CN119818256A

CN119818256A - Cable support system

Info

Publication number: CN119818256A
Application number: CN202510032387.7A
Authority: CN
Inventors: D·弗莱明
Original assignee: Mobis Technology Co ltd
Current assignee: Mobis Technology Co ltd
Priority date: 2019-06-10
Filing date: 2020-06-10
Publication date: 2025-04-15
Also published as: CN114072108B; AU2020291528B2; EP3979958A4; CN114072108A; BR112021025027A2; AU2020291528A1; ZA202200395B; CA3142520A1; EP3979958A1; ZA202213043B; WO2020252080A1; MX2021015243A

Abstract

A cable brace system that enhances a natural ligament of a human body to reduce the propensity for injury or re-injury. The present invention is a cable system that acts very similar to the natural ligaments of the human body and is able to resist forces that lead to excessive articulation and injury. The control loop formed by the cable provides external hyper-extension, flexion and rotational support as the ligament travels through the range of motion.

Description

Cable support system

The application relates to a cable support system, which is a divisional application of a Chinese patent application number 202080049608.7 of China, wherein the international application PCT/US2020/037078 is the international application of which the international application date is 2020, 6, 10 and enters the national stage of China.

Incorporated by reference

U.S. patent application Ser. Nos. 13/867,910, 12/987,084, 11/744,213, 62/682,560 and 62/718,529 are incorporated by reference herein.

Priority statement

The present application claims priority from U.S. application Ser. No. 16/436,786, filed on 6/10 of 2019, the entire contents of which are incorporated herein by reference as if fully set forth herein.

Technical Field

The present disclosure relates to a cable brace system, which is a joint and ligament support system for reinforcing a natural ligament of a human body to reduce the propensity for injury or re-injury.

Background

The human body contains a variety of complex mechanisms that are vulnerable to injury. For example, human knees are a complex mechanism that is extremely vulnerable to injury in sports such as football, hockey, skiing, snowboarding, and dirtbike. In these types of exercises, where physical demands are high, the Anterior Cruciate Ligament (ACL) and the Medial Collateral Ligament (MCL) are often injured. In many of the same activities, the wrist, ankle, and elbow are also fragile for many of the same reasons. The wrist consists of many ligaments that may be overstretched, which is painful and slow in the healing process. Without proper support, the ankle and elbow are also at risk of an overstretching event.

Most prior art (conventional) brace devices for ligament protection consist of rigid plates connected by hinges or straps on either side of the ligament or joint, or simply two plates connected by straps. These plates are tightly tied to the leg or arm above and below the ligament/joint with straps that encircle the leg/arm. For example, the current state of the art for functional knee supports generally relies on a hinge frame secured to the knee anatomy by an adjustable strapping system. While adequate to control lower pathology-induced loads, these brace systems have not been shown to be effective in controlling higher loads that are clinically more important. Thus, current knee braces have not been entirely successful in preventing ligament injury or re-injury. There is a need for a brace design that more specifically addresses the mechanism of ligament injury while maintaining a comfortable, conformable, lightweight design and unobstructed athletic function.

Disclosure of Invention

It is an object of the present invention to provide a joint and ligament support system that enhances the natural ligaments of the human body to reduce the propensity for injury or re-injury. In various embodiments, this is accomplished by using a novel control loop strategy in which two or more cables are looped around separate points near the joint in order to provide precise control of joint motion. These control loops provide a higher level of adjustability and transmit their tightening force toward the center of the loop, thereby improving the stability and effectiveness of the brace.

One embodiment of the present invention is a cable system that functions very similar to the natural Anterior Cruciate Ligament (ACL) and Medial Collateral Ligament (MCL) of the human body. The cables are routed around the knee joint in a manner that resists forces that lead to excessive joint movement and ACL and/or MCL injury. When the leg is advanced through the range of motion such that the first control loop is extended, the opposing control loop portion of the cable tightens, thereby preventing the tibia from moving anteriorly (hyper-extension) or twisting (lateral rotation) or bending laterally relative to the femur.

The cable systems described herein may be custom-made or adapted to prior art (conventional) braces, thereby improving their effectiveness.

Drawings

Fig. 1 is an exterior front/side view of the right leg, showing normal fully extended and over extended (torn ACL) views.

Fig. 2 is a top/front view with the right leg fully extended, showing normal and sideways turned or sideways bent (tearing ACL and/or MCL) views.

Fig. 3 is an external front/side view with the right leg fully extended, showing the main cable resisting over-extension of the leg.

Fig. 4 is a top/front view with the right leg fully extended, showing the main cable resisting lateral rotation of the leg.

Figure 5 is an external front/side view of the right leg in a bent position showing the main cable knee brace system.

Figure 6 is an exploded isometric view showing the various components of the main cable knee brace system.

Fig. 7 is an exterior front/side view of the left leg fully extended, showing the auxiliary cable resisting over-extension of the leg.

Fig. 8 is a top/front view with the right leg fully extended, showing the auxiliary cable resisting lateral rotation and/or lateral bending of the leg.

Fig. 9 is an exterior front/side view of the left leg in a flexed position, showing the auxiliary cable resisting lateral flexure or lateral rotation.

Fig. 10 is an exploded isometric view of various components of the auxiliary cable knee brace system.

Fig. 11 is an inside elevation/side view of the auxiliary cable guide plate guiding the auxiliary cable through the pivot point.

Fig. 12 is an inside elevation/side view of an alternative cable guide plate guiding auxiliary cables below and above the pivot point.

Fig. 13 is an inside elevational/side view of another alternative cable guide plate guiding auxiliary cables above and below the pivot point.

Fig. 14 is a top view of a portion of a Q-adjustable tibial shell in accordance with an embodiment of the present invention.

Fig. 15 is a three-quarter view of a Q-adjustable leg brace according to an embodiment of the invention.

Fig. 16 is a top-down view of a Q-adjustable leg brace according to an embodiment of the invention.

Fig. 17 is a top-down view of a Q-adjustable leg brace according to an embodiment of the invention.

Figure 18 is an interior front/side view of a wrist brace shown on the right wrist according to an embodiment of the invention.

Figure 19 provides a detailed view of an extension stop mechanism for a wrist brace according to an embodiment of the invention.

Figure 20 is a top view of a wrist brace on the right wrist according to an embodiment of the invention.

Figure 21 is a bottom view of a wrist brace according to an embodiment of the invention.

Figures 22A-22C provide a number of views of a wrist brace embodiment of the invention.

Fig. 23 is an interior front/side view of an elbow brace on a right elbow according to an embodiment of the invention.

Fig. 24 is a top view of an elbow brace on a right elbow according to an embodiment of the invention.

Figure 25 is an exterior front/side view of an ankle brace on a right foot in accordance with an embodiment of the invention.

Fig. 26 is a rear view of an ankle brace on the right foot in accordance with an embodiment of the invention.

Detailed Description

Various embodiments of a cable-regulated joint and ligament brace having at least two control loops are described herein. The basic principles of the present invention may be applied to support various joints and corresponding ligaments, if desired. In each of the various embodiments, at least two control loops are formed by a cable system that is attached to one or more plates or shells near the joint or ligament that is to be supported.

Knee brace

To effectively prevent injury to ACL22 and/or MCL23, the knee brace must prevent the tibia 26 from moving anteriorly (hyperextension) or laterally bending and/or rotating (torsion) relative to the femur 18 (see fig. 1) (see fig. 2). For completeness, the patella 20 and fibula 24 are shown. The knee brace of the present invention as best shown in fig. 3-17 incorporates a novel cable system that more effectively prevents overstretching, lateral bending and/or lateral rotation of the knee joint, where like reference numerals refer to like elements throughout the views.

Fig. 3 shows the main cable system of the present invention which creates an effective differential force against tibia 26 relative to femur 18 and strengthens ACL22. When the main cable 1 of the system is properly tensioned, the brace acts like the body's own ACL22, causing the brace to become taut as the leg stretches, resisting anterior movement of the tibia 26 relative to the femur 18. Fig. 4 shows the main cable system of the present invention which resists lateral rotation of the tibia 26 relative to the femur 18. Figure 5 shows the main cable system of the present invention when the legs are flexed. As shown in fig. 3, the main cable 1 becomes progressively tighter as the leg approaches full extension, because the tibial plate 2 moves farther away from the femoral plate 4 as the leg extends. When the hyperextension force 28 is applied to the leg as shown in fig. 3, the tibial plate 2, the patella plate 3, and the femoral plate 4 are compressed together as the main cable 1 is subjected to progressively greater tension. The tension in the main cable 1 pulls the tibial plate 2 downwards and pulls the backboard 5 upwards, creating differential resistance on the knee joint to prevent leg hyperextension. Fig. 7 shows the auxiliary cable system of the present invention which creates an effective differential force against tibia 26 relative to femur 18 and strengthens ACL22 and MCL23. When the leg is extended, the auxiliary cable 40 resists anterior movement of the tibia 26 relative to the femur 18. Fig. 8 illustrates the auxiliary cable 40 resisting lateral flexion and/or lateral rotation of the tibia 26 relative to the femur 18. Fig. 9 shows the auxiliary cable system of the present invention as the leg is flexed, the auxiliary cable 40 resisting lateral flexion and lateral rotation throughout the range of motion of the leg. When the leg is extended, the patella plate 3 acts like a hinge for flexion-extension movement of the tibial plate 2 and the femoral plate 4, approximating a knee joint, to pivot about pivot points 17a and 17b, respectively.

As shown in fig. 4, when the lateral turning force 30 is applied to the leg, the tibial plate 2, the patella plate 3, the femoral plate 4, and the backboard 5 are kept rigid by the tension generated in the main cable 1. The tensile forces in the main cable 1 cross behind the legs, so that when the tensile forces pass through the back plate 5, cable crossing points 31 are created, resisting rotation and bending on the knee joint and preventing the legs from bending or rotating sideways. As shown in fig. 8, when a lateral bending or lateral turning force is applied to the leg, the tibial plate 2, the patella plate 3, and the femoral plate 4 are kept rigid by the tension generated in the auxiliary cable 40. Tension in the auxiliary cable 40 prevents the brace from bending over the knee joint, thereby preventing the leg from bending or rotating sideways.

The invention comprises a main cable 1 and an auxiliary cable 40, which may be made of any flexible material having a sufficiently high tensile strength. The tibial plate 2, which may be made of any rigid or semi-rigid material, is shaped to conform to the tibia 26, beginning just below the knee and ending at approximately the midpoint of the tibia 26. Tibial plate 2 is held in place by straps 11b and 11 c. The foam pad 12 is attached to the underside of the tibial plate 2 for comfort and to provide a firm grip on the individual's tibia 26. The patella plate 3, which may be made of any rigid or semi-rigid material, connects the tibial plate 2 to the femoral plate 4. The femoral plate 4, which may be made of any rigid or semi-rigid material, is positioned on top of the thigh, from directly above the knee to approximately the mid-femur 18 and held in place by straps 11 a. The backboard 5 may be made of any rigid or semi-rigid material and is positioned directly over the knee joint and behind the legs to hold the cable 1 in place and to securely hold the femur 18 as the differential forces of the main cable 1 are transferred through the joint. A foam pad 14 is attached to the inner side of the back plate 5 to help distribute the force of the main cable 1 comfortably onto the legs. The cable tensioner dial 6 and the lock/release button 7 with spring 8 are attached to the femoral plate 4 with set screws 9. They may be made of any metal or rigid material that will withstand the forces required to keep the main cable 1 locked in place during use. Other cable tensioning and locking mechanisms may be used, but turntable tensioning and locking systems provide a very wide range of fine tuning cable adjustability and ease of use.

The essential element of the invention is the cabling of the cable. As best shown in fig. 6, the main cable 1 begins to attach to the femoral plate 4 by means of a cable connection 15a, passes behind the legs through a cable guide hole 13a and a cable guide hole 13b in the posterior plate 5, and extends through a cable guide hole on the opposite side of the tibial plate 2. Then, the main cable 1 is looped over the leg, reaches the other side of the tibial plate 2, and passes through a cable guide hole. From this cable guide hole in the tibial plate 2, the main cable 1 again crosses itself behind the leg through the cable guide hole 13c, forming a cable intersection point 31, after which it passes through the cable guide hole 13d in the posterior plate 15 and is attached to the opposite side of the femoral plate 4 by the second cable connector 15 b.

In a further embodiment, the main cable 1 starts to be attached to the femoral plate 4 by means of a first cable connector 15a, passes behind the legs through a first cable guide hole 13a and a second cable guide hole 13b in the backboard 5, and is attached to the opposite side of the tibial plate 2 with clamping screws 10a. The main cable 1 is then looped over the leg, attached to the other side of the tibial plate 2 with a clamping screw 10 b. From the clamping screw 10b, the main cable 1 passes through the third and fourth cable guide holes 13c, 13d in the back plate 5 again behind the legs, forming a cable intersection 31, and is attached to the opposite side of the femoral plate 4 by a second cable connector 15 b.

As best shown in fig. 10, the auxiliary cable 40 begins to attach to the outer or lateral side of the femoral plate 4 by a femoral cable connector 42a and extends through a femoral cable guide hole 44a. The auxiliary cable 40 passes through the femoral pivot point 17a and the tibial pivot point 17b by cable guide plate 48. From this cable guide plate, the auxiliary cable 40 extends through the tibial plate guide hole 44b and is attached to the outer or lateral side of the tibial plate 2 by the tibial cable connector 42b, thereby completing the wiring.

In some embodiments, a single cable is used that passes through each guide. In alternative embodiments, the cable may be made up of individual segments that are connected together to form a complete wiring. For example, the first main cable section 1a and the second main cable section 1b may be connected together by a tibial plate 2 to complete the loop. The first main cable section 1a starts to be attached to the femoral plate 4 by means of a first cable connection 15a, passes behind the legs through a cable guide hole 13a and a cable guide hole 13b in the posterior plate 5 and is attached to the opposite side of the tibial plate 2 with clamping screws 10 a. The second main cable section 1b does not need to be looped over the leg, but is attached to the opposite side of the tibial plate 2 with a clamping screw 10 b. Starting from the clamping screw 10b, the second main cable section 1b passes through the cable guiding hole 13c behind the leg and crosses over itself, forming a cable crossing point 31, after which the loop is completed through the cable guiding hole 13d in the back plate 5 and by attaching to the opposite side of the femoral plate 4 with the cable connector 15 b.

The segment of the cable extending from the cable junction 31 to the tibial plate portion of the brace and back to the cable junction 31 forms the tibial control loop portion 32 of the cable. The segment of the cable extending from the cable junction 31 to the femoral plate portion of the brace and back to the cable junction 31 forms the femoral control loop portion 33 of the cable. For example, fig. 6 shows these control loop sections 32 and 33. During use, for example when the knee is over-extended, the tibial control loop will grow, causing the femoral control loop to tighten in the opposite direction.

The main cable 1 is adjusted by turning the cable tensioner dial 6 to retract excess main cable 1 length. The main cable 1 is automatically locked in place by a ratchet gear 16 on the cable tensioner dial 6 and a spring 8 actuated lock/release button 7. The push button 7 is also used to release tension in the main cable 1 for mounting and dismounting the brace.

Although the cable may be routed across the pivot point an unlimited number, it is most desirable to pass directly through the pivot point, as shown at 46a in fig. 9, to achieve optimal tension on the auxiliary cable 40 throughout the range of motion of the leg. Fig. 11 shows a cable guide plate that guides the cable directly through the pivot point, auxiliary cable routing 46a, as described above. Alternative auxiliary cable guide plate configurations as shown in fig. 12 and 13 may be used to guide the auxiliary cable around the pivot point. For example, an alternative auxiliary cable routing 46b may be implemented using a cable guide plate as shown in fig. 13 that guides the auxiliary cable 40 above or anterior to the femoral pivot point 17a and below or posterior to the tibial pivot point 17 b.

Fig. 15 depicts an alternative tibial shell arrangement. When configured in this manner, tibial shell 2B is mounted to tibial shell 2A at location 51, thereby forming an axis of rotation. The tibial shell 2B is secured to the tibial shell 2A using a tibial adjustment locking screw 52. The tibial shell 2B is rotated about axis 51 to establish the desired Q angle, as shown in fig. 16. Screws 53A, 53B on both sides of tibial shell 2B are used to control the relative rotation of tibial shell 2B about axis 51, as shown in fig. 14. By increasing or decreasing the set screw pushing against the corresponding bearing surface 55A, 55B, the tibial shell pivots about axis 51 accordingly.

Fig. 14 best depicts the adjustment mechanism, showing the adjustment screws 53A, 53B threaded through the fixation nuts 54A, 54B in the tibial shell 2B. As best shown in fig. 16, after unscrewing the adjustment locking screw 52 and then shortening the adjustment screw 53A, the adjustment screw 53B is increased to push against the bearing surface 55B on the tibial shell 2A, forcing the tibial shell 2B to rotate clockwise about the axis 51 until the adjustment screw 53A contacts the bearing surface 55A on the tibial shell 2A, after which the adjustment locking screw 52 is tightened.

The cable guide receives a cable comprised of one or more segments that transmit energy to control knee motion and prevent knee hyperextension in the same manner as described above, e.g., with respect to the other embodiments of fig. 2-6. In the same way as in the above embodiments, the cable may be composed of one or more parts. Although the cabling of the cables is not depicted, in a preferred embodiment, the cables extend from the junction 31 to a first side of the tibial shell 2A, through one or more cable guide holes, then extend through one or more cable guide holes on the tibial shell 2B, then extend down through one or more cable guide holes back to the opposite side of the tibial shell 2A, then extend back to the cable junction 31, forming the tibial control loop 32.

As the user's knee extends, the portion of the cable extending from the junction 31 around the tibial shell 2B and back to the junction, i.e., the tibial control loop 32, grows accordingly. This produces a direct response in the portion of the cable extending from the junction 31 on and around the femoral plate, i.e., the femoral control loop. This portion of the cable is tightened, bringing the femoral plate and the backboard 5 into the leg and behind the knee respectively, and preventing further extension of the knee by controlling the length of the tibial control loop.

Fig. 15 depicts both the femoral shell 4 and the tibial shells 2A, 2B of the knee brace in accordance with an embodiment of the invention. Notably, there are no backplates, straps, and cabling to more clearly depict the arrangement of the adjustable tibial shell 2B. As depicted, the invention in accordance with this alternative embodiment maintains many of the features described in the alternative embodiments herein, including 4, 6, 17C, and 17D. Fig. 15 depicts the tibial shell 2B of fig. 14 and its mounting surface 56 on the tibial shell 2A. The axis of rotation 51 is clearly depicted as extending through the location where the tibial shells 2A, 2B are connected.

Foam padding may be strategically placed at various locations on the medial portion of the brace shown in fig. 15. For example, on the sides near the hinge points 17C and 17D, under the tibial shells 2A and 2B and the femoral shell 4. Such foam provides increased comfort to the user.

Fig. 16 depicts the adjustability of the tibial shell 2B, which produces a selected Q-angle 57. The angle between the tibia and femur forms the quadriceps angle, referred to herein as Q angle 57. The angle varies according to the physiology of the user. The tibial shell 2B is adjustable to customize the Q angle 57 to suit each user. By turning the adjustment screws 53A, 53B, the q angle 57 may be changed as the tibial shell 2B pivots 58. The Q angle can be adjusted in either direction. In a preferred embodiment, the Q angle 57 is adjustable in either direction by up to 4 degrees Δq. The Q angle less than the average is defined as varus. In this embodiment, the Q angle 57 may be referred to as negative, e.g., the brace may adjust by-4 degrees Δq from the average, resulting in a sharper Q angle 57. The Q angle greater than normal is referred to as eversion and may be formed by adjusting the brace to increase the Q angle, for example +4 degrees from the average. For example, the arrangement depicted in fig. 16 shows an everting arrangement, wherein the Q-angle Q2 of the brace is greater than the average angle Q1. To achieve this, tibial plate 2B has been adjusted towards the outside of the user's leg (right side of the knee brace). Once the user is satisfied with their customized Q-angle, they can lock the brace using locking screw 52. This prevents the Q angle from changing when the device is worn by the user.

Fig. 17 depicts an embodiment of the invention with a femoral backplate 5 mounted. As shown, the backboard is positioned directly above the knee joint, behind the user's knee. The back plate 5 guides the parts of the cable 1 to the crossing point 31 (not shown) at its back side. Each portion of the cable 1 is then directed back up towards the upper portion of the brace, for example to either side of the femoral plate 4 and the first tibial plate 2A. Also shown are cable guide holes along the periphery of tibial plate 2A that receive cables from femoral backboard 5 and guide cable 1 along tibial plate 2A toward tibial plate 2B and to tibial plate 2B where cable 1 enters another guide hole in tibial plate 2B before traversing to the other side of tibial plate 2B and returning along the same path on the opposite side of the brace. The portion of the cable path from the junction 31 to the tibial plate 2B and back forms the tibial control loop 32. A similar path may occur in which the cable 1 extends from the junction 31 on the femoral back plate 5 all the way to the cable guides on either side of the femoral plate 4 and then connects to the adjustment mechanism 6.

In further embodiments of the invention, the tibial plate may include additional portions that increase the retention of the wearer's tibia. Additional protection is provided by adding tibial control to prevent overextension. This region is ideal for leg control because there is little tissue between the tibia and the outer portion of the leg. In some embodiments, the underside of the tibial plate closest to the user's leg may include an additional half ridge portion. For example, as the cable system is tightened, the half ridge portion conforms to the shape of the user's tibia. This provides increased retention of the tibia.

In further embodiments of the present invention, the tibial plate may be configured such that the tibial plate has varying flexibility on its own. For example, such varying flexibility will allow the tibial paddle to conform to the shape of the user's leg while also providing the necessary rigidity. In this example, the second half-ridge portion may not be required, or alternatively, may be additionally provided.

In further embodiments of the invention, the user may of course use the brace as a prophylactic device before any injury occurs, rather than after. In this case, additional protection may be required. For example, a user engaged in extreme exercises may require supplemental impact protection. Accordingly, embodiments of the present invention may include a knee cap that protects the knee from impact forces. In some embodiments, the knee cap portion is disposed between the tibial plate and the femoral plate such that the knee cap remains in place when the tibial plate and the femoral plate pivot away from each other. In such examples, the tibial and femoral plates slide over or under the knee cap portion to allow the necessary flexibility. In addition, additional padding may be added in front of the knee to both support the knee and protect the knee from impact forces.

When force is applied to the knee joint, the cable tightens and resists excessive movement that can lead to ligament injury. As the cable tightens, it squeezes the brace shells that grip the tibia and femur. The tibial shell is designed to grasp the tibial tuberosity of the control calf, while the femoral shell and the tendinous backboard grasp the femur. The patella cup incorporated into the articulating mechanism provides increased structural rigidity, which provides better protection against collateral ligament injury. In addition, because the tibial plate is rigidly fixed to the patella cup, which in turn is well fixed to the distal femur, resisting posterior translational forces against the tibia, the PCL is protected from the usual mechanisms on flexed knees that directly impact the anterior proximal tibia.

Changes and modifications can be readily made to adapt the tibial shell Q angle adjustment invention to a conventional knee brace. It is also contemplated that the present invention may be adapted to elbow braces by replacing an adjustable tibial shell with an adjustable radial shell. This allows the symmetrical elbow brace to be adjusted to fit the angle between the humerus and radius of the user's arm, and may be adjusted to fit either the right or left arm.

Wrist brace

A further embodiment of the invention is a cable system for a wrist brace. The cable system supports the wrist and does not cause chamber syndrome. The cable system provides progressive buckling support for the wrist while having a low profile and taking up less space than conventional braces.

Another embodiment of the present invention provides a wrist brace for a user using one or more cables to provide progressive support through flexion of the wrist such that increased wrist motion is supported by increased support. Such an embodiment enables easy adjustment of the extension, but also provides increased support for the wrist ligament. Many of the components discussed above are generic to wrist brace embodiments.

Conventional braces have limited effectiveness in resisting excessive articulation that may cause wrist injury. Even when the binding device is tightened to an uncomfortable degree, the conventional brace is limited in its effect of preventing excessive movement of the wrist. The prior art braces also do not provide support over the entire range of motion, progressive support.

In addition, prior art wrist braces typically require expensive customization, such as sending gloves to the manufacturer to sew parts onto them. Due to the manner in which conventional braces are mounted to a user's arm and the degree of tightness required, wearers often complain of "chamber syndrome".

Furthermore, conventional braces do not allow the user to continue to use their hand or provide extremely limited use. For this reason, users are very dislike to wear such braces, and such braces cannot be actually worn as a preventive measure in many activities.

Wrist support apparatus according to the present disclosure may be used after injury as well as to prevent injury. This is unique in that the present invention allows the user to maintain use of his/her hands.

Preferably, the wrist brace has a low profile and conforms to the lower arm and wrist region of the user. One or more plates are located on the upper portion of the user's arm and hand. The smaller second plate is positioned towards the underside of the user's hand and arm. The cables extend between the plates. These guide plates themselves include small openings for receiving cables to control the path of the cables. The adjustment mechanism according to the disclosure herein may be used to tighten the cable. The cable may also provide an adjustable progressive resistance while also providing a stop point through which movement of the wrist would be prevented or limited. Providing progressive resistance so that when the user bends his or her wrist, additional tension is created on the wrist, thereby preventing over-extension.

In various embodiments, the upper plate is comprised of a metacarpal shell and a radius shell, which may together form a single shell or separate shells, and the lower plate is comprised of one or more tendon backplate.

Various embodiments may include multiple smaller metacarpal and radius shells and multiple tendon backplates. For example, in embodiments employing separate metacarpal and radius shells and one or more tendon backplates, two cables may also be present.

The cable or cables may form two or more loops, wherein the upper and lower guide plates are connected further forward (towards the user's hand) (metacarpal control loop) and further rearward (towards the upper arm) (radius control loop). In embodiments with one cable, the cable may not be fully connected such that the cable may include two separate distal ends.

In various further embodiments, the metacarpal shell and radius shell or tendon backboard may be shaped so as to achieve additional goals. For example, if the wrist requires upward movement, the radius shell may not extend as far as the back of the user's hand. In addition, the shape of the tendon backplate may be designed to conform to the underside of the wrist near the palm. Or alternatively, depending on the use and activity, the tendon backplate may be placed further back, for example, if the user wishes to keep some up-and-down motion of the wrist, but prevent torsion or lateral movement. In an alternative embodiment, the tendon backplate may be shaped in an X-shaped pattern starting near the palm and extending posteriorly, with the legs of the X extending toward the metacarpal and radius shells, respectively. These legs may provide a guide for the cable (or cables).

The metacarpal shell or radius shell may also include portions that extend downward toward the tendon backplate to receive and guide the cable. In many embodiments, the metacarpal shell or radial shell portion will also include an adjustment mechanism in accordance with the description and teachings herein that allows for limited adjustment of the length of the cable. One or more straps may also be included (e.g., on the forearm) that form a loop around the forearm via a hook-and-loop fabric extending from the radius shell.

The metacarpal shell and the radius shell may also include one or more hinges. For example, the radius shell may be attached to the metacarpal shell by a hinge located near the wrist pivot. This may allow control of the wrist in an upward and downward direction. In some aspects, the pivot may include a hinge or other similar mechanism that may be adjustable in degree, resistance, or both. In further embodiments, the hinge may be locked or absent. In addition to the hinge, the metacarpal shell and the radius shell may also include providing one or more straps. For example, the radius shell may include a protrusion (relief) to allow the strap to wrap around the underside of the user's arm. These straps may help position the brace on the arm and prevent the brace from moving or sliding on the arm during use.

In further embodiments, the metacarpal shell, radius shell, and tendon backplate may be connected to a softer material that contacts the arm of the user. Such softer material may extend beyond the area covered by the upper or lower plate. For example, in some embodiments, the radius shell includes such softer material on its underside, between the radius shell and the user's arm, and further, in some embodiments, such softer material may extend over one or more fingers of the user to provide increased stability to the device. The cabling of the cable preferably provides a secure, comfortable attachment to the user, while also providing progressive support to the wrist.

As in the knee brace embodiment, the cable may be made of any flexible material having a sufficiently high tensile strength. The upper and lower plates may be made of any rigid or semi-rigid material and shaped to conform to the desired area, such as the top of the lower arm and the underside of the lower arm and palm of the hand.

The cable system provides progressive support and adjustable extension stops with the shells by extension. Such support over a range of motion can greatly prevent wrist injuries and hyperextension.

Wrist support devices are a relatively low cost alternative to manufacturing, and are relatively simple in design. It also has a low profile, allowing the user to actively wear the brace to prevent injury.

Various additional attachment mechanisms may be employed. For example, as shown, a strap may be included. In various embodiments, a strap may be included toward the rear of the brace and toward the upper arm. In other embodiments, the strip may be further forward.

The cable system of the present invention may extend from the upper plate (e.g., radius shell), through a plurality of guides, through the base plate or tendon backplate back to the optional articulating portion, metacarpal shell, and then turn around ending on the opposite side of the radius shell at the adjustment mechanism housing. When a lateral rotational force is applied to the wrist, the radial shell, the divided or integrated metacarpal shell (optionally hinged), and the tendon backplate remain rigid by the tension created in the cable. As the main cable passes through the tendon backplate, tensile forces in the main cable may cross behind the wrist, preventing rotation and bending of the wrist joint, thereby preventing lateral bending or rotation of the wrist. The force is applied from all points along each control loop created at either side of the intersection point, applying the force to the center of the loop. Tension in the cable prevents the brace from bending over the wrist joint, thereby preventing lateral bending or rotation of the wrist.

The tendon backboard provides progressive support for tendons in the wrist throughout the motion of the wrist. For example, when the user's hand is flexed upward, the posterior control loop (radius) portion of the cable tightens, which pulls the tendon backplate toward the radius plate and metacarpal plate. This provides additional support to the wrist by offloading the tendons, and also prevents the anterior control loop (metacarpal) from continuing to extend. The more the user's wrist bends, the more support is provided as the tendon backplate is pulled into the tendon region.

As shown in fig. 18, a brace is shown that stabilizes the wrist of the user to prevent over-extension. As shown, the wrist brace is comprised of a semi-rigid shell, preferably a radial shell 104, a metacarpal shell 102, and a tendon backplate 105. The shells are preferably constructed of an elastomeric material and are shaped to ergonomically conform to the wrist of the user. In some embodiments, the material is moldable to the user, such as by heating. The shell may take any number of shapes to accommodate various design variations. For example, as shown, the radius plate 104 may include a tab that extends downward to guide the cable 101 toward the lower portion. These ears may be moved forward or backward to change the limit point. In some embodiments, the ears may be movable such that they may be adjusted, while in other embodiments they may be permanent, fixed, and/or rigid.

The adjustment mechanism 106 may be located on the radial shell 104, or alternatively on any other shell. The adjustment mechanism dial 106 and ratchet 107 allow tightening of the cable system. The cable 101 engages the metacarpal shell 102, the radius shell 104 and the tendon backplate 105 and, when tightened, brings the shells close to each other.

The cable system also provides progressive support such that increased extension is increasingly limited when the user's wrist is subjected to the overstretching force 128. Two control loops are also formed by the cable sections. The metacarpal control loop 132 is formed by the portion of the cable that extends from the cable junction 131 at the tendon backplate 105, travels along the tendon backplate through one or more guides, then toward the metacarpal shell 102, through additional guides in the metacarpal shell, and then back along the same path on the opposite side of the brace. In a similar manner, a radius control loop is formed that extends from the intersection 131 through one or more guides in the tendon backplate 105 toward the radius shell 104 and, in some embodiments, into the adjustment mechanism 106/107.

Each shell may include a pad section to provide a degree of cushioning between the more ridged plate and the user's arms, wrists and hands. In various embodiments, the pad section may also be constructed of a material that reduces movement of the device by providing a high level of static friction between the material and the user. In various embodiments, the pad sections may conform to the plate almost identically. In other embodiments, the pad section may extend well beyond the plate and may provide additional benefits or features, such as mounting holes, restraints, or locations for guides.

Fig. 22 shows the cabling of the cable 101, which begins to attach to the radius shell 104, then passes through the tendon backplate 105, extends over and through the metacarpal shell 102, back through the tendon backplate 105, crosses itself, and returns up to and attaches to the opposite side of the radius shell 104.

The cable system also provides progressive support such that when the user's wrist is subjected to a lateral bending or rotational force 130 as shown in fig. 20, increased bending and/or rotation is increasingly limited.

As shown in fig. 18 and 19, the radius shell 104 may be connected to the metacarpal shell 102 at least one point 117. Preferably, the point at which the connection is made is allowed to pivot as shown. The pivot may be adjusted with an adjustment screw 103 to provide a specified amount of movement, or alternatively, it may be locked against movement. The pivoting may be controlled in one or both of the degree of movement and resistance. In further embodiments, the metacarpal plate may not be hinged at all, but may be constructed of a material having natural elasticity, as shown in fig. 22, such that some movement of the user's hand in an upward direction is permitted, but as the spring tension (which the material is intended to return to the original shape) increases, the movement encounters increased forces.

As depicted in fig. 18, the radius shell 104 may be connected to the metacarpal shell 102 at least one point, thereby forming a unitary body. Preferably, the point at which the connection is made forms a hinge point 117 and is allowed to pivot as shown.

Various additional attachment mechanisms may be employed. For example, as shown, the strip 111 may be included, or the strip 111 may not be included at all, as shown in fig. 22. As shown in fig. 18 and 20, the soft liner 112 may extend over one or more fingers of the user in order to increase the stability of the device. In various embodiments, additional straps may be included toward the rear of the brace and toward the upper arm. In other embodiments, additional straps may be used, or instead of finger holes in liner 112.

The semi-rigid shells are shaped such that they skin-engage the user's bones, namely the radius 118, the ulna 124 and the metacarpal 126, in a manner that facilitates their rigidity for movement during use. By properly engaging the bone, there is less deflection caused by skin, fat or other tissue.

Fig. 21 shows tendon backplate 105 according to an embodiment of the present invention. Tendon backplate 105 may include a plurality of guides to control the movement of the cable system. For example, the depicted embodiment includes four regions where the cable first contacts the tendon backplate. Additional guides may also be used. Further, depending on the configuration, various embodiments may include a guide on which the cable system crosses at the crossing point 131. For example, the depicted embodiment includes a central guide that allows the cables to cross as the cables are diagonally stretched. In other embodiments, the cables may not intersect, but may merely extend near each other, and additional or different guides may be used. Furthermore, the depicted embodiment is shaped such that the outward portion of tendon backplate 105 extends upward toward the upper shells 102 and 104.

Although the shape of the tendon backplate 105 is preferably designed to ergonomically conform to the contours of the lower wrist, arm, and palm, the shape is not limited thereto. Furthermore, additional plates or components may be added, for example, hinged portions of the support hand towards the hand. Or in alternative embodiments tendon backplate 105 may be comprised of two or more plates. For example, the depicted embodiment may be composed of three separate plates, one for the front guide, one for the center guide, and one for the rear guide. Many additional configurations are possible and contemplated herein.

Fig. 21 also depicts that the cabling of the cable forms two separate control portions 132 and 133, each on their respective sides of the cable junction 131. Loops also appear in other figures. The metacarpal control loop 132 extends upwardly from the cable junction and over the metacarpal shell 102, on the other side back to the cable junction 131. The radius control loop 133 extends upwardly from the cable junction 131 and extends over the posterior portion of the radius shell 104 away from the hand, back to the cable junction 131. In use, the lengths or control loops 132 and 133 are inversely related. For example, if the user's wrist is flexed, thereby lengthening the metacarpal control loop 132, the radius control loop 133 shortens, which pulls the tendon backplate 105 and the radius plate 104 together, thereby stopping further lengthening of the metacarpal control loop 132 and thereby preventing over-extension.

The routing of the cables may vary according to embodiments of the present invention. For example, in the position where the hinge portion, i.e., the metacarpal shell, is fixed as shown in fig. 22A-22C, the wiring may be moved forward or backward. Additionally, in some embodiments, more than one adjustment mechanism may be present. For example, a front adjustment mechanism and a rear adjustment mechanism may be present.

Although the invention has been described and illustrated with respect to a particular embodiment, variations and modifications may be readily made, and it is intended that the appended claims cover any variations, modifications, or adaptations falling within the spirit and scope of the present invention.

Ankle support

In addition to the embodiments described above, another embodiment of the present invention provides support for the ankle of a user. Ankle brace embodiments incorporate many of the features described herein for alternative ligament braces.

As shown in fig. 25-26, a brace is shown that stabilizes the ankle of a user against lateral bending. As shown, the ankle brace combines a soft boot portion with a plurality of semi-rigid shells. The portions of the semi-rigid shell are preferably the fibular shell 305, the tibial shell 304, and the calcaneal shell 302. The adjustment mechanism 306 may be located on the tibial shell 304, or alternatively on any other shell. The adjustment mechanism 306 allows the cable (or cables) 301 to be tightened. The cable 301 engages the fibular shell 305, tibial shell 304 and calcaneal shell 302 and when tightened, brings these shells close to each other. The cable system also provides progressive support such that as the user's ankle flexes, the increased flex is increasingly limited.

As with the other embodiments, two control loops, an upper loop 333 and a lower loop 332 are formed. These loops cooperate to prevent unwanted ankle movement, for example, when lower loop 332 is extended (as the ankle flexes), upper loop 333 shortens, pulling shells 304 and 305 into the leg. This in turn prevents the lower loop 332 from allowing the ankle/foot to continue its motion, thereby preventing lateral bending.

The cable system may be routed in a variety of ways. For example, the cables may intersect at the fibula shell 305, forming an intersection 331, and form loops at both the tibial shell 304 and the calcaneal shell 302.

As shown in fig. 25, the fibula shell 305 may be connected to the calcaneus shell 302 at a pivot point 317. Preferably, the point at which the connection is made is allowed to pivot. The pivot 317 may be adjusted to provide a specified amount of movement or, alternatively, the pivot may be locked against movement.

The semi-rigid shells are shaped such that they engage the user's bones 318, 324 and 326 through the skin in a manner that facilitates their rigidity for movement during use. By properly engaging the bone, there is less deflection caused by skin, fat or other tissue. The cable 301 and control loops 332 and 333 assist by guiding forces from points around the loop to the bone, stabilizing the brace itself, which further improves its effectiveness.

Elbow support

The brace system and its novel control loop system described above can be adapted to the elbow to prevent arm overextension.

In such an embodiment, the humerus plate 204 would replace the femoral plate 4, the ulna plate 202 would replace the tibial plate 2, and the bicep plate would replace the femoral backplate 5, in contrast to the knee brace described above, creating differential resistance on the elbow joint, preventing arm overextension. In much the same way as the embodiments described herein, two control loops are formed, an ulna control loop 232 and a humerus control loop 233, each extending from the intersection 231.

As shown in fig. 23 and 24, a brace is shown that stabilizes the elbow of the user against overextension. As shown, the elbow brace is comprised of a semi-rigid shell, preferably a humeral shell 204, an ulna shell 202, and a tendon backplate 205. The adjustment mechanism may be located on the humeral shell 204, or alternatively on any other shell. The adjustment mechanism dial 206 and ratchet 207 allow tightening of the cable system. The cable 201 engages the ulna shell 202, humerus shell 204 and tendon backplate 205 and when tightened, brings the shells close to each other.

The cable system also provides progressive support such that increased extension is increasingly limited when the user's elbow is subjected to excessive extension forces 228. For example, as the user's elbow stretches, the control loop 232 grows. In response, the control loop 233 shortens, which pulls the tendon backplate 205 and humeral shell 204 toward the arm, thereby resisting and then stopping any further extension of the control loop 232, thereby preventing over extension. The cable system also benefits from these loops because the tightening force is directed from every point around the loop to the center of the arm. This provides good brace stability and thus good control of arm movement. Fig. 24 depicts the loops by means of arrows, showing the position of the loops around the arm of the user.

As shown in fig. 23, the ulna shell 202 may be connected to the humeral shell 204 at least one point 217. Preferably, the point at which the connection is made is allowed to pivot as shown. The pivot may be adjusted to provide a specified amount of movement, or alternatively, the pivot may be locked against movement.

Various additional attachment mechanisms may be employed. For example, as shown, strips 211A-211B may be included. In various embodiments, a strap 211B may be included toward the rear of the brace and toward the upper arm. In other embodiments, additional bands may be used, such as ulna band 211A. For example, another strap may be added to the ulna shell 202 and one or more straps may be added to the humeral shell 204.

The semi-rigid shells are shaped such that they skin-engage the user's bones, namely the ulna 226, radius 224 and humerus 218, in a manner that facilitates their rigidity to movement during use. By properly engaging the bone, the skin, fat or other tissue causes less deflection.

Claims

1. A ligament support brace, comprising:

first shell;

a second shell hingedly coupled to the first shell;

third shell;

a first control loop, the first control loop comprising a first cable portion extending from a first side of a junction on the third shell to a first side of the first shell, through a second side of the first shell, and back to a second side of the junction;

A second control loop, the second control loop includes a second cable portion, the second cable portion extends from the first side of the intersection on the third shell to the first side of the second shell, passes through the second shell and returns down along the second side of the second shell to the second side of the intersection, wherein the first control loop and the second control loop are connected, and wherein the expansion of the second control loop causes the contraction of the first control loop.

2. The ligament support brace of claim 1, wherein the first cable portion and the second cable portion comprise a single piece of cable.

3. The ligament support brace of claim 1, wherein the first cable portion and the second cable portion comprise two or more cable segments.

4. The ligament support brace of claim 1, wherein an adjustment mechanism is positioned on the second shell and coupled to a cable.

5. A ligament support brace, comprising:

a first shell, the first shell being selected from the group of a metacarpal shell, a radial plate, a tibial plate, or a calcaneal shell;

a second shell selected from the group consisting of an ulna shell, a humeral plate, a femoral plate, or a tibial shell, the second shell being hingedly coupled to the first shell;

a third shell, the third shell being selected from the group consisting of a tendinous dorsal plate, a biceps plate, a femoral dorsal plate, or a fibular shell;

A second control loop, wherein the second control loop includes a second cable portion, the second cable portion extending from the first side of the intersection on the third shell to the first side of the second shell, passing through the second shell and returning down along the second side of the second shell to the second side of the intersection, wherein the first control loop and the second control loop are connected, and wherein the extension of the second control loop causes the contraction of the first control loop.