Source: https://patents.google.com/patent/US7112227B2/en
Timestamp: 2019-06-16 19:35:02
Document Index: 177058614

Matched Legal Cases: ['art 134', 'art 134', 'art 134', 'art 184', 'art 184', 'art 234', 'art 234', 'art 234']

US7112227B2 - Multi-axis prosthetic ankle joint - Google Patents
US7112227B2
US7112227B2 US10/770,833 US77083304A US7112227B2 US 7112227 B2 US7112227 B2 US 7112227B2 US 77083304 A US77083304 A US 77083304A US 7112227 B2 US7112227 B2 US 7112227B2
US10/770,833
US20050015157A1 (en
2001-06-29 Priority to US09/893,887 priority Critical patent/US6699295B2/en
2004-02-03 Application filed by Ohio Willow Wood Co filed Critical Ohio Willow Wood Co
2004-02-03 Priority to US10/770,833 priority patent/US7112227B2/en
2004-10-06 Assigned to OHIO WILLOW WOOD COMPANY reassignment OHIO WILLOW WOOD COMPANY ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: ARBOGAST, ROBERT E., CAPPER, JAMES W., COLVIN, JAMES M., DODDROE, JEFFREY L.
2005-01-20 Publication of US20050015157A1 publication Critical patent/US20050015157A1/en
2005-02-03 Priority claimed from GB0814134A external-priority patent/GB2449007B/en
2005-04-15 Assigned to THE OHIO WILLOW WOOD COMPANY reassignment THE OHIO WILLOW WOOD COMPANY CORRECTIVE ASSIGNMENT TO CORRECT THE TO REMOVE THE NAME OF AN INCORRECTLY LISTED ASSIGNOR, JAMES W. CAPPER, AND INSERT THE CORRECT ASSIGNOR, CHI L. LEE PREVIOUSLY RECORDED ON REEL 015871 FRAME 0713. ASSIGNOR(S) HEREBY CONFIRMS THE JEFFREY L. DODDROE, ROBERT E. ARBOGAST, JAMES M. COLVIN, AND JAMES W. CAPPER TO OHIO WILLOW WOOD COMPANY. Assignors: ARBOGAST, ROBERT E., COLVIN, JAMES M., DODDROE, JEFFREY L., LEE, CHI L.
2006-06-01 Priority claimed from US11/421,595 external-priority patent/US7563288B2/en
2006-09-26 Publication of US7112227B2 publication Critical patent/US7112227B2/en
2006-12-20 Priority claimed from US11/613,843 external-priority patent/US7833287B2/en
A multi-axis prosthetic ankle for connection of a prosthetic lower leg to a prosthetic foot. In one embodiment, a prosthetic foot connection component is connected to a prosthetic lower leg connection component only by means of an elastomeric material, thereby allowing for multi-axis movement of the ankle without requiring direct contact between the two components. In other embodiments of the ankle, a prosthetic foot connection component may be mechanically connected to a prosthetic lower leg connection component. However, the design of the mechanical connection and the use of an elastomeric material casing allows for movement of the ankle without surface-to-surface sliding contact between the two components. Compression of the elastomeric material, as well as one or more mechanical stops may be used to control and limit movement of the ankle.
This application is a continuation-in-part of U.S. patent application Ser. No. 09/893,887 Now U.S. Pat. No. 6,699,295, which was filed on Jun. 29, 2001.
The present invention relates generally to prosthetic devices, and more particularly to multi-axis prosthetic ankle joints.
As force is applied to either of these ankles, the ankle 5 moves in rotation and translation with a fluid motion by deforming the elastomeric medium. According to a further feature of the invention, at least one mechanical stop may also be positioned on/in either of these multi-axis ankle embodiments to prevent the relative angular movement of the ankles from deforming the elastomeric material beyond the elastic limit thereof. Since the deformation of the elastomeric material in both multi-axis ankle embodiments is thus always kept within the elastic limit, any tendency toward breakdown of the elastomeric material is further reduced.
FIG. 6 is a front elevation view of a bracket for mounting to the lower leg connection component of FIGS. 4–5;
FIG. 8 is a sectional front elevation view of the multi-axis prosthetic ankle of FIG. 1, taken along lines A—A of FIG. 7;
FIG. 9 is a sectional isometric view of the multi-axis prosthetic ankle of FIG. 1, taken along lines B—B of FIG. 1;
FIG. 19 is a sectional side elevation view of the multi-axis prosthetic ankle of FIG. 10, taken along lines C—C thereof;
FIG. 30 is a sectional side elevation view of the multi-axis prosthetic ankle of FIG. 21, taken along lines D—D thereof;
FIG. 40 is a sectional side elevation view of the multi-axis prosthetic ankle of FIG. 31, taken along lines E–E thereof;
FIG. 41 b shows the multi-axis prosthetic ankle of FIG. 32 in a heel strike position; and
FIG. 41 c shows the multi-axis prosthetic ankle of FIG. 32 in a toe-off position.
A first exemplary embodiment of a multi-axis prosthetic ankle according to the present invention can be observed by reference to FIGS. 1–9. As can be seen, particularly with respect to FIGS. 2–3, for clarity of illustration the elastomeric casing is shown in phantom lines, thereby revealing the encased components of the mechanical device (rigid mechanical means). In this particular embodiment, the main components of the multi-axis prosthetic ankle 5 are the bottom component 10, the lower leg connection component 20, the mechanical device 30 (rigid mechanical means), and the elastomeric casing 40, which is bonded to the bottom component and the lower leg connection component and floatingly encases the elements of the mechanical device.
During assembly of the multi-axis prosthetic ankle, the second bracket 31 is interlockingly positioned within the slot like aperture 16 of the first bracket 14 to form the mechanical device 30, after which the second bracket 31 is bolted to the lower surface of the base 22 of the lower leg connection component 20 via the bolts 32 and the optional shim 38. At this time, a shim 38 of a proper thickness is selected on the basis described below, and is positioned between the end of the shorter one of the legs of the second bracket 31 and the lower surface of the base 22. As will be readily understood by those skilled in the art, the shim has a through hole for the bolt 32, and the legs 31 a and 31 b of the second bracket 31 have respective threaded through holes 31 c and 31 d. The resulting assembly is generally shown in FIGS. 1–3.
Internal/External rotation: 15°/15° (30° total).
Plantar flexion: 15°.
Dorsi flexion: 15°.
Inversion/Eversion: 10°/10° (20° total).
An alternate embodiment of a multi-axis prosthetic ankle 100 of the present invention is depicted in FIGS. 10–20. This particular embodiment of the multi-axis prosthetic ankle 100 is well suited to use with a low-profile prosthetic foot, such as a prosthetic foot that may be used by an amputee having a long residual limb.
The multi-axis prosthetic ankle 100 can be seen to include a bottom, prosthetic foot connection component 110, that is adapted for attachment to a prosthetic foot, and a lower leg connection component 130 that is adapted to attach the ankle to a prosthetic socket component.
This particular embodiment of the lower leg connection component 130 is shown to have a generally circular, disk-like base 132, although other shapes are also possible. A pyramid part 134 may be affixed/integral to the base and may project upward from a central dome-like portion thereof. The pyramid part 134 can be used to connect the ankle 100 to the prosthetic socket component. The pyramid part 134 may be of a generally conventional design.
Once the above-described assembly and molding process is accomplished, the completed multi-axis ankle assembly 100 can be attached to a prosthetic socket and prosthetic foot.
As can be seen in the sectional view of FIG. 20, a reinforcing material 124 can be installed to the top surface 120 of the prosthetic foot connection component 110. Alternatively, the reinforcing material 124 may be installed to the top surface of the dorsi-flexion stop 136. The reinforcing material 124 acts to protect the elastomeric material from erosion due to contact with the moving base 132 of the lower leg connection component 130. The reinforcing material 124 may be, for example, a section of Kevlar® mat, or a may be comprised of another similarly abrasion resistant material, or combination of materials.
Internal/External rotation: 18°/18° (36° total).
Dorsi flexion: 5°.
Inversion/Eversion: 5°/5° (10° total).
As can be understood from a reading of the above description and reference to the drawing figures related to the ankles 5, 100, during walking, relative motion (translation and multi-axis rotation) between the component 10, 110 mounted to the prosthetic foot, and the component 20, 130 mounted to the prosthetic socket is permitted by the elastic deformation of the elastomeric material. The motion is thus polycentric and multi-axial, with no fixed center of rotation or translation. Moreover, surface-to-surface contact that could lead to a breakdown of the material used to manufacture the rigid components of each ankle 5, 100 has been eliminated. For example, even the small gap between the ledge 144 and the stop 126 is preferably filled with elastomeric material. In addition to allowing relative motion (translation and multi-axis rotation) between the component 10, 110 mounted to the prosthetic foot and the component 20, 130 mounted to the prosthetic socket, the elastomeric material also absorbs impact energies and, therefore, further acts as a vibration dampening device.
Variations of yet another embodiment of a multi-axis prosthetic ankle 150, 200 of the present invention are illustrated in FIGS. 21–30 and 31–41, respectively. Unlike the previously-described prosthetic ankles 5, 100, these embodiments of the multi-axis prosthetic ankle 150, 200 employ a direct mechanical connection between components thereof.
The multi-axis prosthetic ankle 150 of FIGS. 21–30 can be seen to include a bottom, prosthetic foot connection component 160, that is adapted for attachment to a prosthetic foot, and a lower leg connection component 180 that is adapted to attach the ankle 150 to a prosthetic socket component.
As can best be observed in FIGS. 27–29, this embodiment of the lower leg connection component 180 may have a generally circular, disk-like base 182—although other shapes are also possible. A pyramid part 184 may project upward from a central dome-like portion of the base. The pyramid part 184 may be of a generally conventional design.
Once the above-described assembly and molding process is accomplished, the completed multi-axis ankle assembly 150 can be attached to a prosthetic socket and prosthetic foot in a conventional manner.
Internal/External rotation: 5°/5° (10° total).
Plantar flexion: 13°.
Dorsi flexion: 4°.
Inversion/Eversion: 8°.
Like the multi-axis prosthetic ankle 150 of FIGS. 21–30, the multi-axis prosthetic ankle 200 of FIGS. 31–41 can be seen to include a bottom, prosthetic foot connection component 210 that is adapted for attachment to a prosthetic foot, and a lower leg connection component 230 that is adapted to attach the ankle 200 to a prosthetic socket component.
The prosthetic foot connection component 210 is essentially formed in a like manner to the prosthetic foot connection component 160 of the ankle 150 of FIGS. 21–30: with a pair of spaced apart and upwardly-extending support arms 214, having one end thereof attached to a base 212. The base 212 and the pair of support arms 214 again combine to form a mounting bracket for attaching the ankle 200 to a prosthetic foot, and for pivotally retaining the lower leg connection component 230. A space 220 is formed between the support arms 214 for receiving a connecting projection 240 of the lower leg connection component 230. A retaining pin receiving aperture 216 is located in each of the upwardly-extending support arms 214. As can be best observed in FIGS. 33 and 36, a flexion limiting aperture 218 is also located in each of the upwardly-extending support arms 214. A threaded or unthreaded bore(s) 222 may be located in the base 212 to facilitate attachment of the ankle to a prosthetic foot.
This embodiment of the lower leg connection component 230 may also have a generally circular, disk-like base 232, although other shapes are also possible. The base 232 may have a pyramid part 234 projecting upward from a dome-like central portion thereof. The pyramid part 234 can be used to connect the ankle 200 to the prosthetic socket component. The pyramid part 234 may be of a generally conventional design.
The ankle 200 shown in FIGS. 31–41 is assembled in substantially the same manner as the ankle 150 shown in FIGS. 21–30. The primary difference between the two ankles is that a flexion limiting pin 246 is installed to the connecting projection 240 of this embodiment of the ankle 200, as opposed to installation of a flexion limiting pin 172 to the slot 168 in the support arms 164 of the previously described ankle 150. Hence, once the prosthetic foot connection component 210 and the lower leg connection component 230 of the ankle 200 have been connected using the retaining pin 198, the flexion limiting pin 246 is passed through the flexion limiting aperture 218 in one of the support arms 214 and installed to the pin receiving aperture 244 in the connecting projection 240. Preferably, the flexion limiting pin 246 is retained by the connecting projection 240 in a position such that each end of the pin resides at least partially within a corresponding one of the flexion limiting apertures 218. Preferably, the flexion limiting pin 246 is force or press fit to the pin receiving aperture 244 so that it cannot be easily dislodged.
In a neutral (midstance) position of this embodiment of the assembled ankle 200, the base 232 of the lower leg connection component 230 is substantially level, and the ends of the flexion limiting pin 246 reside within the flexion limiting apertures 218 in corresponding support arms 214. The neutral position of the assembled ankle 200 can best be observed by reference to FIGS. 33, 40 and 41 a.
Subsequent to coupling of the prosthetic foot connection component 210 to the lower leg connection component 230, and installation of the flexion limiting pin 246, the assembly of components is placed within a mold (not shown). The mold is preferably adapted to maintain the components in the neutral position shown in FIGS. 33, 40 and 41 a, and described above. With the components held in this position, an elastomeric material in a flowable state is injected or otherwise introduced into the mold and permitted to harden. The elastomeric material is preferably a rubber, and more preferably a thermoset rubber polymer having a high resistance and memory under cyclical loading. Non-limiting examples include butyl rubber, ethylene-propylene rubber, neoprene rubber, nitrile rubber, polybutadiene rubber, polyisoprene rubber, stereo rubber, styrene-butadiene rubber, natural rubber, or a combination of two or more of these rubbers. It is also possible to mold the components while they are maintained in a flexed state. More specifically, the components may be molded in a position such that the resulting ankle will have a raised heel when in its neutral position. Such an ankle may be particularly appropriate for use with boots, high heel shoes, and other footwear having a similar forward slope.
Once the above-described assembly and molding process is accomplished, the completed multi-axis ankle assembly 200 can be attached to a prosthetic socket and prosthetic foot in a conventional manner.
In this embodiment of the ankle 200, the limit of both dorsi-flexion and plantar-flexion is further controlled by the size and location of the flexion limiting aperture 218 in the support arms 214. As can be best understood by reference to FIGS. 33, 40, and 41 a–41 c, a flexion limiting aperture 218 of smaller diameter would allow for less total dorsi/plantar-flexion, while a flexion limiting aperture 218 of greater diameter would allow for more total dorsi/plantar flexion. Additionally, each of dorsi-flexion and plantar-flexion can be allocated a different percentage of the total available movement in such direction. For example, when the center of each flexion limiting aperture 218 is located at the mid-line of the support arms 214 (i.e., substantially in line with the center of the retaining pin 198), the amount of dorsi-flexion and plantar-flexion will be essentially equal. By shifting the center of the flexion limiting apertures 218 toward the anterior or posterior of the ankle 200, however, the amount of dorsi-flexion and plantar-flexion can be made to be unequal. For example, as shown in FIGS. 41 a–41 c, the flexion limiting apertures 218 are shifted slightly anterior to the midline of the ankle 200, which results in a total amount of possible plantar-flexion that is greater than the total possible amount of dorsi-flexion. As shown in FIGS. 41 a–41 c, the diameter and location of the flexion limiting apertures 218 of this particular embodiment of the ankle 200 provides for approximately 12 degrees of maximum flexion at heel strike and approximately 3 degrees of maximum flexion at toe off, for a total of 15 degrees of total movement in the dorsi/plantar-flexion plane. Therefore, as can be understood, greater or lesser amounts of dorsi-flexion and/or plantar-flexion are possible by altering the diameter and/or location of the flexion limiting apertures 218. It should also be understood that a similar adjustment to dorsi-flexion and/or plantar-flexion can be achieved by manipulating the size and/or location of the flexion limiting pin 246, instead of the flexion limiting apertures 218. Alternatively, an adjustment to the size and/or location of both the flexion limiting apertures 218 and the flexion limiting pin 246 can also be made for this purpose.
1. A multi-axis prosthetic ankle, comprising:
a prosthetic foot connection component having a pair of spaced apart and upwardly extending support arms connected to a base;
a lower leg connection component having a base, an upwardly extending prosthetic leg connection portion, and a downwardly extending connecting projection that substantially resides within a space between said support arms;
a retaining pin;
a flexion limiting means; and
wherein said prosthetic foot connection component and said lower leg connection component are pivotally connected by passing said retaining pin through apertures in said support arms and said connecting projection; and
wherein, after said prosthetic foot connection component and said lower leg connection component have been pivotally connected, said elastomeric material is made to substantially encase all components residing between said base of said prosthetic foot connection component and said base of said lower leg connection component.
2. The multi-axis prosthetic ankle of claim 1, wherein said flexion limiting means comprises a flexion limiting aperture located in each of said support arms and a flexion limiting pin installed to said connecting projection, at least one end of said flexion limiting pin residing in a corresponding one of said flexion limiting apertures so as to limit plantar-flexion and dorsi-flexion of said ankle.
3. The multi-axis prosthetic ankle of claim 1, wherein the combination of said flexion limiting pin and said flexion limiting aperture also provides for a mechanical limit to internal/external rotation, and inversion/eversion movement of said ankle.
4. The multi-axis prosthetic ankle of claim 1, wherein compression of said elastomeric material by said flexion limiting pin acts as a damper to plantar-flexion and dorsi-flexion of said ankle.
5. The multi-axis prosthetic ankle of claim 1, wherein said retaining pin passes through a bore of a spherical bearing that is installed in said connecting projection, said spherical bearing facilitating movement of said ankle in other than a dorsi-flexion/plantar-flexion plane.
6. The multi-axis prosthetic ankle of claim 5, wherein said spherical bearing allows said ankle to undergo internal/external rotation, inversion/eversion, and medial/lateral translation.
7. The multi-axis prosthetic ankle of claim 1, wherein said connecting projection is substantially centered within said space that separates said support arms once said support arms and said connecting projection are connected by said retaining pin.
8. The multi-axis prosthetic ankle of claim 1, wherein said upwardly extending prosthetic socket connection portion of said lower leg connection component is dome-like in shape and includes a pyramid connector, said pyramid connector for connecting said ankle to a prosthetic leg.
9. The multi-axis prosthetic ankle of claim 1, wherein said elastomeric material is bonded to at least said prosthetic foot connection component and said connecting projection of said lower leg connection component.
10. The multi-axis prosthetic ankle of claim 1, further comprising one or more threaded or unthreaded bores in said prosthetic foot connection component for facilitating its connection to a prosthetic foot.
11. The multi-axis prosthetic ankle of claim 1, wherein said elastomeric material is a polymer rubber.
12. The multi-axis prosthetic ankle of claim 1, wherein said polymer rubber has a shore A hardness of 50 to 99.
13. The multi-axis prosthetic ankle of claim 1, wherein mechanical stops prevent the elastomeric material from reaching its elastic limit.
14. The multi-axis prosthetic ankle of claim 1, wherein compression of said elastomeric material between said connecting projection and inner walls of said support arms acts as a hard stop to ankle movement.
15. The multi-axis prosthetic ankle of claim 1, wherein compression of said elastomeric material between said flexion limiting pin and walls of said flexion limiting apertures acts as a hard stop to ankle movement.
16. The multi-axis prosthetic ankle of claim 1, wherein peripheral edges of said prosthetic foot connection component are provided with recesses or other features that increase adhesion of said elastomeric material.
17. A multi-axis prosthetic ankle, comprising:
a lower leg connection component having a base, a prosthetic leg connection portion extending upward from said base, and a connecting projection extending downward from said base to substantially reside within a space between said support arms;
a retaining pin receiving aperture in each of said support arms, and in said connecting projection;
a flexion limiting aperture in each of said support arms;
a flexion limiting pin installed near a distal end of said connecting projection, at least one end of said flexion limiting pin residing in a corresponding one of said flexion limiting apertures so as to limit plantar-flexion and dorsi-flexion of said ankle; and
wherein said elastomeric material encases and bonds to all components residing between said base of said prosthetic foot connection component and said base of said lower leg connection component after said prosthetic foot connection component and said lower leg connection component have been pivotally connected.
18. The multi-axis prosthetic ankle of claim 17, wherein internal/external rotation, inversion/eversion, and medial/lateral translation of said ankle are allowed by a space between said retaining pin receiving aperture in said connecting projection and said retaining pin.
19. The multi-axis prosthetic ankle of claim 17, further comprising a spherical bearing installed in said connecting projection, said retaining pin passing through a bore in said spherical bearing.
20. The multi-axis prosthetic ankle of claim 18, wherein said spherical bearing facilitates internal/external rotation, inversion/eversion, and medial/lateral translation movement of said ankle.
21. The multi-axis prosthetic ankle of claim 17, wherein compression of said elastomeric material in said flexion limiting apertures by said flexion limiting pin acts as a damper to plantar-flexion and dorsi-flexion of said ankle.
22. The multi-axis prosthetic ankle of claim 17, wherein said connecting projection is substantially centered within said space that separates said support arms once said support arms and said connecting projection are connected by said retaining pin.
23. The multi-axis prosthetic ankle of claim 17, wherein said prosthetic socket connection portion of said lower leg connection component is dome-like in shape and includes a pyramid connector, said pyramid connector for connecting said ankle to a prosthetic leg.
24. The multi-axis prosthetic ankle of claim 17, further comprising one or more threaded or unthreaded bores in said prosthetic foot connection component for facilitating its connection to a prosthetic foot.
25. The multi-axis prosthetic ankle of claim 17, wherein said elastomeric material is a polymer rubber.
26. The multi-axis prosthetic ankle of claim 17, wherein said polymer rubber has a shore A hardness of 50 to 99.
27. The multi-axis prosthetic ankle of claim 17, wherein mechanical stops prevent the elastomeric material from reaching its elastic limit.
28. The multi-axis prosthetic ankle of claim 17, wherein compression of said elastomeric material between said connecting projection and inner walls of said support arms acts as a hard stop to ankle movement.
29. The multi-axis prosthetic ankle of claim 17, wherein compression of said elastomeric material between said flexion limiting pin and walls of said flexion limiting apertures acts as a hard stop to ankle movement.
30. The multi-axis prosthetic ankle of claim 17, wherein peripheral edges of said prosthetic foot connection component are provided with recesses or other features that increase adhesion of said elastomeric material.
US10/770,833 2001-06-29 2004-02-03 Multi-axis prosthetic ankle joint Expired - Fee Related US7112227B2 (en)
US09/893,887 US6699295B2 (en) 2001-06-29 2001-06-29 Multi-axis prosthetic ankle joint
US10/770,833 US7112227B2 (en) 2001-06-29 2004-02-03 Multi-axis prosthetic ankle joint
DE200510004794 DE102005004794A1 (en) 2004-02-03 2005-02-02 Multi-axis prosthetic ankle link
GB0502251A GB2410692A (en) 2004-02-03 2005-02-03 Multi-axis prosthetic ankle joint
GB0814134A GB2449007B (en) 2004-02-03 2005-02-03 Multi-axis prosthetic ankle joint
US11/421,595 US7563288B2 (en) 2001-06-29 2006-06-01 Multi-axis prosthetic ankle
US11/613,843 US7833287B2 (en) 2001-06-29 2006-12-20 Adjustable multi-axis prosthetic ankle and method of use thereof
US09/893,887 Continuation-In-Part US6699295B2 (en) 2001-06-29 2001-06-29 Multi-axis prosthetic ankle joint
US11/421,595 Continuation-In-Part US7563288B2 (en) 2001-06-29 2006-06-01 Multi-axis prosthetic ankle
US20050015157A1 US20050015157A1 (en) 2005-01-20
US7112227B2 true US7112227B2 (en) 2006-09-26
ID=34314250
US10/770,833 Expired - Fee Related US7112227B2 (en) 2001-06-29 2004-02-03 Multi-axis prosthetic ankle joint
US (1) US7112227B2 (en)
DE (1) DE102005004794A1 (en)
GB (1) GB2410692A (en)
US4645508A (en) 1984-07-11 1987-02-24 Chas. A. Blatchford & Sons Limited Artificial ankle joint
JPH06225898A (en) * 1993-01-29 1994-08-16 Imasen Gijutsu Kenkyusho:Kk Joint device between leg section and foot section in prosthetic leg
JPH0984814A (en) * 1995-09-21 1997-03-31 Imasen Gijutsu Kenkyusho:Kk Joint device of artifical leg
JPH11345A (en) * 1997-06-12 1999-01-06 Imasen Gijutsu Kenkyusho:Kk Ankle joint device for artificial leg
US20030004582A1 (en) * 2001-06-29 2003-01-02 Ohio Willow Wood Company Multi-axis prosthetic ankle joint
2004-02-03 US US10/770,833 patent/US7112227B2/en not_active Expired - Fee Related
2005-02-02 DE DE200510004794 patent/DE102005004794A1/en not_active Withdrawn
2005-02-03 GB GB0502251A patent/GB2410692A/en not_active Withdrawn
GB0502251D0 (en) 2005-03-09
US20050015157A1 (en) 2005-01-20
DE102005004794A1 (en) 2005-09-15
GB2410692A (en) 2005-08-10
EP0810846B1 (en) 2001-05-16 Adjustable prosthesis joint
JP5122921B2 (en) 2013-01-16 The slide member and the shoe sole
US20090306792A1 (en) 2009-12-10 Foot prosthesis with resilient multi-axial ankle
US20090204230A1 (en) 2009-08-13 Orthopedic Foot Part and Method for Controlling an Artificial Foot
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:DODDROE, JEFFREY L.;COLVIN, JAMES M.;ARBOGAST, ROBERT E.;AND OTHERS;REEL/FRAME:015871/0713
Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE TO REMOVE THE NAME OF AN INCORRECTLY LISTED ASSIGNOR, JAMES W. CAPPER, AND INSERT THE CORRECT ASSIGNOR, CHI L. LEE PREVIOUSLY RECORDED ON REEL 015871 FRAME 0713;ASSIGNORS:DODDROE, JEFFREY L.;LEE, CHI L.;COLVIN, JAMES M.;AND OTHERS;REEL/FRAME:015905/0482