  • the trace-lines Lt 1 and Lt 2 of contact points are both located on the corresponding spherical surface Sc 1 and Sc 2 . As can be seen in FIG.
  • the shapes of the guiding curves Be, Bi for the tibial and femoral condyles are identical.
  • the two reference spheres Sc 1 and Sc 2 always remain concentric, causing the spheres to slide on top of each other while tangency between the trace-lines Lt 1 , Lt 2 is maintained.
  • the three dimensional trace-line Lt 1 of contact points Pt 1 is generated by projecting a two dimensional curve in the lateral sagittal plane 4 on the spherical surface Sc 1 of the tibia component in the mediolateral direction.
  • the matching trace of contact points on the femur is created by keeping the tibia fixed, and incrementally moving the femur with respect to the tibia starting from ⁇ 5° of flexion and finishing at 160°, following the desired kinematics; in each increment the point Pt 1 on the trace-line Lt 1 of contact points of the tibia which is associated with the current flexion angle is added as a contact point Pt 2 to the femoral sphere. The motion continues until 160°, and at the end all the Pt 2 points added to the femur form the trace-line Lt 2 of contact points on the femur. Because of the identical geometries of the tibia and femoral spheres, the trace of contact points Lt 2 on the femur is exactly placed over the femoral sphere Sc 2 .
  • the flexion axis is on a plane E 1 parallel to the XZ plane of the tibia and the pivoting axis is defined perpendicular to the flexion axis on reference plane E 1 .
  • So cadaver tests and results, as shown in FIG. 3 and FIG. 5 are adapted to be used as inputs for mathematical modelling of implant surfaces.
  • the trace-lines Lt 1 and Lt 2 are very important as they are the basis for the definition of the guiding surfaces. Nevertheless they must not be part of the guiding surfaces and could be left out. They can be virtuel for the definition of the guiding surfaces and for the relative motion between femur and tibia.
  • FIG. 11 is a view from approximately distal, which shows a conical surface 17 at the lateral femoral condyle.
  • a band of this conical surface 17 could provide additional articular surface and support to its matching tibial counterpart 18 , whereas the relation between gliding and rolling is controlled by the guiding curves Bi and Be.
  • the conical surface 18 is shown on the tibia component 2 as if the lateral femur part would be transparent.
  • FIGS. 13 and 14 shows a large conical bearing surface 18 in extension and a small conical bearing surface 18 at a large flexion angle ⁇ . This arrangement allows for sufficient bearing surface at all flexion angles.
  • the clearances between the tibial and femoral guiding features can be enlarged by machining the tibial parts with slightly larger guiding curves for the medial and lateral aspects. Having different tibial parts a surgon can choose which one would suit best a patient depending on the condition of the cruciates of the particular patient.
  • the first guiding surface which drives from extension to flexion and the second guiding surface, which drives from flexion to extension may not be engaged simultaneously at the same flexion angle.
  • Such guiding surfaces would form an envelope of laxities around a central path, whilst still allowing for steering effects of the contact surfaces.
  • the range of laxities can be set correspondingly for different types of prostheses including ACL or PCL deficient knees.
  • the trace-line Lt 1 or the third segment can deflect allowing for the side curves to partially engage and can produce traction. If the material is not elastic enough, then there could be a pinching load between the articular surfaces, that can cause surface damage to the tibia component in a long run.
  • Elastic materials could be as an example PU, elastomeric PU, PCU, PE or UHMW Polyethylene.
US13/389,950 2009-08-10 2010-08-10 Knee prosthesis Abandoned US20120179265A1 (en)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
EP09167563 2009-08-10
EP09167563.7 2009-08-10
PCT/EP2010/061572 WO2011018441A1 (en) 2009-08-10 2010-08-10 Knee prosthesis

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US13/389,950 Abandoned US20120179265A1 (en) 2009-08-10 2010-08-10 Knee prosthesis
US14/844,992 Active US10292826B2 (en) 2009-08-10 2015-09-03 Knee prosthesis

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US14/844,992 Active US10292826B2 (en) 2009-08-10 2015-09-03 Knee prosthesis

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EP (1) EP2464314B1 (zh)
JP (1) JP5775870B2 (zh)
CN (1) CN102596108B (zh)
CA (1) CA2769376C (zh)
WO (1) WO2011018441A1 (zh)

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US20150025644A1 (en) * 2011-07-13 2015-01-22 Zimmer Gmbh Femoral knee prosthesis with diverging lateral condyle
US20150209149A1 (en) * 1999-06-16 2015-07-30 Btg International Limited Tibial component
WO2017015458A2 (en) 2015-07-22 2017-01-26 William Hodge Lateral and medial pivoting knee prosthesis
US9615929B2 (en) 2009-01-23 2017-04-11 Zimmer, Inc. Posterior-stabilized total knee prosthesis
US9861484B2 (en) 2010-04-13 2018-01-09 Zimmer, Inc. Anterior cruciate ligament substituting knee implants
EP3397200A4 (en) * 2015-12-30 2020-03-11 Eva15 LLC KNEE PROSTHESIS IMPLANT

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DE102009029360A1 (de) * 2009-09-10 2011-03-24 Aesculap Ag Kniegelenkendoprothese
KR101902350B1 (ko) * 2010-01-29 2018-10-01 스미스 앤드 네퓨, 인크. 십자인대-보존 무릎 보철물
EP2595574B1 (en) * 2010-07-24 2017-05-03 Zimmer, Inc. Asymmetric tibial components for a knee prosthesis
JP5826025B2 (ja) * 2011-12-28 2015-12-02 京セラメディカル株式会社 人工膝関節インプラント
DE102014106012B9 (de) 2014-04-29 2015-09-17 Aesculap Ag Kniegelenkendoprothese
CN105030384B (zh) * 2015-08-03 2018-04-10 北京威高亚华人工关节开发有限公司 一种全膝关节置换假体
EP3359093B1 (de) * 2015-10-07 2019-12-11 CeramTec GmbH Knieendoprothese zum ersatz von zumindest teilen des kniegelenks
DE102015119105A1 (de) 2015-11-06 2017-05-11 Aesculap Ag Kniegelenkendoprothese
EP3400912B1 (en) 2017-05-10 2019-11-20 Howmedica Osteonics Corporation Patient specific composite knee replacement
EP3698761B1 (en) 2019-02-22 2021-11-17 Stryker European Operations Limited Total ankle prosthesis
US11129720B2 (en) 2019-03-05 2021-09-28 Jonathan P. GARINO Cruciate replacing artificial knee
CN113631123A (zh) * 2019-04-11 2021-11-09 帝人中岛医疗株式会社 人工膝关节

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Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
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US9615929B2 (en) 2009-01-23 2017-04-11 Zimmer, Inc. Posterior-stabilized total knee prosthesis
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EP2464314A1 (en) 2012-06-20
CA2769376C (en) 2016-02-23
EP2464314B1 (en) 2015-12-23
WO2011018441A1 (en) 2011-02-17
JP2013501555A (ja) 2013-01-17
US10292826B2 (en) 2019-05-21
CN102596108B (zh) 2014-10-01
CA2769376A1 (en) 2011-02-17
CN102596108A (zh) 2012-07-18
US20160151162A1 (en) 2016-06-02

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