US20020010512A1 - Artificial knee joint - Google Patents
Artificial knee joint Download PDFInfo
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- US20020010512A1 US20020010512A1 US09/907,792 US90779201A US2002010512A1 US 20020010512 A1 US20020010512 A1 US 20020010512A1 US 90779201 A US90779201 A US 90779201A US 2002010512 A1 US2002010512 A1 US 2002010512A1
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- Prior art keywords
- condylar
- knee joint
- section
- femoral
- medial
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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
- A61F2/3886—Joints for elbows or knees for stabilising knees against anterior or lateral dislocations
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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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00023—Titanium or titanium-based alloys, e.g. Ti-Ni alloys
Definitions
- the present invention relates to an artificial knee joint which is used as a replacement of a biological knee joint.
- Such an artificial knee joint is substantially comprised of a femoral component in which two protruding surfaces, i.e., medial and lateral protruding surfaces, are joined in a front and back relationship to form a femoral condylar portion, and a tibial component in which recessed surfaces that support the femoral condylar portion so that the femoral condylar portion is capable of a sliding movement and a rolling movement are joined in a front and back relationship to form a tibial condylar portion.
- the femoral condylar portion has an medial condylar section and an lateral condylar section, and both of these portions are formed so that the Trajectory connecting the lowest points of the two portions constitutes an approximate circular-arc curve in two dimensions as seen in the side view.
- imaginary extended lines of this approximate circular-arc curve in the anteroposterior direction are set parallel to each other.
- the tibial condylar portion that supports the femoral condylar portion forms an elliptical groove that has its long axis in the anteroposterior direction as seen in a plan view.
- the femoral condylar portion rotates while sliding and rolling through this elliptical groove, thus allowing flexion of the knee.
- the femoral condylar portion is contained within the vertically projected plane of the tibial condylar portion, and does not protrude from this plane in extension.
- the femoral condylar portion protrudes from the vertically projected plane of the elliptical surface of the tibial condylar portion. Since the edge of the femoral condylar portion, and especially the posterior portion, contacts the running part of the hamstring on both the medial and lateral, this protrusion of the femoral condylar portion interferes with the normal tension of the hamstring, and therefore impedes flexion.
- the tibial condylar portion is more or less planar in the anteroposterior direction, and the attitude of the femur during flexion is controlled by the anterior and posterior cruciate ligaments. More specifically, the posterior cruciate ligaments gradually extend up to a flexion angle of approximately 60°, and then remain more or less fixed, so that the attitude is controlled.
- the side-surface shape of the tibial condylar portion is formed with the standing position of 0° as the deepest point, and with recessed shapes showing the shape of a “ship hull” before and after this deepest point, so that smooth rotation of the femoral condylar portion is achieved.
- the condylar portion In order for the femoral condylar portion to obtain a large flexion angle, the condylar portion must be correspondingly extended upward and to posterior. However, in the case of parallel setting that requires a wide area, this interferes with ligaments and tendons that are present in the upper posterior area, so that this extension cannot be made very long. As a result, the flexion angle in a conventional artificial knee joint is limited to approximately 110 to 120°. However, flexion of approximately 150° is necessary for, for instance, an upright sitting on a plane surface or a Japanese-style sitting position, etc.
- the object of the present invention is to solve the above problems.
- a femoral component comprising a femoral condylar portion that consists of an medial condylar section and an lateral condylar section, the medial and lateral condylar sections extending in a anteroposterior direction of the knee joint and have protruding exterior surfaces;
- a tibial component comprising a tibial condylar portion that consists of an medial condylar section and lateral condylar section, the medial and lateral condylar sections extending in a anteroposterior direction of the knee joint and have recessed interior surfaces so as to support the medial and lateral condylar sections of the femoral condylar portion in such a manner that the medial and lateral condylar sections of the femoral condylar portion can make sliding and rolling movements; and wherein
- a spacing between the respective medial condylar sections and lateral condylar sections of the femoral condylar portion and of the tibial condylar portion is formed so as to be gradually narrower toward the posterior side of the knee joint, thus forming a “rear-in” configuration.
- the spacing of the femoral condylar portions is formed in a “rear-in” configuration, the spacing (distance of separation) of the femoral medial condylar section and lateral condylar section decreases as the flexion angle increases. Accordingly, even in the case of a high degree of flexion, the femoral condylar portion does not protrude from the tibial condylar portion, but remains within the vertically projected plane of the tibial condylar portion. As a result, there is no interference with the hamstring or impairment of the normal tension of the hamstring.
- FIG. 1 is a perspective view of a femoral component illustrating one embodiment of the present invention
- FIG. 2 is a back view of the mounted state of an artificial knee joint illustrating one embodiment of the present invention
- FIG. 3 is a side view of the mounted state of an artificial knee joint illustrating one embodiment of the present invention
- FIG. 4 is an explanatory back view of a femoral component illustrating one embodiment of the present invention
- FIG. 5 is an explanatory side view of a femoral component illustrating one embodiment of the present invention
- FIG. 6 is a plan view of the mounted state of an artificial knee joint illustrating one embodiment of the present invention.
- FIG. 7 is a plan view of the mounted state of an artificial knee joint illustrating another embodiment of the present invention.
- FIG. 8 is a back view of the mounted state of an artificial knee joint illustrating another embodiment of the present invention.
- FIG. 9 is a side view of the mounted state of an artificial knee joint illustrating another example of the present invention.
- the artificial knee joint is comprised of a pair of femoral component 1 and tibial component 2 .
- the femoral component 1 is constructed from a biocompatible metal such as a titanium alloy, etc. and is mounted on the distal end of the femur.
- the outline of this femoral component 1 is substantially circular when viewed from the side.
- a high floor section 3 that extends horizontally in the anteroposterior direction is formed in the center of the interior of the femoral component 1 , and low floor sections 4 are formed on both sides of this high floor section 3 .
- Front walls 5 and rear walls 6 are formed in upright positions on the front and rear ends of the floor sections 3 and 5 .
- a pocket 7 is formed in the center of the under side of the high floor section 3 .
- the pocket 7 is oriented in the anteroposterior direction.
- the outlines of the areas on the left and right of the pocket 7 are formed as protruding surfaces that protrude downward or outward. These protruding or outwardly curved surfaces are joined in the front and rear at a specified curvature radius R (see FIG. 3), thus forming a femoral condylar portion 8 consisting of an medial condylar section 8 a and lateral condylar section 8 b .
- the femoral component 1 comprises, along with the high floor section 3 , low floor sections 4 , and front walls 5 , etc., a femoral condylar portion 8 that consists of a pair of condylar sections 8 a and 8 b ; and each one of the condylar sections 8 a and 8 b is formed so that the exterior surface are curved in the anteroposterior direction as seen from FIG. 5 (only the exterior surface being shown).
- each of the condylar sections 8 a and 8 b has a protruding or convex surface with respect to the width direction of the condylar sections 8 a and 8 b so that a curved ridge T extends at substantially the center thereof as seen in FIG. 6.
- the spacing in the femoral condylar portion 8 i.e., the spacing between the medial condylar section 8 a and lateral condylar section 8 b , is made narrower or gradually decreases toward the back or rear side of the femoral component 1 as seen from FIG. 6. In other words, this spacing is formed in a “rear-in” configuration.
- both the medial condylar section 8 a and the lateral condylar section 8 b be arranged symmetrically in a “rear-in” configuration with respect to the centerline L.
- the line connecting the respective lowest points or the outermost points on the medial condylar section 8 a and lateral condylar section 8 b form a circular arc when viewed from behind as shown in FIG. 2.
- This circular arc (that correspond to the ridge line T) is set so that the imaginary lines extended from the ridgeline T intersect on the centerline L of the femoral component 1 as seen from FIG. 2.
- the tibial component 2 is comprised of a plate 9 and a base 10 that supports the plate 9 .
- the plate 9 supports the femoral condylar portion 8 of the femoral component 1 so that the femoral condylar portion 8 is capable of making a sliding movement and a rolling movement.
- the plate 9 is constructed from an ultra-high-molecular-weight polyethylene for medical use, etc.
- a pair of curved, recessed or concave surfaces that correspondingly receive the respective protruding surfaces or the outwardly curved exterior surface of the respective medial and lateral condylar section 8 a and 8 b of the femoral condylar portion 8 are formed so as to extend anterior to posterior on the upper surface of the plate 9 with a specified curvature radius S.
- the recessed surfaces that thus extend in the anteroposterior direction form a pair of medial condylar section 11 a and lateral condylar section 11 b .
- the medial condylar section 11 a and lateral condylar section 11 b form a tibial condylar portion 11 .
- the recessed surfaces of the medial condylar section 11 a and lateral condylar section 11 b are viewed from above, they show a “kidney bean shape” with convergence toward the back side, thus corresponding to the curved shape of the medial and lateral condylar sections 8 a and 8 b of the femoral component 1 .
- the plate 9 that is a part of the tibial component 2 is formed with the tibial condylar portion 11 that is comprised of the medial condylar section 11 a and the lateral condylar section 11 b ; and each one of the medial condylar section 11 a and the lateral condylar section 11 b is formed so that the interior surface thereof is curved in the anteroposterior direction (in view of FIG.
- the curvature radius S of the tibial condylar portion 11 of the tibial component 2 is set so as to be larger than the curvature radius R of the femoral condylar portion 8 of the femoral component 1 .
- substantially a curved bottom line V in the rear half of the tibial component 2 is formed substantially flat so as to have no curvature.
- the spacing of the tibial condylar portion 11 i.e., the spacing between the medial condylar section 11 a and lateral condylar section 11 b , is also formed in a “rear-in” configuration toward the rear side, in the same manner as the spacing of the femoral condylar portion 8 .
- a post 12 which interacts with the pocket 7 of the femoral component 1 is disposed in an upright position between the medial condylar section 11 a and lateral condylar section 11 b . The detail of this post 12 will be described later.
- the base 10 that is as described above a part of the tibial component 2 , is formed from a titanium alloy, etc., and is fastened to the proximal end of the tibia. Since the positions of the plate 9 and base 10 must not shift, mutually interlocking recesses and projections, etc. are formed in the joining surfaces of these components, so that the fastening of the plate 9 and base 10 is reinforced.
- the artificial knee joint consisting of the above-described femoral component 1 and tibial component 2 is mounted on the knee joint by a surgical procedure.
- the femoral component 1 is mounted on the femur so that the distal end of the femur is shaped and the front and rear portions of the femur are respectively inserted between the front walls 5 and rear walls 6 of the femoral component 1 , while the medial and lateral portions of the femur are set on the low floor sections 4 straddling the high floor section 3 .
- the mounting of the tibial component 2 on the tibia is accomplished by flattening the proximal end of the tibia and fastening the base 10 to the end surface.
- a stem 13 can be provided to protrude from the undersurface of the base 10 . Fastening of such a stem 13 into the tibia reinforces the mounting of the tibial component 12 .
- the pocket 7 has is narrower at an upper area thereof and wider at an lower area thereof and has side inclined surfaces 7 a that run along the curvature of the protruding surfaces of the femoral condylar portion 8 .
- the side surface portions 12 a of the post 12 are in contact with the side inclined surfaces 7 a .
- a funnel-shaped dropping portion 7 b is formed in front of the pocket 7
- a hemispherical cam 14 is formed in the rear side of the dropping portion 7 b with a foot portion 7 c disposed in a high position interposed.
- the post 12 has a front inclined portion 12 b and a top portion 12 c that correspond to the shapes of the dropping portion 7 b and foot portion 7 c with a fixed gap left between the front inclined portion 12 b and the top portion 12 c .
- the post 12 also has a rear inclined portion 12 d which is hollowed out in a recessed surface shape from the top portion 12 c.
- the femoral condylar portion 8 rolls while appropriately sliding forward. In any case, however, the center of rotation O of the femoral condylar portion 8 moves rearward.
- the cam 14 formed in the pocket 7 and the rear inclined portion 12 d of the post 12 that acts on the cam 14 control the sliding movement and rolling movement during this flexing operation, so that the attitudes of the sliding movement and rolling movement are stabilized.
- the femoral condylar portion 8 rotates relative to the tibial condylar portion 11 while a state in which these portions are in contact is maintained (i.e., while forward movement is restricted).
- This rotation is performed from a standing position of 0° to a Japanese-style upright sitting position of 150°.
- the shapes of the cam 14 and rear inclined portion 12 d are designed in order to make this possible.
- contact between the side surface portions 12 a of the post 12 and the side inclined surfaces 7 a of the pocket 7 is maintained during this rotation, so that a tight movement with the post 12 as a pivot is guaranteed, and so that the contact surface area is increased, thus lowering the surface pressure, so that wear, etc., is reduced.
- the femoral condylar portion 8 and tibial condylar portion 11 are both formed in a “rear-in” configuration as shown in FIG. 2.
- the top or ridge line T of the convex surfaces of the femoral condylar portion 8 and the bottom line V of the concave surfaces of the tibial condylar portion 11 are correspondingly formed in a “rear-in” configuration.
- FIG. 4 is an explanatory rear view of the femoral component 1 which shows the state of contact between the femoral condylar portion 8 and tibial condylar portion 11 according to the flexion angle
- FIG. 5 is an explanatory side view thereof.
- the load is applied to the knee joint parallel to the axes of the bones, and the direction of the load is not affected by the flexion angle.
- the line A that connects the maximum load points (centers of gravity) is more or less parallel, thus differing from the top line T and bottom line V, which are in a “rear-in” configuration.
- this line A is naturally positioned to the outside of the top line T, etc.
- the establishment of the relationship between the femoral condylar portion 8 and the tibial condylar portion 11 depends on the above-described line A as described above. Accordingly, if this line A is positioned to the outside of the top line T, etc., the actual rotational radius is correspondingly decreased, so that a large flexion angle can be obtained with a small displacement, and so that only a small force is required for flexion.
- the above-described line A is set at a distance of 20 mm from the center of the medial condylar section 8 a and lateral condylar section 8 b .
- a line B with a distance of 23.5 mm from the center and a line C with a distance of 27 mm from the center were experimentally set in FIG. 4.
- the trajectories of the respective lines A through C that were observed when the joint was flexed are shown in FIG. 5. It is seen from these results that the rotational radius in the case of an increased flexion angle decreases with an increase in the distance from the center.
- this top line T is set in accordance with the conditions of the respective patients (age, symptoms, desires and living habits).
- FIG. 6 is a plan view showing a state in which the femoral condylar portion 8 is flexed 90 ° with respect to the tibial condylar portion 11 .
- the femoral condylar portion 8 and the tibial condylar portion 11 are thus formed with a “rear-in” structure, the femoral condylar portion 8 will not protrude from the vertically projected plane of the plate 9 formed by the tibial condylar portion 11 even if the femoral condylar portion 8 is flexed to a great degree.
- the femoral condylar portion 8 and the tibial condylar portion 11 are set parallel as in the conventional joint, the femoral condylar portion 8 will protrude from the plate 9 as indicated by the shaded portion Z as a result of the center of rotation O moving to a rear side. If this happens, there will be interference with the hamstring, etc., as described above.
- FIG. 7 is a plan view showing the mounting of an artificial knee joint of this type on the knee.
- FIG. 8 is a rear view thereof, and
- FIG. 9 is a side view thereof.
- the femoral condylar portion and tibial condylar portion are formed in a “rear-in” configuration.
- stable flexion with smaller vertical movement and lateral oscillation can be obtained over a large angle by means of a light force.
Abstract
Description
- 1. Field of the Invention
- The present invention relates to an artificial knee joint which is used as a replacement of a biological knee joint.
- 2. Prior Art
- In cases where a knee joint has ceased to function as a result of deformative joint disorders, rheumatism or external injury, etc., this knee joint is replaced by an artificial knee joint.
- Such an artificial knee joint is substantially comprised of a femoral component in which two protruding surfaces, i.e., medial and lateral protruding surfaces, are joined in a front and back relationship to form a femoral condylar portion, and a tibial component in which recessed surfaces that support the femoral condylar portion so that the femoral condylar portion is capable of a sliding movement and a rolling movement are joined in a front and back relationship to form a tibial condylar portion. In this case, the femoral condylar portion has an medial condylar section and an lateral condylar section, and both of these portions are formed so that the Trajectory connecting the lowest points of the two portions constitutes an approximate circular-arc curve in two dimensions as seen in the side view. In a conventional artificial knee joint, imaginary extended lines of this approximate circular-arc curve in the anteroposterior direction are set parallel to each other.
- This parallel setting sets limitations on the region of possible movement of the artificial knee joint. In particular, it is difficult to achieve maximum flexion. Examples of the deleterious effects of such a construction may be cited as follows:
- 1. The tibial condylar portion that supports the femoral condylar portion forms an elliptical groove that has its long axis in the anteroposterior direction as seen in a plan view. The femoral condylar portion rotates while sliding and rolling through this elliptical groove, thus allowing flexion of the knee. In this case, the femoral condylar portion is contained within the vertically projected plane of the tibial condylar portion, and does not protrude from this plane in extension. However, since the center of rotation of the femoral condylar portion moves to the rear as the angle of flexion increases, the femoral condylar portion protrudes from the vertically projected plane of the elliptical surface of the tibial condylar portion. Since the edge of the femoral condylar portion, and especially the posterior portion, contacts the running part of the hamstring on both the medial and lateral, this protrusion of the femoral condylar portion interferes with the normal tension of the hamstring, and therefore impedes flexion.
- 2. In a biological knee joint, the tibial condylar portion is more or less planar in the anteroposterior direction, and the attitude of the femur during flexion is controlled by the anterior and posterior cruciate ligaments. More specifically, the posterior cruciate ligaments gradually extend up to a flexion angle of approximately 60°, and then remain more or less fixed, so that the attitude is controlled. In an artificial knee joint, on the other hand, the side-surface shape of the tibial condylar portion is formed with the standing position of 0° as the deepest point, and with recessed shapes showing the shape of a “ship hull” before and after this deepest point, so that smooth rotation of the femoral condylar portion is achieved. In this case as well, a semi-constrained type configuration in which the curvature radius of the recessed shapes of the tibial condylar portion is greater than the curvature radius of the protruding shapes of the femoral condylar portion is most common. Consequently, as the femoral condylar portion bends, the position of the contact surface with the tibial condylar portion gradually becomes higher, which differs from the movement of a biological knee joint. Accordingly, when the cruciate ligaments are retained, the extension of these ligaments becomes excessive, so that attitude control becomes difficult to achieve. Even in cases where the cruciate ligaments are excised, the extension of the medial and lateral collateral ligaments is excessive, and smooth flexion is impeded.
- 3. In order for the femoral condylar portion to obtain a large flexion angle, the condylar portion must be correspondingly extended upward and to posterior. However, in the case of parallel setting that requires a wide area, this interferes with ligaments and tendons that are present in the upper posterior area, so that this extension cannot be made very long. As a result, the flexion angle in a conventional artificial knee joint is limited to approximately 110 to 120°. However, flexion of approximately 150° is necessary for, for instance, an upright sitting on a plane surface or a Japanese-style sitting position, etc.
- 4. In a biological knee joint, the smoothness of flexion is aided by an internal and external axial rotation movement of the femur as the flexion angle increases. However, if the femoral condylar portion and tibial condylar portion are set parallel to each other, this internal and external axial rotation movement is restricted. In other words, when the flexion angle increases, the femoral condylar portion leaves the recessed groove of the tibial condylar portion and is lifted upward, so that normal axial rotation is hindered, and the cruciate ligaments and medial and lateral collateral ligaments are excessively extended. Thus, smooth flexion and axial rotation are difficult.
- The object of the present invention is to solve the above problems.
- The above object is accomplished by a unique structure for an artificial knee joint in which the knee joint comprises:
- a femoral component comprising a femoral condylar portion that consists of an medial condylar section and an lateral condylar section, the medial and lateral condylar sections extending in a anteroposterior direction of the knee joint and have protruding exterior surfaces; and
- a tibial component comprising a tibial condylar portion that consists of an medial condylar section and lateral condylar section, the medial and lateral condylar sections extending in a anteroposterior direction of the knee joint and have recessed interior surfaces so as to support the medial and lateral condylar sections of the femoral condylar portion in such a manner that the medial and lateral condylar sections of the femoral condylar portion can make sliding and rolling movements; and wherein
- a spacing between the respective medial condylar sections and lateral condylar sections of the femoral condylar portion and of the tibial condylar portion is formed so as to be gradually narrower toward the posterior side of the knee joint, thus forming a “rear-in” configuration.
- With the respective medial condylar sections and lateral condylar sections of the femoral condylar portion and tibial condylar portion formed in a “rear-in” configuration, which is a characterizing feature of the present invention, the following advantages are obtained:
- 1. Since the spacing of the femoral condylar portions is formed in a “rear-in” configuration, the spacing (distance of separation) of the femoral medial condylar section and lateral condylar section decreases as the flexion angle increases. Accordingly, even in the case of a high degree of flexion, the femoral condylar portion does not protrude from the tibial condylar portion, but remains within the vertically projected plane of the tibial condylar portion. As a result, there is no interference with the hamstring or impairment of the normal tension of the hamstring.
- 2. This means that the degree to which the femoral condylar portion is elevated from the tibial condylar portion is small even in the case of a high degree of flexion, so that the tension of the collateral ligaments is not extended, thus allowing smooth flexion.
- 3. In the “rear-in” configuration as well, the load applied to the knee joint during flexion is applied to the positions of the centers of gravity of the medial and lateral condylar sections. Accordingly, when a large flexion angle is adopted, the center of gravity move to the medial or lateral of the top line that connects the lowest points of the condylar portions, and the curvature radius is correspondingly decreased, because the mediolateral radius of the femoral component portions are smaller than the anteroposterior. If the curvature radius is small, the amount of displacement of the center of rotation is also correspondingly decreased, so that a large flexion angle can be obtained with a small displacement, thus allowing a high degree of flexion. Furthermore, if the rotational radius is small, flexion can be accomplished by means of a light force.
- 4. With the “rear-in” configuration, the axial rotation of the femur about the axis of the tibia can also be accomplished by means of a light force, since the rotational radius is reduced. Furthermore, the joint is stable with no oscillation, etc. Accordingly, the flexion action is aided, and a large flexion angle can be obtained.
- FIG. 1 is a perspective view of a femoral component illustrating one embodiment of the present invention;
- FIG. 2 is a back view of the mounted state of an artificial knee joint illustrating one embodiment of the present invention;
- FIG. 3 is a side view of the mounted state of an artificial knee joint illustrating one embodiment of the present invention;
- FIG. 4 is an explanatory back view of a femoral component illustrating one embodiment of the present invention;
- FIG. 5 is an explanatory side view of a femoral component illustrating one embodiment of the present invention;
- FIG. 6 is a plan view of the mounted state of an artificial knee joint illustrating one embodiment of the present invention;
- FIG. 7 is a plan view of the mounted state of an artificial knee joint illustrating another embodiment of the present invention;
- FIG. 8 is a back view of the mounted state of an artificial knee joint illustrating another embodiment of the present invention; and
- FIG. 9 is a side view of the mounted state of an artificial knee joint illustrating another example of the present invention.
- An embodiment of the present invention will be described below with reference to the attached figures.
- The artificial knee joint is comprised of a pair of
femoral component 1 andtibial component 2. Of these components, thefemoral component 1 is constructed from a biocompatible metal such as a titanium alloy, etc. and is mounted on the distal end of the femur. - The outline of this
femoral component 1 is substantially circular when viewed from the side. Ahigh floor section 3 that extends horizontally in the anteroposterior direction is formed in the center of the interior of thefemoral component 1, andlow floor sections 4 are formed on both sides of thishigh floor section 3.Front walls 5 andrear walls 6 are formed in upright positions on the front and rear ends of thefloor sections - A
pocket 7 is formed in the center of the under side of thehigh floor section 3. Thepocket 7 is oriented in the anteroposterior direction. The outlines of the areas on the left and right of thepocket 7 are formed as protruding surfaces that protrude downward or outward. These protruding or outwardly curved surfaces are joined in the front and rear at a specified curvature radius R (see FIG. 3), thus forming afemoral condylar portion 8 consisting of anmedial condylar section 8a andlateral condylar section 8 b. In other words, thefemoral component 1 comprises, along with thehigh floor section 3,low floor sections 4, andfront walls 5, etc., afemoral condylar portion 8 that consists of a pair ofcondylar sections condylar sections condylar sections condylar sections femoral condylar portion 8, i.e., the spacing between themedial condylar section 8 a andlateral condylar section 8 b, is made narrower or gradually decreases toward the back or rear side of thefemoral component 1 as seen from FIG. 6. In other words, this spacing is formed in a “rear-in” configuration. - In this “rear-in” configuration, it is desirable that both the
medial condylar section 8 a and thelateral condylar section 8 b be arranged symmetrically in a “rear-in” configuration with respect to the centerline L. The line connecting the respective lowest points or the outermost points on themedial condylar section 8 a andlateral condylar section 8 b form a circular arc when viewed from behind as shown in FIG. 2. This circular arc (that correspond to the ridge line T) is set so that the imaginary lines extended from the ridgeline T intersect on the centerline L of thefemoral component 1 as seen from FIG. 2. - On the other hand, the
tibial component 2 is comprised of aplate 9 and a base 10 that supports theplate 9. Theplate 9 supports thefemoral condylar portion 8 of thefemoral component 1 so that thefemoral condylar portion 8 is capable of making a sliding movement and a rolling movement. Theplate 9 is constructed from an ultra-high-molecular-weight polyethylene for medical use, etc. - More specifically, a pair of curved, recessed or concave surfaces that correspondingly receive the respective protruding surfaces or the outwardly curved exterior surface of the respective medial and
lateral condylar section femoral condylar portion 8 are formed so as to extend anterior to posterior on the upper surface of theplate 9 with a specified curvature radius S. The recessed surfaces that thus extend in the anteroposterior direction form a pair of medial condylar section 11 a andlateral condylar section 11 b. The medial condylar section 11 a andlateral condylar section 11 b form atibial condylar portion 11. Accordingly, when the recessed surfaces of the medial condylar section 11 a andlateral condylar section 11 b are viewed from above, they show a “kidney bean shape” with convergence toward the back side, thus corresponding to the curved shape of the medial and lateralcondylar sections femoral component 1. In other words, theplate 9 that is a part of thetibial component 2 is formed with thetibial condylar portion 11 that is comprised of the medial condylar section 11 a and thelateral condylar section 11 b; and each one of the medial condylar section 11 a and thelateral condylar section 11 b is formed so that the interior surface thereof is curved in the anteroposterior direction (in view of FIG. 5) and also has a concave shape with a curved bottom line V at the center thereof so as to correspond to the curved ridge T of the medial and lateralcondylar sections femoral condylar portion 8 of thefemoral component 1. - The curvature radius S of the
tibial condylar portion 11 of thetibial component 2 is set so as to be larger than the curvature radius R of thefemoral condylar portion 8 of thefemoral component 1. However, substantially a curved bottom line V in the rear half of thetibial component 2 is formed substantially flat so as to have no curvature. - The spacing of the
tibial condylar portion 11, i.e., the spacing between the medial condylar section 11 a andlateral condylar section 11 b, is also formed in a “rear-in” configuration toward the rear side, in the same manner as the spacing of thefemoral condylar portion 8. Apost 12 which interacts with thepocket 7 of thefemoral component 1 is disposed in an upright position between the medial condylar section 11 a andlateral condylar section 11 b. The detail of thispost 12 will be described later. - The
base 10, that is as described above a part of thetibial component 2, is formed from a titanium alloy, etc., and is fastened to the proximal end of the tibia. Since the positions of theplate 9 andbase 10 must not shift, mutually interlocking recesses and projections, etc. are formed in the joining surfaces of these components, so that the fastening of theplate 9 andbase 10 is reinforced. - The artificial knee joint consisting of the above-described
femoral component 1 andtibial component 2 is mounted on the knee joint by a surgical procedure. In this case, thefemoral component 1 is mounted on the femur so that the distal end of the femur is shaped and the front and rear portions of the femur are respectively inserted between thefront walls 5 andrear walls 6 of thefemoral component 1, while the medial and lateral portions of the femur are set on thelow floor sections 4 straddling thehigh floor section 3. Meanwhile, the mounting of thetibial component 2 on the tibia is accomplished by flattening the proximal end of the tibia and fastening the base 10 to the end surface. In this case, astem 13 can be provided to protrude from the undersurface of thebase 10. Fastening of such astem 13 into the tibia reinforces the mounting of thetibial component 12. - A description will be given with reference to the shape of the
pocket 7 that is formed between themedial condylar section 8 a andlateral condylar section 8 b of thefemoral condylar portions 8 and the shape of thepost 12 that is formed between the medial condylar section 11 a andlateral condylar section 11 b of the tibialcondylar portions 11. - First, when the
femoral condylar portion 8 is mounted on the upper surface of thetibial condylar portion 11, as seen in FIG. 2 that is a rear view, thepocket 7 has is narrower at an upper area thereof and wider at an lower area thereof and has sideinclined surfaces 7 a that run along the curvature of the protruding surfaces of thefemoral condylar portion 8. Theside surface portions 12 a of thepost 12 are in contact with the side inclinedsurfaces 7 a. Furthermore, as seen in from FIG. 3 that is a side view, a funnel-shapeddropping portion 7 b is formed in front of thepocket 7, and a hemispherical cam 14 is formed in the rear side of the droppingportion 7 b with a foot portion 7 c disposed in a high position interposed. - Furthermore, the
post 12 has a frontinclined portion 12 b and atop portion 12 c that correspond to the shapes of the droppingportion 7 b and foot portion 7 c with a fixed gap left between the frontinclined portion 12 b and thetop portion 12 c. Moreover, thepost 12 also has a rearinclined portion 12 d which is hollowed out in a recessed surface shape from thetop portion 12 c. - With the structure described above, the operation that makes flexion of the knee will be described with reference to FIG. 3. When the
femoral component 1 and thetibial component 2 are caused to rotate relative to each other in FIG. 3, thefemoral condylar portion 8 rotates and moves rearward with respect to the tibial condylar portion 11 (when the tibial side is viewed as being fixed). In this case, if there were no sliding of thefemoral condylar portion 8 relative to thetibial condylar portion 11, thefemoral condylar portion 8 would soon fall out of thetibial condylar portion 11. Accordingly, thefemoral condylar portion 8 rolls while appropriately sliding forward. In any case, however, the center of rotation O of thefemoral condylar portion 8 moves rearward. The cam 14 formed in thepocket 7 and the rearinclined portion 12 d of thepost 12 that acts on the cam 14 control the sliding movement and rolling movement during this flexing operation, so that the attitudes of the sliding movement and rolling movement are stabilized. - In concrete terms, the
femoral condylar portion 8 rotates relative to thetibial condylar portion 11 while a state in which these portions are in contact is maintained (i.e., while forward movement is restricted). This rotation is performed from a standing position of 0° to a Japanese-style upright sitting position of 150°. Accordingly, the shapes of the cam 14 and rearinclined portion 12 d are designed in order to make this possible. Furthermore, contact between theside surface portions 12 a of thepost 12 and the side inclinedsurfaces 7 a of thepocket 7 is maintained during this rotation, so that a tight movement with thepost 12 as a pivot is guaranteed, and so that the contact surface area is increased, thus lowering the surface pressure, so that wear, etc., is reduced. - In the present invention, the
femoral condylar portion 8 and tibialcondylar portion 11 are both formed in a “rear-in” configuration as shown in FIG. 2. As a result, the top or ridge line T of the convex surfaces of thefemoral condylar portion 8 and the bottom line V of the concave surfaces of thetibial condylar portion 11 are correspondingly formed in a “rear-in” configuration. - FIG. 4 is an explanatory rear view of the
femoral component 1 which shows the state of contact between thefemoral condylar portion 8 and tibialcondylar portion 11 according to the flexion angle, and FIG. 5 is an explanatory side view thereof. Here, the load is applied to the knee joint parallel to the axes of the bones, and the direction of the load is not affected by the flexion angle. Accordingly, the line A that connects the maximum load points (centers of gravity) is more or less parallel, thus differing from the top line T and bottom line V, which are in a “rear-in” configuration. - Accordingly, in the rear half, this line A is naturally positioned to the outside of the top line T, etc. However, when the
femoral condylar portion 8 and tibialcondylar portion 11 rotate, the establishment of the relationship between thefemoral condylar portion 8 and thetibial condylar portion 11 depends on the above-described line A as described above. Accordingly, if this line A is positioned to the outside of the top line T, etc., the actual rotational radius is correspondingly decreased, so that a large flexion angle can be obtained with a small displacement, and so that only a small force is required for flexion. At the same time, in the case of internal rotation or external rotation, since the rotational radius of this axial rotation is also decreased, there is no lateral oscillation, etc., and smooth rotation can be obtained with a light force. Furthermore, since the curvature radius S of thetibial condylar portion 11 is set at a large value in the latter half, upward floating of thefemoral condylar portion 8 during flexion is reduced, so that a flexing action with little vertical movement can be obtained, thus allowing a high degree of flexion. - The above-described line A is set at a distance of 20 mm from the center of the
medial condylar section 8 a andlateral condylar section 8 b. However, a line B with a distance of 23.5 mm from the center and a line C with a distance of 27 mm from the center were experimentally set in FIG. 4. The trajectories of the respective lines A through C that were observed when the joint was flexed are shown in FIG. 5. It is seen from these results that the rotational radius in the case of an increased flexion angle decreases with an increase in the distance from the center. Accordingly, it may be said that as line A, which constitutes the maximum load point, is separated further to the outside of the top line T (or in other words, as the top line T is set further to the inside of line A), the flexuosity of the joint increases. Accordingly, this top line T is set in accordance with the conditions of the respective patients (age, symptoms, desires and living habits). - FIG. 6 is a plan view showing a state in which the
femoral condylar portion 8 is flexed 90° with respect to thetibial condylar portion 11. - It should be noted that if the
femoral condylar portion 8 and thetibial condylar portion 11 are thus formed with a “rear-in” structure, thefemoral condylar portion 8 will not protrude from the vertically projected plane of theplate 9 formed by thetibial condylar portion 11 even if thefemoral condylar portion 8 is flexed to a great degree. If thefemoral condylar portion 8 and thetibial condylar portion 11 are set parallel as in the conventional joint, thefemoral condylar portion 8 will protrude from theplate 9 as indicated by the shaded portion Z as a result of the center of rotation O moving to a rear side. If this happens, there will be interference with the hamstring, etc., as described above. - The above description is made for an artificial knee joint which is applied to a knee joint from which the cruciate ligaments have been excised. However, this artificial knee joint can also be mounted on a knee joint in which there has been little damage to the cruciate ligaments, and especially a knee joint in which a relatively undamaged posterior cruciate ligament is retained. FIG. 7 is a plan view showing the mounting of an artificial knee joint of this type on the knee. FIG. 8 is a rear view thereof, and FIG. 9 is a side view thereof.
- The basic structures of both the
femoral component 1 and thetibial component 2 are unchanged from the previous embodiment. However, in an artificial knee joint shown in FIGS. 7 through 9, attitude control during rotation is accomplished by means of the posteriorcruciate ligament 15. Accordingly, arecess 16 between the living femoral condyles and arecess 17 between the tibial condyles, through which the posteriorcruciate ligament 15 passes, remain in this artificial knee joint, and the shaping of the distal end of the femur and proximal end of the tibia on which this joint is mounted is performed accordingly. - In addition, no cam14 or rear
inclined portion 12 d of thepost 12 is installed. Also, agroove 18 that allows the passage of the posteriorcruciate ligament 15 is cut out in thehigh floor section 3 between thefemoral condylar portion 8 from a rear side. Here, in regard to thepost 12 located between the medial condylar section 11 a andlateral condylar section 11 b of the tibialcondylar portions 11, a post that is low in height and its rear half is cut away to an extent that prevents interference with the posteriorcruciate ligament 15 is formed. As in the previous embodiment, the side inclinedsurfaces 7 a of thepocket 7 contact thispost 12. Furthermore, thefemoral condylar portion 8 and tibialcondylar portion 11 have a “rear-in” structure, and the behavior during flexion and internal and external axial rotation is also the same as that in the previous embodiment. - As seen from the above, in the artificial knee joint of the present invention, the femoral condylar portion and tibial condylar portion are formed in a “rear-in” configuration. As a result, stable flexion with smaller vertical movement and lateral oscillation can be obtained over a large angle by means of a light force. At the same time, there is no damage to surrounding ligaments or tendons even in the case of a high degree of flexion.
Claims (16)
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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JP2000-218220 | 2000-07-19 | ||
JP2000218220A JP3679315B2 (en) | 2000-07-19 | 2000-07-19 | Knee prosthesis |
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US20020010512A1 true US20020010512A1 (en) | 2002-01-24 |
US6406497B2 US6406497B2 (en) | 2002-06-18 |
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US09/907,792 Expired - Lifetime US6406497B2 (en) | 2000-07-19 | 2001-07-18 | Artificial knee joint |
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Cited By (26)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20040191106A1 (en) * | 2002-11-08 | 2004-09-30 | Howmedica Osteonics Corp. | Laser-produced porous surface |
US20040243245A1 (en) * | 2003-04-24 | 2004-12-02 | Sylvie Plumet | Postero-stabilised prosthesis with non-shifting tibial stud |
US20060025866A1 (en) * | 2003-03-07 | 2006-02-02 | Serafin Louis A Jr | Ceramic manufactures |
US20060147332A1 (en) * | 2004-12-30 | 2006-07-06 | Howmedica Osteonics Corp. | Laser-produced porous structure |
US20070135925A1 (en) * | 2005-12-14 | 2007-06-14 | Walker Peter S | Surface guided knee replacement |
US20070135926A1 (en) * | 2005-12-14 | 2007-06-14 | Peter Walker | Surface guided knee replacement |
US20070288021A1 (en) * | 2006-06-07 | 2007-12-13 | Howmedica Osteonics Corp. | Flexible joint implant |
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US20090306783A1 (en) * | 2008-06-06 | 2009-12-10 | Blum Michael F | Total Knee Prosthesis and Method for Total Knee Arthroplasty |
US20090306785A1 (en) * | 2003-02-08 | 2009-12-10 | Richard Farrar | Knee joint prosthesis |
US20090319049A1 (en) * | 2008-02-18 | 2009-12-24 | Maxx Orthopedics, Inc. | Total Knee Replacement Prosthesis With High Order NURBS Surfaces |
US20090319047A1 (en) * | 2008-06-24 | 2009-12-24 | Peter Stanley Walker | Recess-ramp knee joint prosthesis |
US20110125279A1 (en) * | 2009-11-16 | 2011-05-26 | New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery | Constrained condylar knee device |
US20110125275A1 (en) * | 2009-11-16 | 2011-05-26 | New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery | Prosthetic condylar joints with articulating bearing surfaces having a translating contact point during rotation thereof |
US20110190898A1 (en) * | 2010-01-29 | 2011-08-04 | Lenz Nathaniel M | Cruciate-retaining knee prosthesis |
US8142886B2 (en) | 2007-07-24 | 2012-03-27 | Howmedica Osteonics Corp. | Porous laser sintered articles |
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US20130297020A1 (en) * | 2007-11-02 | 2013-11-07 | Biomet Uk Limited | Prosthesis For Stimulating Natural Kinematics |
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US9364896B2 (en) | 2012-02-07 | 2016-06-14 | Medical Modeling Inc. | Fabrication of hybrid solid-porous medical implantable devices with electron beam melting technology |
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Families Citing this family (46)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6695848B2 (en) | 1994-09-02 | 2004-02-24 | Hudson Surgical Design, Inc. | Methods for femoral and tibial resection |
US8603095B2 (en) | 1994-09-02 | 2013-12-10 | Puget Bio Ventures LLC | Apparatuses for femoral and tibial resection |
US8066776B2 (en) * | 2001-12-14 | 2011-11-29 | Btg International Limited | Tibial component |
US8062377B2 (en) | 2001-03-05 | 2011-11-22 | Hudson Surgical Design, Inc. | Methods and apparatus for knee arthroplasty |
ATE513533T1 (en) * | 2001-04-17 | 2011-07-15 | Exactech Inc | ARTIFICIAL KNEE JOINT |
FR2835738B1 (en) * | 2002-02-14 | 2004-10-01 | Jacques Afriat | TOTAL KNEE PROSTHESIS |
US20040054416A1 (en) * | 2002-09-12 | 2004-03-18 | Joe Wyss | Posterior stabilized knee with varus-valgus constraint |
AU2003299851B2 (en) | 2002-12-20 | 2009-12-10 | Smith & Nephew, Inc. | High performance knee prostheses |
US7160330B2 (en) * | 2003-01-21 | 2007-01-09 | Howmedica Osteonics Corp. | Emulating natural knee kinematics in a knee prosthesis |
JP4045194B2 (en) * | 2003-02-25 | 2008-02-13 | 京セラ株式会社 | Artificial knee joint |
US7081137B1 (en) * | 2003-06-23 | 2006-07-25 | Howmedica Osteonics Corp. | Knee prosthesis with extended range of motion |
AU2004281743B2 (en) | 2003-10-17 | 2011-06-09 | Smith & Nephew, Inc. | High flexion articular insert |
US8114083B2 (en) | 2004-01-14 | 2012-02-14 | Hudson Surgical Design, Inc. | Methods and apparatus for improved drilling and milling tools for resection |
US8021368B2 (en) | 2004-01-14 | 2011-09-20 | Hudson Surgical Design, Inc. | Methods and apparatus for improved cutting tools for resection |
US20060030854A1 (en) | 2004-02-02 | 2006-02-09 | Haines Timothy G | Methods and apparatus for wireplasty bone resection |
US20060030855A1 (en) * | 2004-03-08 | 2006-02-09 | Haines Timothy G | Methods and apparatus for improved profile based resection |
US7413577B1 (en) | 2005-09-22 | 2008-08-19 | Howmedica Osteonics Corp. | Total stabilized knee prosthesis with constraint |
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AU2007269203B2 (en) | 2006-06-30 | 2014-03-06 | Smith & Nephew, Inc. | Anatomical motion hinged prosthesis |
KR100901528B1 (en) * | 2008-01-08 | 2009-06-08 | 주식회사 코렌텍 | Artificial knee joint apparatus for preventing from damaging ligament |
US7896924B1 (en) | 2008-01-09 | 2011-03-01 | Howmedica Osteonics Corp. | Unicondylar femoral prosthetic implant component |
WO2010085656A1 (en) | 2009-01-23 | 2010-07-29 | Zimmer, Inc. | Posterior stabilized total knee prosthesis |
EP2272466A1 (en) * | 2009-07-10 | 2011-01-12 | Medizinische Hochschule Hannover | Knee joint prosthesis and method for producing said prosthesis |
US9132014B2 (en) | 2010-04-13 | 2015-09-15 | Zimmer, Inc. | Anterior cruciate ligament substituting knee implants |
BR112013001673B1 (en) | 2010-07-24 | 2021-02-09 | Zimmer, Inc | asymmetric tibia components for a knee prosthesis |
US8764840B2 (en) | 2010-07-24 | 2014-07-01 | Zimmer, Inc. | Tibial prosthesis |
US8926709B2 (en) | 2010-08-12 | 2015-01-06 | Smith & Nephew, Inc. | Structures for use in orthopaedic implant fixation and methods of installation onto a bone |
EP2613739B1 (en) | 2010-09-10 | 2017-06-07 | Zimmer, Inc. | Motion facilitating tibial components for a knee prosthesis |
US8603101B2 (en) | 2010-12-17 | 2013-12-10 | Zimmer, Inc. | Provisional tibial prosthesis system |
US8747479B2 (en) | 2011-04-26 | 2014-06-10 | Michael A. McShane | Tibial component |
CN103648442B (en) | 2011-07-13 | 2016-03-23 | 捷迈有限责任公司 | There is the femoral knee prostheses of expansion lateral condyle |
EP3308726A3 (en) | 2011-07-13 | 2018-10-24 | The General Hospital Corporation d/b/a Massachusetts General Hospital | Devices for knee joint replacement with anterior cruciate ligament substitution |
EP2779948B1 (en) | 2011-11-18 | 2016-11-02 | Zimmer, Inc. | Tibial bearing component for a knee prosthesis with improved articular characteristics |
CN106214292B (en) | 2011-11-21 | 2018-06-15 | 捷迈有限公司 | The tibial baseplate of fixed structure with asymmetry setting |
JP5826025B2 (en) * | 2011-12-28 | 2015-12-02 | 京セラメディカル株式会社 | Total knee implant |
US9649195B2 (en) * | 2011-12-29 | 2017-05-16 | Mako Surgical Corp. | Femoral implant for preserving cruciate ligaments |
USD744103S1 (en) | 2011-12-29 | 2015-11-24 | Mako Surgical Corp. | Tibial baseplate |
USD744104S1 (en) | 2011-12-29 | 2015-11-24 | Mako Surgical Corp. | Femoral implant component |
USD745158S1 (en) | 2011-12-29 | 2015-12-08 | Mako Surgical Corp. | Tibial implant components |
KR20140133836A (en) | 2012-01-30 | 2014-11-20 | 짐머, 인크. | Asymmetric tibial components for a knee prosthesis |
US9925052B2 (en) | 2013-08-30 | 2018-03-27 | Zimmer, Inc. | Method for optimizing implant designs |
CN108135701B (en) | 2015-09-21 | 2019-12-24 | 捷迈有限公司 | Prosthesis system including tibial bearing component |
EP4014930A1 (en) | 2017-03-10 | 2022-06-22 | Zimmer, Inc. | Tibial prosthesis with tibial bearing component securing feature |
WO2018208612A1 (en) | 2017-05-12 | 2018-11-15 | Zimmer, Inc. | Femoral prostheses with upsizing and downsizing capabilities |
US11426282B2 (en) | 2017-11-16 | 2022-08-30 | Zimmer, Inc. | Implants for adding joint inclination to a knee arthroplasty |
US10835380B2 (en) | 2018-04-30 | 2020-11-17 | Zimmer, Inc. | Posterior stabilized prosthesis system |
Family Cites Families (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB1600661A (en) * | 1978-02-17 | 1981-10-21 | Howmedica | Bicondylar joint prosthesis |
US4888021A (en) * | 1988-02-02 | 1989-12-19 | Joint Medical Products Corporation | Knee and patellar prosthesis |
US4892547A (en) * | 1988-02-03 | 1990-01-09 | Biomet, Inc. | Partially stabilized knee prosthesis |
US5007933A (en) * | 1989-01-31 | 1991-04-16 | Osteonics Corp. | Modular knee prosthesis system |
US5059216A (en) * | 1989-09-29 | 1991-10-22 | Winters Thomas F | Knee joint replacement apparatus |
US5147405A (en) * | 1990-02-07 | 1992-09-15 | Boehringer Mannheim Corporation | Knee prosthesis |
CH686611A5 (en) * | 1992-01-14 | 1996-05-15 | Sulzer Medizinaltechnik Ag | Art Royal knee. |
US5330534A (en) * | 1992-02-10 | 1994-07-19 | Biomet, Inc. | Knee joint prosthesis with interchangeable components |
US5370699A (en) * | 1993-01-21 | 1994-12-06 | Orthomet, Inc. | Modular knee joint prosthesis |
US5728162A (en) * | 1993-01-28 | 1998-03-17 | Board Of Regents Of University Of Colorado | Asymmetric condylar and trochlear femoral knee component |
FR2704141A1 (en) * | 1993-04-21 | 1994-10-28 | Luer Sa | Family of modular bicompartmental knee prostheses |
US5702458A (en) * | 1994-12-09 | 1997-12-30 | New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery | Joint prosthesis |
FR2735682B1 (en) * | 1995-06-21 | 1997-12-12 | Afriat Jacques | TOTAL KNEE JOINT PROSTHESIS |
GB9707717D0 (en) * | 1997-04-16 | 1997-06-04 | Walker Peter S | Knee prosthesis having guide surfaces for control of anterior-posterior translation |
US6325828B1 (en) * | 1997-12-02 | 2001-12-04 | Rose Biomedical Research | Apparatus for knee prosthesis |
US6080195A (en) * | 1998-07-08 | 2000-06-27 | Johnson & Johnson Professional, Inc. | Rotatable and translatable joint prosthesis with posterior stabilization |
US6152960A (en) * | 1998-10-13 | 2000-11-28 | Biomedical Engineering Trust I | Femoral component for knee endoprosthesis |
-
2000
- 2000-07-19 JP JP2000218220A patent/JP3679315B2/en not_active Expired - Fee Related
-
2001
- 2001-07-17 EP EP01117296A patent/EP1174099B1/en not_active Expired - Lifetime
- 2001-07-17 DE DE60113483T patent/DE60113483T2/en not_active Expired - Lifetime
- 2001-07-18 US US09/907,792 patent/US6406497B2/en not_active Expired - Lifetime
Cited By (66)
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---|---|---|---|---|
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US9861488B2 (en) | 2003-02-08 | 2018-01-09 | Depuy International, Ltd. | Knee joint prosthesis |
US9833542B2 (en) | 2003-03-07 | 2017-12-05 | Louis A. Serefin, Jr. Trust | Ceramic manufactures |
US9162008B2 (en) | 2003-03-07 | 2015-10-20 | Louis A. Serafin, Jr. | Ceramic manufactures |
US9694102B2 (en) | 2003-03-07 | 2017-07-04 | Louis A. Serafin, Jr. Trust | Ceramic manufactures |
US9259508B2 (en) | 2003-03-07 | 2016-02-16 | Louis A. Serafin, Jr. Trust | Ceramic manufactures |
US20060025866A1 (en) * | 2003-03-07 | 2006-02-02 | Serafin Louis A Jr | Ceramic manufactures |
US20040243245A1 (en) * | 2003-04-24 | 2004-12-02 | Sylvie Plumet | Postero-stabilised prosthesis with non-shifting tibial stud |
US20060147332A1 (en) * | 2004-12-30 | 2006-07-06 | Howmedica Osteonics Corp. | Laser-produced porous structure |
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US8292964B2 (en) * | 2005-12-14 | 2012-10-23 | New York University | Surface guided knee replacement |
US8211181B2 (en) * | 2005-12-14 | 2012-07-03 | New York University | Surface guided knee replacement |
US20070135925A1 (en) * | 2005-12-14 | 2007-06-14 | Walker Peter S | Surface guided knee replacement |
US20070135926A1 (en) * | 2005-12-14 | 2007-06-14 | Peter Walker | Surface guided knee replacement |
US20070288021A1 (en) * | 2006-06-07 | 2007-12-13 | Howmedica Osteonics Corp. | Flexible joint implant |
US20080050412A1 (en) * | 2006-08-15 | 2008-02-28 | Howmedica Osteonics Corp. | Antimicrobial implant |
US7837737B2 (en) | 2006-08-15 | 2010-11-23 | Howmedica Osteonics Corp. | Femoral prosthesis |
US20080140214A1 (en) * | 2006-08-15 | 2008-06-12 | Howmedica Osteonics Corp. | Femoral prosthesis |
US8147861B2 (en) | 2006-08-15 | 2012-04-03 | Howmedica Osteonics Corp. | Antimicrobial implant |
US8142886B2 (en) | 2007-07-24 | 2012-03-27 | Howmedica Osteonics Corp. | Porous laser sintered articles |
US9433494B2 (en) | 2007-11-02 | 2016-09-06 | Biomet Uk Limited | Prosthesis for simulating natural kinematics |
US10531948B2 (en) | 2007-11-02 | 2020-01-14 | Biomet Uk Limited | Prosthesis for simulating natural kinematics |
US9675441B2 (en) | 2007-11-02 | 2017-06-13 | Biomet Uk Limited | Prosthesis for simulating natural kinematics |
US9381079B2 (en) * | 2007-11-02 | 2016-07-05 | Biomet Uk Limited | Prosthesis for stimulating natural kinematics |
US20130297020A1 (en) * | 2007-11-02 | 2013-11-07 | Biomet Uk Limited | Prosthesis For Stimulating Natural Kinematics |
US8292965B2 (en) | 2008-02-11 | 2012-10-23 | New York University | Knee joint with a ramp |
US20090204221A1 (en) * | 2008-02-11 | 2009-08-13 | Peter Stanley Walker | Knee joint with a ramp |
US20090319049A1 (en) * | 2008-02-18 | 2009-12-24 | Maxx Orthopedics, Inc. | Total Knee Replacement Prosthesis With High Order NURBS Surfaces |
US9788955B2 (en) * | 2008-02-18 | 2017-10-17 | Maxx Orthopedics, Inc. | Total knee replacement prosthesis with high order NURBS surfaces |
US7998203B2 (en) | 2008-06-06 | 2011-08-16 | Blum Michael F | Total knee prosthesis and method for total knee arthroplasty |
US20090306783A1 (en) * | 2008-06-06 | 2009-12-10 | Blum Michael F | Total Knee Prosthesis and Method for Total Knee Arthroplasty |
US8298288B2 (en) | 2008-06-24 | 2012-10-30 | New York University | Recess-ramp knee joint prosthesis |
US20090319047A1 (en) * | 2008-06-24 | 2009-12-24 | Peter Stanley Walker | Recess-ramp knee joint prosthesis |
US20110125275A1 (en) * | 2009-11-16 | 2011-05-26 | New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery | Prosthetic condylar joints with articulating bearing surfaces having a translating contact point during rotation thereof |
US8900315B2 (en) * | 2009-11-16 | 2014-12-02 | New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery | Constrained condylar knee device |
US20110125279A1 (en) * | 2009-11-16 | 2011-05-26 | New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery | Constrained condylar knee device |
US8870964B2 (en) * | 2009-11-16 | 2014-10-28 | New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery | Prosthetic condylar joints with articulating bearing surfaces having a translating contact point during rotation thereof |
US20110190898A1 (en) * | 2010-01-29 | 2011-08-04 | Lenz Nathaniel M | Cruciate-retaining knee prosthesis |
US10952862B2 (en) | 2010-01-29 | 2021-03-23 | Smith & Nephew, Inc. | Cruciate-retaining knee prosthesis |
US8900316B2 (en) | 2010-01-29 | 2014-12-02 | Smith & Nephew, Inc. | Cruciate-retaining knee prosthesis |
US9364896B2 (en) | 2012-02-07 | 2016-06-14 | Medical Modeling Inc. | Fabrication of hybrid solid-porous medical implantable devices with electron beam melting technology |
US9180010B2 (en) | 2012-04-06 | 2015-11-10 | Howmedica Osteonics Corp. | Surface modified unit cell lattice structures for optimized secure freeform fabrication |
US10614176B2 (en) | 2012-04-06 | 2020-04-07 | Howmedica Osteonics Corp. | Surface modified unit cell lattice structures for optimized secure freeform fabrication |
US9135374B2 (en) | 2012-04-06 | 2015-09-15 | Howmedica Osteonics Corp. | Surface modified unit cell lattice structures for optimized secure freeform fabrication |
US11759323B2 (en) | 2012-04-06 | 2023-09-19 | Howmedica Osteonics Corp. | Surface modified unit cell lattice structures for optimized secure freeform fabrication |
US20170266013A1 (en) * | 2014-10-21 | 2017-09-21 | Kyocera Medical Corporation | Artificial knee joint implant |
US10201429B2 (en) * | 2014-10-21 | 2019-02-12 | Kyocera Corporation | Artificial knee joint implant |
US11298747B2 (en) | 2017-05-18 | 2022-04-12 | Howmedica Osteonics Corp. | High fatigue strength porous structure |
US11684478B2 (en) | 2017-05-18 | 2023-06-27 | Howmedica Osteonics Corp. | High fatigue strength porous structure |
CN109124832A (en) * | 2018-10-18 | 2019-01-04 | 北京四正医疗器械有限责任公司 | A kind of lateral femoral condyle prosthesis suitable for female patient |
Also Published As
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JP2002028170A (en) | 2002-01-29 |
EP1174099A1 (en) | 2002-01-23 |
JP3679315B2 (en) | 2005-08-03 |
DE60113483D1 (en) | 2005-10-27 |
EP1174099B1 (en) | 2005-09-21 |
US6406497B2 (en) | 2002-06-18 |
DE60113483T2 (en) | 2006-07-06 |
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