MULTIAXIS CONTROLLED MOTION KNEE ORTHOSIS

Abstract: The present invention relates to an orthosis for control­ ling an unstable knee joint in the sagital, cononal and trans­ verse planes, comprising femural and tibial cuffs (17, 25) joined by links (34, 35) which are interconnected to provide a novel mechanical joint wherein camming slots (55, 57) are formed in one of the links with cams disposed on the other link, the slots (55, 57) comprising straight segments (60) and arcuate seg­ ments (62) so as to provide approximately 8 millimeters of slid­ ing movement betveen the femur and tibia, followed by relative rotation about the center of radius of the femural condyle as the leg is flexed. The tibial cuff (25) is conformed about the bo­ ney prominence (100) or shin of the tibia to inhibit rotation of the leg beneath the knee within the brace (15) itself.

Description: MULTIAXIS CONTROLLED MOTION KNEE ORTHOSIS BACKGROUND OF THE INVENTION Field of the Invention The present invention relates to orthopaedic devices for the stabilization and control of a human knee joint along several axes and has as its primary purpose the stabilization of the knee joint which has been injured. Stabilization and control is achieved in such a manner as to permit the user relative freedom in the normal use of the bones while, at the same time, permitting control over the joint so as to optimize healing. The human knee is acknowledged as one of the weakest joints in the body. It is the articulating joint between the thigh and calf muscle groups which support the body's weight while walking or running, and it is held together primarily by two small but powerful ligaments, the anterior and posterior cruciate ligaments. Knee instability arising out of cartilage damage, ligament strain and other such causes is relatively commonplace since the knee joint is subjected to significant loads during the course of almost any kind of physical activity requiring the use of the legs. Devices for adding support and strength to the knee joint have been known at least since the very early Sears and Roebuck catalogs, which provided elasticized support members intended to circumscribe the joint to apply a squeezing pressure which results in a "feeling" of additional support even though that support may be physiologically minimal. While the public has been sports-minded for years, it was not until the late 1960's, with a great increase in the volume of televised professional sports, and very highly paid athletes, and, in particular, contact sports such as football, basketball and soccer, that sports medicine, as a specialized field, evolved. Until that time, knee braces typically consisted of two sets of links connected by a pivot pin which were disposed on either side of the knee and sewn into an elasticized sleeve which was slipped over the knee joint like an elastic sock so that the pivot pins were disposed on either side of the knee. Such devices afforded virtually no protection to an athlete engaged in a contact sport, or in a sport where there is a large amount of stress placed on the knee joint due to running, jumping, pivoting and the like. Survey of the Prior Art Perhaps one of the first and most highly publicized breakthroughs, or at least advances in knee orthoses, occurred when the Lennox Hill brace was developed to protect the knees of Joe Namath, then one of the highest paid athletes in any sport. Several deficiencies in the Lennox Hill design have been recognized, however, and sports medicine people have spawned a plethora of other braces in attempts to improve knee stabilization. The designs include single and double pivot designs, although the double pivot design available typically includes a center link with pivot points at each end, and with the center link being axially aligned with the femur and tibia. Among such braces are included the model 4521 offered by Orthopedic Systems, Inc. of Hayward, California, and the polyaction knee orthos offered by Scott Orthopedic Labs in Denver, Colorado. Still another, called c.t.i. brace, is offered by Innovation Sports of Irvine, California. The patent art also offers several exemplars of efforts to stabilize injured knee joints, and among them are the following U.S. patents: Foster, 4,353,361; Gardner, 3,799,158; Deibert, 4,271,831; Home, 3,779,654; Taylor, 3,902,482; Gromes, 1,336,695; Buring, et al., 4,409,689; Almedia, 4,139,002; and Meierhofer, 2,379,538. The bulk of the prior art offerings comprise a variety of braces ranging from very simple to quite complex mechanical joints, all of which have a unity of intent, i.e., stabilization of an injured knee. Some of the braces are intended to protect and stabilize particular injuries and others are more general in their application. As will become apparent from the following detailed description of a preferred embodiment of the present invention, however, none of these prior efforts accomplished the high degree of stabilization with relative simplicity offered by the present invention. BRIEF DESCRIPTION OF THE INVENTION Generally speaking, the invention relates to an appliance for stabilizing a knee joint in the sagital, cononal and transverse planes, having leg grasping means for clasping the appliance to the wearer's leg above and below the knee, means defining a mechanical joint at the medial and lateral sides of the knee, each mechanical joint means comprising depending opposed femural links, each said link terminating in a bulged portion, a pair of opposed upwardly extending tibial links terminating in a bulged portion, said bulged portion of said tibial links being disposed in overlapping relation to said bulged portion of said femural links, cam follower means mounted in said bulged portion of said femural links, said cam follower means being disposed in a plane transverse to the plane of the leg of the wearer extended and extending outwardly from the knee in said plane, said tibial bulge being formed with opposed camming means, each said cam follower means being positioned to engage said camming means to be cammed therewith such that from a leg straight position the tibia is permitted to, as the knee joint is flexed, slide relative to the femur for a predetermined distance and thereafter rotate relative thereto in a predetermined arcuate path. Description of the Drawings With the foregoing as historical perspective, a preferred embodiment of the present invention will now be described in detail, which description should be read in conjunction with the accompanying drawings, wherein Figure 1 is a lateral side elevation of the orthosis of the present invention shown as mounted to the right leg of the user; Figure 2 is a front elevation of the same leg showing the orthosis in a different aspect; Figure 3 is a perspective of the othosis showing the overall construction, and the arrangement for mounting the same, in its operative position, on the user's leg; ; Figure 4 is a sectional view of the orthosis, mounted on the leg, taken along section 4-4 of Figure 2, and is intended to show the relative position of the orthosis with respect to the tibia and the calf area of the leg, to illustrate one of the unique features of the invention; Figure 5 is a side elevation of a typical joint of the present invention, indicating the relative position of the components at various stages of flexion of the knee; Figure 6 is a side elevation, in partial section, showing the knee joint of Figure 5; and Figure 7 is an exploded perspective view of a typical joint of the present invention, showing the relative interfitting arrangement of components thereof. Detailed Description of the Preferred Embodiment With reference now to the drawings, and more particularly to Figures 1 and 2, a multiaxis controlled motion knee orthosis, or brace, 15 is depicted in its proper mounted position on the right leg of a wearer. So that the fit of the orthosis may be clearly understood, the drawing also depicts the relative positions of the femur F and the tibia T as well as the patella P, forming a . . . typical knee joint of an adult male, indicating the alignment of each with respect to the brace 15, with the wearer standing erect and the right leg in the longitudinally extended position. The brace 15, as may be seen best in Figure 3, includes means for securing the brace to the leg of the wearer, comprising a pair of leg grasping devices in the form of an upper thigh, or femoral, cuff 17 having a major closure means 19 and a minor closure means 21, both of which are constructed so as to encircle the thigh to snugly fit the cuff 17 thereto. The major closure means encircles the entire upper thigh and is, preferably, of an elastic material, e.g., latex, so as to provide some give as the muscles are flexed, and may be of a latex material, or such other suitable elastic fabric, as desired. The femoral cuff includes a pair of opposed spaced wings 21, adapted to engage the lateral and medial sides of the thigh. The major closure is attached to the medial wing, such as by rivets 22, and a velcro closure is provided as at 23. The minor closure 20, attaches to the lateral wing at pivot pin 24 and, as illustrated, employs a "D" ring through which the closure is fed and doubled back on itself to provide the desired firmness of fit. Once again, a velcro closure, or some other closure, is employed. A calf, or tibial, cuff 25 is disposed beneath the knee joint and partially encircles the calf area, as best seen in Figures 1 and 2. In order to ensure snug fit of the tibial cuff 25, there are provided transverse closure members 27, of which three are shown in longitudinally spaced relation. In order to assure a more precise fit, the femoral and tibial cuffs are formed to specially fit the exact leg upon which the brace is to be worn. This is accomplished by forming a cast about the leg of the intended wearer. The cast is then cut and thereupon serves as a mold to form a model of the leg. Each cuff is then precisely fabricated of a laminate material right on the cast in the proper position. In order to provide optimum strength, both graphite and kelvar filaments are used in a liquid resin, which is then formed about a casting to create the cuffs. Thereafter, the cuffs are lined with some suitably resilient, shock absorbent material such as, for example, sorbathane, and are ready to wear. The femoral cuff 17, as previously described, is formed with a pair of wings positioned relative to one another by a bridge section 26 spanning the lower part of the thigh above the knee. This construction allows some freedom to allow the larger, upper thigh muscles to expand and contract with loss of control. The area engaged by the tibial cuff includes the greater portion of the calf muscle at the rear of the leg. For that reason, the tibial cuff is more "C" shaped, encircling the majority of the naterior portion of the lower leg, as seen in Figure 4. The cuff is open at the rear of the leg to permit the cuff to be slipped on, and, further, to permit flexing of the calf muscle when the cuff is in place. The closure members 27 are of a similar construction to the minor closure member 20 secured to the femoral cuff. Thus, each member includes an elastic strap 28 riveted, or otherwise secured, at some point on the medial side of the cuff. A "D" ring is affixed in the lateral plane of the strap by means of a hanger 29 which is shown as attached to the lateral side of the cuff by a fastener 30. The fastener, which may be of any suitable construction, permits limited, essentially longitudinal positioned adjustment by rotation of the hanger 29 along a path A-A so as to permit snug fit over the severe contours of the calf as it flexes during movement. As before, the strap may pass through the "D" ring and close by means of velcro, or some other suitable closure means. While the formation and construction of the femoral and tibial cuffs is an important aspect of the invention as a whole, a major feature of the invention rests in the construction of the unique mechanical joint 32, which joins the cuffs to define the brace 15 into an orthosis capable of stabilizing the wearer's knee joint in each of the transverse, cononal and sagital planes. The detailed construction of the joint 32 of the present invention will now be described with respect to such a joint position at the lateral side of the right knee. It will be appreciated that the medial joint is the mirror image of the lateral joint, and that both will operate in unison as the leg is flexed. With reference first, primarily, to Figure 3, the femoral cuff 17 is provided with depending, spaced apart, parallel supporting links 34 and 35 respectively. As seen in Figure 3, link 34 is the lateral link and link 35 is the medial link. The links 34 and 35 are readily laminated into the tibial cuff, in a known manner, although it will be appreciated that they may be sewn in, or otherwise fastened, without departure from the invention. The free end of each link 34 and 35, terminates in a bulged, or widened, end 35 and 36, respectively. As previously stated, the links are essentially parallel and are disposed on the medial and lateral sides of the thigh, respectively, and depending therefrom to and through a transverse plane R-R shown in Figure 1. The plane R-R is transverse to the longitudinal plane of the tibia F and passes through a center point 40, which represents the center of radius of rotation of the femoral condyle relative to the tibia. In a like manner, the tibial cuff 25 is provided with upwardly extending, spaced parallel links 44 and 45, respectively, link 44 being on the lateral side, and link 45 being on the medial side of the cuff, as shown. As in the case of the femoral links 34 and 35, the tibial links 44 and 45 extend upwardly, passing through the transverse plane R-R, and each terminates in a widened, or bulged, portion 46 and 47. As in the case of the femoral links, the tibial links may be molded into, sewn, or otherwise attached, to the tibial cuff in some convenient well-known manner. Once again, referring to Figure 3, it will be seen that the lateral femoral and tibial links 34 and 44 are essentially aligned in adjacent planes such that the terminus of each of the links overlaps and is disposed immediately adjacent to one another in a transverse plane, as is the case with the medial links. In each case, the femoral links are disposed slightly inwardly of the tibial links, once again, as best seen in Figure 6. Overlapping bulged termini portions of the respectively lateral and medial links intersect and lie within the plane R-R to provide the nucleus of the highly unique joint mechanism indicated generally at 34 and illustrated in detail in Figures 5, 6 and 7, respectively. In order to provide optimum stability for an injured knee, and particularly a knee in which the injury involves either the anterior or posterior cruciate ligament, it is necessary to emulate, insofar as reasonably possible, natural, relative movement of the femur and tibia. Most prior art devices appear to have taken for granted that such movement consists of a relative rotation about a single center of rotation, typically in the center of the knee, which is the philosophy resulting in the familiar single pivot brace. Since that is not the natural relative movement of the knee joint, such single pivot braces inherently cause undue stress during flexion of the knee joint, rather than stabilizing, which is the ultimate goal of the present brace. In fact, it has been found that commencing from the leg extended position, the initial movement of the tibia relative to the femur through the first 250 of flexion is an approximate 8 millimeter front to rear slide, followed by rotation as the knee continues to flex through a 1250 angle, or for whatever angle may be traversed, as limited by the injury or natural limitations. It has been determined that if the knee is permitted to move in a natural fashion, stress on the cruciate ligaments and the quadraceps muscles, which play a major role in the function of the knee, is so minimal that an injury to the knee is actually permitted to heal more effectively when the user wears the brace of the present invention. With the foregoing biomechanics in mind, the joint mechanism of the present invention is constructed to permit the knee joint to be constrained to move with the natural glide and rotation of a normal knee, to, thereby, protect the injury and minimize stress by the provision of spaced camming devices, which as illustrated, take the form of longitudinally spaced camming slots 55 and 57, respectively. For purposes of identification, the camming slot 55 will be referred to as the femural camming slot and camming slot 57 may be referred to as the tibial camming slot. Each slot is formed in a straight line segment 60 and 62, respectively, which adjoins arcuate segments 64 and 66, respectively. It will be noted that the stright line segments 60 and 62 terminate at the end remote from the juncture with the arcuate segments 64 and 66 on the plane R-R. It will also be noted that the arcuate segments are generated about the same radial center which is aligned with the center point 40. The camming slots are adapted to receive and operate in conjunction with camming follower means, which, as illustrated, comprise screws 73 and 75. As illustrated in Figure 7, a two-part post and screw assembly manufactured by Chicago Screw is shown, although other forms of camming devices could be employed. The camming screws 73 and 75 pass through holes 77 and 78 formed in the terminus 80 of the femoral link (free end). The holes 77 and 78 lie in plane R-R. Bushings 82 are provided, having an inside diameter sufficient to fit over the circumferential surfaces of the posts 73 and 75 in bearing relation with respect thereto, and an outside diameter sufficient to snugly fit in bearing relation within the slots 55 and 57, respectively. A cap, or cover plate, 85 having holes 87 and 88, respectively, permit the receipt of posts 73 and 75, which are then secured by screws 90 to form the joint. The cover plate not only holds the screws, but further serves as a reaction member, sandwiching the bulged terminus of the tibial link between the plate 85 and the bulged terminus 80 of the femoral link, as best seen in Figure 6, such that relative movement of the femoral link relative to the tibial link is strictly controlled by movement of the posts 73 and 75 in the slots 55 and 57, respectively. In Figures 5, 6 and 7, there is shown, by way of example, a lateral joint for the right leg. The medial joint is the mirror image of the lateral joint, so that the relative movement of the lateral and medial links are coordinated and the same. In order to achieve optimum relative natural movement of the knee joint, which, of course, is a principal feature of the present invention, the interaction of the femoral and tibial surfaces must be taken into account. To this end, while both straight segments 60 and 62 begin with pins 73 and 75, resting in plane R-R, when the leg is extended and essentially straight (see Figure 5), as flexion begins, there is an approximate 8 millimeter lateral movement between the tibial and femoral surfaces, which is permitted as the pins slide along the straight segments 60 and 62. In a very tall person, the slide may be slightly longer, and in a small child, it may be shorter, and the precise length of the slot may be adjusted to meet specific conditions. A range of 6 to 9 millimeters meets most needs. The slide of the femur and tibia, however, does not take place in plane R-R, but, rather, a slight relative tilt is experienced as the leg is flexed through the first 250 of flexion. To accommodate this movement, the straight line segment 60 forms a 500 angle with the plane R-R, whereas, the straight segment 62 forms an angle of 560 30". Thus, as the leg is flexed through the first 250 of flexion, camming posts 73 and 75 respectively, move in a straight line along the straight segments 60 and 62, each at the previously disclosed angle. There is a small tolerance permitted to meet specific needs, but most needs are met within + 20 of the angles herein specified. At 250, they intersect the arcuate sections 64 and 66, respectively, at intersections 94 and 96. Beyond 250 of flexion, the natural movement of the knee through further flexion is a relative rotation of the tibia relative to the center point R on the femoral condyle. In order that this movement may be emulated with the greatest possible accuracy, arcuate sections 64 and 66 have been formed around center point 70 and it has been found that a radius of .43 inches, or 11 millimeters, provides the desired resultant rotational movement in a typical knee. Approximately 960 30" is required to provide full knee flexion. It will be appreciated, however, that if a lesser knee flexion is required because of the particular instability found in the user's knee, the arc may traverse a greater or lesser angle without departure from the invention. Indeed, stops may be used to limit flexion simply by inserting a blocking device of known construction and, therefore, not shown, at the appropriate point within the slot 55 and 57 to thereby limit the amount of flexion that the user can experience using the brace. While in a normal knee there is a slight outward rotation of the tibia relative to the femur upon flexion, such rotation may be pronounced in the case of certain knee injuries resulting in instability. The present invention, in still another of its inventive aspects, limits and constrains such rotation upon flexion of the knee, thereby enhancing the stability thereof. This is accomplished, as best seen in Figure 4, by forming, or molding, the tibial cuff over the anterior boney prominence 100 of the tibia, sometimes referred to as the shin. As seen in Figure 4, the cuff has been molded, or formed, about that prominence, such that any tendency of the tibia to rotate about its longitudinal axis upon flexion, is resisted by the cuff. The structure of the cuffs and links is of such integrity that not only is rotation controlled within the cuff, but when the leg is flexed, the wings 21 of the femural cuff, work with the tibial cuff by acting against the wearer's thigh through the links to resist any rotation of the brace, thereby totally inhibiting undesirable rotation. In order to avoid irritation by rubbing of the tibia against this tightly molded section of the cuff, a spongey material, such as sorbathane, may be provided in this area about the interior of the cuff, at or about the location 99, or about the entire area which contacts the skin of the wearer if it is so desired. Strong closure members 27, 28 and 29, of course, permit the tibial cuff to be held in position firmly against the shin, while at the same time, minimizing the discomfort which might otherwise be experienced by the wearer. Having now described a preferred embodiment of the invention, what is claimed is:

Claims: 1. In an appliance for stablilizing a knee joint in the sagital, cononal and transverse planes, having leg grasping means for clasping the appliance to the wearer's leg above and below the knee, means defining a mechanical joint at the medial and lateral sides of the knee, each mechanical joint means comrising depending opposed femural links, each said link terminating in a bulged portion, a pair of opposed upwardly extending tibial links terminating in a bulged portion, said bulged portion of said tibial links being disposed in overlapping relation to said bulged portion of said femural links, cam follower means mounted in said bulged portion of said femural links, said cam follower means being disposed in a plane transverse to the plane of the leg of the wearer extended and extending outwardly from the knee in said plane, said tibial bulge being formed with opposed camming means, each said cam follower means being positioned to engage said camming means to be cammed therewith such that from a leg straight position the tibia is permitted to, as the knee joint is flexed, slide relative to the femur for a predetermined distance and thereafter rotate relative thereto in a predetermined arcuate path. 2. The appliance as set forth in claim 1 wherein two said camming means are provided, each comprising a slot formed in said tibial bulge, longitudinally spaced from one another, the uppermost slot being the femural camming slot and the lowermost being the tibial camming slot. 3. The appliance as set forth in claim 2 wherein each said camming slot comprises a straight segment adjoining an arcuate segment. 4. The appliance as set forth in claim 2 or 3 wherein said cam follower means comprises a camming screw extending outwardly from said femural bulge, and passing through said camming slot, means defining a cap, said cap means disposed adjacent to and outwardly of said tibial bulge, said cap means receiving said camming screw in holding engagement. 5. The applicance as set forth in claim 4, wherein bushing means is mounted on said camming screw in bearing relation and has a circumferential surface in bearing engagement with said camming slot. 6. The appliance as set forth in any one of the preceding claims, wherein said cam follower means are disposed in a horizontal plane intersecting a center point representing the center of radius of the femural condyle of the wearer. 7. The appliance as set forth in claim 3, wherein the arcuate segment of each said camming slot is of equal radius circumscribed about a center point representing the radius of the femural condyle of the wearer. 8. The appliance as set forth in claim 3 or 7, wherein the straight segement of one of said camming slots extends from the arcuate segment toward the posterior of the joint, and the straight segment of the other camming slot extends towards the anterior of the knee. 9. The appliance as described in claim 3, wherein said straight segment is 8 millimeters + 2 millimeters in length, and wherein the longitudinal axis of said straight segment of said femural camming slot requires a 500 + 20 angle with respect to said transverse plane, and the longitudinal axis of said tibial slot defining a 560 30' + 20 angle with respect to said transverse plane, and the radius of each said arcuate segment is about 11 millimeters. 10. In an orthosis for supporting an unstable knee joint along its sagital, cononal and transverse plane, the combination of a first femural cuff formed to fit snugly about a portion of the thigh, closure means attached to said cuff for securing said cuff to a portion of a leg above the knee joint, a second tibial cuff formed to fit snugly about the anterior portion of the tibia and calf of the leg below the knee joint, closure means attached to said tibial cuff for securing said second cuff in place, said first and second cuffs being interconnected by medial and lateral articulating joints, said tibial cuff being molded about the boney prominence of the tibia so as to prevent rotation of said tibia on its longitudinal axis. 11. The orthosis as described in claim 10, wherein said closure means attached to said tibial cuff comprises at least three spaced elastic straps being adjustable to vary tightness of said tibial cuff about the leg while holding said cuff in proper position, and means permitting limited longitudinal movement of said elastic straps. 12. The appliance as described in claim 10 or 11, wherein said femural cuff comprises spaced wings positioned to engage the lateral and medial area of the wearer's thigh, and means defining a bridge and joining said wings to form a rigid unit. 13. The appliance as described in claim 10, 11 or 12, wherein said medial and lateral articulating joints comprise depending opposed femural links, each said link terminating in a bulged portion, a pair of opposed upwardly extending tibial links terminating in a bulged portion; said bulged portion of said tibial links being disposed in overlapping relation to said bulged portion of said femural links, cam follower means mounted in said bulged portion of said femural links, said cam follower means being disposed in a plane transverse to the plane of the leg of the wearer extended and extending outwardly from the knee in said plane, said tibial bulge being formed with opposed camming means, each said cam follower means being positioned to engage a camming means to be cammed therein such that from a leg straight position the tibia is permitted to, as the knee joint is flexed, slide relative to the femur for a predetermined distance and thereafter rotate relative thereto in a predetermined arcuate path.

Inventors: TOWNSEND, JEFFREY H.
Applicants: TOWNSEND INDUSTRIES, INC.
Application year: 1985
Main classification: A61F5
IPC codes: A61F5