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WO2013043264A1 - Prothèse implantable destinée à répartir le poids sur un membre amputé et son procédé d'utilisation en association avec une prothèse externe - Google Patents

Prothèse implantable destinée à répartir le poids sur un membre amputé et son procédé d'utilisation en association avec une prothèse externe Download PDF

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Publication number
WO2013043264A1
WO2013043264A1 PCT/US2012/049263 US2012049263W WO2013043264A1 WO 2013043264 A1 WO2013043264 A1 WO 2013043264A1 US 2012049263 W US2012049263 W US 2012049263W WO 2013043264 A1 WO2013043264 A1 WO 2013043264A1
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WIPO (PCT)
Prior art keywords
force distribution
prosthetic
bladder
strut
boot
Prior art date
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Ceased
Application number
PCT/US2012/049263
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English (en)
Inventor
Larry N. SMITH
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Individual
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Individual
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Filing date
Publication date
Priority claimed from US13/237,114 external-priority patent/US8882851B2/en
Application filed by Individual filed Critical Individual
Publication of WO2013043264A1 publication Critical patent/WO2013043264A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/78—Means for protecting prostheses or for attaching them to the body, e.g. bandages, harnesses, straps, or stockings for the limb stump
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/30721—Accessories
    • A61F2/30749—Fixation appliances for connecting prostheses to the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/68—Operating or control means
    • A61F2/70—Operating or control means electrical
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/78—Means for protecting prostheses or for attaching them to the body, e.g. bandages, harnesses, straps, or stockings for the limb stump
    • A61F2/80—Sockets, e.g. of suction type
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/60—Artificial legs or feet or parts thereof
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2002/5003—Prostheses not implantable in the body having damping means, e.g. shock absorbers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2002/501—Prostheses not implantable in the body having an inflatable pocket filled with fluid, i.e. liquid or gas
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/60—Artificial legs or feet or parts thereof
    • A61F2002/608—Upper legs
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/68—Operating or control means
    • A61F2002/6863—Operating or control means magnetic
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/68—Operating or control means
    • A61F2/70—Operating or control means electrical
    • A61F2002/704—Operating or control means electrical computer-controlled, e.g. robotic control
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/76—Means for assembling, fitting or testing prostheses, e.g. for measuring or balancing, e.g. alignment means
    • A61F2002/7615—Measuring means
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/78—Means for protecting prostheses or for attaching them to the body, e.g. bandages, harnesses, straps, or stockings for the limb stump
    • A61F2002/7887—Means for protecting prostheses or for attaching them to the body, e.g. bandages, harnesses, straps, or stockings for the limb stump for connecting limb exoprostheses to the stump bone

Definitions

  • Limb amputations have been part of humankinds' existence from its beginning as evidenced by hieroglyphics depicting techniques to fashion amputee prosthetics. Traumatic limb amputations were a common battlefield wound in the age of combat fought with swords and axes. Cautery of the residual limb or stump with hot oil or heated metal was the preferred method to stem the flow of blood on these ancient battlefields. It was not until the 1500's when Ambroise Pare demonstrated that ligation of the artery and vein with delayed or primary closure of the amputee wound provided superior healing and rehabilitation when compared to the cauterization techniques. Injury to or loss of extremities on the modern battlefield are particularly common today and is seen in 70.5 percent of all wounded soldiers.
  • the PTA also supplies the medial calcaneus region and has lateral anastomatic connections with the external Calcanean, the terminal branches of the posterior Peroneal artery (PPA) through the PTA's internal Calcanean branches.
  • PPA posterior Peroneal artery
  • this artery is ligated as it is encountered during the development of the plantar flap, just proximal and between the first and second metacarpal -phalangeal joints.
  • the methods and devices used to hold the prosthetic in place on the residual limb present a whole different set of problems.
  • the manner in which a prosthetic device is attached to the residual limb can determine the amount of control the amputee has over the prosthesis and, consequently, their ease and range of movement.
  • Patients have utilized a variety of belts, bands, straps, cuffs, harnesses, sockets, suction sleeves and the like to secure a prosthesis against a residual limb.
  • the disadvantage with most of these devices is that they are inconvenient and usually cause chafing, which leads to sores and abrasions and, in some cases, secondary skin infections.
  • the embodiments of the subject invention successfully address the above-described disadvantages associated with the previously known prosthetic devices and their methods of use, and provide certain attributes and advantages, which have not been realized by these known devices.
  • the embodiments of the subject invention provide novel and P T/US2012/049263
  • the embodiments of the subject invention provide an implantable, orthopedic, hydrodynamic amputee prosthesis designed to provide a non-compressible space that distributes the weight and force of walking over the entire surface of the residual limp.
  • the devices and methods disclosed herein improve the dynamic interaction between the newly reconstructed residual limb and the external walking prosthesis and prevent the otherwise dysfunctional boney stump from receiving all the weight of walking on a single point.
  • Embodiments of the subject invention provide a bladder or variable density semi-solid that individually or together because of its non-compressibility or variable compressibility acts hydraulically to accept the forces and then transfers the weight and force of walking evenly over the reconstructed stump.
  • This hydraulic system (as in, for example, a natural fluid filled joint) allows for the force of walking to be directed to the bone, so the axial skeleton now accepts the weight and force of walking instead of the amputee stump skin.
  • This system provides for a more functional weight bearing and walking surface.
  • an implantable prosthesis will in effect reconstruct the natural hydraulic damping and walking dynamics to the residual boney stump of the amputated prosthesis. This can be a critical component of any reconstruction, which will, ideally, restore the role of the skeleton in absorbing the dynamic force of walking.
  • the problem of weight distribution on a reconstructed stump is solved by an implantable force-distribution boot internally fixed to the terminal end of the residual limb bone or bones stump.
  • the boot acts as a hydrodynamic force distributor and effectively replaces the natural hydraulic system of the joints lost with the amputation.
  • Embodiments of the subject invention provide efficient and rapid techniques for harvesting a significant portion of the plantar skin and transplanting the resultant free flap to the terminal end of the residual limb.
  • the harvesting techniques disclosed include procedures for preserving the integrity of the flap vasculature and enervation of the tissue for reimplantation.
  • the next step is fitting and using a prosthetic limb.
  • Embodiments of the subject invention include a prosthetic limb attachment that utilizes ferromagnetic materials, magnets and a controllable electromagnetic mechanism.
  • embodiments include implanted ferromagnetic materials, magnets and/or electromagnetic devices that are fixed to the internal supporting struts that attach the implanted hydrodynamic force-distribution boot to the bone stump. Externally in the prosthesis socket, there can be aligned electromagnets that are controlled by sensor switches that relay on-off signals to the electromagnets during the walking cycle. Further, to reduce or prevent ischemia of tissues, the electromagnetic devices can be regulated by the motion of the residual limb, which causes them to be activated only when needed to support the weight of the prosthesis during the leg swinging motion of walking.
  • Embodiments of the prosthetic limb include proximity sensors located in the heel of the foot portion of the prosthesis.
  • embodiments may not be lifetime devices. It is anticipated that additional unplanned surgeries on the residual limb may be necessary because of complications, discomfort, or unacceptable cosmetic outcomes. These additional surgeries can include implant removal with or without replacement, or they can include other surgical procedures as advancements in the device are made.
  • the modularity provided by embodiments of the subject invention allows certain components to be removed, replaced, or upgraded if necessary. But, the device disclosed herein can provide a patient with a more convenient and comfortable alternative prosthetic that reduces overall stress on the residual limb, as well as the entire body.
  • Figure 1 is an illustration of an embodiment of a femoral subperiosteal strut and above-knee hydraulic dashpot combined to form a modular, implantable force-distribution boot.
  • This illustration shows the force-distribution boot installed on the femur bone of an above-knee-amputation (AKA).
  • AKA above-knee-amputation
  • Figure 2 is an enlarged perspective view of the embodiment of the force-distribution boot installed on the femur bone of an above-knee-amputation (AKA).
  • AKA above-knee-amputation
  • Figure 3 is an enlarged perspective view of an embodiment of the force-distribution boot installed on the femur bone of an above-knee-amputation (AKA), indicating one optional placement of the anchoring screws .
  • AKA above-knee-amputation
  • Figure 4 shows a top view of an embodiment of the hydraulic dashpot. This embodiment has a single socket receiver designed to cooperatively engage with a set-screw.
  • Figure 5A shows a cross-sectional side view of the hydraulic dashpot.
  • Figure 5B shows a cross-section side view of the hydraulic dashpot, wherein the bladder can comprise different materials or one or more materials with different densities.
  • Figure 6 shows a perspective view of an alternative embodiment of the modular, implantable force-distribution boot, wherein the blades are horizontally aligned.
  • Figure 7A, 7B, and 7C show illustrations of embodiments of set-screws.
  • Figure 7A illustrates a set-screw that combines an anchoring screw (proximal end) and external mounting screw (distal end).
  • the set-screw is used to attach the P T/US2012/049263
  • Figure 7B illustrates a set-screw having a collar.
  • Figure 7C illustrates a modified set-screw that can engage with just a set- screw bore.
  • Figure 7D shows an illustration of a spacer according to embodiments of the subject invention.
  • Figure 8 shows a top plan view of an embodiment of a subperiosteal strut with attached blades in a vertical alignment. Also seen in this view is the central set-screw bore.
  • Figure 9A and 9B shows perspective views of embodiments of a subperiosteal strut.
  • Figure 9 A shows a subperiosteal strut with a set-screw bore.
  • Figure 9B shows a subperiosteal strut with external threading on the sleeve.
  • Figure 10 shows a cross-sectional perspective view of an embodiment of a subperiosteal strut with vertically aligned blades.
  • Figure 11 shows a perspective view of an embodiment of a tibial-fibial subperiosteal strut prior to insertion into an embodiment of a below-knee hydraulic dashpot.
  • the below-knee dashpot is designed with a dual socket receiver for cooperatively engaging with the tibial-fibial subperiosteal strut.
  • Figure 12 shows a perspective view of an embodiment of the tibial-fibial subperiosteal strut inserted into a below-knee hydraulic dashpot.
  • Figure 13 is a top plan view of an embodiment of the below-knee dashpot showing a dual socket receiver.
  • Figure 14A, 14B and 14C are top plan views of different embodiments of a tibial- fibial subperiosteal strut.
  • Figure 14A illustrates an embodiment wherein the sockets are bands that surround the terminal ends of the bones.
  • Figure 14B illustrates an embodiment wherein the sockets are cup-like receptacles into which the terminal bones ends are received.
  • Figure 14C illustrates an embodiment wherein the distance between the sockets is adjustable.
  • Figure 15 is a side view of the tibial-fibial subperiosteal strut, with the fibial socket receiver foremost.
  • Figure 16 is a left side perspective view of one embodiment of a prosthetic device with multiple electromagnets within the socket well.
  • the electromagnets are controlled by a switch in the foot of the prosthetic that is wired to the electromagnets.
  • Figure 17 is a cross-sectional, right side elevational view of an embodiment of a prosthetic device showing alternative positions of electromagnets within the socket well.
  • This embodiment is an example of a switch that controls the electromagnets remotely, such as, for example, by radio or sound waves.
  • Figure 18 is a cross-section, front elevational view of a socket well with an inserted residual limb, showing how the blades operably connect to the electromagnets.
  • Figure 19 is a front elevation view of an embodiment having at least two blades surrounding the subperiosteal strut and crossing over one another, to form contiguous overlapping loops around the stanchions.
  • Figure 20 is a photograph showing an example of a plantar surface that can be harvested utilizing the surgical methods disclosed herein.
  • Figure 21 is a photograph showing an example of the dissection plane and demonstrating cut long and short plantar flexor tendons with transition into deep plantar space that provides an avascular plane to the calcaneus. This space can allow for the reflection of the plantar myocutaneous flap inferiorly and can provide an approach and subperiosteal removal of the calcaneus tissue. The only arterial ligation typically needed is the communicating artery that j oins the plantar arch.
  • Figure 22 is a photograph showing a plantar myocutaneous flap based on posterior tibial artery (PTA) with short and long flexor tendons reflected inferiorly protecting the distal branches of the PTA.
  • PTA posterior tibial artery
  • This approach can allow for release of the tendonus origin of the Quadratus and Flexor Digitorum Brevis muscles and quick access to the calcaneus subperiosteal plan. This can also ensure preservation of the internal and external Calcanean Anastomosis.
  • Figure 23 is a photograph showing an example of a plantar myocutaneous flap reflected inferior-posterior demonstrating remaining interosseous, adductor, abductor muscles and deep long plantar ligament of foot, as well as calcaneus after subperiosteal dissection of the flap.
  • the hemostat in the photograph points to the neurovascular pedicle with remaining soft tissue investments. Note cut long flexor tendons.
  • Figure 24 is a photograph showing three examples of vascularized plantar free flaps
  • VPFF VPFF inset into BKA and AKA stumps Left to Right - proximal BKA, distal BKA and distal AKA Plantar heal superior.
  • Figure 25 is a photograph showing an example of a proximal tibial amputation with posterior long flap VPFF inset with plantar heal anterior Long flap bisected and trimmed to allow flap inset (not recommended flap)
  • Figure 26 is a photograph showing an example of a lateral view of distal tibial BKA with VPFF inset with modified fish mouth or bivalve flap.
  • the plantar heal is anterior (Right) with distal plantar skin posterior (Left). Flap provides for anterior skin protection from boney prominence of anterior tibia and glabrous surface for weight bearing in future prosthetic socket pressure.
  • Figure 27 is a photograph showing an example of a fish mouth or bivalve amputation flap for distal AKA.
  • Figure 28 is a photograph showing an example of a distal fish mouth or bivalve AKA flap and an exposed PTA with dissected plantar flap.
  • Figure 29 is a photograph showing an example of an AKA Popliteal vein, artery and tibial nerve - superior to inferior.
  • Figure 30 is a photograph showing an example of a Faux neuroraphy End-to-End (scissors) Faux arterial and venous end-to-side anastomosis (hemostat). It is suggested that identification and preservation of Greater Saphenous Vein be done, so that it can be used as intermediate reducing conduit from femoral artery to PTA for end-to-end anastomosis.
  • Figure 31 is a photograph showing a lateral view of an example of an AKA with VPFF inset into fish mouth or bivalve AKA flap.
  • the plantar heal is superior (indicated by the clamp) and distal plantar skin is posterior (indicated by the scissors).
  • VPFF provides excellent coverage for future prosthetic socket weight bearing area.
  • the subject invention in general pertains to methods and devices for providing an amputee with a prosthetic limb system for comfortable, long-term ambulation. More specifically, the subject invention pertains to one or more embodiment(s) of an implantable prosthetic component, a surgical technique for preparing the residual limb and an external prosthetic limb that works with the implantable component.
  • patient or "amputee” as used herein, describes an animal, including mammals to which the systems and methods of the present invention are applied.
  • Mammalian species that can benefit from the disclosed systems and methods include, but are not limited to, humans, apes, chimpanzees, orangutans, monkeys; domesticated animals (e.g., pets) such as dogs, cats, guinea pigs, hamsters; veterinary uses for large animals such as cattle, horses, goats, sheep; and any wild animal for veterinary or tracking purposes.
  • anchoring screw refers to any device that can be used to secure components of the subject invention to bone or other tissues within the body.
  • Such devices can include, but are not limited to, medullary screws, cortico-medullary screws, intramedullary screws, entramedullary screws, hollow cortical screws, self-tapping screws, non-self tapping screws, compression plate compatible screws and similar devices. It can also include, but is not limited to, adhesives, bone-pastes, tapes or other winding material, or other types of biocompatible substances or devices for attaching components to bone or other tissues.
  • the term “dashpot” or “hydraulic dashpot” as used in the subject application refers to a device that transfers and distributes weight, pressure, force and/or energy over a given area while dampening these motion forces (weight, force, pressure and/or energy) by redistributing these applied forces. By absorbing, redistributing or canceling out this energy a more natural biomechanical interface is established.
  • the hydraulic dashpot as described in the embodiments herein, when installed at the terminal end of an amputated limb, can slow, T U 2012/049263
  • the hydraulic dashpot embodiments of the subject invention can be considered a bio-mechanical device that acts similar to a fluid-filled chamber of a mechanical dashpot, but may experience changes from semisolid to solid as it transitions through its adaptive and absorptive phases.
  • operable communication means that the particular elements are connected in such a way that they cooperate to achieve their intended function or functions.
  • connection or engagement may be direct, or indirect, physical or remote.
  • distal end As used herein, the proximal end is that end nearest the hip joint of an amputee. Conversely, the distal end of the device is that end furthest from the hip joint of an amputee.
  • the embodiments of the subject invention comprise in general a subperiosteal strut 100 and a hydraulic dashpot 200 that can be operatively connected to create an implantable force- distribution boot 10.
  • the force-distribution boot can be operatively engaged with an external prosthetic limb 20.
  • the force-distribution boot and the external prosthetic limb can be operatively engaged by the use of intermittent and/or variable electromagnetic forces created between components on each of these devices.
  • vascularized planter free flap VPFF
  • Embodiments of this procedure include techniques for harvesting a plantar myocutaneous free flap that can be inset into the residual limb terminal end.
  • the disclosed procedures provide a larger durable free flap for greater coverage of the residual limb terminal end and improved vascularization and re- enervation for a sensate transplantation.
  • Figure 1 shows a generalized example attached to the terminal end of an amputated bone.
  • a subperiosteal strut 100 can act as a support structure that engages with the hydraulic dashpot 200, which is distal 600 to the subperiosteal strut.
  • the subperiosteal strut is, in general, a bracket-like structure that can be attached around or to the terminal end of a bone(s) in a residual limb.
  • the residual limb can have a single terminal bone end, such as in the case of an above-knee-amputation (AKA), or two terminal bone ends, such as in the case of a below-knee amputation (BKA).
  • AKA above-knee-amputation
  • BKA below-knee amputation
  • a femoral subperiosteal strut 102 can be utilized.
  • Figures 2, 3, 6, 9A, and 10 illustrate one embodiment of a femoral subperiosteal strut according to the subject invention.
  • a tubular sleeve 105 has a diaphragm 110 disposed therein that separates the interior space of the sleeve into a femur socket 115 that opens at the proximal end 500 and a set-screw bore 120 that opens towards the distal end.
  • the height of the femur socket from the diaphragm to the top of the femur socket wall 116 can vary depending upon numerous factors, such as, for example, the quality and/or stability of the terminal bone end, the material utilized for the sleeve, dimensions of the bone, and other factors that would be understood by a person with skill in the art. Ideally, the height of the femur socket wall is sufficient to provide support to the bone and adequate attachment to the bone.
  • the femur socket can receive the terminal bone end, which can abut the diaphragm and be held in place with one or more, preferably two or more, anchoring screws 700.
  • Anchoring screws and their use in the body are well-known in the art.
  • the femur socket end of the sleeve can have appropriately placed screw holes 750.
  • the anchoring screws are placed substantially opposite each other around the periphery of the femur socket or with maximum available distance there between.
  • Figure 9 illustrates one example of this embodiment.
  • one or more stanchions 125 extend proximally from the femur socket wall 116, such as shown, for example in Figures 2, 3, 9A, and 10.
  • the stanchions can be a separately attached component or be formed as part of the femur socket wall, as shown in the Figure 10.
  • the length of the stanchions can vary, but should be sufficient to provide support and attachment to the bone.
  • a stanchion is a rigid extension or attachment that extends, in general, parallel to the bone. In one embodiment, there is more than one stanchion, each of the same length. In an alternative embodiment, there is more than one stanchion and they have different length(s).
  • a stanchion has a length sufficient to include at least one, preferably two, screw holes. In a further embodiment, a stanchion has a length sufficient to include the anchoring screw hole(s), as well as supports for a blade 800, as shown, for example, on Figures 2, 3, 9A, and 10 and will be discussed in more detail below.
  • stanchions can also be multiple stanchions extending from the femur socket wall. In one embodiment, there is at least one. In a more preferred embodiment, there are at least two stanchions.
  • Figure 9A illustrates an embodiment having four stanchions. A person with skill in the art, having benefit of the subject disclosure, would be able to determine an appropriate number and length for one or more stanchions.
  • the materials that can be utilized for a subperiosteal strut are preferably non-reactive and/or biocompatible materials capable of long-term in vivo use.
  • Such materials can include, by way of non-limiting examples, various types of metals, metal alloys, plastics, ceramics, naturally-derived products, or combinations thereof. More specific examples can include, but are not limited to, titanium, cobalt-chromium-molybdenum alloy, steel, titanium-carbide- coated stainless steel, nylons, polyethylenes, hydroxyapatite (phosphocalcic ceramic), bone fusion matrix materials, or combinations of these or other materials that are suitable for in vivo use.
  • the selection of an appropriate non-reactive and/or biocompatible material is within the competence of those skilled in the art. It is contemplated that such modifications are within the scope of the subject invention.
  • the femoral subperiosteal strut is operably connected to an above-knee hydraulic dashpot 250.
  • the attachment of the above-knee hydraulic dashpot 250 to the femoral subperiosteal strut is accomplished by using a dual-end set-screw 400 between the components, such as the one shown, for example, in Figures 7 A and 7B.
  • a dual-end set-screw can have the same or different diameters on the proximal side 510 and the distal side 610. In one embodiment, the proximal side 510 has a smaller diameter than the distal side 610.
  • the proximal side of the dual-end set-screw is configured with anchoring screw threads such as, for example, intermedullary or intramedullary screw threads 405 and the distal side is configured with machine threads 415.
  • the diaphragm has a set-screw port 112, an example of which is shown in Figures 8, 9A, and 10, to accommodate the dual-end set-screw.
  • the length of the dual -end set-screw and/or either side of the dual-end set-screw can vary depending upon the dimensions of the sleeve and/or the length of the residual bone remaining within the residual limb, as will become apparent below.
  • the dual-end set-screw is placed into the set-screw bore 120, an example of which is shown in Figures 2, 9A, and 10, so that the proximal end of the dual- end set-screw will protrude from the set-screw port 112 in the diaphragm 110 into the socket receiver 115.
  • the set-screw bore 120 has threads complementary to the machine threads 415 on the distal side 610 of the dual-end set-screw, so that the distal side of the dual-end set-screw can be screwed into the set-screw bore, as shown for example in Figure 12.
  • the distal side 610 can be configured to slide into the set-screw bore and can have only partial threading that engages with the set-screw bore, or threading only near the most distal portion that does not engage with the set-screw bore, as shown, for example, in Figure 9A.
  • the depth of the set-screw bore is such that the distal side 610 of the dual-end set-screw 400 will extend beyond the distal end 600 of the tubular sleeve 105. This can provide an external mounting screw portion 420, shown, for example, on Figure 2, extending from the sleeve after the dual set-screw is sufficiently screwed into, slide into, or otherwise, engaged with, the set-screw bore 120.
  • the proximal side of the dual-end set-screw 400 having the intramedullary threads, can be screwed into the terminal end of the residual bone, so that it anchors within the intramedullary space. This can be done simultaneously as the set-screw is being screwed into the set-screw bore. Alternatively, the distal side of the set-screw can be fully or partially engaged with the set-screw bore, then the proximal end of the set-screw, with the attached subperiosteal strut, can be screwed into the intramedullary space.
  • the terminal end of the residual bone and the distal end of the set-screw will abut against their respective sides of the diaphragm 110 to achieve maximum support.
  • this is not a required configuration and in some circumstances may not be possible.
  • spacers or washers 417 known to those with skill in the art, can be utilized between the bone and the diaphragm, such as those shown, for example, in Figure 7C.
  • the subperiosteal strut and the above-knee hydraulic dashpot are coupled utilizing a combined collared set-screw 450, shown, for example, in Figure 7B, and a threaded sleeve 130, shown, for example, in Figure 9B.
  • the collared set- screw can be similar to the dual-end set-screw, in that the proximal side 510 can be configured with intramedullary threads 455 and the distal side 610 can be configured with machine threads 457.
  • Each side of a collared set-screw can have the same or different diameters. In one embodiment, the proximal side 510 and distal side 610 have the same or similar diameter.
  • the length of the collared set-screw and/or either end of the collared set-screw can vary depending upon the dimensions of the sleeve, the thickness of the diaphragm, the length of the residual bone remaining within the residual limb, and other factors known to those with skill in the art.
  • the set-screw port 112 in the diaphragm 110 is threaded.
  • the set- screw port can go through the diaphragm and communicate the socket receiver 115 with the set-screw bore 120.
  • the set-screw port does not go through the diaphragm, but, is a depression or hole 113 that opens into the socket receiver, as illustrated, for example, in Figure 9B.
  • the distal side of the collared set- screw can be coupled with the threaded set-screw port.
  • the collar abuts the diaphragm, when the collared set-screw is fully screwed into the set-screw port.
  • the proximal side of the collared set-screw 450 can be screwed into the terminal end of the residual bone, so that it anchors within the intramedullary space. This can be done simultaneously as the collared set-screw is being screwed into the set-screw port.
  • the distal side of the set-screw can be fully or partially engaged with the set-screw port, then the proximal end of the set-screw, with the attached subperiosteal strut, can be screwed into the intrarmedullary space.
  • the threaded sleeve 150 can be used alone. Particularly if sufficient anchoring screws are utilized to secure the terminal bone end in the femur socket 115 and to the one or more stanchions 125. Ideally, the terminal end of the residual bone will abut against the diaphragm and/or the collar to achieve maximum support. However, this is not a required configuration and in some circumstances may not be possible. If necessary, various spacers or washers, known to those with skill in the art, can be utilized between the bone and the diaphragm, such as, for example, one shown in Figure 7C.
  • the femoral subperiosteal strut can be affixed to the residual bone without the use of a dual-end set-screw or a collared set-screw.
  • the femoral subperiosteal strut can be affixed to the bone by use of only the anchoring screws.
  • An alternative embodiment utilizes a modified set-screw 475, which is similar to a dual-end set-screw, but lacks the proximal end with intramedullary threads and has only the distal end 610 with machine threads, as shown, for example, in Figure 7C.
  • the modified set- screw can engage with the set-screw bore and can negate the necessity for a set-screw port 112.
  • FIGS 11, 12, 14 and 15 illustrate one embodiment of a tibial-fibial subperiosteal strut 150 that can be utilized to stabilize these residual bone ends and attach them to a hydraulic dashpot 200. More specifically, the tibial-fibial subperiosteal strut can be used to attach the terminal bone ends to a below-knee hydraulic dashpot 300.
  • the tibial-fibial subperiosteal strut has a fibial socket 152 and a tibial socket 154.
  • the tibial socket is generally justaposed with the fibial socket.
  • the fibial socket 152 can receive the terminal bone end of the fibia and the tibial socket 154 can receive the terminal bone end of the tibia.
  • these sockets 152, 154 are, in general, bands that surround the terminal bone ends.
  • the sockets 152, 154 are cuplike openings into which the terminal bone ends can be seated against a socket floor 156, an example of which is shown in Figure 14B.
  • the tibia bone has a larger diameter than the fibia bone in human patients and can vary between patients. Therefore, the sizes or diameters of the tibial and fibial sockets can vary depending upon the diameter of these bones in a particular patient. In one embodiment, the tibial socket is larger than the fibial socket.
  • the height 157 of the tibial and/or femoral socket can vary depending upon numerous factors, such as, for example, the quality and/or stability of the terminal bone end, the material utilized for the sockets, dimensions of the bone, and other factors that would be understood by a person with skill in the art.
  • the height of the tibial and femoral socket walls is sufficient to provide support and adequate attachment to the bone.
  • a person with skill in the art, having benefit if the subject disclosure would be able to determine an appropriate height for tibial-fibial subperiosteal strut 150. It is contemplated that such variations, as would be made to the tibial-fibial subperiosteal strut to accommodate specific patients, would not deviate from the scope of the invention.
  • the tibial and fibial sockets are joined together by a support bridge 158, such as shown, for example, in Figures 1 1, 12 and 14.
  • the support bridge can act to connect the tibial and fibial sockets.
  • the support bridge 158 maintains the tibia and fibia at an appropriate distance, after they are inserted into their respective sockets.
  • the length of the support bridge 158, and the distance between the tibial and fibial sockets can vary depending upon a variety of factors that would be understood by a person skilled in the art.
  • the support bridge 158 is a solid, single piece of material fixedly attached between the two sockets.
  • Figures 1 1, 14A and 14B illustrate examples of this embodiment, wherein the tibial and fibial sockets and the support bridge together form a single unified piece.
  • the surgeon would implant a tibial-fibial subperiosteal strut 150 with the appropriate socket dimensions and bridge size to accommodate the particular patient.
  • this embodiment of a tibial-fibial subperiosteal strut provides a solid structure for supporting the terminal bone ends.
  • the distance between the tibia and fibia can or will change over time.
  • Pediatric patients for example, can require adjustment of the tibial- fibial subperiosteal strut as they grow.
  • Other patients can also require adjustment as the residual limb and the terminal bone ends heal or settle into different positions over time. In these situations, it can be beneficial if the tibial-fibial subperiosteal strut can be adjusted.
  • the support bridge 158 is moveably attached to the fibial socket 152 and the tibial socket 154.
  • the support bridge 158 is affixed to one or more fibial socket and tibial socket flanges 159, a non-limiting example of which is shown in Figure 14C.
  • the support bridge 158 and socket flange(s) 159 have holes 161 or slots 162 that can be aligned and adjusted to provide the appropriate distance between the fibial and tibial sockets.
  • any of a variety of fastener types can be used to secure the socket flanges to the support bridge, such as, but not limited to, screws, bolts, rivets, pins, and the like.
  • a person with skill in the art would be able to devise numerous techniques and devices for providing an adjustable support bridge attachable to the tibial and fibial sockets. It is contemplated that such variations can be utilized with the embodiments of the subject invention without departing from the scope of the invention.
  • the tibial-fibial subperiosteal strut 150 can receive the terminal bone ends and be held in place with one or more, preferably two or more, anchoring screws 700.
  • Anchoring screws and their use in the body are well-known in the art.
  • the sockets 152 and 154 can have appropriately placed screw holes 750.
  • the anchoring screws are placed substantially opposite each other around the periphery of each of the sockets.
  • one or more stanchions 125 extend proximally from the socket walls 116.
  • a stanchion is a rigid extension or attachment that extends, in general, parallel to the bone.
  • a stanchion has one or more screw holes 750.
  • the tibia is typically the larger of the two bones in the lower leg. As such, it can be more practical to use that bone for attachment structures, such as, for example, stanchions and one or more anchoring screws, or the like.
  • the fibia could also be utilized.
  • one or more stanchions could extend from the fibial socket wall as well.
  • a stanchion can be a separately attached component, such as shown in Figure 15, or be formed as part of the socket wall, as shown, for example, in the Figure 1 1.
  • the length of a stanchion can vary, but should be sufficient to provide support and attachment to the bone. In one embodiment, there is more than one stanchion, each of the same length.
  • the multiple stanchions can be on the same socket or on different sockets. In an alternative embodiment, there is more than one stanchion and they have different length(s).
  • a stanchion has a length sufficient to include at least one, preferably two, screw holes.
  • a stanchion has a length sufficient to include the anchoring screw hole(s), as well as supports for a blade 800, as shown, for example, on Figures 2, 3, 9, and 10 and discussed in more detail below.
  • the subperiosteal strut 100 is attached to a hydraulic dashpot 200, as shown in Figure 1.
  • the devices and methods of attachment can depend upon which type of subperiosteal strut is utilized.
  • the hydraulic dashpot is designed to replace the natural joint hydraulic system that is lost with an amputation.
  • the purpose of the hydraulic dashpot is to absorb and distribute the forces applied to the residual limb and, more particularly, to the terminal bone ends during ambulation.
  • the fully assembled and implanted force distribution boot 10 is a biocompatible device that effectively replaces the one or more lost joint systems and acts as a hydrodynamic force distributor.
  • a hydraulic dashpot 200 the components of a hydraulic dashpot 200 are, in general, a strut receiver 210 and a bladder 230.
  • the design of the strut receiver can vary depending upon the type of subperiosteal strut to which it will be attached.
  • the strut receiver has one or more openings on the proximal side for receiving a subperiosteal strut and the bladder can be attached so that it extends from the distal end.
  • Figures 4 and 5 illustrate one embodiment of a hydraulic dashpot that can be operably attached to embodiments of a femoral subperiosteal strut 102.
  • the hydraulic dashpot utilizes a femoral strut receiver 252.
  • the femoral strut receiver is a rigid or semi-rigid device into which the external mounting screw portion 420 or the externally threaded sleeve 130, discussed above for the femoral subperiosteal strut, can be attached.
  • the femoral strut receiver is a generally tubular-shaped housing 254 having internal threads 255 compatible with those of the external mounting screw portion 420 and/or the externally threaded sleeve 130.
  • the circumferential shape of the receiver housing 254 is the same as, similar to, or otherwise compatible with the shape of the external mounting screw portion 420 or the externally threaded sleeve 130.
  • the receiver housing is circular.
  • the external mounting screw portion 420 or the externally threaded sleeve 130 of the femoral subperiosteal strut embodiments described above can be screwed into the femoral strut receiver. Once completely screwed into place, it is anticipated that the threading between the components, as well as the surrounding tissues of the residual 12 049263
  • the hydraulic dashpot can be operably attached to embodiments of a subperiosteal strut 102, by use of a dual-strut receiver 302, as example of which is shown in Figures 1 1 and 13.
  • the dual strut receiver is a rigid or semi-rigid device to which the tibial-fibial subperiosteal strut 150 can be attached.
  • the dual strut receiver is a hollow chamber 304 having two socket-like or cup-like seats 305 at either end and a channel 306 there between that communicates the seats 305, providing an approximate "figure-8" shape.
  • the tibial-fibial subperiosteal strut is able to fit within the dual strut receiver, so that the sockets 152 and 154 fit into the respective, and appropriately sized, seats 305 and the support bridge 158 fits within the channel 306.
  • one or more securing set-screws 751 can be used in conjunction with screw holes 750 in the dual- strut receiver, as shown, for example, in Figure 11, to hold the tibial-fibial subperiosteal strut into the dual-strut receiver.
  • the hydraulic features of the force distribution boot 10 are provided by the bladder 230.
  • the bladder can be fixedly attached to at least some portion of, or the entire exterior surface 213 of, a strut receiver 210, so that it can distribute the forces exerted by a strut receiver 210, a subperiosteal strut 100, and the terminal bone end(s).
  • the bladder, and/or the substances therein can be comprised of a solid, semi-solid, liquid, semi-liquid, gel, gas, or combinations thereof.
  • the bladder, or the substances therein comprise a material or materials that can absorb forces exerted by the terminal bone end(s) through a subperiosteal strut and a strut receiver, with minimal shape distortion.
  • the materials utilized in or for the bladder are non-compressible or minimally compressible.
  • the material(s) utilized for the bladder can be inert or otherwise biocompatible and capable of long-term or permanent in vivo use.
  • the bladder 230 is a hollow balloon-like structure having an interior 232 filled with a liquid or semi-liquid material, such as, but not limited to, silicone gel, saline solution, or sterilized water.
  • the bladder is a tough, silicone material that can be filled with an appropriate liquid, semi-liquid, or gel material.
  • the bladder is made of a silicone elastomer that is designed for durability. This specific embodiment can have a thicker outer shell and a silicone barrier material covering the entire surface. The thicker outer shell can enable the bladder to withstand excessive or above-normal forces without failure.
  • the bladder is flexible, but has minimal elasticity and is resistant to puncturing or tearing.
  • the bladder can react to forces by adjusting its shape to allow fluid within the balloon to be redistributed as forces are absorbed.
  • the minimal elasticity of the material of the bladder can ensure that the liquid or semi-liquid material therein is redistributed within the balloon to absorb and redistribute forces, rather than causing an expansion of the bladder material itself.
  • the bladder comprises a sturdy, flexible or elastic material, such as, for example, corrugated materials, woven fiber materials, and elastic materials, or other non-homogeneous materials.
  • the bladder comprises a woven, flexible fiber embedded in a strong, flexible silicone elastomer.
  • This embodiment of an embedded fiber weave can assist in maintaining the shape of the bladder when forces are exerted thereon.
  • the weave direction of the embedded fibers can be diagonal or cross-woven relative to the central axis CA of the force distribution boot. This can also assist is preventing unscrewing of the hydraulic dashpot from the subperiosteal strut.
  • the corrugated material or other bladder material can have an asymmetric thickness.
  • less elastomer and more reinforcing fiber can be utilized in one area of the bladder than in another.
  • the posterior portion can have less reinforcing fiber and more elastomer material and less reinforcing material and more elastomer in the anterior portion, making the anterior portion less flexible and the posterior portion more flexible, but stronger and more durable. Similar techniques can be utilized with other materials utilized for the bladder. This configuration can be advantageous for patients wherein the applied forces are inconsistent or uneven. As forces are applied, the bladder can flex more in the posterior portion, but will expand less, and the anterior portion can expand more, but will have less flexibility.
  • the bladder is a solid material that has sufficient elastic properties to absorb applied forces.
  • the bladder is a homogeneous material that can be compressed and deformed as forces are applied. This can include, by way of non-limiting examples, rubber, silicone, semi-solid gel matrix, foam, or similar materials.
  • the bladder can be solid, non-homogenous material comprising two or more materials. The combined materials can provide elastic properties for absorbing applied forces.
  • the bladder can be a solid of varying density that can have different compressible, non-compressibility and elastic properties at different areas.
  • the bladder can provide increasing resistance as forces applied to the bladder increase.
  • the bladder is a homogeneous material that exhibits gradual, increasing density towards the center. This, there can be an elastic, deformable surface, but an increasingly less elastic and less deformable central core.
  • the bladder is a non-homogeneous solid comprised of two or more materials.
  • the bladder comprises an external material that can provide resistance to normal forces and internal material that provides greater resistance to more extreme forces applied to the bladder. Further alternative embodiments can include successive layers of increasingly resistant materials.
  • the bladder can be a combination of the filled balloon like structure and the solid or semi-solid/variable density embodiments described above.
  • a solid or semi solid/variable density component can be attached to the strut receiver.
  • a balloon like structure can then be attached to the solid or semi-solid/variable density component to form a bladder that more closely mimics the hydraulic function of a natural joint.
  • the bladder 230 is attached to a strut receiver 210.
  • the bladder can include one or more structures, such as, but not limited to, flanges, tabs, hooks, or the like that allow it to be attached to various points on the strut receiver.
  • the bladder includes multiple attachment tabs 235 that are contiguous with and extend therefrom that can be attached to the sides of a strut receiver.
  • the bladder can be attached directly to a strut receiver, such as by various adhesives, heat or cold sealing techniques.
  • Figure 5 illustrates an example of a bladder that has been adhesively attached around a strut receiver.
  • the bladder can be attached to a strut receiver with a clamping ring.
  • the bladder can be wrapped around the strut receiver.
  • that part of the bladder that wraps around a strut receiver has a smaller diameter than a strut receiver, so that it can stretch and be fit over the strut receiver.
  • the position of the bladder can be maintained with the use of one or more clamping rings 237 ( Figure 1 1 ) which are positioned over some portion of the bladder and securely clamps the bladder to the strut mechanism.
  • a strut receiver can have one or more grooves 238 into which the one or more clamping rings can fit to more securely hold the bladder against the strut receiver.
  • the attachment of the bladder to a strut receiver 210 can be achieved by any of a variety of techniques and devices. It would be well within the skill of a person trained in the art, having benefit of the subject disclosure, to determine any of a number of techniques and devices that could be used to permanently or removably attach a bladder to a strut receiver. In either case, it should provide a biocompatible, secure attachment that allows the strut receiver and bladder to operate as necessary. It should be understood, therefore, that such variations in the attachment means are considered to be within the scope of the subject invention.
  • a prosthetic device 20 can be attached to the end of the residual limb.
  • the attaching and securing of a prosthetic device can be accomplished in several ways. Typically, a variety of belts, bands, straps, cuffs, harnesses, sockets, suction sleeves and the like are used to secure a prosthesis against a residual limb. It is important that the prosthesis be attached securely, so there is sufficient control of the prosthesis and ease and range of movement. Further, if the prosthesis is not secure against the residual limb it can cause chafing or abrading of the skin, which can lead to other complications.
  • skeletal extensions such as rods or various mechanisms that protrude from the body.
  • the advantage to these devices is that the prosthetic is attached to the extension and pressure is exerted directly on the bone. This reduces stress on the tissues and often provides very secure attachment of the prosthesis.
  • the disadvantage with most of these systems, however, is that the tissue around the extension exit area may not heal properly or can leave a sinus or other wound opening that is susceptible to infections and other complications.
  • Embodiments of the subject invention include an intermittent and/or variably controlled electromagnetic attachment system, whereby the above-described implantable force distribution boot 10 includes components that allow it to be magnetically attached to an external prosthesis. Additional embodiments reduce ischemia in the tissues and increase the comfort of the patient. These embodiments can also be utilized with an improved surgical technique for preparing the residual limb, which will also be discussed below.
  • a typical electromagnetic system includes an electromagnet and an armature plate.
  • the electromagnet is attached to one device and the armature plate to another device.
  • a current passing through the electromagnet causes it to be attracted to the armature plate, which can hold the two devices together.
  • the two devices can be maintained in a predetermined position. Also, by adjusting the amount of electrical current, the force of attraction between the electromagnet and the armature plate can be controlled.
  • a subperiosteal strut 100 includes one or more blades 800, as shown, for example, in Figures 2, 6 and 8.
  • a blade can act as a specialized, implanted armature plate that can be used in conjunction with an electromagnet associated with an external prosthesis. When the electromagnet is activated by electric current, it is attracted to the one or more blades on the implanted subperiosteal strut. This attractive force holds the prosthesis against the residual limb.
  • a blade is a structure made of one or more biologically compatible magnetically attractable materials.
  • a blade can be covered or sealed in one or more biologically compatible materials that do not affect the overall magnetic properties of the blade.
  • a blade is a biologically compatible ferromagnetic material to which an electromagnet can be attracted. Iron, nickel, and cobalt are non-limiting examples of ferromagnetic materials that can be utilized with the embodiments of the subject invention. Other natural or man-made materials could also be utilized. A person with skill in the art would be able to determine appropriate materials, ferromagnetic or otherwise, that would be suitable for a blade according to the embodiments of the subject invention. Such variations are contemplated to be within the scope of the subject invention.
  • a blade 800 is attached directly to a subperiosteal strut.
  • a blade is attached directly to a stanchion 125 that can be, or is, part of a subperiosteal strut.
  • a blade it can be advantageous for a blade to be permanently attached to a subperiosteal strut and/or a stanchion. In other cases, it can be preferable for a blade to be removably attached, which allows for alteration or replacement if necessary.
  • a blade 800 is attached to a post 805, which is removably or permanently attached to a subperiosteal strut and/or a stanchion.
  • a blade is attached to more than one post.
  • Figures 3, 6, and 9A show examples of an embodiment where a blade is affixed to a stanchion using two posts.
  • the shape of a blade should be such that it is compatible with the normal shape of the residual limb, and should be comfortable and compatible with the internal tissues.
  • the shape of a blade is curved to match the shape of the residual limb and is generally smooth, particularly on the front surface 810.
  • the front surface 810 is a convex shape.
  • Figure 6 illustrates an example of an embodiment where the blades are elongated with a horizontally-aligned curvilinear shape.
  • Figure 9A illustrates an example of an embodiment where the blades are elongated with a vertically-aligned curvilinear shape.
  • Other embodiments include blades that are aligned to one or more angles. In a specific 12 049263
  • At least two blades can surround the subperiosteal strut 100 and cross-over one another, to form contiguous overlapping loops around the stanchions, an example of which is shown in Figure 19. Since the purpose of the one or more blades is to be attracted to one or more electromagnets 815 on or within the prosthesis, it can be beneficial if the blades are aligned appropriately, at whatever angle, to operably and comfortably connect with the electromagnets. Variations in the angle of a blade are considered to be within the scope of the subject invention.
  • a prosthesis 20 is configured with one or more electromagnets, 815 that are on or within, e.g., "on-board" the prosthesis, can be activated to be attracted to the implanted blades.
  • Figure 16 illustrates an embodiment of a prosthetic device 20 fitted with multiple electromagnets 815. To enhance the connectivity between a blade and an electromagnet, it can advantageous for the electromagnets to reside within or otherwise be associated with that part of the prosthesis that would be closest to the blades implanted within the residual limb.
  • Figure 17 illustrates an embodiment where the electromagnets are located within, or are part of, a socket well 25 of a prosthetic device 20.
  • the power source for the electromagnet can be incorporated as part of the prosthesis and can be operably connected by any of a variety of techniques or devices known in the art. Alternatively, the power source could be separate from the prosthesis. It would be well within the skill of a person trained in the art to determine any of a variety of techniques and devices for providing power to the one or more electromagnets incorporated into a prosthesis. Such variations are considered to be within the scope of the subject invention.
  • the electromagnets have a shape that is compatible with the shape of the blades, such that when the blades and the electromagnets come together, the tissue there between is not pinched, cut or otherwise hurt.
  • the electromagnets have a slightly concave shape into which the curvilinear shape of a blade can be fit.
  • Figure 17 illustrates two embodiments wherein the electromagnets are vertically- aligned and/or horizontally-aligned to fit with vertically-aligned or horizontally-aligned blades. As discussed above, the alignment of the electromagnets can vary and it can be most beneficial if the electromagnets are aligned appropriately, at whatever angle, to operably and comfortably connect with the implanted blades.
  • one or more sensors 830 operably connected to the electromagnets, can detect when the prosthesis is in a position where the magnetic force between a blades and an electromagnets can be released without risk of the prosthesis being disengaged from the residual limb.
  • the sensor is a motion- or gravity-activated device, such as, by way of non-limiting examples, a ball-bearing switch, mercury switch, weighted trip-switch and the like operably attached to the electromagnet.
  • the sensor is a motion or proximity activated relay or switch such as, for example, laser activated, infrared activated, radio-wave activated or acoustically activated switches.
  • the senor is a pressure- activated device, such as, by way of non-limiting examples, a push-button, pressure-pad, spring-button, and the like operably attached to the electromagnet.
  • a sensor When a sensor is in the "on" or activated position, the electromagnetic forces are in operation. Likewise, when the sensor is in the "off or deactivated position, the electromagnetic forces cease.
  • an appropriately placed sensor or sensors could detect signals received during walking or other ambulation and the magnetic forces can cycle on and off, independently, in groups, or all together, depending upon the position of the prosthesis, or even the opposite leg.
  • a person with skill in the art, having benefit of the subject disclosure would be able to determine the appropriate placement of a sensor or sensors that can detect specific signals generated by ambulation or other motion to control the electromagnetic forces.
  • one or more sensors 830 can be positioned on or within, i.e., "onboard", the prosthetic device, so that when the prosthetic device is aligned, such that gravity will hold the prosthesis in place against the residual limb, the sensor can cease, or reduce, the flow of electric current.
  • the electric current is reduced or is no longer coursing through the electromagnet at all, the attraction between the blade and the electromagnet is also reduced or ceases entirely, reducing or eliminating pressure on the tissues therebetween, allowing circulation. It can be advantageous if the sensor and/or electromagnet have the ability to be activated and deactivated quickly, so that motion is not restricted due to a delayed response.
  • a prosthetic device is configured with an appropriate sensor that can be activated and deactivated during normal walking motions.
  • the prosthetic device when the prosthetic device is sufficiently vertically-aligned and the foot is against the ground or other surface, the residual limb can rest within and against the bottom of the socket well 25. In this position, gravity can be the sole force holding the prosthesis against the residual limb.
  • the sensor can, therefore, be activated, by whatever means dictated, to turn off the electromagnet and allow perfusion of the tissues.
  • the sensor When the sensor detects a change in the position of the prosthesis, or some part thereof, such as, for example, when the patient resumes or continues the walking motion, when some portion of the prosthesis foot is no longer against the surface, when the opposite leg changes position, when the prosthetic device is no longer vertically-aligned, or when some other pre-defined event occurs, the sensor can immediately detect the change in position and quickly activate the electric current to reactivate the electromagnets.
  • an electromagnet could cycle through being turned on and off multiple times, reducing or eliminating ischemia of the tissues.
  • the electromagnetic forces are applied in variable strength or intermittently to adjust or adapt to the forces and pressures of walking.
  • one or more on-board sensors are utilized with the prosthetic that can sense when the prosthetic is in, or is about to be in, a position where gravity can maintain the position of the prosthetic against the limb.
  • the sensor or sensors such as, for example, a laser-light sensor or radio-wave sensor, will detect the approaching proximity of the surface and can gradually reduce the electrical current through the electromagnet. This allows tissue perfusion to begin.
  • the electromagnetic forces can be completely off or sufficiently reduced that full tissue perfusion can occur.
  • the sensor detects a change in position, such as, for example, the foot being raised from the surface, and the electromagnetic forces are gradually reapplied to ensure that the prosthesis stays firmly attached to the residue limb.
  • the electromagnets can be paired or grouped, so that they cycle through the above-described process in a rotational fashion.
  • a prosthesis can be configured with two or more groups of electromagnets controlled by one or more sensors. During the walking motion, when the sensors detect the various changes described above, each group of electromagnets can be activated or deactivated at opposite times.
  • a first group of electromagnets will remain at full strength, while a second set of electromagnets will be reduced in strength or turned off, allowing tissue perfusion in that area to occur.
  • the first group of electromagnets will be reduced in strength or turned off, allowing tissue perfusion in those areas, while the second set will remain at full strength.
  • prosthetic devices it is not uncommon for prosthetic devices to include various switches, controls or manually operated mechanisms to manipulate the prosthetic device in different situations, such as standing, leaning or sitting.
  • a manual on/off switch for the electromagnets, knee-locking and unlocking mechanisms e.g. , bail-locks, Swiss locks, or French locks
  • other devices can be utilized with the embodiments of the subject invention. It is contemplated that the addition of such devices, where they do not significantly alter the function of the embodiments described herein, are within the scope of the subject invention.
  • the PTA also supplies the medial calcaneus region and has lateral anastomatic connections with the External Calcanean, the terminal branches of the Posterior Peroneal Artery (PPA) through the PTA's Internal Calcanean branches.
  • PPA Posterior Peroneal Artery
  • This artery is typically ligated as it is encountered during the development of the plantar flap, just proximal and between the first and second metacarpal-phalangeal joints.
  • the embodiments disclosed herein demonstrate a feasible Myocutaneous Flap that can be developed using the knowledge of this anatomy.
  • the surgical technique of implanting vascularized plantar glabrous skin free flaps can improve the surgical management of traumatic or elective lower extremity amputations with the goal of preparing an amputee residual limb that is better suited for weight bearing and the activities of daily life. More specifically, the the surgical techniques described herein allow for harvesting of myocutaneous flaps that are different from the traditional amputation flap designs used today (such as skew, sagittal, or long posterior flaps), and provide a Plantar Myocutaneous Free Flap that can be inset within a residual limb terminal end for maximum efficiency and coverage. When utilized in conjunction with embodiments of the herein described implantable prosthetic device, external prosthetics can be used with less discomfort and few complications.
  • the force distribution boot described herein is utilized with the surgical technique of implanting vascularized plantar glabrous skin free flaps over the terminal end of a residual limb.
  • the electromagnetically controlled prosthetic device described herein is utilized with a residual limb that has been prepared by implantation of a vascularized plantar glabrous skin free flap. The utilization of a vascularized plantar glabrous skin free flap can improve the successful use of the force distribution boot and the accompanying electromagnetically controlled external prosthesis.
  • the embodiments disclosed herein were perfected through cadaver dissections of lower extremities, which assisted in the development of an efficient and rapid Plantar Surface Myocutaneous Free Flap harvest technique.
  • the cadaver dissections were preformed in the Psychomotor Surgical Skills Laboratory at the University of Florida, Department of Orthopedics Orthopedic and Rehabilitation Institute in Gainesville, Florida.
  • One complete hip disarticulated extremity and two below the knee disarticulated extremities were used to develop the three flaps.
  • These same specimens were used to create two BKAs and one AKA that the improved plantar flaps were inset on.
  • Standard surgical instruments, sutures and techniques were used to design, dissect and remove the plantar flaps. Therefore, the embodiment disclosed herein will be described with regard to the faux vascular and neuroraphy procedures as performed on cadaverous tissue. It is anticipated these techniques and procedures would be directly applicable to a patient.
  • VPFF Vascularized Plantar Free Flaps
  • Partial lower extremity cadaver legs were used for development of VPFF and creation of BKA or AKA amputations. Dissection of the VPFF was then undertaken on three separate lower extremities as outlined below.
  • the VPFF area to be harvested can be outlined with a standard marking pen.
  • This area can include all the skin of the plantar surface using the lateral-anterior surface of the metatarsals of the great toe and little toe as the lateral edges of the flap.
  • the line of dissection can then continue anterio-plantar to include the plantar tissue just beyond the metatarsal -phalange joint of the plantar surface, joining the medial and lateral lines of dissection.
  • the line of dissection can be carried posterior just inferior to the medial and lateral malleolus of the ankle and joined posterior at the Achilles tendon above its calcaneus insertion and just inferior to the medial and lateral malleolus.
  • PTA Posterior Tibial Artery
  • the first route involves exposure of the PTA by incising the skin just medial to the medial edge of the tibia and identifying the Greater Saphenous Vein (GSV) which was preserved and harvested.
  • GSV Greater Saphenous Vein
  • the plane between the Flexor Digitorum Longus inferior and the Soleus superior can then be identified and using this fascial plane, the posterior neurovascular compartment can be entered, exposing the PTA, veins and nerve.
  • the PTA and Posterior Tibial Nerve can then be used as the plan of dissection, carrying the dissection distally behind the medial malleolus of the ankle.
  • the PTA, PTN and the venea comitantes can be reflected posterior with the developing flap.
  • the entire plantar surface of the foot can then be dissected free by incising through the skin into and below the periosteum of the medial and lateral metatarsals, incising the superficial and deep plantar flexors (Flexor Digitorum Longus and Brevis, Lumbricals, and Flexor Hallucis Longus and Brevis) into the periosteum.
  • the dissection can then be carried along the periosteum and the plane of dissection transitioned into the deep plantar space. This space creates a natural plan of dissection from which to harvest the fully vascularized plantar myocutaneous free flap.
  • the dorsal perforating artery can be ligated proximal to the greater metatarsal-phalange joint as it penetrates dorsally.
  • the flap is developed proximal towards the calcaneus.
  • the short flexors are carried with the flap taking the Quadratus Plantae with the flap, but leaving the lumbricals, interosseous, abductors muscles and the long plantar ligament in place.
  • the PTA is superficial to this plane of dissection and its passage between the Quadratus and the Flexor Digitorum Brevis.
  • the dissection can be carried to and below the periosteum of the calcaneus, using this plane to free the flap from the calcaneus.
  • 34 tendons can then be cut as they rotate behind the ankle into the plantar surface of the foot, protecting the Neurovascular pedicle during these divisions.
  • the dissection can then be carried over to and below the periosteum of the calcaneus where the insertion of the Achilles tendon is then freed and the flap is left tethered to the neurovascular pedicle.
  • the posterior peroneal artery is not dissected although identified laterally ligated at its termination of the external calcanean, which communicates with the internal calcanean of the PTA. ( Figures 19-22)
  • two free microvascular plantar tissue grafts can be dissected free, with little risk to the vascular pedicle, since it is deep to all planes of dissection.
  • the pedicle may be at some risk when freeing the neurovascular pedicle as it passes posterior and deep to the medial malleolus.
  • This free flap can be de-bulked, if desired, of flexor tendons and excess muscle if done carefully without injuring the vascular pedicel distribution.
  • a flap not dissected with this method was a subcutaneous supra-muscular plantar dissection that lacked significant bulk and fibrous tissue such as calcaneus periosteum and flexor tendons and muscles.
  • proximal and distal BKAs Two standard surgical proximal and distal BKAs were created on two separate cadaver legs, with a long posterior flap (that would have traditionally covered the Tibial boney stump).
  • the proximal PTA and Anterior Tibial Artery (ATA) can be also indentified for possible anastomatic vessels along with the PTN.
  • a VPFF can be placed over the exposed surface of the BKA stumps with the neurovascular pedicle matched to its corresponding proximal counterpart with a microvascular anastomosis and tibial nerve neuroraphy completed.
  • the neurovascular pedicle can be positioned to prevent pressure on it that could compromise blood flow during healing.
  • the flaps can then be sutured into position by placing the heel tissue anteriorly and distal plantar skin tissue posteriorly.
  • the long posterior flap can then be modified.
  • the thickest plantar skin is positioned over the anterior boney prominences.
  • an AKA was created on another cadaver leg using a lateral fish mouth flap and the femoral bone cut proximal at the angle of fish mouth flap.
  • the femoral boney stump was covered with the VPFF after the neurovascular attachments were completed.
  • the heal tissue of the VPFF was place anteriorly and distal plantar skin tissue was placed posteriorly with the pedicle carefully protected deep, as the wound was closed.
  • any reference in this specification to "one embodiment,” “an embodiment,” “example embodiment,” “further embodiment,” “alternative embodiment,” etc., is for literary convenience. The implication is that any particular feature, structure, or characteristic described in connection with such an embodiment is included in at least one embodiment of the invention. The appearance of such phrases in various places in the specification does not necessarily refer to the same embodiment. Further, when a particular feature, structure, or characteristic is described in connection with any embodiment, it is submitted that it is within the purview of one skilled in the art to affect such feature, structure, or characteristic in connection with other ones of the embodiments.
  • Weight-bearing plantar reconstruction using versatile medial plantar sensate flap Suk Joon Oha, Mincheol Moona, Jeongho Chaa, Sung Hoon Koha, Chul Hoon Chungb; PJRAS; Volume 64, No. 2, February 2011 ; pp 248-254

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  • Health & Medical Sciences (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Prostheses (AREA)

Abstract

La présente invention concerne, selon divers modes de réalisation, une gaine implantable de répartition des forces dotée d'éléments hydrauliques imitant l'hydraulique naturelle d'une articulation. L'invention concerne, selon d'autres modes de réalisation, une prothèse externe de jambe dotée d'éléments électromagnétiques à fonction intermittente et/ou variable pouvant coopérer avec des lames magnétiques présentes sur la gaine implantable de distribution des forces. Lors de l'utilisation, la prothèse externe de jambe peut être maintenue sur le moignon par une force magnétique s'exerçant entre les lames implantées et les électroaimants externes. L'invention concerne également des techniques chirurgicales permettant de préparer un moignon pour un meilleur accueil d'une prothèse et une meilleure adaptation à celle-ci. Lesdites techniques comprennent une méthode chirurgicale améliorée permettant le recueil d'un lambeau libre de peau glabre et vascularisée.
PCT/US2012/049263 2011-09-20 2012-08-02 Prothèse implantable destinée à répartir le poids sur un membre amputé et son procédé d'utilisation en association avec une prothèse externe Ceased WO2013043264A1 (fr)

Applications Claiming Priority (4)

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US13/237,114 US8882851B2 (en) 2011-09-20 2011-09-20 Implantable prosthetic device for distribution of weight on amputated limb and method of use with an external prosthetic device
US13/237,114 2011-09-20
US201261678197P 2012-08-01 2012-08-01
US61/678,197 2012-08-01

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018227252A1 (fr) * 2017-06-16 2018-12-20 Alfred Health Implant chirurgical pour supporter un dispositif prothétique
CN113288328A (zh) * 2021-06-02 2021-08-24 上海卓昕医疗科技有限公司 截骨手术器械

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5904722A (en) * 1996-06-11 1999-05-18 Caspers; Carl A. Hypobarically-controlled, double-socket artificial limb with mechanical interlock
WO2002026158A2 (fr) * 2000-09-27 2002-04-04 Caspers Schneider Technologies Doublure d'emboiture de membre artificiel
US20040193286A1 (en) * 2003-02-17 2004-09-30 Eska Implants Gmbh & Co. Leg prosthesis
US7302296B1 (en) * 1999-07-06 2007-11-27 Neurostream Technologies, Inc. Electrical stimulation system and methods for treating phantom limb pain and for providing sensory feedback to an amputee from a prosthetic limb
US20100152864A1 (en) * 2008-12-15 2010-06-17 University Of Utah Osseointegrated implant with electrical stimulation
WO2010070614A1 (fr) * 2008-12-19 2010-06-24 Nicola Sturrock Système de raccordement de membre artificiel à un corps

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5904722A (en) * 1996-06-11 1999-05-18 Caspers; Carl A. Hypobarically-controlled, double-socket artificial limb with mechanical interlock
US7302296B1 (en) * 1999-07-06 2007-11-27 Neurostream Technologies, Inc. Electrical stimulation system and methods for treating phantom limb pain and for providing sensory feedback to an amputee from a prosthetic limb
WO2002026158A2 (fr) * 2000-09-27 2002-04-04 Caspers Schneider Technologies Doublure d'emboiture de membre artificiel
US20040193286A1 (en) * 2003-02-17 2004-09-30 Eska Implants Gmbh & Co. Leg prosthesis
US20100152864A1 (en) * 2008-12-15 2010-06-17 University Of Utah Osseointegrated implant with electrical stimulation
WO2010070614A1 (fr) * 2008-12-19 2010-06-24 Nicola Sturrock Système de raccordement de membre artificiel à un corps

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018227252A1 (fr) * 2017-06-16 2018-12-20 Alfred Health Implant chirurgical pour supporter un dispositif prothétique
CN113288328A (zh) * 2021-06-02 2021-08-24 上海卓昕医疗科技有限公司 截骨手术器械

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