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WO1989009036A1 - Prothese de pied - Google Patents

Prothese de pied Download PDF

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Publication number
WO1989009036A1
WO1989009036A1 PCT/US1989/001322 US8901322W WO8909036A1 WO 1989009036 A1 WO1989009036 A1 WO 1989009036A1 US 8901322 W US8901322 W US 8901322W WO 8909036 A1 WO8909036 A1 WO 8909036A1
Authority
WO
WIPO (PCT)
Prior art keywords
keel
prosthetic foot
foot
forefoot
heel
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/US1989/001322
Other languages
English (en)
Inventor
John A. Sabolich
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sabolich Inc
Original Assignee
Sabolich Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Sabolich Inc filed Critical Sabolich Inc
Publication of WO1989009036A1 publication Critical patent/WO1989009036A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

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
    • A61F2/60—Artificial legs or feet or parts thereof
    • A61F2/66—Feet; Ankle joints
    • 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
    • A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30316—The prosthesis having different structural features at different locations within the same prosthesis; Connections between prosthetic parts; Special structural features of bone or joint prostheses not otherwise provided for
    • A61F2002/30329—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2002/30433—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements using additional screws, bolts, dowels, rivets or washers e.g. connecting screws
    • 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
    • A61F2/66—Feet; Ankle joints
    • A61F2002/6614—Feet
    • A61F2002/6657—Feet having a plate-like or strip-like spring element, e.g. an energy-storing cantilever spring keel
    • 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
    • A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2220/0041—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements using additional screws, bolts, dowels or rivets, e.g. connecting screws

Definitions

  • the present invention relates generally to prosthetic devices and in particular to prosthetic feet.
  • U. S. Patent No. 4,721,510 describes a foot comprising a rigid keel clamped to the top of a longer flexible stiffener supported inside a hollow cosmesis.
  • the stiffener has a heel and a toe portion, and the keel also has a heel and a toe portion, each of which is spaced a distance above the corresponding portion of the stiffener.
  • the keel and stiffener are attached to a thickened instep region in the cosmesis by means of an instep reinforcement plate.
  • a prosthetic foot with a monolithic cantilever spring keel is shown in U. S. Patent No. 4,645,509.
  • the keel is C-shaped, the back of the "C” forming a heel transition portion and the bottom of the "C” extending a length into a forefoot portion. Shock absorption results from the vertical compression of the curved heel transition portion.
  • the keel is provided with an integral heel spur which is short spike extending downwardly from the back of the heel transition portion. The stated purpose of the spur is to absorb energy and provide rebound at heel strike.
  • a combination foot and leg prothesis is the subject of U.S. Patent No. 4,547,913.
  • the forefoot portion and the leg portion are integrally formed of a single flat strip of flexible material with a bend at the level of the ankle.
  • a second and separate strip is riveted to the posterior aspect of the first portion to form the heel of the prosthesis.
  • the heel portion is C-shaped with the back of the "C" facing posteriorly.
  • No. 778,732 discloses a foot comprising an integrally formed shock absorber housed in a shell which is filled with foam.
  • the shock absorber has a lower branch, which repeats the curvature of the arch of the human foot, and an upper branch which slidably contacts the upper surface of the lower branch in the area of the metatarsophalangeal joints.
  • the upper branch is supported over the lower branch by a curved transition portion in the heel area. When a load is applied to the foot, the transition portion is compressed verti-cally, and the upper branch slides anteriorly upon the lower branch.
  • the upper and lower branches of the shock absorber function as a leaf spring.
  • most known prosthetic feet lack the flexibility in the heel required for balanced absorption of purely vertical impacts, which occur frequently during athletic activities.
  • most of these devices primarily on vertical compression of a sharp bend, such as a C-shaped heel portion.
  • the rebound resulting from this compression particularly in response to a substan-tially vertical impact, often throws the wearer backwards.
  • a configuration which depends for flexibility upon compression of a sharp bend is more susceptible to breakage.
  • the present invention provides a prosthetic foot having as its primary structural element a single flexible keel with a forefoot portion, an ankle portion and a heel portion.
  • the inferior aspect of the ankle portion defines an arch which expands in response to a load.
  • the forefoot portion is contoured so that the medial side is thicker than the lateral side, and the toe end of the forefoot is biased along the natural toe break line.
  • the upper portion of the ankle portion defines a platform, and the posterior aspect of the ankle portion under the platform and the superior aspect of the heel portion continuous therewith define a concavity.
  • the ankle portion of the keel may be provided with a vertical throughbore for connecting the foot to any of several commercially available leg assemblies in a known manner. Due to the particular design of the present foot, the apex of the keel's arch is anterior to the central axis of the pylon of most leg assemblies. To adjust for this, the central axis of the bore is posterior to the apex of the arch of the keel. In most instances it will be desirable to cover the keel with a flexible cosmetic covering.
  • the preferred covering of this foot is solid except for a cavity disposed under the ankle portion of the keel and extending a distance under the heel and forefoot portions as well. To prevent damage to the inside of the cosmetic covering, the ends of the forefoot and heel portions of the keel may be provided with bumpers.
  • a prosthesis constructed in accordance with the present invention overcomes the aforementioned problems common in prior art devices.
  • the strength and dynamics of this prosthesis are derived mainly from the basic arched configuration of the keel.
  • the arch has long been recognized as the strongest architectural shape.
  • the inherent strength of the arched design permits the keel of the foot to be thinner, and thus lighter and more flexible.
  • the arch operating in concert with the uniquely shaped heel and forefoot portions provides pure balanced vertical shock absorption, most appreciated in running and jumping and the more strenuous athletic movements. Due to the configuration of the ankle portion, with the concavity formed at the point where the heel portion joins the ankle portion, the length and thus the flexibility of the heel portion is increased. Yet, the entire keel fits nicely inside a naturally shaped cosmesis.
  • the forefoot portion of a prosthesis constructed in accordance with this invention will flex as much as 40 to 60 degrees. This configuration also increases the medio-lateral flexibility contributing to eversion and inversion of the foot.
  • the contoured forefoot with its biased toe end shifts medially the longitudinal midline of the wearer's weight distribution. This allows the wearer to walk vigorously and to run with the foot in a more natural toed-out position.
  • the unique design of the cosmetic covering provides the prosthesis with a pleasing appearance without obstructing the dynamic movements of the keel or adding unnecessarily to the weight of the foot. '
  • Figure 1 is a perspective view of a prosthetic foot constructed in accordance with the present invention.
  • the outer contours of the cosmetic covering are shown in phantom.
  • Figure 2 is an elevational view of the medial side of the foot shown in Figure 1.
  • Figure 3 is an elevational view of the lateral side of the foot shown in Figure 1.
  • Figure 4 is a plan view of the foot shown in Figure 1.
  • Figure 5 is a sectional view of the foot connected to a leg assembly.
  • Figure 6 is a sectional view taken along line 6-6 of Figure 5.
  • Figure 7 is a sectional view taken along line 7-7 of Figure 5.
  • Figure 8 is a sectional view taken along line 8-8 of Figure 5.
  • Figure 9 is a side elevational view of another foot constructed in accordance with the present invention.
  • the ends of the heel and forefoot portions of the keel are covered by protective bumpers.
  • Figure 10 is a top plan view of the foot shown in Figure 8.
  • FIGS 11A-11B illustrate schematically the vertical or lift dynamics of the foot of this invention.
  • Figures 12A-12E illustrate schematically the thrust dynamics of the foot during the stance phase of the gait cycle.
  • the foot 10 has as it primary structural element a single arched keel 12 which preferably is contained within a cosmetic covering 14 shown in dot-dash lines in Figures 1-4.
  • the keel 12 is integrally formed of a sturdy but resilient material.
  • the density of the material and the degree of resiliency may vary and should be selected according to the physique and activity level of the intended wearer.
  • a preferred resilient material is a hardened acetal copolymer, such as that marketed under the brand name Celcon by the Celanese Corporation (Westlake, Ohio) . This material has been found to be significantly more flexible than other materials including acetal homopoly ers. In order to achieve the maximum flexibility afforded by the unique configuration of the keel, the more flexible copolymer composition should be used.
  • the method of forming the keel may vary according to the resilient material selected. Where a solid copolymer acetal is used, the keel may be formed by known milling techniques. However, it will be appreciated that suitable polymer compositions are available in liquid form, and that these may be used to form the keel by injection molding procedures.
  • the resilient material is formed .- to provide a keel 12 having a forefoot portion 16 and a heel portion 18 continuous with an ankle portion 20 therebetween.
  • the inferior aspect of the ankle portion 20 defines an arch 22.
  • the keel 12 is integrally formed, that is carved or molded from a single piece of flexible material.
  • the dimensions of the keel 12, including the heel height, may be varied to suit the wearer. Generally, a wider keel will provide better stability for heavier persons and those who enjoy strenuous physical activity. On the other hand, a smaller and narrower keel is best for children, and women may prefer an elevated heel which permits them to wear fashionable high heeled shoes.
  • the arch 22 may be higher or lower to provide more or less flexibility. For example, an unusually heavy individual requires a flatter arch, a so-called "low profile" version. It also will be appreciated a low profile keel may be necessary where the lower leg of the wearer is unusually long.
  • the symmetrical shape of the internal components which form the forefoot of the device causes the foot to fall in an unnaturally straight forward position at midstance.
  • the prosthetic foot of this invention overcomes this problem by providing the forefoot 16 of the keel 12 with an asymmetrical contour. Specifically, referring still to Figure
  • the forefoot portion 16 preferably is contoured so that the medial side 24 (Figure 2) is thicker than the lateral side 26 ( Figure 3) .
  • the effect of this contouring of the forefoot is illustrated in Figure 4.
  • the solid arrow 30 designates the longitudinal midline of weight distribution across the forefoot 16 at midstance.
  • the broken arrow 32 designates the true longitudinal centerline of the forefoot 16. Thus, the load is shifted to the medial side of the forefoot 16.
  • the midline of weight distribution 30 remains generally parallel to the line of progression, while the true longitudinal midline 32 of the foot is at a slight angle to the line of progression in a normal fashion.
  • this prosthesis not only mimics the slightly toed-out position of the human foot during the stance phase, but in effect duplicates the biomechanics of weight distribution in the human foot as well.
  • the toe end 2S preferably is biased so that the medial side 24 is longer than the lateral side 26. In this way, the toe end conforms to the line along which the toes in the natural foot flex relative to the forefoot, referred to as the toe break line. This enhances the toeing out effect caused by the contoured shape of the forefoot 16, described previously.
  • the toe end 28 also may be upturned slightly. This will prevent tearing of the cosmetic covering 14, and also will provide a smoother toe-off.
  • All prosthetic feet must be attached in some manner to the end of the wearer's affected limb. This may be accomplished by using a variety of known leg components, including pylons (these form the lower leg) , ankle and knee joints and sockets. The components which combine to serve as the lower leg portion are referred to herein simply as a "leg assembly”. A prosthetic foot in combination with a leg assembly is referred to herein as a "lower limb prosthesis”.
  • leg assembly 36 which comprises a pylon 38 inside a cosmetic covering 40, to form a complete lower limb prosthesis 42. It will be understood that the foot 10 could be adapted for use with virtually any commercially available leg assembly.
  • the upper portion of the ankle portion 20 preferably defines a platform 44 (see also Figure 1) , which engages the inferior aspect of the leg assembly 36.
  • the periphery of the platform 44 may be shaped to fit within the ankle portion of the cosmetic covering 14.
  • the ankle portion 20 has a bore 46 through which a bolt 48 extends.
  • the threaded end 50 of the bolt 48 threadedly engages the threaded bore 52 in the lower end of the pylon 38.
  • the bore 46 should be positioned in the ankle portion 20 so that the central axis of the bore is disposed slightly posterior to the apex of the arch 22 in the keel 12.
  • the posterior aspect 54 of the ankle portion 20 defines a concavity 56 which is continuous with the inferior aspect 58 of the platform 44 and the superior aspect 60 of the heel portion 18.
  • This configuration increases extends the length of the heel 18 and permits the heel to have a slender shape.
  • the heel portion 18 is deformable along almost its entire length. It will be appreciated that in some instances the throughbore 46 may intersect the concavity 56.
  • the keel can absorb a vertical shock and balance the impact therefrom between the heel 18 and forefoot 16.
  • the arch 22 expands evenly and without throwing or tipping the wearer anteriorly or posteriorly.
  • the covering 14 preferably consists of self-skinning polyurethane foam composition which when cured retains a soft, flesh- like consistency and color.
  • the covering 14 is solid with an outer shape resembling a natural foot and an upper surface 62 at the level of the ankle and flush with the platform 44 of the keel 12 for close engagement with the inferior aspect of the leg assembly 36.
  • the covering 14 conforms closely to the keel 12 except for a cavity 64 immediately beneath the arch 22 of the ankle portion 20.
  • the cavity 48 extends a distance under the forefoot and heel portions 16 and 18 of the keel 12.
  • the cavity 64 reduces the weight of the foot 10 and prevents the covering 14 from interfering with the flexibility of the keel 12.
  • the cavity 64 may be formed at the time the cosmetic covering 14 is formed by employing the so-called "void wax” technique.
  • a wedge of wax in the shape of the desired cavity is applied to the underside of the arch of the keel before the foam is applied.
  • a bore 66 is drilled through the foot.
  • the wax is melted and drained out of the foot 10 through the bore 66.
  • the bore 66 then permits the bolt 48 to be inserted into the keel 12, as described above.
  • friction patches 68 and 70 may be placed immediately beneath the pressure points between the keel 12 and the cosmetic covering 14, namely under the toe end 28 of the forefoot portion 16 -and beneath the heel portion 18. These patches most conveniently can be applied, by gluing or the like, prior to application of the cosmetic covering 14.
  • the patches preferably are made of a sturdy fabric, such as polyethylene terephthalate cloth, laminated with a resin, such as urethane.
  • the patches 68 and 70 will reduce wear on the covering and thus prolong the life of the foot 10.
  • the foot 72 comprises a keel 74 with a cosmetic covering 76 provided as described above.
  • each of the toe end 78 of the forefoot portion 80 and the heel portion 82 is provided with a flexible, bulbous tip or bumper 84 and 86, respectively.
  • the bumpers 84 and 86 preferably are formed of a foam of greater density than the covering 76.
  • Figure 11A depicts the keel in a relaxed or static position.
  • Figure 11B depicts the arch of the keel in response to a load or sudden impact.
  • the arch of the keel expands as shown in Figure 11B, and absorbs the shock of impact.
  • the arch of the keel springs back returning the keel to the shape shown in Figure 11A. Because of the flexibility of the heel and the forefoot portion, the keel remains relatively level during this motion.
  • Figures 12A through 12E depict the forward motion or thrust dynamics of the prosthetic foot of this invention during the stance phase of the gait cycle.
  • Figure 12A depicts heel strike, the first of the stance phases. This is the point immediately following the swing phase (not shown) at which the heel touches down and just prior to weight being shifted from the other foot to the prosthesis.
  • the heel portion of the keel flexes, as shown in Figure 12B.
  • the heel provides controlled movement of the foot from heel strike to midstance and eliminates the slapping effect sometimes experienced in prostheses with less resilience in the heel. Accordingly, the flexibility of the heel portion in this foot substitutes for the anterior muscles of the lower leg.
  • the present invention provides a prosthetic foot having unique shock absorbing characteristics. Because of its shape and flexibility, all of the directional components of a single stride, from heel strike to toe-off are progressively absorbed by this foot as each portion of the keel is deformed and then rebounds to its original shape in a single, sustained and fluid movement. Similarly, purely vertical shocks are absorbed by balanced expansion of the arch. The positive energy produced by the rebound action actively participates in the mechanics of walking and running throughout the stance phase. Further, because of its simple construction, this lightweight and sturdy prosthesis can be produced economically and requires virtually no maintenance or repair.

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  • Health & Medical Sciences (AREA)
  • Transplantation (AREA)
  • Biomedical Technology (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Orthopedic Medicine & Surgery (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)
  • Prostheses (AREA)

Abstract

La prothèse de pied décrite (10) comprend une quille flexible formée solidaire (12) placée de préférence dans une enveloppe cosmétique. La quille (12) comporte une partie d'avant-pied (16) et une partie de talon (18) jointe par une partie de cheville (20). La section inférieure de la partie de cheville (20) définit une voûte (22) qui se dilate en réponse à une charge et la section supérieure de la partie de cheville (20) forme une plate-forme (44) s'engageant dans une unité de jambe utilisée traditionnellement (36). La partie d'avant-pied est profilée, avec une épaisseur plus large sur la face médiane (24) que sur la face latérale (26) ce qui déplace la bissectrice (30) de répartition du poids dans la partie d'avant-pied (16) vers le centre. On obtient ainsi un alignement plus naturel du pied pendant le cycle des mouvements de la marche. L'extrémité (28) de la partie d'avant-pied (16) qui correspond aux orteils est inclinée le long de la ligne de rupture des orteils naturels. La section postérieure (54) de la partie de cheville (20) définit une concavité (56) sous la plate-forme (44) en continu avec la section supérieure (60) de la partie de talon (18), ce qui accroît la longueur du talon et augmente ainsi sa flexibilité et sa capacité d'absorption des chocs. L'enveloppe cosmétique (14) est pleine à l'exception d'une cavité (64) située sous la voûte.
PCT/US1989/001322 1988-03-31 1989-03-30 Prothese de pied Ceased WO1989009036A1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US17630088A 1988-03-31 1988-03-31
US176,300 1988-03-31
US21775888A 1988-07-11 1988-07-11
US217,758 1988-07-11

Publications (1)

Publication Number Publication Date
WO1989009036A1 true WO1989009036A1 (fr) 1989-10-05

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Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1989/001322 Ceased WO1989009036A1 (fr) 1988-03-31 1989-03-30 Prothese de pied

Country Status (2)

Country Link
AU (1) AU3424489A (fr)
WO (1) WO1989009036A1 (fr)

Cited By (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5037444A (en) * 1989-01-05 1991-08-06 Phillips L Van Prosthetic foot
FR2661087A1 (fr) * 1990-04-23 1991-10-25 Proteor Sa Prothese a ossature monobloc pour amputation de la jambe et procede de fabrication de cette prothese.
US5066305A (en) * 1988-10-25 1991-11-19 Model & Instrument Development Corporation Prosthetic foot having a low profile cantilever spring keel
US5116385A (en) * 1991-05-06 1992-05-26 Universite De Montreal Medio-lateral control enhancing, cantilever-spring type prosthetic foot
FR2685194A1 (fr) * 1992-03-20 1993-06-25 Phillips Van Lehn Prothese de pied.
US5258039A (en) * 1991-11-15 1993-11-02 The National University Of Singapore Energy storing composite prosthetic foot
US5290319A (en) * 1991-02-28 1994-03-01 Phillips L Van Prosthetic foot incorporating adjustable bladders
FR2698538A1 (fr) * 1992-11-27 1994-06-03 Proteor Sa Nouvelle structure de pied prothétique à restitution d'énergie.
US5387246A (en) * 1989-04-13 1995-02-07 Phillips; Van L. Prosthetic ski leg
US6406500B1 (en) * 1989-04-13 2002-06-18 Van L. Phillips Foot prosthesis having curved forefoot
US6936074B2 (en) 2000-12-22 2005-08-30 Barry W. Townsend Prosthetic foot
US7108723B2 (en) 2000-12-22 2006-09-19 Townsend Barry W Prosthetic foot
WO2023237994A1 (fr) * 2022-06-06 2023-12-14 Össur Iceland Ehf Ensemble protège-pied pour pied prothétique

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AU629922B2 (en) * 1988-10-25 1992-10-15 Seattle Orthopedic Group, Inc. Prosthetic foot having a low profile cantilever spring keel

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE295807C (fr) *
US2075583A (en) * 1935-08-31 1937-03-30 Lange Gottlieb Foot for artificial limbs
US2440075A (en) * 1946-04-24 1948-04-20 Campbell Edwards Pneumatic Art Ankle joint and reinforcing member for pneumatic feet
DE883321C (de) * 1951-06-17 1953-07-16 Walter Dr Wisbrun Beinprothese
GB1371996A (en) * 1973-05-08 1974-10-30 Blatchford & Sons Ltd Artificial leg and foot assembly
US4547913A (en) * 1983-07-11 1985-10-22 Flex Foot, Inc. Composite prosthetic foot and leg
US4645509A (en) * 1984-06-11 1987-02-24 Model & Instrument Development Corporation Prosthetic foot having a cantilever spring keel
EP0234886A1 (fr) * 1986-02-28 1987-09-02 J.E. HANGER & COMPANY LIMITED Pied prothétique

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE295807C (fr) *
US2075583A (en) * 1935-08-31 1937-03-30 Lange Gottlieb Foot for artificial limbs
US2440075A (en) * 1946-04-24 1948-04-20 Campbell Edwards Pneumatic Art Ankle joint and reinforcing member for pneumatic feet
DE883321C (de) * 1951-06-17 1953-07-16 Walter Dr Wisbrun Beinprothese
GB1371996A (en) * 1973-05-08 1974-10-30 Blatchford & Sons Ltd Artificial leg and foot assembly
US4547913A (en) * 1983-07-11 1985-10-22 Flex Foot, Inc. Composite prosthetic foot and leg
US4645509A (en) * 1984-06-11 1987-02-24 Model & Instrument Development Corporation Prosthetic foot having a cantilever spring keel
EP0234886A1 (fr) * 1986-02-28 1987-09-02 J.E. HANGER & COMPANY LIMITED Pied prothétique

Cited By (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5066305A (en) * 1988-10-25 1991-11-19 Model & Instrument Development Corporation Prosthetic foot having a low profile cantilever spring keel
US5037444A (en) * 1989-01-05 1991-08-06 Phillips L Van Prosthetic foot
US5387246A (en) * 1989-04-13 1995-02-07 Phillips; Van L. Prosthetic ski leg
US6406500B1 (en) * 1989-04-13 2002-06-18 Van L. Phillips Foot prosthesis having curved forefoot
EP0454524A1 (fr) * 1990-04-23 1991-10-30 Etablissements Proteor Prothèse de jambe à ossature monobloc et son procédé de fabrication
FR2661087A1 (fr) * 1990-04-23 1991-10-25 Proteor Sa Prothese a ossature monobloc pour amputation de la jambe et procede de fabrication de cette prothese.
US5290319A (en) * 1991-02-28 1994-03-01 Phillips L Van Prosthetic foot incorporating adjustable bladders
US5116385A (en) * 1991-05-06 1992-05-26 Universite De Montreal Medio-lateral control enhancing, cantilever-spring type prosthetic foot
US5258039A (en) * 1991-11-15 1993-11-02 The National University Of Singapore Energy storing composite prosthetic foot
FR2685194A1 (fr) * 1992-03-20 1993-06-25 Phillips Van Lehn Prothese de pied.
FR2698538A1 (fr) * 1992-11-27 1994-06-03 Proteor Sa Nouvelle structure de pied prothétique à restitution d'énergie.
US6936074B2 (en) 2000-12-22 2005-08-30 Barry W. Townsend Prosthetic foot
US7108723B2 (en) 2000-12-22 2006-09-19 Townsend Barry W Prosthetic foot
WO2023237994A1 (fr) * 2022-06-06 2023-12-14 Össur Iceland Ehf Ensemble protège-pied pour pied prothétique

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