US20110137619A1 - High Performance Knee Prostheses - Google Patents

Abstract

Knee prostheses featuring components that more faithfully replicate the structure and function of the human knee joint in order to provide, among other benefits: greater flexion of the knee in a more natural way by promoting or at least accommodating internal tibial rotation in a controlled way, replication of the natural screw home mechanism, and controlled articulation of the tibia and femur respective to each other in a more natural way. In a preferred embodiment, such prostheses include an insert component disposed between a femoral component and a tibial component, the insert component preferably featuring among other things a reversely contoured posterolateral bearing surface that helps impart internal rotation to the tibia as the knee flexes. Other surfaces can also be specially shaped to achieve similar results, preferably using iterative automated techniques that allow testing and iterative design taking into account a manageable set of major forces acting on the knee during normal functioning, together with information that is known about natural knee joint kinetics and kinematics.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS
• This application is a continuation application of U.S. patent application Ser. No. 12/023,112 filed Jan. 31, 2008, which is a continuation application of U.S. patent application Ser. No. 10/743,885 filed Dec. 22, 2003, now patented as U.S. Pat. No. 7,326,252, which application claims priority to U.S. Ser. No. 60/435,426 entitled “Knee Prosthesis Having Improved Stability and Rotational Control” filed Dec. 20, 2002, the entire contents of all of which are herein incorporated by this reference.
BACKGROUND
• 1. Field of the Invention
• The invention relates generally to knee prostheses and, more specifically, to knee prostheses which more closely emulate the anatomy and function of the knee and thereby feature range of flexion, rotation of the tibia relative to the femur, the screw home mechanism, and other structural and functional characteristics of the actual knee joint.
• 2. General Background of the Invention
• Disease and trauma affecting the articular surfaces of the knee joint are commonly treated by surgically replacing the ends of the femur and tibia with prosthetic femoral and tibial implants, and, in some cases, replacing the patella with a patella component. Such surgeries are sometimes referred to as total knee replacement (TKR). In TKR surgery, a surgeon typically affixes two prosthetic components to the patient's bone structure; a first to the patient's femur and a second to the patient's tibia. These components are typically known as the femoral component and the tibial component respectively.
• The femoral component is placed on a patient's distal femur after appropriate resection of the femur. The femoral component is usually metallic, having a highly polished outer condylar articulating surface, which is commonly J-shaped.
• A common type of tibial component uses a tray or plateau that generally conforms to the patient's resected proximal tibia. The tibial component also usually includes a stem that extends at an angle to the plateau in order to extend into a surgically formed opening in the patient's intramedullary canal. The tibial component and tibial stem are both usually metallic.
• A plastic or polymeric (often ultra high molecular weight polyethylene) insert or bearing fits between the tray of the tibial component and the femoral component. This insert provides a surface against which the femoral component condylar portion articulates, i.e., moves in gross motion corresponding generally to the motion of the femur relative to the tibia.
• Modern TKR's are tricompartmental designs; they replace three separate articulating surfaces within the knee joint: the patello-femoral compartment and the lateral and medial inferior tibio-femoral compartments. Most currently available TKR's are designed to articulate from a position of slight hyperextension to approximately 115 to 130° flexion. A tricompartmental design can meet the needs of most TKR patients even though the healthy human knee is capable of a range of motion (ROM) approaching 170°. However, there are some TKR patients who have a particular need to obtain high flexion in the knee joint. For many, a TKR that permits patients to achieve a ROM in excess of 130° is desirable to allow deep kneeling, squatting and sitting on the floor with the legs tucked underneath.
• Additionally, a common complaint of TKR patients is that the replaced knee does not does function like a normal knee or “feel normal.” The replaced knee does not achieve normal knee kinematics or motion and generally has a more limited ROM than a normal knee. Currently available designs produce kinematics different than the normal knee during gait, due to the complex nature of the knee joint and the motion of the femur and tibia relative to one another during flexion and extension. For example, it is known that, in addition to rotating about a generally horizontal axis during flexion and extension, the tibia also rotates about its longitudinal axis. Such longitudinal rotation is typically referred to as either external or internal rotation, depending on whether reference is being made to the femur or tibia respectively.
• Very few currently available designs allow this longitudinal rotation. One known method to allow rotation is a mobile-bearing knee prosthesis. In mobile-bearing knee prostheses, the insert has increased contact with the condyles of the femoral component and rotates on top of the tibial component. However, mobile-bearing knee prostheses are less forgiving of soft tissue imbalance, increasing the incidence of bearing spin-out and dislocation. Another concern is that the mobile-bearing prostheses create an additional interface and underside wear may occur.
• Constructing a total knee prosthesis which replicates the kinematics of a natural knee has been an on-going challenge in the orthopaedic field. Several attempts have been made and are well known in the prior art, including those shown in U.S. Pat. Nos. 6,264,697 and 6,325,828. Conventional designs such as these, however, leave room for improvement in simulating the structure and operation of actual knee joints, in at least the aspects of range of motion, internal rotation of the tibia relative to the femur as the knee flexes, and rotation of the tibia relative to the femur in overextension in order to allow the knee to be stabilized more efficiently.
SUMMARY
• Devices according to aspects of the invention achieve more faithful replication of the structure and function of the actual knee joint by, among other things, adoption and use of structure and shaping of at least the polymeric insert and the femoral component to cause these components to cooperate with each other in new and unconventional ways (at least in the art of prosthetics) at various stages throughout the range of knee motion.
• According to certain aspects and embodiments of the invention, there is provided a knee prosthesis in which the insert features a lateral posterior surface which slopes in a distal direction (as compared to the corresponding medial posterior surface) as it continues toward the posterior aspect of the insert, in order to cooperate with the lateral condyle of the femoral component to impart internal rotation to the tibia as the knee flexes between substantially 0 and substantially 130 degrees of flexion, to allow the prosthesis to induce or allow tibial internal rotation in a controllable manner as a function of flexion, to reduce the forces of any femoral component cam acting upon a post or other raised portion of the insert, or any combinations of these.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis in which the insert features a greater thickness in certain lateral portions to increase durability, accommodate a more anatomic femoral component which features a lateral condyle smaller in some dimensions than its medial condyle, to impart a joint line more accurately replicating natural physiology, or any combinations of these.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis in which the insert features more anatomic sulcus placement in order improve operation of the prosthesis by more anatomically applying forces imposed on the prosthesis by quadriceps and the patellar tendon, allow the prosthesis to replicate natural anatomy more effectively, or any combinations of these.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis in which the insert features a lateral surface that is curved or “swept” in plan, in order to allow the lateral condyle to track in arcuate fashion on the bearing surface at certain ranges of knee flexion and rotation, to assist in facilitating the screw home mechanism, or combinations of these.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis in which the insert features a post or other raised portion whose anterior surface is shaped to serve effectively as an anterior cruciate ligament when engaged with a cam during ranges of flexion such as after heel strike upon actuation of the quadriceps.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis in which the insert features a post or other raised portion whose posterior surface is shaped to assist internal rotation of the tibia relative to the femur as the knee flexes, such as starting at angles such as in a range of substantially 50 or more degrees, to help ensure that post/cam forces are directed net anteriorly, or a combination of these.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis in which the insert features rounded or chamfered peripheral edges to help reduce wear on surrounding tissue and/or for other purposes.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis with any desired combination or permutation of any of the foregoing features, properties or results.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis including a femoral component that includes a lateral condyle that is in some distal and posterior aspects smaller than corresponding dimensions of the medial condyle, in order to simulate more closely natural physiology, allow adequate insert thickness under the lateral condyle so that, for instance, the posteriolateral surface of the insert can feature convexity or slope, assist internal rotation of the tibia relative to the femur as the knee flexes from substantially 0 degrees to substantially 130 degrees, or any combinations of these.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis including a femoral component that includes a lateral condyle with anterior surfaces more pronounced than corresponding anterior surfaces on the medial condyle, in order to replicate more closely natural anatomic structures in retaining the patella in lower ranges of flexion, cause the patella or substitute structure to track more physiologically at such ranges of motion, cause the quadriceps more physiologically to apply force to the prosthetic components and tibia in lower ranges of flexion, or any combinations of these.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis including a femoral component that includes a cam that cooperates with a post or other raised portion on the insert to assist internal rotation on the tibia, ensure that cam/post forces are directed net anteriorly or a combination of these.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis including a femoral component that includes an anterior cam which cooperates with a post or other raised portion on the insert to simulate action of the anterior cruciate ligament at lower ranges of flexion.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis including a femoral component and an insert in which during operation in situ, the femoral component is situated more anteriorly on the insert at low angles of flexion than in conventional knee prostheses, in order to reduce the forces on the post of the insert, to resemble more closely actual operation and kinematics of the knee, or a combination of these.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis including a femoral component and an insert which during operation in situ reduces paradoxical motion and actual cam to post contact, and when there is contact, reduces impact of contact and force of contact, between the femoral component cam and the insert post or other raised portion during desired ranges of motion.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis including a femoral component which features a backdrafted anterior slope of the interior surfaces of the posterior condylar portions, in order to allow the distal portion of the femur to be resected so that the anterior cut and the posterior cut are not parallel, such that the distal extremity of the femur is physically greater in anterior-posterior dimension than portions more proximal, whereby the distal extremity of the femur can be physically captured by the interior surfaces of the femoral component.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis which helps impart internal rotation to the tibia as the knee flexes from substantially 0 degrees of flexion to substantially 130 degrees of flexion, such that the tibia is substantially fully internally rotated to an angle of at least approximately 8 degrees in order to allow such flexion to occur in more physiological fashion, to reduce the possibility that the quadriceps will pull the patella undesirably relative to the knee in a lateral direction (lateral subluxation), to allow the patella or its replacement to track the trochlear groove, or any combinations of these.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis which helps impart internal rotation of the tibia as the knee flexes between substantially zero degrees and substantially 130 degrees, to at least substantially 8 degrees of internal rotation of the tibia relative to the femur at flexion angles greater than 130 degrees.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis which imparts internal rotation of the tibia relative to the femur as the knee flexes from substantially 0 degrees to substantially 130 degrees of flexion, so that the tibia is substantially fully internally rotated relative to the femur to an angle of at least substantially 8 degrees at a flexion angle of substantially 130 degrees, such flexion and internal rotation of the tibia being facilitated at least in part by a twisting moment created by contact of the condyles of the femoral component on the insert.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis which imparts internal rotation of the tibia relative to the femur as the knee flexes from substantially 0 degrees to substantially 130 degrees of flexion, so that the tibia is substantially fully internally rotated relative to the femur to an angle of at least substantially 8 degrees at a flexion angle of substantially 130 degrees, such flexion and internal rotation of the tibia being facilitated at least in part by a twisting moment created by contact between the post or other raised portion of the insert and at least one cam of the femoral component.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis whose structure facilitates the screw home mechanism.
• According to certain aspects and embodiments of the invention, there is further provided a knee prosthesis which allows flexion at flexion angles greater than 130 degrees while allowing internal rotation of the tibia relative to the femur as the knee flexes from substantially 0 degrees to substantially 130 degrees, without the need for a mobile bearing design or to allow the insert to swivel or rotate relative to the tibial component.
• According to certain aspects and embodiments of the invention, there are provided methods of designing knee prosthetic components using simulation of a femoral, patella and insert structure, physiological data regarding structure and function of natural knees, and applying at least six force vectors to the structure throughout a desired range of motion to effectively and efficiently simulate forces applied to the tibia in the body: force applied by the patella ligament, ground reaction force, relative force applied by the lateral condyle on the insert, relative force applied by the medial condyle on the insert, force applied by the hamstring muscles, and relative force applied by the cam surfaces of the femoral component on the post or other raised portion of the insert.
• According to certain aspects and embodiments of the invention, there are provided methods of designing knee prosthetic components using simulation of a femoral and insert structure and applying to the structure throughout a desired range of motion, force vectors that represent relatively greater forces applied by some ligaments, tendons and muscles than others, such as the relatively great forces applied by the quadriceps when they actuate and by the hamstrings when they actuate.
• According to certain aspects and embodiments of the invention, there are provided methods of designing knee prosthetic components using simulation of a femoral and insert structure and applying to the structure a desired set of forces, evaluating the performance of the structure, modifying the structure as simulated in the computer, and repeating the process until a desired design is reached.
• According to additional aspects and embodiments of the invention, there is provided a knee prosthesis comprising: a femoral component adapted to fit on a distal end of a femur, the femoral component including a lateral condylar structure and a medial condylar structure, the geometry of the lateral condylar structure being different from the geometry of the medial condylar structure; and an accommodation structure including a lateral proximal surface adapted to cooperate with the lateral condylar structure of the femoral component, and a medial proximal surface adapted to cooperate with the medial condylar structure of the femoral component, the geometry of the lateral proximal surface and the medial proximal surface being different from each other, to assist in imparting internal rotation on the tibia relative to the femoral component as the knee flexes from substantially zero degrees of flexion to substantially 130 degrees of flexion.
• According to additional aspects and embodiments of the invention, there is provided a knee prosthesis comprising a femoral component adapted to fit on a distal end of a femur, the femoral component including: an anterior portion which includes an interior surface adapted to interface with the femur; a lateral condylar structure which includes a posterior section which in turn includes an interior surface adapted to interface with the femur; and a medial condylar structure which includes a posterior section which in turn includes an interior surface adapted to interface with the femur; wherein the interior surfaces are adapted to physically capture at least a portion of the femur in the femoral component relative to a distal translation substantially parallel to the anatomic axis of the femur; and wherein all interior surfaces of the femoral component are adapted to allow the femoral component to clear resected portions of the femur physically as the femoral component is rotated onto the femur about its posterior portions during installation.
• Certain embodiments and aspects of the invention also provide other characteristics and benefits, and other objects, features and advantages of various embodiments and aspects of the invention will be apparent in the other parts of this document.
BRIEF DESCRIPTION OF THE DRAWINGS
• FIG. 1A shows a perspective view of a left knee prosthesis according to an embodiment of the invention.
• FIGS. 1B-1C show an exploded front perspective view of a femoral component and an insert of a left knee prosthesis according to an embodiment of the invention.
• FIG. 2 shows an exploded back perspective view of a femoral component and an insert of a left knee prosthesis according to an embodiment of the invention.
• FIG. 3 shows an exploded front perspective view of a femoral component and an insert of a left knee prosthesis according to an embodiment of the invention.
• FIG. 4 is a side view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the left knee at full extension.
• FIG. 5 is a side view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 30° flexion.
• FIG. 6 is a side view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 60° flexion.
• FIG. 7 is a side view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 90° flexion.
• FIG. 8 is a side view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 120° flexion.
• FIG. 9 is a side view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 130° flexion.
• FIG. 10 is a side view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 140° flexion.
• FIG. 11 is a side view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 150° flexion.
• FIG. 12 is a top plan view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at full extension.
• FIG. 13 is a top plan view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 30° flexion.
• FIG. 14 is a top plan view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 60° flexion.
• FIG. 15 is a top plan view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 90° flexion.
• FIG. 16 is a top plan view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 120° flexion.
• FIG. 17 is a top plan view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 130° flexion.
• FIG. 18 is a top plan view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 140° flexion.
• FIG. 19 is a top plan view of portions of a left knee prosthesis according to an embodiment of the invention showing the kinematics of the knee at 150° flexion.
• FIG. 20 shows a front plan view of a left knee prosthesis according to an embodiment of the invention.
• FIG. 21 shows certain aspects of a femoral component of a knee prosthesis according to an embodiment of the invention.
• FIG. 22 shows certain aspects of a cam of a femoral component of a knee prosthesis according to an embodiment of the invention.
• FIG. 23 shows certain aspects of a proximal surface of an insert of a knee prosthesis according to an embodiment of the invention.
• FIG. 24 is a cross sectional view showing certain aspects of a lateral bearing surface of a knee prosthesis according to an embodiment of the invention.
DETAILED DESCRIPTION
• Various embodiments of the invention provide improved knee prostheses for replacing at least a portion of a knee joint between the distal end of a femur and the proximal end of a tibia.
• While not wishing to be bound by any particular theory, the inventors have discovered that knee prostheses which more faithfully and closely replicated the function, anatomy and physiology of the normal human knee would yield a number of advantages. Among other things, such prostheses would provide an increased range of motion and would function more normally particularly in extension, deep flexion and during normal gait. They would take into account the forces imposed on the knee by quadriceps and hamstrings actuation, forces which great in magnitude but not fully considered in conventional knee prosthesis design. Knee prostheses according to various aspects of the invention recognize that during movement of the knee, particularly during flexion, the position and orientation (kinematics) of the bones of the knee are a result of achieving equilibrium of the forces that cause motion of the knee (kinetics). Additionally, the shape of the articular surfaces (anatomy) acting in combination with forces imposed by various muscles, ligaments and tendons, determines the direction of the large contact forces. Therefore, aspects of the invention take into account that anatomy influences kinetics and kinetics determine kinematics.
• Conventional knee prostheses have been developed without recognition of the full range of kinetics of active knee movement. Many are primarily concerned with achieving greater flexion. However, in addition to flexion and extension, motion of the knee is both rotational and translational. The femoral condyles both roll and glide as they articulate with respect to the tibial plateaus. As the knee moves from full extension into flexion the axis of rotation between the femur and the tibia moves posteriorly relative to both the femur and the tibia. Additionally, in the normal human knee, internal rotation of the tibia relative to the femur occurs as the knee flexes between full extension and approximately 130° of flexion. Knee prostheses according to various aspects of the invention provide various surfaces on at least the femoral component and the insert which promote such greater flexion, the screw home mechanism, internal rotation of the tibia relative to the femur as the knee flexes, and other characteristics of the natural knee.
• According to some aspects of the invention, the design of knee prosthesis components is conducted using a process which (1) tests various performance aspects of a proposed design using computer simulation of the design and various forces imposed upon it, (2) allows analysis of the test results for development of improvements to the proposed design; (3) uses test results to change the proposed design (either manually or automatically), (4) tests various performance aspects of the modified design using computer simulation of the design and various forces imposed upon it, and (5) repeats these tasks in an iterative fashion until the performance testing shows an iteratively modified design to feature acceptable performance characteristics. It is also significant that in such performance testing, the performance of the proposed design is tested using forces that occur at various points in various activities, so that the performance testing is dynamic across extended ranges of motion and takes into account considerable forces placed on the design by actuation of the quadriceps and hamstring muscles, for example, and the consequent kinetic and kinematic effects of such forces.
• A preferred embodiment of a knee prosthesis according to the invention is shown inFIGS. 1A-1C and2-4, and identified by the numeral100. Theknee prosthesis100 shown in these figures is designed to replace at least a portion of a left knee joint between the distal end of a femur and the proximal end of a tibia. A mirror image (not shown) ofknee prosthesis100 will replace at least a portion of a right knee between the distal end of a femur and the proximal end of a tibia.
• Theknee prosthesis100 includes afemoral component200 for mounting to a distal end of a femur, atibial component300 for mounting to a proximal end of a tibia, and aninsert400.
• Embodiments of thefemoral component200 preferably include amedial condylar section202, alateral condylar section204 and atrochlear groove206 joining theanterior portions214,216 of the medial and lateralcondylar sections202,204 together. The medial and lateralcondylar sections202,204 are disposed apart from one another to form an intercondylar recess or notch208. Eachcondylar section202,204 has anouter surface210,212 for engaging atibial component300 or insert400 as will become apparent. Theouter surfaces210,212 of eachcondylar section202,204 preferably havedistal portion218,220 for engaging a portion of thetibial component300 or insert400 when the knee joint is extended and partially flexed, andposterior portions222,224 for engaging a portion of thetibial component300 or insert400 when the knee joint is flexed at angles of substantially 90° or greater.
• Embodiments of afemoral component200 according certain aspects of this particular nonlimiting embodiment of the invention also replicate the physiologicaljoint line227 of a normal knee as shown inFIG. 20. The physiologicaljoint line227 may be considered to be a line extending between the distal most portions of each condyle at a knee flexion angle of zero degrees. This physiological joint line is oriented at an angle of approximately 93 degrees from the mechanical axis of the leg (which could also be considered to be 87 degrees from the mechanical axis of the leg depending on perspective), or approximately 3 degrees from horizontal as shown inFIG. 20. The joint line established by prostheses according to certain embodiments and aspects of the invention preferably replicate this physiologicaljoint line227 as shown in that drawing.
• Embodiments of thefemoral component200 preferably have a thickness approximately matching the bone resection necessary for the total knee replacement.
• Embodiments of thefemoral component200 also preferably have alateral condylar section204 that is different in geometry than the geometry of themedial condylar section202. In the embodiment shown inFIG. 1, the size of lateralcondylar section204 is smaller than the size of medialcondylar section202 so that its outer surfacedistal portion220 does not extend as far distally as does the outer surfacedistal portion218 of medialcondylar section202.
• Thefemoral component200 may include a rounded medial profile. According to certain embodiments, for example, it may feature a medial profile which includes a single radius from 15-160°, and may also include a lateral profile that is less round or curved distally, with a single radius from 10-160°.
• In the normal human knee, the patella glides caudally on the femoral condyles from full extension to full flexion. By 20 to 30° of flexion, the patella first begins to articulate with the trochlear groove. At extreme flexion, the patella lies in the intercondylar recess. Initially the patella contact occurs distally and with increased flexion the contact areas shift proximally on the patella. Patellofemoral contact force is substantially body weight when walking, and increases to substantially 5 times body weight when stair climbing. These contact forces therefore impose a substantial load on the knee joint, which prostheses according to certain embodiments and aspects specifically take into account.
• Knee prostheses according to certain embodiments and aspects of the invention incorporate features that allow the patellar implant of the knee prostheses to move in a way similar to the normal human knee and to withstand the normal patellofemoral contact force without unnecessary ligament release. These features include various aspects of the shape of portions of themedial condylar section202 and thelateral condylar section204, to be more consistent with natural anatomical geometry. For instance,anterior portion216 of lateralcondylar section204 can be configured to extend further anteriorly thananterior portion214 of medialcondylar section202, or to be more abruptly shaped on its surface that cooperates with the patella, so that it acts as a buttress to guide the patella at low flexion angles and in extension.
• Femoral components according to certain embodiments and aspects of the invention can also include a patella-friendlytrochlear groove206. Thetrochlear groove206 in such embodiments is substantially S-shaped and lateralizes thepatella500. Thetrochlear groove206 further allows for a smooth transition between theanterior portions214,216 of the condylar sections andintercondylar notch208. This further reduces the contact forces on thepatella500.
• Femoral components200 according to certain embodiments and aspects of the invention can include flexed or backdrafted substantially planar interior or bone interface surfaces223 and225 (collectively, backdrafted surface229), on the anterior surfaces of posterior portions ofmedial condyle section222 andlateral condyle section224. Preferably, theinterior surfaces223,225 are coplanar and are oriented so that their planes converge with a plane formed by theinterior surface215 on the posterior side ofanterior portions214 and216 of thefemoral component200 as shown more clearly inFIG. 21. In this way, proximal portions of these posterior condylarinterior surfaces223 and225 are located closer to the plane of theinterior surface215 of the anterior portion of thefemoral component200 than are distal portions ofsurfaces223 and225. Preferably, the convergence angle is in a range of between 1 and 30 degrees, and more preferably, the convergence angle is approximately 15 degrees. Thebackdrafted surface229 extends the articular surface of thefemoral component200 with minimal bone resection. Removing less bone decreases the likelihood of later femoral fracture. It also minimizes the likelihood that thefemoral component200 will be forced off the end of the femur in deep flexion, since it serves to lock onto or capture the distal end of the femur in thefemoral component200.
• Thefemoral component200 with thebackdrafted surface229 can be installed by hinging and rotating thefemoral component200 onto the resected femur about the posterior portions of the condyles of the femur. The inventors have discovered that it is possible, by configuring all anterior surfaces of thefemoral component200 correctly, as shown inFIGS. 4-11 and21, for example, to allow those surfaces to physically clear the resected bone as the femoral component is rotated onto the femur during installation. Among other ways to accomplish this configuration are: (1) to cause the interior surfaces to create a shallow interior space; and/or (2) to adjust angles and/or dimensions of the chamfered surfaces that connect theinterior surfaces223,225 ofcondylar sections202 and204 and/orinterior surface215 of the anterior portion of thecomponent200 to the bottom interior surface of thecomponent200.
• Interior surfaces of thecomponent200, includingsurfaces215,223 and225, need not be planar or substantially planar to accomplish the objective of capturing or locking onto the femur. For instance, one or more of them may be curved or partially curved and accomplish this objective by orienting one or both of the interior surfaces of thecondylar sections202,204 relative to the interior surface of the anterior portion of the femoral component at other than parallel.
• Certain embodiments of thefemoral component200 may include ananterior cam230, as shown inFIGS. 4-11. As explained further below, theanterior cam230 works with the post or other raisedportion422 of theinsert400 to provide anterior stabilization during early gait. Theanterior cam230 preferably includes a large radius to increase the contact area between theanterior cam230 and thepost422. Theanterior cam surface230 preferably does not engage the anterior surface of thepost422 for approximately 1-2 mm.
• Certain embodiments of thefemoral component200 may include aposterior cam232 as shown inFIGS. 4-11, among other places as well as in a closer view inFIG. 22. Preferably, theposterior cam232 is asymmetrical. Thelateral side238 may be larger than themedial side240, for example, as shown inFIG. 22. As explained further below, the largerlateral side238 provides optimal contact between theposterior cam232 and thepost422 during axial rotation, to assist in imparting internal rotation to the tibia relative to the femur as the knee flexes. In general, theposterior cam232 engages thepost422 between 50-60° flexion. Thepost422 may be thickened distally for additional strength.
• Prostheses according to certain embodiments of the invention, which do not need to serve a posterior stabilization function, such as those which can be characterized as cruciate retaining, need not have a post or other raisedsurface422 oninsert400, or cams, such ascams232 or230. In such embodiments and aspects, other surfaces such as portions of the medial and lateralcondylar sections202,204 acting without a post or raisedsurface422, for example, achieve or help achieve objectives of aspects of the invention, including allowing or imparting internal rotation to the tibia relative to the femur as the knee flexes, such as from substantially 0 degrees to substantially 130 degrees.
• Certain embodiments of thefemoral component200 may include conventional attachment aids for helping to secure thefemoral component200 to a distal end of a femur. Such attachment aids may include one or more pegs, fins, surface treatments including bone ingrowth surfaces, surfaces for accommodating spacers, shims or other structures, or as otherwise desired.
• Tibial components300 according to certain embodiments and aspects of the invention include a tray or base member for being secured to a proximal end of a tibia. The base member can include a stabilizing post, which is insertable into the tibial medullary canal and provides for the stabilization of thetibial component300 on the tibia.
• Tibial components according to embodiments and aspects of the invention feature a tray member which includes a proximal or upper surface, a distal or lower surface, a medial surface, a lateral surface, an anterior or front surface, and a posterior or rear surface. The proximal surface may be substantially flat and planar. The tray member preferably includes attachment aids for helping to secure the tray member to a proximal end of a tibia. Such attachment aids may include one or more pegs, fins, screws, surface treatments, etc.
• Femoral components200 andtibial components300 according to certain embodiments and aspects of the invention may be constructed in various manners and out of various materials. For example, thefemoral component200 andtibial component300 may be machined, cast, forged or otherwise constructed as a one-piece integral unit out of a medical grade, physiologically acceptable metal such as a cobalt chromium alloy or the like, in various sizes to fit a range of typical patients, or may be custom-designed for a specific patient based on data provided by a surgeon after physical and radiography examination of the specific patient.
• Inserts400 according to certain embodiments and aspects of the invention include a proximal orupper surface402, a distal orlower surface404, amedial surface406, alateral surface408, an anterior orfront surface410, and a posterior orrear surface412. For convenience, such aninsert400 may be considered to feature amedial side414 and alateral side416, corresponding to medial and lateral sides of the limb in which the insert is to be installed.
• Theproximal surface402 of theparticular insert400 according to one embodiment of the invention shown in the drawings has amedial portion418 for engaging theouter surface210 of themedial condylar section202 of thefemoral component200, and alateral portion420 for engaging theouter surface212 of thelateral condylar section204 of thefemoral component200.
• Inserts400 according to certain embodiments and aspects of the invention can include a central post or raisedportion422 as shown in the drawings. Thepost422 includes aproximal surface424, ananterior surface426, aposterior surface428 and medial and lateral side surfaces430,432. Theanterior surface426 ofpost422 in an embodiment of the insert, is tapered or curved at a desired angle with respect to thedistal surface404 of theinsert400 to minimize impingement of the patella or apatellar implant500 in deep flexion. The base can be tapered as desired in a posterior direction from theanterior surface426 to minimize impingement of theintercondylar notch208 offemoral component200 in hyperextension.
• Inserts400 of certain embodiments and aspects of the invention as shown in the drawings include an anterior curved surface. The anterior curved surface allows room for the patellar tendon (not shown). The insert may also include a posterior curved surface. The result of the posterior curved surface is the removal of material that may impinge on the posterior cortex of the femur in deep flexion. The radius of curvature may vary as desired to provide sufficient room for maximal flexion.
• The distal surface of theinsert400 according to certain embodiments and aspects of the invention may be substantially flat or planar for contacting the proximal surface of the tray member of thetibial component300. The distal surface preferably includes a dovetail or other appropriate locking mechanism that consists of an anterior portion and a posterior portion. However, any conventional method for positioning and/or retaining the insert relative to the tray member, whether constrained or unconstrained, may be used. In other embodiments, theinsert400 may be allowed to articulate relative to the tray of thetibial component300.
• On theproximal surface402 ofinserts400 according to certain embodiments and aspects of the invention, parts of themedial portion418 of the proximal surface and parts of thelateral portion420 are shaped to cooperate withouter surfaces210 of the medial condylar section offemoral component200 andouter surfaces212 of the lateral condylar section of the femoral component, as the knee flexes and extends. These parts are referred to as medialinsert bearing surface440 and lateralinsert bearing surface442.
• From a sagittal aspect, as shown inFIGS. 4-11 and also inFIGS. 23 and 24, posterior parts of thelateral bearing surface442 of the particular insert shown in the drawings features a reverse slope; that is, the lateral bearing surface slopes toward the bottom or distal surface of theinsert400 as the lateral bearing surface progresses toward the posterior or back periphery of theinsert400, preferably either through a convex arc or a straight slope. The purpose of the slope is to change the direction of the contact force between thelateral bearing surface442 and thelateral condylar section204, in order to add an anterior force on thelateral bearing surface442 greater than a corresponding anterior force on themedial bearing surface440 at some angles of knee flexion, to produce or help produce a twisting moment about the longitudinal axis of the tibia or impart or assist in imparting internal rotation of the tibia as the knee flexes. Preferably, this rotation-impartingsurface444 is configured to impart or assist inward tibial rotation relative to the femur as the knee flexes between substantially 0 degrees of flexion to substantially 130 degrees of flexion, the internal rotation angle achieving a magnitude of at least substantially 8 degrees at substantially 130 degrees of knee flexion. Since the contact force vector is perpendicular to thelateral bearing surface442, during rollback in the lateral compartment, a component of the contact force vector is generally parallel to the generally anteriorly oriented contact vector acting on thepost422. Accordingly, this contact force not only can help delay engagement of thepost422 with theposterior cam232, but it can also beneficially reduce the force required by thepost422 to produce lateral rollback, resist anterior motion of thefemoral component200 relative to theinsert400, and resist total force which is absorbed by thepost422 in accomplishing posterior stabilization of the knee.
• It is also possible to generate the tibial inward rotation inducing couple on theinsert400 by thefemoral component200 not only by using theposterior cam232 as discussed below, but also by altering the shape of parts of the medialinsert bearing surface440 or using other structures, surface shaping or other techniques, or any combination of them, as desired.
• Preferably, the lateralinsert bearing surface442 of the insert as shown in the drawings features a curved generally concave portion which sweeps laterally from its anterior extremity to approximately its middle, and then back medially from its middle to its posterior extremity, as shown inFIG. 23, for example. Such a swept surface helps guide thelateral condylar section202 as the locus of its contact points with theinsert400 move in a posterior direction as the knee flexes.
• Inserts400 according to certain embodiments and aspects of the invention may be constructed in various manners and from various materials. For example, they may be machined, molded or otherwise constructed as a one-piece, integral unit out of medical grade, physiologically acceptable plastic such as ultra high molecular weight polyethylene or the like, in various sizes to fit a range of typical patients, or may be custom-designed for a specific patient based on data provided by a surgeon after physical and radiographic examination of the specific patient. The material can be treated, for example, by radiation, chemistry, or other technology to alter its wear properties and/or strength or hardness. Portions of various surfaces ofinserts400 can be treated with radiation, chemicals or other substances or techniques to enhance wear resistance properties; they can also be subjected to suitable surface treatments for such purposes and others.
• If themedial condylar section202 and thelateral condylar section204 of thefemoral component200 were the same size, theinsert400 shown in the drawings would be thinner between its lateralinsert bearing surface442 and itsdistal surface404 than between its medialinsert bearing surface440 and thatdistal surface404. Such thinness may become unacceptable in regions between therotation inducing surface444 and thedistal surface404 in the posteriolateral region of theinsert400. To compensate, lateral parts of theinsert400 may be created thicker than medial parts, as shown for example inFIG. 20, so that the lateralinsert bearing surface442 is “higher” or more proximal than the medialinsert bearing surface440. In certain embodiments of theinsert400 as shown for example inFIG. 20, a line drawn between the most distal part of the medialinsert bearing surface440 and the most distal part of the lateralinsert bearing surface442 and denominated physiologicaljoint line227, forms an approximately 3 degree angle from a line perpendicular to the mechanical axis of the leg or in many insert400 structures, substantially 3 degrees from the plane of the distal surface of theinsert400. This 3 degree angle is similar to the structure of the human knee, where the physiological joint line is usually substantially 3 degrees from the mechanical axis of the joint. Thelateral contact point436 of thefemoral component200 and theinsert400 is initially higher than themedial contact point434. During flexion, as thelateral condyle204 rolls posteriorly, the lateralfemoral condyle204 moves down the arc or slope of tibialrotation inducing surface444 ofinsert400.
• In some cases, the epicondylar axis242 (the line connecting the lateral epicondylar prominence and the medial sulcus of the medial epicondyle) could have a tendency to decline, which could cause rotation about the long axis of the femur and might cause laxity of the LCL. According to certain embodiments of the invention, it would be possible to keep the epicondylar axis242 at the same height, by causing the sagittal curve of theposterior portion224 of thelateral condyle204 to be extended outwardly as could be visualized with reference to, for instance,FIGS. 4-11. For example, at 155° flexion, thelateral contact point434 could decline approximately 2.6 mm, so that 2.6 mm would be added to thelateral condyle204 thickness at a point corresponding to 155° flexion on the condyle to accomplish such a result, although other structures could be created to achieve the same end.
• When assembled, thefemoral component200 shown in the drawings is positioned on theinsert400 so that there is a slight posterior overhang. This optimizes the anterior-posterior patella ligament force components. The overhang may be much less than in conventional knee prostheses. For example, in conventional knee prostheses, the posterior overhang of thefemoral component200 may be as much as 6 mm. However, in knee prosthesis according to certain embodiments and aspects of the invention, the posterior overhang of thefemoral component200 is approximately 2 mm.
• As explained above, axial rotation is normal in knee joint motion. The “screw-home” mechanism is example of this motion. In the normal knee, during knee extension, the femur is positioned anteriorly on the tibial plateau. During the last 20° of knee extension, the femur glides anteriorly on the tibia and produces external tibial rotation. This screw-home mechanism in terminal extension results in tightening of both cruciate ligaments and locks the knee such that the tibia is in the position of maximal stability with respect to the femur.
• When the normal knee begins to flex, posterior glide of the femur begins first on the lateral tibial surface. Between approximately 0° and 130° of flexion, posterior glide on the lateral side produces relative tibial internal rotation, a reversal of the screw-home mechanism.
• Knee prostheses100 according to certain embodiments of the invention incorporate an allowance that mimics the screw-home mechanism. The screw-home allowance may be achieved by incorporating a swept surface on thelateral surface416 of theinsert400. The screw-home allowance is illustrated most clearly inFIG. 12.FIGS. 12-19 demonstrate that as the knee flexes from approximately zero degrees to approximately 130 degrees, thefemoral component200 and theinsert400 rotate relative to each other generally about a closely grouped set of medial contact points436. As the knee flexes, thefemoral component200 rotates externally relative to theinsert400, which would be fixed on atibial component300 in a fully assembledknee prosthesis100; or considered from the other perspective, theinsert400 and the tibia rotate internally relative to thefemoral component200 and the femur. The asymmetrical shape of theposterior cam232 reduces force on thecentral post422 that would oppose this rotation.
• This rotation, along with the increased flexion of theknee prostheses100 of the invention, is evident in the series of side views of portions of aknee prosthesis100 shown inFIGS. 4-11. To demonstrate the rotation between thefemoral component200 and theinsert400, which would be fixed on atibial component300 in a fully assembledknee prosthesis100, theinsert400 shown remains stationary, as thefemoral component200 rotates substantially about the medial contact point. Thus, as shown inFIG. 4, the knee is fully extended. As the knee flexes to 90 degrees (shown inFIG. 7), thelateral condylar section204 of thefemoral component200 rotates posteriorly on thelateral side416 of theinsert400. The rotation continues as the knee flexes to 130 degrees, as shown inFIG. 9, reaching at least approximately 8 degrees of internal rotation of the tibia relative to the femur. As the knee continues to flex beyond approximately 130 degrees, as shown inFIGS. 10-11, the internal rotation stays substantially the same, as the relative motion is primarily posterior translation of the femoral component on the insert.
• As the drawings show, when theknee prosthesis100 is assembled, the central post or raised portion of theinsert400 fits within the intercondylar recess. Because thefemoral component200 and theinsert400 are not fastened to each other, thefemoral component200 is able to easily articulate on theinsert400.
• FIGS. 4-11 thus sequentially show, from a side cross sectional aspect, kinematics of components of a knee prosthesis according to a preferred embodiment of the invention.FIGS. 12-19 show the same kinematics from a plan aspect, looking “down” on the prosthesis. These figures show kinematics of the prosthesis components at flexion angles of 0, 30, 60, 90, 120, 130, 140, and 150 degrees, respectively. At flexion angles of approximately 50 to 60 degrees, thecam232 begins contacting thepost422 for posterior stabilization, as shown inFIG. 6. As the rotation of thefemoral component200 continues, thepatella implant500 moves down thetrochlear groove206, which is structured according to aspects of the invention to simulate natural anatomy in order to allow thepatella implant500 to track properly, and generally from a lateral to medial position relative to thefemoral component200 as flexion continues. In this fashion, the shape of the femoral component accommodates the natural action of the kneecap as a fulcrum on the knee joint for the considerable forces applied by the quadriceps and the patellar ligament. As the knee flexes from substantially zero degrees of flexion to substantially 130 degrees of flexion, the tibialrotation inducing surface444 of the particular (nonlimiting) structure shown in the drawings acting in combination with thelateral condylar section204, plus the action of theasymmetrical posterior cam232 of thefemoral component200 on thepost422 of the insert, impart inward rotation to theinsert400 relative to the femur. This inward rotation corresponds to such inward rotation in the normal knee, and allows, among other things, the lower leg to be “folded” inward relative to the upper leg so that the patellar ligament and tendons from the quadriceps are not forced to be extended over the lateral part of the knee as is the case in some conventional designs. Yet the structure of the components shown in these drawings allows such natural internal rotation and other natural articulation of the tibia and femur relative to each other without freeing rotation of the insert relative to the tibial implant, or freeing other components in the prosthesis to move relative to each other, thereby taxing the other, weaker ligaments and tendons forming part of the knee, which are required to assume the new task of restraining the freed prosthetic components.
• Designs more closely approximating the structure and/or operation of the natural knee may be carried out according to the present invention by considering forces acting on the knee that are of more considerable magnitude than other forces. For instance, 6 major forces on the tibia can be used to simulate what a natural knee experiences during certain activities such as walking: (1) ground reaction force which can range from some part up to multiples of body weight in a normal knee kinetic environment; (2) tension imposed by the quadriceps acting through the patella tendon in a generally proximal direction tending to proximal-posterior in flexion and to proximal-anterior in extension; (3) tension applied by the hamstrings in a generally posterior direction; (4, 5) contact force of each condyle on its corresponding bearing surface of the tibial plateau; and (6) posterior stabilization force imposed by the posterior cruciate ligament or insert on the femur. The inventors have recognized that reducing the myriad of forces acting on the knee (such as from various more minor tendons and ligaments) to a manageable number, which may increase as time and processing power continue to evolve, allows for reliable and effective testing of proposed knee prosthesis designs, by accurately simulating what real knees experience. This manageable set of conditions may be combined with information that is known about the structure and the kinematics of natural knees to impose an essentially realistic test regime for computer testing and development of acceptable knee prosthetic designs.
• Applying a testing regime using a manageable but essentially realistic set of conditions allows iterative proposal of a design, testing it for performance in virtual, automated fashion in a computer, modification of the proposed design to reduce negative performance characteristics and to enhance positive ones, and repeated iteration of these tasks until an acceptable design is reached. The developers may therefore accordingly proceed at least partially iteratively, using test conditions that simulate what a real knee joint experiences and how it performs in such an environment, rather than attempting to design the complicated knee prosthetic components in a deterministic fashion based on anecdotal information, observation of knee components being articulated in the operating room, or based on assumptions that can be static and not reflect the complexity of nature.
• The foregoing is provided for disclosure of various embodiments, aspects and structures relating to the invention. Various modifications, additions and deletions may be made to these embodiments and/or structures without departing from the scope and spirit of the invention.

Claims (19)

1-37. (canceled)

38. A process for designing a knee prosthesis using a computing device, comprising:

(a) accessing, by the computing device, a simulation of a femoral component, the femoral component including a lateral condylar articulating surface, a medial condylar articulating surface, and a patellar articulating surface;

(b) accessing, by the computing device, a simulation of a tibial component, the tibial component including a medial articular surface for articulation with the medial condylar articulating surface and a lateral articular surface for articulation with the lateral condylar articulating surface;

(c) applying, by the computing device, a set of forces to the simulations of the femoral and tibial components, the set of forces including a patella ligament force, a ground reaction force, a relative force applied by the lateral condylar articulating surface on the lateral articular surface, a relative force applied by the medial condylar articulating surface on the medial articular surface, and a hamstring muscle force;

(d) after applying the set of forces, evaluating, by the computing device, a performance aspect of the simulated femoral and tibial components.

39. The process for designing a knee prosthesis ofclaim 38, further comprising, after evaluating the performance aspect, modifying, by the computing device, at least one of the simulated femoral and tibial components based on the evaluation of the performance aspect.

40. The process for designing a knee prosthesis ofclaim 39, further comprising, after modifying at least one of the simulated femoral and tibial components, re-applying, by the computing device, the set of forces to the simulated femoral and tibial components; and, after re-applying the set of forces to the simulated femoral and tibial components, evaluating, by the computing device, a second performance aspect of the simulated femoral and tibial components.

41. The process for designing a knee prosthesis ofclaim 38, wherein applying the set of forces to the simulations of the femoral and tibial components further comprises applying the set of forces to the simulations of the femoral and tibial components, the set of forces further comprising a relative force applied by an anterior cam of the simulation of the femoral component on an anterior post surface of the simulation of the tibial component.

42. The process for designing a knee prosthesis ofclaim 41, wherein applying the set of forces to the simulations of the femoral and tibial components further comprises applying the set of forces to the simulations of the femoral and tibial components, the set of forces further comprising a relative force applied by a posterior cam of the simulation of the femoral component on a posterior post surface of the simulation of the tibial component.

43. The process for designing a knee prosthesis ofclaim 38, wherein accessing, by the computing device, the simulation of the tibial component, comprises accessing a simulation of a tibial insert.

44. The process for designing a knee prosthesis ofclaim 38, wherein applying the set of forces comprises applying the set of forces to the simulations of the femoral and tibial components throughout a range of motion.

45. The process for designing a knee prosthesis ofclaim 44, wherein, during the application of the set of forces to the simulations of the femoral and tibial components, at least one of the set of forces changes at least once throughout the range of motion.

46. The process for designing a knee prosthesis ofclaim 45, wherein, during the application of the set of forces to the simulations of the femoral and tibial components, the patella ligament force increases to reflect an actuation of a quadriceps muscle.

47. The process for designing a knee prosthesis ofclaim 45, wherein, during the application of the set of forces to the simulations of the femoral and tibial components, the hamstring muscle force increases to reflect an actuation of a hamstring muscle.

48. The process for designing a knee prosthesis ofclaim 40, further comprising, after evaluating the second performance aspect, manufacturing a femoral implant and a tibial implant based on the simulated femoral and tibial components.

49. The process for designing a knee prosthesis ofclaim 48, wherein manufacturing the femoral implant comprises manufacturing the femoral implant to include an anterior cam.

50. The process for designing a knee prosthesis ofclaim 49, wherein manufacturing the femoral implant comprises manufacturing the femoral implant to include a radiused contact surface on the anterior cam.

51. The process for designing a knee prosthesis ofclaim 48, wherein manufacturing the femoral implant comprises manufacturing the femoral implant to include a posterior cam, the posterior cam including a medial side and a lateral side, wherein the medial side is asymmetric with respect to the lateral side.

52. The process for designing a knee prosthesis ofclaim 48, wherein manufacturing the femoral implant comprises manufacturing the femoral implant to include an anterior medial side and an anterior lateral side, wherein the anterior lateral side projects further anteriorly than the anterior medial side to define a buttress for cooperation with a patella.

53. The process for designing a knee prosthesis ofclaim 48, wherein manufacturing the tibial implant comprises manufacturing the tibial implant to include a lateral articular surface; wherein the lateral articular surface defines a sagittal cross-section including at least a posterior articular segment and an anterior articular segment; wherein the posterior articular segment slopes in a distal-posterior direction; and wherein the anterior articular segment does not slope in a distal-anterior direction.

54. The process for designing a knee prosthesis ofclaim 53, wherein manufacturing the tibial implant comprises manufacturing the tibial implant to include a medial articular surface that is asymmetric with respect to the lateral articular surface of the tibial implant.

55. The process for designing a knee prosthesis ofclaim 48, wherein:

(a) manufacturing the femoral component comprises manufacturing the femoral component to include a medial condyle and a lateral condyle; wherein the medial condyle comprises an anterior-medial condyle segment, a posterior-medial condyle segment, and a distal-medial condyle segment connecting the anterior-medial condyle segment to the posterior-medial condyle segment; wherein the lateral condyle comprises an anterior-lateral condyle segment, a posterior-lateral condyle segment, and a distal-lateral condyle segment connecting the anterior-lateral condyle segment to the posterior-lateral condyle segment; the distal-medial condyle segment projecting further distally relative to the distal-lateral condyle segment; and

(b) manufacturing the tibial component comprises manufacturing the tibial component to include a medial articular surface configured to articulate with the medial condyle of the femoral component and a lateral articular surface configured to articulate with the lateral condyle of the femoral component; wherein the medial articular surface is asymmetric with respect to the lateral articular surface; and wherein the lateral articular surface comprises an anterior half and a posterior half, the anterior half being asymmetric with respect to the posterior half.

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