Lower-limb prosthetic system including support assembly
Patent Information
- Authority / Receiving Office
- WO · WO
- Patent Type
- Applications
- Current Assignee / Owner
- Filing Date
- 2026-02-09
- Publication Date
- 2026-08-13
Smart Images
Figure US2026014508_13082026_PF_FP_ABST
Abstract
Description
LOWER-LIMB PROSTHETIC SYSTEM INCLUDING SUPPORT ASSEMBLY
[0001] FIELD OF THE DISCLOSURE
[0002] The present disclosure relates generally to prosthetic systems and, more particularly, to a lower-limb prosthetic system including a support assembly configured to resist injurious hyperextension of a joint of a user during high-load activities.
[0003] BACKGROUND
[0004] Various types of lower-limb prosthetic systems are used to replace human lower limbs. Some of these systems and devices are designed specifically for elite and recreational amputee athletes who engage in activities such as sprinting, jumping, and long jumping. Prosthetic devices for these sports are usually built to store and release energy produced by the user to improve performance.
[0005] For example, in cases of individuals with bclow-thc-kncc amputations, performance in long jumping can be enhanced by maximizing the vertical and horizontal velocities generated by the athlete. The horizontal velocity results from the speed developed during the athlete’s run-up, while the vertical velocity is produced by the push-off from the ground with the takeoff leg. The higher the vertical velocity, the longer an athlete can stay airborne, which increases the jump distance.
[0006] Existing lower-limb prosthetic systems can increase the risk of knee hypcrcxtcnsion injuries, especially during jumping or leaping. During take-off, a significant extension force may be applied to the knee joint. To lower injury risk, users of earlier systems often try to keep their knees flexed, which can negatively impact performance and requires deliberate effort. Additionally, medial-lateral and rotational stability may be diminished in users with shorter residual limbs, further increasing the risk of injury.
[0007] Accordingly, there is a need for a lower-limb prosthetic system that provides structural support and controlled energy storage while reducing the risk of injurious joint hyperextension during high- load activities. There is a need for a lower- limb prosthetic system that prevents knee hyperextension injuries for long jumpers and other athletes who place exceptionally heavy loads on their prostheses during jumping or leaping.
[0008] SUMMARY
[0009] This disclosure describes a lower-limb prosthetic system featuring a support assembly designed to prevent injurious hyperextension of a joint, especially during high-impact activities such as jumping, leaping, or sprinting. The disclosure pertains to actions associated with activities such as the Paralympic long jump, as well as other sporting or dynamic movements in which prosthetic devices, systems, or assemblies may be subjected to excessive forces.
[0010] The principles outlined herein can apply to a variety of scenarios that present a risk of joint hyperextension. The take-off step from a plank occurs in a fraction of a second, and because excessive force can be exerted on the knee at take-off, the margin for error is especially narrow for elite athletes. The embodiments described herein provide an approach to address these challenges by incorporating a support assembly including a resilient member that provides both physical support and proprioceptive feedback, thereby helping to prevent injurious hyperextension of the knee.
[0011] The resilient member of the support assembly reinforces the knee by contacting the thigh or anterior upper leg before injurious hyperextension is achieved. The prosthetic system holds the thigh and knee under load as the resilient member, configured as a spring, is compressed. As the spring is compressed, energy is stored in the resilient member, and a stabilizing force increases. At a certain point, for example, at or near maximum compression, the energy stored in the resilient member is sufficient to counter the extension moment acting on the knee, thereby preventing hypcrcxtcnsion.
[0012] According to the disclosure, the lower- limb prosthetic system includes a socket, a foot (for example, a prosthetic sports blade) connected to the socket, and a support assembly including a resilient member. The resilient member has an anchored portion secured to the socket of the prosthetic system and a movable portion extending proximally relative to the socket. The movable portion is positioned to engage an upper leg of the user as the joint approaches extension. Under load, the resilient member flexes to store energy and generates a counteracting force that resists further extension of the joint.
[0013] The resilient member may be configured as a cantilevered spring structure and may include flat (planar) or contoured shapes. In some embodiments, the support assembly further includes a load-distribution interface, such as a cuff, configured to distribute forces over a contact area of the upper leg. The support assembly may also include an extension-limiting mechanism configured to restrict excessive deflection of the resilient member. Positioned tocontact the user’s thigh, the resilient member stabilizes the thigh and knee under load as the spring compresses.
[0014] The resilient member may be shaped according to the needs of the application to accommodate the anatomical size and dimensions of the user. In embodiments in which the resilient member is flat or planar, the anchored portion is attached to an anterior facet of the socket. In embodiments in which the resilient member is curvilinear, the anchored portion may be secured to a distal facet of the socket. In other embodiments, the anchored portion of a curvilinear resilient member may be secured to the anterior facet of the socket. The curvilinear resilient member may include a curved segment connecting a base portion to an elongated portion, with the elongated portion spaced from the anterior facet of the socket. Likewise, the resilient member may be segmented in shape in that it is planar or curvilinear at least within a midspan or middle portion thereof, generally defined between proximal and distal portions of the resilient member.
[0015] The resilient member is configured to flex and unflex in response to forces exerted during jumping, leaping, or similar activities. During flexion, the resilient member stores energy as the thigh deflects the movable portion. During no flexion, the resilient member releases the stored energy back against the thigh to help counteract hyperextension forces acting on the knee. In a preferred embodiment, the resilient member comprises a single monolithic spring extending between the anchored portion and the movable portion. Alternative embodiments may include a multicomponent spring or two or more resilient members, such as those arranged on the lateral and medial sides of the knee, to tailor the force distribution acting on the user. The support assembly may further include an end-stop adjustment mechanism configured to limit deflection of the resilient member, allowing a user to tune the response and control the extent of allowable joint extension.
[0016] The support assembly may include a first adapter that secures the anchored portion of the resilient member to the socket, and a second adapter that adjustably secures a loaddistribution interface, such as a cuff, to the movable portion of the resilient member. The movable portion and the load-distribution interface are detached from the thigh during normal joint flexion, thereby allowing unrestricted flexion of the knee. The support assembly enables users to run, walk, and jump without maintaining a deliberately bent knee or consciously controlling high extension forces during take-off and similar movements. Additionally, because medial, lateral, and rotational stability may depend on residual limb length, thedisclosed support assembly can help reduce the risk of injuries to the anterior cruciate ligament (ACL) and posterior cruciate ligament (PCL).
[0017] In summary, the disclosed lower- limb prosthetic system, incorporating a support assembly with a resilient member, pennits unrestricted joint flexion during normal gait while providing increasing resistance as the joint approaches hyperextension, thereby enhancing safety without impairing performance. These and other features, aspects, and advantages of the present disclosure will become better understood from the following description, appended claims, and accompanying drawings.
[0018] BRIEF DESCRIPTION OF THE DRAWINGS
[0019] The drawing figures are not necessarily to scale but are intended to better illustrate the components, not to limit the scope, but to show exemplary examples. The figures depict typical configurations of lower-limb prosthetic systems, including a support assembly, and do not restrict the structures or configurations of the present disclosure.
[0020] Fig. 1A illustrates an exemplary long jump sequence of an amputee athlete.
[0021] Fig. IB illustrates a schematic view of a lower-limb prosthetic system of the prior art for an amputee athlete.
[0022] Fig. 2 illustrates a perspective view of an embodiment of a lower- limb prosthetic system including a support assembly according to the present disclosure.
[0023] Fig. 3A illustrates a schematic view of the support assembly, including a resilient member, in relation to a user and the lower- limb prosthetic system.
[0024] Fig. 3B illustrates a schematic view of the support assembly comprising a resilient member and at least one end-stop arrangement.
[0025] Fig. 4 illustrates an embodiment of a support assembly including a resilient member.
[0026] Fig. 5 illustrates the support assembly of Fig. 4 arranged with the lower-limb prosthetic system.
[0027] Fig. 6 illustrates another embodiment of a support assembly including a resilient member.
[0028] Fig. 7 illustrates the support assembly of Fig. 6 arranged with the lower-limb prosthetic system.
[0029] Fig. 8 illustrates a perspective view of another embodiment of a lower-limb prosthetic system including a support assembly according to the present disclosure.
[0030] Fig. 9A is a detail view of a first variation of a cuff arranged at a first angle relative to a resilient member of the support assembly in the embodiment of Fig. 8.
[0031] Fig. 9B is a detail view of a second variation of a cuff arranged at a second angle relative to a resilient member of the support assembly in the embodiment of Fig. 8.
[0032] DEFINITIONS
[0033] A brief explanation of certain terms is provided below to facilitate understanding of the lower-limb prosthetic system, including the support assembly described herein. The definitions provided herein are intended to aid interpretation and are not intended to limit the scope of the claims.
[0034] The singular forms “a,” “an,” and “the” include plural referents unless the context clearly dictates otherwise.[OO35| As used herein with respect to a stated property or circumstance, the term “substantially” refers to a degree of deviation that is sufficiently small so as not to materially affect the stated property or circumstance. The exact degree of deviation may depend on the specific context. The terms “about” and “approximately” introduce flexibility and imprecision associated with a stated term, measurement, or value, as would be understood by a person of ordinary skill in the art. Unless otherwise indicated, “about” generally refers to a variation of less than 2%, most often less than 1%, and in some cases less than 0.01%. The term “generally” refers to a component or portion thereof that deviates by no more than 10% from a referenced norm. For example, “generally straight” indicates that straightness may deviate by up to 10% over a length while still being considered straight.
[0036] As used herein, the term “proximal” refers to a location closer to the heart than another location, and the term “distal” refers to a location farther from the heart than another location. The term “posterior” refers to a position behind or toward the rear of another location, and the term “anterior” refers to a position ahead of or toward the front of another location. The terms “lateral” and “medial” are used in their conventional anatomical sense and refer to directions facing outward and inward, respectively, such that the medial side of one foot faces the medial side of the user’ s other foot.
[0037] The term “adapter,” as used herein, refers to a system, device, interface, or apparatus configured to connect or couple one prosthetic component to another prosthetic component, including to a socket, either directly or indirectly.
[0038] The term “hyperextension” refers to extension of a joint beyond its natural range of motion. For example, extending a knee joint beyond approximately 0 degrees may be considered hyperextension. A person of ordinary skill in the art will appreciate that a limited degree of natural hyperextension may be present in some individuals without causing injury; however, the support assembly and resilient member described herein are configured to resist injurious hyperextension that may result in tissue, ligament, or joint damage.
[0039] The terms “prosthetic” and “prosthesis,” as used herein, refer to a system, device, or apparatus configured to function as an artificial substitute for, or support of, a body part.
[0040] The term “saltation,” as used herein, refers to the action or process of leaping, hopping, or jumping.
[0041] The term “socket,” as used herein, refers to a component of a prosthetic system configured to couple the prosthetic system to a body part. In one embodiment, the socket comprises a portion of a prosthesis configured to receive and at least partially surround a residual limb and may be configured to bear weight during use.
[0042] As used herein, the term “support assembly” refers to a structural assembly associated with a lower-limb prosthetic system and including at least one resilient member configured to resist injurious hyperextension of a joint of a user. The support assembly may further include one or more adapters, mounting interfaces, load-distribution interfaces, extension-limiting mechanisms, or combinations thereof.
[0043] As used herein, the term “resilient member” refers to an energy-storing structural element that forms part of the support assembly and is configured to flex under load and generate a restoring force. The resilient member may be formed as a spring, including a planar spring or a contoured spring, may be monolithic or multi-component, and may function as a cantilevered structure.
[0044] As used herein, the term “anchored portion” refers to a portion of the resilient member that is secured, directly or indirectly, to the socket. The term “movable portion” refers to a portion of the resilient member that deflects or displaces relative to the socket under load.
[0045] As used herein, the term “load-distribution interface” refers to a structure associated with the support assembly and arranged to contact an upper leg of a user, thereby distributing forces applied by the resilient member over a contact area. In some embodiments, the loaddistribution interface comprises a cuff.
[0046] As used herein, the term “joint” refers to an anatomical joint of a user, including at least a knee joint.
[0047] The term “take-off,” as used herein, refers to a transitional phase between a final ground-contact step and becoming airborne during an activity involving running, jumping, or leaping.
[0048] DETAILED DESCRIPTION OF VARIOUS EMBODIMENTS
[0049] Fig. 1A illustrates an exemplary long jump sequence of an amputee athlete 10. As mentioned, athletes 10 aim to maximize both horizontal and vertical velocity to achieve the greatest distance in sporting events like the long jump. The horizontal velocity of athlete 10 at take-off to is generated by the speed accumulated during the run-up. In contrast, the vertical velocity is created by pushing off the ground with the prosthetic leg system 12 at take-off to. The greater the vertical velocity, the longer the athlete remains airborne, thus increasing the jump distance to touch-down ti.
[0050] As shown in Fig. IB, prosthetic leg systems 12 for amputee athletes 10 can experience a significant moment M applied to the knee center Kc during the take-off to from the plank 18. The prosthetic leg system 12 consists of a foot 14 and a socket 16. This creates a risk of hyperextending the knee K. In prior art devices, to prevent knee K from hyperextending (i.e., buckling), athlete 10 must maintain a slightly bent, stable knee K during the take-off to phase from plank 18. In other words, a straight knee generates high moments on the knee K at takeoff to. while a slightly flexed knee K, such as at angle A, lowers the risk of hyperextension at take-off to. The athlete 10 must consider these forces in their technique and training.
[0051] The present disclosure describes a lower-limb prosthetic system 100 that provides support and proprioception to the user during activities that require leaping or jumping, before the risk of injurious hyperextension of the knee arises. Fig. 2 illustrates a perspective view of the lower-limb prosthetic system 100, which includes a socket 102, a foot 104, and a support assembly 106 including a resilient member. The lower-limb prosthetic system 100 is shown as a trans-tibial prosthetic assembly; however, it is envisioned that embodiments of the supportassembly 106 could be used with various prosthetic devices, systems, or assemblies, or limb enhancements, to prevent hyperextension of joints.
[0052] The socket 102 fits around and envelops the residual limb, attaching to both the foot 104 and the support assembly 106. It is made from a material that has adequate structural strength and rigidity to fully support the loads exerted by the user' s residual limb during the operation of the lower-limb prosthetic system 100. For instance, socket 102 may be constructed from a resin-impregnated carbon fiber matrix suitable for use in prosthetic devices, systems, or assemblies, including prosthetic sockets.
[0053] In one embodiment, the socket 102 includes a posterior facet 108, an anterior facet 110, and a distal facet 112. As shown in Fig. 2, the foot 104 is attached to the socket 102 at the posterior facet 108. However, the foot 104 may also connect to another surface of the socket 102, such as the distal facet 112. In one embodiment, the foot 104 is linked to the socket 102 using an adapter of the type detailed in U.S. Patent No. 9,737,420, published on August 22, 2017, which is incorporal cd by reference. The socket 102 can connect with various types of prosthetic attachments, including liners, straps, and compression garments, to securely fit the user’s residual limb.
[0054] The foot 104 of the lower-limb prosthetic system 100 is designed to absorb shock and maintain contact with the ground. In one embodiment, the foot 104 is a monolithic, curved blade constructed from a composite fiber material (e.g., carbon fiber). The foot 104, also referred to as a sports blade, can be made of another suitable material that flexes to store and return energy during motion. For example, the foot 104 can compress and expand while walking or running. In another embodiment, the foot 104 offers feedback or response that corresponds to the user’s weight and impact level.
[0055] This disclosure presents various examples and features of prosthetic feet. For instance, in some embodiments, the foot 104 may be a prosthetic running foot. In other embodiments, a prosthetic sports foot might function as a prosthetic cycling foot. Additionally, the prosthetic sports foot can be adapted for use in different sports or for regular activities such as Walking. The user's weight determines the stiffness of the foot 104, and this stiffness can be adjusted by changing the material used to construct foot 104.
[0056] During sporting events like the long jump, foot 104 experiences an increased load as the user pushes it into the ground at take-off. The horizontal force generated at take-off is transformed into a vertical force as foot 104 compresses and releases. In elite athletes, thevertical force acting on the lower- limb prosthetic system 100 is about seven times the athlete’s body weight. This creates a significant moment on the knee center, prompting the inclusion of the support assembly 106, including the resilient member described below, in the lower- limb prosthetic system 100 to counteract harmful hyperextension forces on the knee.
[0057] The support assembly 106 includes a resilient member comprising a spring 114 with an anchored portion or fixed end 116 secured to the socket 102 and a movable portion or free end 118 extending in the proximal direction and superior to the socket 102. As used herein, the term “free end” means the unsupported end of the spring that is deflected by forces applied to the spring. The spring 114 is configured to flex and unflex in response to the force applied by the user’s weight during saltation or leaping. The flexion of the spring 114 stores energy in the spring 114 as the free end 118 is deflected, e.g., by the thigh (or anterior upper leg) of the user. During no flexion, the resilient member releases the stored energy against the thigh to counteract the hyperextension forces imposed on the knee.
[0058] The support assembly 106 features a first adapter 120 that secures the fixed end 116 of the resilient member (spring 114) to the socket 102. This first adapter 120 is designed to hold the spring 114 in place relative to the socket 102 and can be adjusted to fit users of various sizes. In one embodiment, the fixed end 116 is attached to the anterior facet 110 of the socket 102. A load-distribution interface including a cuff 124 is located at the free end 118 of the spring 114 and is connected to the spring 114 by an adjustment interface, such as a second adapter 122. The second adapter 122 can be configured to secure the cuff 124 in position relative to the spring 114. However, in an alternative embodiment, this second adapter 122 may allow multidirectional movement, including angular adjustment and spacing of the cuff to the spring, and rotation of the cuff 124, facilitating flexible interaction between the user's thigh and the cuff 124. In another embodiment, the spring 114 is integrated with the cuff 124 as a single unit, without the second adapter 122, resulting in a unitary design that conforms to the user’s leg.
[0059] Fig. 3A illustrates the forces associated with the flexion and extension of the resilient member of the support assembly 106 in relation to a user and the lower-limb prosthetic system 100. When moment M is applied to the user's knee K during its extension, such as moving toward hyperextension, spring 114 is compressed until the energy stored in the spring is sufficient to counteract moment M on knee K. The decompression of spring 114 then releases the stored energy to the thigh, applying a counterforce F to prevent injury from hyperextension.
[0060] The resilient member (spring 114) of the support assembly 106 functions as a cantilever beam with the fixed end 116, being restrained against the socket 102, and where deflection of the spring 114 is zero, and with the free end 118, being deflected by the thigh of the user, and where deflection of the spring 114 is maximized. Additionally, the level of compression of the spring 114 can vary based on stiffness, which can be designed based on the weight of the user, or depending on user preference and / or need.
[0061] Fig. 3B illustrates an embodiment of the support assembly 106 that further comprises at least one extension-limiting mechanism, such as an end-stop adjustment mechanism 121, arranged to limit the displacement or deflection of the resilient member 114. In an embodiment, the end-stop adjustment mechanism 121 includes an adjustable strap 123 connected to the foot 104 (or to the posterior facet 108 of the socket 102) and to the free end 118 of the spring 114 (or to the second adapter 122 or cuff 124). The adjustable strap 123 can be connected to the socket 102 (or foot 104) and spring (or second adapter 122 or cuff 124) by one or more hitches 127. The adjustable strap 123 comprises a tensioning member 125 configured to elongate or shorten the length of the strap 123 to adjust the limit of the displacement or deflection of the spring 114. The tensioning member 125 can be a ratchet, buckle, snap fastener, hook-and-loop fastener, etc., configured to adjust the tension and / or length of the strap 123. In other words, the position or location of the end-stop adjustment mechanism 121 is adjusted by the adjustable strap 123 and tensioning member 125.
[0062] In an embodiment, the end-stop adjustment mechanism 121 includes an adjustment pin 129 that extends through the spring 114 (i.e., through a hole formed in the spring 114). The spring 114 may include a plurality of holes through which the adjustment pin 129 can extend to accommodate the size and preference of the user. On the posterior side of the spring 114, the adjustment pin 129 is fixed to the socket 102, e.g., an anterior facet 110 of the socket. On the anterior side of the spring, the adjustment pin 129 is connected to a stopper 131. The stopper 131 is configured to move along the length of the adjustment pin 129 to adjust the limit of the displacement or deflection of the spring 114. The adjustment pin 129 can include threads that interlock with the threads of the stopper 131 to adjust the end-stop adjustment mechanism 121, i.e., a nut-and-bolt configuration. In an embodiment, the end-stop adjustment mechanism 121 includes both adjustable-strap and adjustment-pin configurations.
[0063] Figs. 4-5 illustrate an embodiment of the support assembly 106 wherein the resilient member 114 is a flat or planar spring. In an embodiment, the position of the cuff 124 along thespring 114 is adjustable, for instance, to accommodate users with different preferences or leg sizes. The spring 114 can include apertures through which the first and second adapters 120, 122 can connect. In some examples, the cuff 124 can be locked into position after an adjustment. One of ordinary skill in the art would appreciate the position of the cuff 124 and the first and second adapters 120, 122 may be adjusted in a variety of different ways. The cuff 124 can also include padding 126 to provide added cushion and support to the user. In an embodiment, the padding 126 is formed to the contour of the user’s leg. In some examples, the padding 126 is a foam pad. The cuff 124 can provide increased support by reducing strain on the user's leg.
[0064] As depicted, the second adapter 122 is adjustably fixed to the spring 114. The second adapter 122 includes an anterior plate 128 positioned along the anterior surface of the spring 114 and a posterior plate 130 positioned along the posterior surface of the spring 114. The anterior plate 128 and posterior plate 130 can be secured to the spring 114 by one or more fasteners 132, e.g., screws, bolts, or the like. The first and second adapters 120, 122 may be of the type described in U.S. Patent No. 9,737,420, which is incorporated by reference in its entirety.
[0065] Figs. 6-7 illustrate an embodiment of the support assembly 106 comprising a resilient member in the form of a curvilinear spring 134. The curvilinear spring 134 has a fixed end 136 secured to the socket 102 and a free end 138 that extends proximally, superior to the socket 102. The curvilinear spring 134 functions similarly to the flat spring 114, in that it is configured to flex and unflex in response to the force applied by the user's weight during saltation or leaping. The flexion of the curvilinear spring 134 likewise stores the energy in the curvilinear spring 134 as the free end 138 is deflected, e.g., by the thigh of the user, and the un- flexion of the curvilinear spring 134 releases the stored energy against the thigh to counteract the hyperextension forces imposed on the knee.
[0066] In an embodiment, the curvilinear spring 134 has a base portion 140 at the fixed end 136 secured to a distal facet 112 of the socket 102. The curvilinear spring 134 also has a curved segment 144 formed between the base portion 140 and an elongated portion 142. The elongated portion 142 is detached or separated from the anterior facet 110 of the socket 102. The curvilinear spring 134 can effectively absorb and release energy to prevent hyperextension of the knee, while allowing the user to freely flex it during walking or running. For example,responsive to vertical forces generated by the user and foot 104 during take-off, the curvilinear spring 134 can flex and support the user before hyperextension of the knee occurs.
[0067] According to some aspects, the curvilinear spring 134 can be a single, shaped member formed with the base portion 140, elongated portion 142, and curved segment 144. In some aspects, the curvilinear spring 134 can combine two or more attached portions. For example, the elongated portion 142 can include one or more joints connecting one or more portions of the curvilinear spring 134 to the base portion 140. In an embodiment, the spring 134 is formed together with the cuff 124 as a monolithic unit, without the second adapter 122, and has a unitary construction that conforms to the user’s leg.
[0068] The lower-limb prosthetic system described in any of the embodiments can be adapted for non-athletic uses. The support assembly, as shown in any of the disclosed embodiments and their variations, may be used with a conventional socket when extra support is needed for the user, especially at the anterior aspect or front part. For example, Fig. 3A shows how an adapter or other prosthetic component 113, such as a knee or pylon, can be attached to an adapter or connector 111 at the distal end or facet 112 of a socket that includes the support assembly 106. The prosthetic component 113 connects to a pylon or ankle and foot assembly at the distal portion 112 of the socket, similar to what is used in a typical trans-tibial or transfemoral lower-limb prosthetic system, as someone skilled in the field would recognize. In fact, someone skilled in the art would understand that the socket in a conventional lower-limb prosthetic system connects to a prosthetic foot at the end of the socket, unlike the embodiment in Fig. 3 A where the prosthetic foot attaches to the posterior facet 108.
[0069] Alternatively, the support assembly is not restricted to being attached only to the front or anterior side of the socket. It can also be positioned on the rear or posterior side, or on the lateral or medial sides, depending on whether the user needs additional support and stability. The support assembly is not limited to just a single resilient member; multiple support assemblies can be installed on different sides of the socket based on the user's need for extra stability beyond what the socket provides. In fact, the flexibility or resiliency of the resilient members can be adjusted according to the user's specific support requirements.
[0070] Fig. 8 illustrates another embodiment of the lower-limb prosthetic system 200, which includes the socket 202, similar to that detailed above in connection with the embodiment of Fig. 2. In this embodiment, the lower- limb prosthetic system 200 includes a support assembly 206 having a resilient member 207 with a geometry and mounting configuration distinct fromthe embodiments of Figs. 2-7. The socket 202 defines a proximal end portion 214 that is open and configured and dimensioned to accommodate a residual limb. The socket 202 likewise defines a distal end portion 212 that is closed and may be used to mount prosthetic components.
[0071] The system 200 includes a foot 204, as described above in connection with Fig. 2, extending from a posterior facet 216 of the socket 202. The posterior facet 216 is arranged to receive the proximal end 205 of the foot 204. It may have a facet, preferably defined as a flat surface 217, that is generally obliquely arranged relative to a longitudinal axis A- A, generally between the distal and proximal end portions 212, 214 of the socket 202. The foot 204 is preferably mounted to the posterior facet 217 by at least one fastener 220.
[0072] The socket 202 defines an anterior portion 218, which may include an anterior facet 219, that may be formed as a flat surface. The support assembly 206 includes the resilient member 207, configured as a contoured support spring, having a distal portion 224 configured and dimensioned to be secured to the socket 202 at the anterior facet 219 by at least one fastener 222. Unlike the earlier embodiments, the resilient member 207 of the support assembly 206 follows a multi-segmented path relative to the socket 202, defining a middle portion 226 having an outward curvature that protrudes anteriorly relative to the longitudinal axis A-A and extends around a lip 215 at the proximal portion 214 of the socket 202. This geometry establishes a distinct load-transfer path and reduces interference between the resilient member and the socket during flexion.
[0073] In this embodiment, the anchored portion (224) of the resilient member (207) is secured to the anterior facet (219) of the socket (202), and the curved middle portion (226) extends around the proximal lip (215) of the socket to position the movable portion (228) forward of the socket during flexion.
[0074] Proximal to the middle portion 226 is a proximal portion 228 of the resilient member 207, configured and dimensioned to secure to a load-distribution interface in the form of a cuff 208. The proximal portion 228 may be generally straight and secured to a cuff mount 210 by fasteners 230. The cuff 208 may be selectively angled relative to the resilient member, as described below, to tailor engagement with the user’s anatomy. Further, a strap 231 may be secured to the cuff 208 to provide additional stability according to the needs of a user, and the cuff 208 may include slots to loop a strap thereabout and secure therewith.
[0075] Figs. 9A and 9B illustrate different embodiments of the cuff 232, 238. In Fig. 9A, the cuff 232 defines a cuff mount 236 arranged to configure the cuff 234 at a first angle 244 relativeto the proximal portion 228 of the resilient member 207. Fig. 9B shows a cuff mount 242 that arranges the cuff 240 at a second angle 246 relative to the proximal portion 228. These alternative cuff-mount geometries distinguish the embodiments of Figs. 8-9B by allowing angular adjustment of the load-distribution interface independently of the resilient member geometry, thereby accommodating user comfort, residual limb shape, and performance requirements.
[0076] Accordingly, while the support assembly 206 operates on the same principles as the earlier embodiments, including progressive resistance to joint hyperextension through controlled flexion of a resilient member, the embodiment of Figs. 8-9B is structurally and geometrically distinct in its socket interface, curvature profile, and cuff mounting configuration.
[0077] It is understood that not all objects or advantages may be achieved under any embodiment of the disclosure. Those skilled in the art will recognize that the resilient member of the support assembly of the lower-limb prosthetic system may be embodied or carried out to achieve or optimize one advantage or group of advantages as taught herein without achieving other objects or advantages as taught or suggested herein. Indeed, the support assembly is not limited to being provided for an athlete, but can be provided in any type of lower-limb prosthetic system whereby support is required for the anterior aspect or to mitigate hyperextension
[0078] The skilled artisan will recognize the interchangeability of various disclosed features. Besides the variations described herein, other known equivalents for each feature can be mixed and matched by an ordinary skill in this art to build and use a lower-limb prosthetic system under the principles of the present disclosure. The skilled artisan will understand that the features described herein may be adapted to other methods and types of orthopedic and prosthetic devices / applications.
[0079] It is intended that the present disclosure should not be limited by the disclosed embodiments described above and may be extended to other applications that may employ the features described herein.
Claims
CLAIMS1. A lower- limb prosthetic system (100), comprising:a socket (102);a foot (104) connected to the socket (102); anda support assembly ( 106) comprising a resilient member (114, 134, 207) having an anchored portion (116, 136, 224) secured to the socket (102) and a movable portion (118, 138, 228) extending proximally relative to the socket (102);wherein the movable portion (118, 138, 228) is arranged to engage an upper leg of a user as a joint approaches extension; andwherein the resilient member (114, 134, 207) is configured to store energy under load and to resist injurious hyperextension of the joint.
2. The lower-limb prosthetic system (100) according to claim 1, wherein the joint comprises a knee joint.
3. The lower-limb prosthetic system (100) according to claim 1, wherein the resilient member (114, 134, 207) comprises a cantilevered spring stmcture.
4. The lower-limb prosthetic system (100) according to claim 3, wherein the resilient member comprises a planar resilient member (114) secured to an anterior facet (110) of the socket (102).
5. The lower-limb prosthetic system (100) according to claim 3, wherein the resilient member comprises a contoured resilient member (134, 207).
6. The lower-limb prosthetic system (100) according to claim 5, wherein the contoured resilient member (134, 207) includes a curved segment (144, 226) disposed between a base portion (140, 224) and an elongated portion (142, 228).
7. The lower-limb prosthetic system (100) according to claim 6,wherein the base portion (140, 224) of the contoured resilient member (134, 207) is secured to an anterior facet (110, 219) of the socket (102, 202), andwherein the curved segment (144, 226) extends anteriorly and around a proximal region (215) of the socket (202) such that the elongated portion (142, 228) is spaced from the socket (102, 202) during flexion.
8. The lower-limb prosthetic system (100) according to claim 1, wherein the support assembly (106) further comprises a mounting interface (120) securing the anchored portion (116, 136, 224) of the resilient member (114, 134, 207) to the socket (102).
9. The lower-limb prosthetic system (100) according to claim 1, wherein the movable portion (118, 138, 228) of the resilient member (114, 134, 207) is coupled to a load-distribution interface (124, 208).
10. The lower- limb prosthetic system (100) according to claim 9, wherein the loaddistribution interface comprises a cuff (124, 208).
11. The lower- limb prosthetic system (100) according to claim 9, wherein the loaddistribution interface (124, 208) is adjustably coupled to the resilient member (114, 134, 207) by an adjustment interface (122, 210).
12. The lower-limb prosthetic system (100) according to claim 10, wherein the cuff (232, 238) is coupled to the resilient member (207) by a cuff mount (236, 242) configured to orient the cuff at a selectable angle (244, 246) relative to the movable portion (228) of the resilient member.
13. The lower- limb prosthetic system (100) according to claim 1, wherein the resilient member (114, 134, 207) is configured to flex in response to forces applied during jumping, leaping, sprinting, or combinations thereof.
14. The lower- limb prosthetic system (100) according to claim 13, wherein flexion of the resilient member (114, 134, 207) stores mechanical energy and no flexion releases the stored mechanical energy to oppose hyperextension of the joint.
15. The lower- limb prosthetic system (100) according to claim 1, wherein the support assembly (106) further comprises an extension-limiting mechanism (121) configured to restrict deflection of the resilient member (114, 134, 207).
16. The lower- limb prosthetic system (100) according to claim 15, wherein the extensionlimiting mechanism (121) comprises an adjustable strap (123) coupled between the resilient member (114, 134, 207) and the socket (102).
17. The lower- limb prosthetic system (100) according to claim 15, wherein the extensionlimiting mechanism (121) comprises an adjustable stop element (129, 131).
18. The lower-limb prosthetic system (100) according to claim 1, wherein the foot (104) comprises an energy-return prosthetic foot.
19. The lower- limb prosthetic system (100) according to claim 18, wherein the foot (104) is connected to a posterior facet (108, 217) of the socket (102, 202).
20. The lower- limb prosthetic system (100) according to claim 1, wherein the support assembly (106) permits unrestricted flexion of the joint during normal gait while providing increasing resistance as the joint approaches hyperextension.