US20060064176A1 - High profile multiaxial prosthetic foot - Google Patents
High profile multiaxial prosthetic foot Download PDFInfo
- Publication number
- US20060064176A1 US20060064176A1 US11/268,129 US26812905A US2006064176A1 US 20060064176 A1 US20060064176 A1 US 20060064176A1 US 26812905 A US26812905 A US 26812905A US 2006064176 A1 US2006064176 A1 US 2006064176A1
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- US
- United States
- Prior art keywords
- frame
- prosthetic foot
- connector
- lower portion
- footplate
- 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.)
- Abandoned
Links
- 210000002683 foot Anatomy 0.000 abstract description 108
- 210000000544 articulatio talocruralis Anatomy 0.000 abstract description 28
- 238000004146 energy storage Methods 0.000 abstract description 11
- 239000000463 material Substances 0.000 description 8
- 229920000049 Carbon (fiber) Polymers 0.000 description 6
- 239000004917 carbon fiber Substances 0.000 description 6
- VNWKTOKETHGBQD-UHFFFAOYSA-N methane Chemical compound C VNWKTOKETHGBQD-UHFFFAOYSA-N 0.000 description 6
- 239000013013 elastic material Substances 0.000 description 5
- 210000003414 extremity Anatomy 0.000 description 5
- 210000003423 ankle Anatomy 0.000 description 4
- 230000006835 compression Effects 0.000 description 4
- 238000007906 compression Methods 0.000 description 4
- 239000002131 composite material Substances 0.000 description 3
- 238000006073 displacement reaction Methods 0.000 description 3
- 239000013536 elastomeric material Substances 0.000 description 3
- 229920000642 polymer Polymers 0.000 description 3
- 230000000694 effects Effects 0.000 description 2
- 229920001971 elastomer Polymers 0.000 description 2
- 239000000806 elastomer Substances 0.000 description 2
- 239000002184 metal Substances 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 230000006978 adaptation Effects 0.000 description 1
- 230000001010 compromised effect Effects 0.000 description 1
- 230000005489 elastic deformation Effects 0.000 description 1
- 229920005570 flexible polymer Polymers 0.000 description 1
- 230000005021 gait Effects 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
- 230000000087 stabilizing effect Effects 0.000 description 1
Images
Classifications
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- 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
- A61F2/50—Prostheses not implantable in the body
- A61F2/60—Artificial legs or feet or parts thereof
- A61F2/66—Feet; Ankle joints
- A61F2/6607—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
- A61F2/50—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
- A61F2002/5038—Hinged joint, e.g. with transverse axle restricting the movement
- A61F2002/5043—Hinged joint, e.g. with transverse axle restricting the movement with rotation-limiting stops, e.g. projections or recesses
-
- 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
- A61F2/5044—Designing or manufacturing processes
- A61F2002/5055—Reinforcing prostheses by embedding particles or fibres during moulding or dipping, e.g. carbon fibre composites
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- 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
- A61F2002/5072—Prostheses not implantable in the body having spring elements
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- 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
- A61F2002/5072—Prostheses not implantable in the body having spring elements
- A61F2002/5079—Leaf springs
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- 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
- A61F2002/665—Soles
-
- 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
Definitions
- the present invention relates to a high-profile prosthetic foot that provides up to 180° of medial-lateral rotation with respect to the prosthesis frame and also provides energy storage capabilities.
- the present invention further relates to a prosthetic ankle joint having an adjustable range of medial-lateral rotation about the prosthesis frame.
- a prosthetic foot must provide stable support to the user under a variety of conditions. Such conditions include a variable stride and a range of different activities.
- a prosthetic foot has long been sought that can provide stable support for a user who is walking on an ever changing terrain, such as that encountered in normal daily activity.
- a prosthetic foot would ideally provide a range of motion in a medial-lateral direction. It is also desirable that the prosthetic foot has energy storage capabilities to provide a more normal gait.
- Dynamic response prosthetic feet are preferred for active amputees.
- the energy storage capabilities of the feet give them a spring-like functionality, which improves the feel and overall function of the prostheses.
- Two widely used types of prosthetic feet are high profile dynamic feet and low profile multiaxial feet.
- High profile dynamic feet consist of a long L-shaped piece of material attached to a base plate.
- the L-shaped piece of material may be alternatively referred to as a frame.
- the frame is elastic and therefore provides some energy storage capability.
- the frame is a composite, such as a carbon fiber laminate or a polymeric material.
- all high profile dynamic feet have a rectangular cross section relative to the frame and therefore movement of the footplate is typically limited.
- Such high profile dynamic feet have advantages because of their high-energy storage capability. High-energy storage occurs in the frame of the prosthesis. High profile dynamic feet have the longest frame, and thus act as the biggest springs and, accordingly, store the most energy. However, high profile dynamic feet also present some drawbacks.
- the high profile dynamic feet have no ankle motion and therefore are not capable to conforming to a changing terrain.
- the foot portion of a high profile dynamic foot stays in the same position relative to the frame regardless of whether the amputee is walking on an incline, walking on uneven terrain or moving in a side-to-side direction.
- the multiaxial dynamic feet of the prior art attempt to simulate motion of the ankle and are generally considered more stable than high profile dynamic feet.
- a disadvantage of the multiaxial dynamic foot is that generally it is a low profile prosthesis.
- low profile multiaxial dynamic feet can only store energy in their keel, which is a much smaller frame and, thus, a much smaller spring. Accordingly, there is correspondingly less energy storage. Therefore, with the prior art devices, there presently is a tradeoff between increased stability and improved energy storage capability.
- the multiaxial feet of the prior art possess an axis of rotation through the ankle joint that lies transverse to the normal anterior-posterior alignment of the foot.
- such multiaxial prosthetic feet although typically providing a range of rotation in an anterior-posterior direction, have limited freedom to move in a medial-lateral direction.
- the prior art multiaxial feet typically only allow a small amount of medial-lateral tilt and do not allow true rotation in the medial-lateral direction. Tilt is distinguishable from true rotation in that tilt may occur along any of a multitude of axes, whereas rotation occurs about one axis. Tilt may also be described as wobble.
- the amount of medial-lateral tilt is a consequence of some looseness in the ankle joint. This looseness is generally accomplished through the use of an elastomeric member in the ankle joint, which member can then compress to a limited degree, thus accommodating medial-lateral tilt.
- it can be difficult to control the tilting motion.
- the prior art devices do not possess an axis of rotation through an ankle joint where the axis of rotation lies in the anterior-posterior direction.
- elastomeric member tends to wear out.
- Some of the prior art prosthetic feet provide a range of motion in an anterior-posterior direction. Providing this range of motion is accomplished, for example, by providing a flexible foot that includes an ankle member that flexes in the anterior-posterior direction.
- Another prior art device provides anterior-posterior motion by using a very high modulus material that permits limited deformation under a high load. This high modulus elastic material is typically positioned between the foot and the frame. As the load on the frame changes during the normal transfer of weight that occurs during walking, the high modulus elastic material flexes to a limited extent.
- Still another prior device uses an o-ring positioned at the end of the frame where the frame connects to the foot. This o-ring is typically made of a high modulus material and will deform to a limited extent as weight is transferred during a normal stride.
- the range of motion is necessarily limited. If the material forming at least part of the connection between the frame and the foot has too low a modulus, then control over the foot during normal walking will be compromised.
- Some of the prior art suggests that a limited degree of medial-lateral movement will occur as a result of the compression of the high modulus elastomeric material positioned between the frame and the foot. Such movement has been described in the art as a slight rocking or a slight tilting motion. The prior art further teaches that although some medial-lateral rocking motion can be accomplished, generally, medial-lateral movement is resisted.
- Still another prior art device provides an elastomeric bushing about a heel ankle connector pin.
- this bushing material is a high modulus elastomer. Accordingly, some compression of the elastomer may take place during the normal weight transfer accompanying walking and result in a small amount of medial-lateral tilt or wobble.
- prostheses that rely on a high modulus elastic material for flexibility tend to have a problem with durability because they wear out with repeated loading and unloading.
- the high profile multiaxial prosthetic foot provides rotation of a footplate in a medial-lateral direction.
- the high profile multiaxial prosthetic foot includes a tubular frame connected to a footplate using a spring connector.
- the spring connector may include a high modulus elastic material, a torsional spring or combinations of these.
- the present invention provides a high profile multiaxial prosthetic foot that includes a high profile component and a multiaxial component.
- the present invention also provides a high profile multiaxial dynamic prosthetic foot having an adjustable range of medial-lateral rotation.
- the medial-lateral rotation of the prosthetic foot of the present invention may be adjusted to accommodate the individual needs of the wearer.
- the present invention provides a prosthetic foot including: a frame having a first axis and a second axis; a connector connected to the frame, the connector being adapted to rotate about the first axis; and a footplate attached to the connector.
- a prosthetic foot that provides both the energy storage capabilities of a high profile prosthesis with the stability of a multiaxial prosthesis.
- the high profile multiaxial prosthetic foot of the present invention provides medial-lateral rotation as compared to the slight medial-lateral tilting or rocking of the prior art devices. In a preferred embodiment, the medial-lateral rotation is controlled about a unitary axis. Furthermore, the high profile multiaxial prosthetic foot of the present invention provides a true hinge in the ankle joint region.
- Embodiments of the present invention further provide a high profile multiaxial prosthetic foot having an ankle joint wherein the axis of rotation lies along the longitudinal axis of the foot.
- the prosthetic foot of the present invention further provides the capability of free rotation about the ankle joint about its axis of rotation.
- FIG. 1 is a side view of an embodiment of the high profile multiaxial prosthetic foot made in accordance with the principles of the present invention.
- FIG. 2 is a schematic showing an end view of the high profile multiaxial prosthetic foot of FIG. 1 .
- FIG. 3 is a side view of the frame of FIG. 1 .
- FIG. 4 is an end view of one embodiment of a frame/connector/footplate assembly made in accordance with the principles of the present invention.
- FIG. 5 is an end view of an alternative embodiment of a frame/connector/footplate assembly made in accordance with the principles of the present invention.
- FIG. 6 is another embodiment of a frame/connector/footplate assembly made in accordance with the principles of the present invention.
- FIG. 7 is an end cross-sectional view of another embodiment of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention.
- FIG. 8 is an end cross-sectional view of the high profile multiaxial prosthetic foot made in accordance with the principles of the present invention illustrating means for rotation control.
- FIG. 9 is an embodiment of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing alternate connector means and means for rotation control.
- FIG. 10 is a side view of still another embodiment of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention.
- FIG. 11 is a side view of still another embodiment of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention.
- FIG. 12 is an end view of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing rotation of the prosthetic foot about an axis aligned with the longitudinal axis of the foot.
- FIG. 13 is an end view of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing rotation of the prosthetic foot about an axis aligned with the longitudinal axis of the foot.
- FIG. 14 a is a side view of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing an adjustable displacement of a frame with respect to the foot.
- FIG. 14 b is a side view of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing an adjustable displacement of a frame with respect to the foot.
- FIG. 15 is an end view of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing the displacement of a frame with respect to the vertical alignment of a residual limb.
- a high profile multiaxial prosthetic foot (“prosthetic foot”) made in accordance with the principles of the present invention is labeled 10 .
- the prosthetic foot 10 includes a frame 12 , a connector 15 and a footplate 19 .
- An upper portion of the frame 12 may be connected to socket (not shown) that is connected to a leg of the human wearer of the prosthetic foot 10 and a lower portion of the frame 12 is adapted to connect to the footplate 19 .
- the frame 12 has a generally circular cross-section. Of course, other suitable cross-sections may be used.
- the connector 15 is adapted to allow rotation of the frame 12 about an axis that is aligned with the longitudinal axis of the footplate 19 . As shown in FIG.
- an ankle joint 23 defines the connection between the frame 12 and the connector 15 .
- the footplate 19 is attached to the connector 15 , and, preferably, the footplate 19 is rigidly attached to the connector 15 .
- the footplate 19 is free to rotate about an axis defined by the ankle joint 23 , the axis of rotation lying along the longitudinal axis of the footplate 19 and the lower portion of the frame 12 .
- the prosthetic foot 10 may also be adapted for anterior-posterior movement, by, for example, providing means for the elastic deformation of the connector 15 , the frame 12 , and/or the footplate 19 .
- the prosthetic foot 10 may provide multiaxial movement.
- the frame may be constructed of a high strength polymer or a composite material such as a carbon fiber laminate, for example.
- the frame is an L-shaped member. Being a generally L-shaped member, the frame defines a first axis and a second axis.
- the footplate may also be constructed of a high strength polymer or a composite material such as a carbon fiber laminate.
- the frame 12 is depicted removed from the connector 15 .
- the frame 12 may be described as having a generally long axis L 1 along the upper portion of the frame 12 and a generally short axis S 1 along the lower portion of the frame 12 , however, long axis L 1 and short axis S 1 may be of any length as required by a wearer of the prosthetic foot 10 .
- the short axis S 1 is connected to the connector 15 through the ankle joint 23 . In one embodiment, when the prosthetic foot 10 is assembled, the short axis S 1 is aligned with the longitudinal axis of the footplate 19 .
- FIGS. 4, 5 and 6 show alternative embodiments of the present invention and more particularly, show alternative means for connecting a frame to a footplate.
- a frame 42 is connected to a connector 45 through an ankle joint 43 .
- the connector 45 may be any general shape so long as it does not preclude the utility of the prosthetic foot 10 .
- the connector 45 is generally configured so that it may provide an ankle joint 43 having an axis of rotation that lies along an anterior-posterior direction.
- the connector 45 is attached to the footplate 49 .
- the connector 45 is adapted to frictionally receive the frame 42 .
- medial-lateral rotation of the frame 42 about its short axis is limited by the coefficient of friction existing between the connector 45 and the frame 42 at the ankle joint 43 .
- the connector 45 may be made of any suitable material that preserves the functionally of the prosthetic foot 10 .
- a high strength polymer, a carbon fiber laminate or a high modulus elastomeric material may be used for the connector 45 .
- a high modulus elastomeric material may allow movement of the footplate 49 in an anterior-posterior direction via compression of the connector 45 .
- FIG. 5 an alternative embodiment of the connector of the present invention is illustrated.
- Frame 52 is connected to a spring 55 through an ankle joint 53 .
- Spring 55 is then attached to a footplate 59 .
- connector 55 is in the form of a torsional spring.
- the spring 55 is generally configured so that it may provide an ankle joint 43 having an axis of rotation that lies along an anterior-posterior direction.
- the spring 55 may be constructed of a carbon fiber laminate or metal, for example.
- the amount of rotation of the footplate 59 about the ankle joint 53 may be limited by the spring constant for the spring 55 .
- the frame 52 be fixedly attached to the spring 55 at the ankle joint 53 .
- the amount of rotation of the footplate 59 about the ankle joint 53 is limited both by the coefficient of friction existing between the short axis of the frame 52 and the spring 55 at the ankle joint 53 and also the spring constant of the spring 55 .
- FIG. 6 yet another embodiment of a frame/connector/footplate assembly made in accordance with the principles of the present invention illustrated.
- a frame 62 is connected to a spring 65 at an ankle joint 63 .
- spring 65 is in the form of a torsional spring.
- the spring 65 is generally configured so that it may provide an ankle joint 63 having an axis of rotation that lies along the short axis of the frame 62 .
- the spring 65 may be constructed of a carbon fiber laminate or metal, for example. Thus, the amount of rotation of the footplate 69 about the ankle joint 63 may be limited by the spring constant for the spring 65 .
- a connector 64 is also used.
- the spring 65 and the connector 64 are both attached to the footplate 69 .
- Rotation of the frame 62 within the ankle joint 63 may be constrained by providing that the spring 65 is adapted to frictionally receive the frame 62 .
- Rotation of the frame 62 within the connector 64 may be constrained by providing that the connector 64 is adapted to frictionally receive the frame 62 .
- the rotation of the footplate 69 may be limited by the coefficient of friction between the frame 62 and the spring 65 , the coefficient of friction between the frame 62 and the connector 64 , or the spring constant of the spring 65 , or combinations thereof.
- FIG. 7 a cross-sectional end view of a high profile multiaxial prosthetic foot 70 is shown.
- the frame 72 is connected to a spring 74 by a setscrew 73 .
- the setscrew 73 may fixedly attach the spring 74 to the frame 72 and limit or even prevent the rotation of the frame 72 within the spring 74 .
- a connector 75 is adapted to rotationally receive the frame 72 .
- the connector 75 is attached to the footplate 79 .
- the spring 74 may abut the footplate 79 .
- FIG. 8 a cross-sectional end view of another embodiment of a prosthetic foot of the present invention is shown.
- a control element 81 is adapted to receive a frame 82 .
- Rotation stop 87 , 88 extend from control element 81 .
- a connector 85 and a footplate 89 are also shown.
- the rotation of the footplate 89 about its axis is limited by the rotation stop 87 , 88 .
- the footplate 89 may rotate either clockwise or counter-clockwise until reaching the rotation stop 87 , 88 .
- the structure of the rotation stop 87 , 88 and the control element 81 are further described below with respect to FIG. 9 .
- FIG. 9 a side-view of a prosthetic foot incorporating a connector 75 , a spring 74 and a control element 81 .
- the frame 72 is connected to a spring 74 by a setscrew 73 .
- the connector 75 is adapted to rotationally receive the frame 72 .
- the connector 75 is also attached to the footplate 79 in a known manner.
- the spring 74 may abut the footplate 79 .
- the control element 81 is adapted to receive the frame 72 .
- the control element 81 is rigidly attached to the frame 72 .
- the control element includes a rotation stop 87 .
- the rotation of the footplate 89 about its axis is limited by the rotation stop 87 .
- a second rotation stop may be included as described above.
- the footplate 89 may rotate either clockwise or counter-clockwise until reaching a rotation stop.
- FIG. 10 yet another embodiment of a prosthetic foot of the present invention is illustrated.
- a frame 112 is connected to a connector 115 , which in turn is attached to a footplate 119 .
- the footplate 119 is formed to allow the use of a frame 112 wherein the angle between the short axis and the long axis of the frame 112 is greater than 90°.
- FIG. 11 yet another embodiment of a prosthetic foot of the present invention is illustrated.
- a frame 112 is rotatably connected to a connector 115 , which in turn is fixedly attached to a footplate 119 .
- the frame 112 is connected to a spring 114 .
- the spring 114 may abut the footplate 119 .
- the footplate 119 is formed to allow the use of a frame 112 wherein the angle between the short axis and the long axis of the frame 112 is greater than 90°.
- FIG. 12 illustrates the ability of a prosthetic foot made in accordance with the principles of the present invention to provide medial-lateral rotation.
- FIG. 12 an end view of the prosthetic foot 10 is shown.
- a frame 12 is connected to a connector 15 at an ankle joint 13 with the connector 15 being attached to a footplate 19 .
- the prosthetic foot is positioned on an inclined plane 11 . This is analogous to a wearer of a prosthetic foot standing sideways on a hill.
- the longitudinal axis of the footplate 19 is transverse to the direction of incline of the incline plane 11 . It can be seen that the high profile multiaxial prosthetic foot of the present invention allows rotation in a medial-lateral direction, thus, stabilizing the footplate 19 in such a position.
- FIG. 13 likewise illustrates an embodiment of a prosthetic foot of the present invention positioned on an inclined plane 11 .
- the angle ⁇ is the angle formed between the plane of the incline and the long axis of the frame 12 . Because of the orientation of the ankle joint 13 , ⁇ may effectively vary between 0 and 180°.
- the prosthetic foot of the present invention may be adapted to provide adjustment of a frame with respect to a connector and a footplate.
- a frame 112 is shown connected to a connector 115 .
- the connector 115 is attached to a footplate 119 .
- One end of the footplate 119 defines an imaginary vertical line v.
- a distance x 1 is defined by the separation distance between v and the long axis of the frame 112 .
- a second distance x 2 may be defined between v and the long axis of the frame 112 .
- the distance x 1 is less than the distance x 2 .
- the position of the long axis of the frame 112 may be adjusted with respect to the connector 115 and the footplate 119 .
- the footplate 119 defines a first end and a second end.
- the adjustable positioning of the frame 112 with respect to the footplate 119 may accomplished, for example, by adjustably connecting the frame 112 to the connector 115 .
- the short axis of the frame 112 may be moved to a desired position along the longitudinal axis of the footplate 119 and then fixed in position by the connector 115 with respect to further movement along the longitudinal axis of the footplate.
- the frame 72 may be adjustably positioned with respect to the footplate 79 as described above and this position fixed by tightening setscrew 73 .
- a frame 112 is shown connected to a connector 115 .
- the connector 115 is attached to a footplate 119 .
- a residual limb 120 is attached to a socket that is attached to the frame 112 .
- the residual limb 120 defines a generally vertical axis v 1 .
- An angle ⁇ 1 is defined by the long axis of the frame 112 and v 1 .
- ⁇ 1 may be varied to allow the residual limb 120 to be offset with respect to the footplate 119 .
- the footplate 119 can be seen to also define a top plane and a bottom plane. As illustrated in FIG.
- the connector 115 is attached to the footplate 119 at the top plane of the footplate 119 .
- the long axis of the frame 112 may be adjustably positioned with respect to the top plane so that the long axis defines an angle with respect to the top plane that is different than 90°.
- the frame 72 may be adjustably positioned with respect to the footplate 79 as described above and this position fixed by tightening setscrew 73 .
- the footplate of the prosthetic foot of the present invention may be covered with an anthropomorphic flexible polymer in the shape of a foot.
- the high profile multiaxial prosthetic foot made in accordance with the principles of the present invention allows free rotation of a prosthetic footplate about an axis that lies along the longitudinal axis of the footplate.
- a prosthetic foot provides free rotation from 0 to 180° in a medial-lateral direction.
- a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention further provides means to control the amount of rotation of the footplate.
- the present invention provides a high profile multiaxial prosthetic foot that allows true medial-lateral rotation as opposed to mere medial-lateral tilt.
Abstract
The present invention provides a prosthetic foot that provides both energy storage capabilities and stability. The prosthetic foot of the present invention provides medial-lateral rotation as compared to the slight tilting or rocking in the medial-lateral plane of the prior art devices. Furthermore, the prosthetic foot of the present invention provides a true hinge in the ankle joint region that may be adapted so that the degree of rotation is controlled.
Description
- This patent application is a continuation of copending U.S. patent application Ser. No. 09/558,570, filed on Apr. 26, 2000, which is incorporated herein by reference in its entirety.
- The present invention relates to a high-profile prosthetic foot that provides up to 180° of medial-lateral rotation with respect to the prosthesis frame and also provides energy storage capabilities. The present invention further relates to a prosthetic ankle joint having an adjustable range of medial-lateral rotation about the prosthesis frame.
- A prosthetic foot must provide stable support to the user under a variety of conditions. Such conditions include a variable stride and a range of different activities. In particular, a prosthetic foot has long been sought that can provide stable support for a user who is walking on an ever changing terrain, such as that encountered in normal daily activity. To achieve this objective, a prosthetic foot would ideally provide a range of motion in a medial-lateral direction. It is also desirable that the prosthetic foot has energy storage capabilities to provide a more normal gait.
- Dynamic response prosthetic feet are preferred for active amputees. The energy storage capabilities of the feet give them a spring-like functionality, which improves the feel and overall function of the prostheses. Two widely used types of prosthetic feet are high profile dynamic feet and low profile multiaxial feet.
- High profile dynamic feet consist of a long L-shaped piece of material attached to a base plate. The L-shaped piece of material may be alternatively referred to as a frame. Typically, the frame is elastic and therefore provides some energy storage capability. Generally, the frame is a composite, such as a carbon fiber laminate or a polymeric material. At present, all high profile dynamic feet have a rectangular cross section relative to the frame and therefore movement of the footplate is typically limited. Such high profile dynamic feet have advantages because of their high-energy storage capability. High-energy storage occurs in the frame of the prosthesis. High profile dynamic feet have the longest frame, and thus act as the biggest springs and, accordingly, store the most energy. However, high profile dynamic feet also present some drawbacks. Principally, the high profile dynamic feet have no ankle motion and therefore are not capable to conforming to a changing terrain. The foot portion of a high profile dynamic foot stays in the same position relative to the frame regardless of whether the amputee is walking on an incline, walking on uneven terrain or moving in a side-to-side direction.
- The multiaxial dynamic feet of the prior art attempt to simulate motion of the ankle and are generally considered more stable than high profile dynamic feet. A disadvantage of the multiaxial dynamic foot is that generally it is a low profile prosthesis. By comparison to the high profile dynamic feet, low profile multiaxial dynamic feet can only store energy in their keel, which is a much smaller frame and, thus, a much smaller spring. Accordingly, there is correspondingly less energy storage. Therefore, with the prior art devices, there presently is a tradeoff between increased stability and improved energy storage capability.
- Typically, the multiaxial feet of the prior art possess an axis of rotation through the ankle joint that lies transverse to the normal anterior-posterior alignment of the foot. Subsequently, such multiaxial prosthetic feet, although typically providing a range of rotation in an anterior-posterior direction, have limited freedom to move in a medial-lateral direction. Subsequently, the prior art multiaxial feet typically only allow a small amount of medial-lateral tilt and do not allow true rotation in the medial-lateral direction. Tilt is distinguishable from true rotation in that tilt may occur along any of a multitude of axes, whereas rotation occurs about one axis. Tilt may also be described as wobble. Typically, in the prior art devices, the amount of medial-lateral tilt is a consequence of some looseness in the ankle joint. This looseness is generally accomplished through the use of an elastomeric member in the ankle joint, which member can then compress to a limited degree, thus accommodating medial-lateral tilt. However, it can be difficult to control the tilting motion. Generally, the prior art devices do not possess an axis of rotation through an ankle joint where the axis of rotation lies in the anterior-posterior direction. Furthermore, elastomeric member tends to wear out.
- Some of the prior art prosthetic feet provide a range of motion in an anterior-posterior direction. Providing this range of motion is accomplished, for example, by providing a flexible foot that includes an ankle member that flexes in the anterior-posterior direction. Another prior art device provides anterior-posterior motion by using a very high modulus material that permits limited deformation under a high load. This high modulus elastic material is typically positioned between the foot and the frame. As the load on the frame changes during the normal transfer of weight that occurs during walking, the high modulus elastic material flexes to a limited extent. Still another prior device uses an o-ring positioned at the end of the frame where the frame connects to the foot. This o-ring is typically made of a high modulus material and will deform to a limited extent as weight is transferred during a normal stride.
- Typical among the devices that rely on a high modulus elastic material for flexibility, the range of motion is necessarily limited. If the material forming at least part of the connection between the frame and the foot has too low a modulus, then control over the foot during normal walking will be compromised. Some of the prior art suggests that a limited degree of medial-lateral movement will occur as a result of the compression of the high modulus elastomeric material positioned between the frame and the foot. Such movement has been described in the art as a slight rocking or a slight tilting motion. The prior art further teaches that although some medial-lateral rocking motion can be accomplished, generally, medial-lateral movement is resisted.
- Still another prior art device provides an elastomeric bushing about a heel ankle connector pin. As with the other prior art devices already described, this bushing material is a high modulus elastomer. Accordingly, some compression of the elastomer may take place during the normal weight transfer accompanying walking and result in a small amount of medial-lateral tilt or wobble. As provided above, prostheses that rely on a high modulus elastic material for flexibility tend to have a problem with durability because they wear out with repeated loading and unloading.
- Lack of a true hinge allowing rotation in the medial-lateral direction is a disadvantage. True control of movement in a medial-lateral direction about a unitary axis is difficult to achieve in the prior art devices. Any medial-lateral movement in these devices is limited to a tilting movement. This tilting movement can occur along any of an infinite number of axes. Because it is not possible to control every possible axis along which the prior art foot may move, medial-lateral directional control can be difficult to achieve and, therefore, medial-lateral movement is typically constrained. Not surprisingly, the prior art devices limit a full range of medial-lateral movement. For example, in many prior art multiaxial feet, movement of the foot occurs through compression of an elastomeric pad positioned in the ankle region of the foot. Thus in order to provide movement of the foot in a medial-lateral direction the entire elastomeric pad must be of a modulus that affects movement in all directions. In such a multiaxial foot, there is no independent control over movement in a singular direction or line of action.
- It would therefore be an advantage to have a prosthetic foot that offered the stability advantages of a multiaxial dynamic foot with the energy storage capabilities of a high profile dynamic foot. It would be an even further advantage to have a prosthetic foot that allows true medial-lateral rotation. It would be at an even further advantage to have an adjustable prosthetic foot that would allow the manufacturer or wearer to select a range of medial-lateral rotation best suited to a wearer's needs.
- It would be an even further advantage to have a high profile multiaxial prosthetic foot that could allow free rotation about an axis that lies in the anterior-posterior direction.
- In accordance with the principals of the present invention, there is provided a high profile multiaxial prosthetic foot providing rotation of a footplate in a medial-lateral direction. According to one embodiment, the high profile multiaxial prosthetic foot includes a tubular frame connected to a footplate using a spring connector. In embodiments of the present invention, the spring connector may include a high modulus elastic material, a torsional spring or combinations of these. Thus, the present invention provides a high profile multiaxial prosthetic foot that includes a high profile component and a multiaxial component.
- The present invention also provides a high profile multiaxial dynamic prosthetic foot having an adjustable range of medial-lateral rotation. The medial-lateral rotation of the prosthetic foot of the present invention may be adjusted to accommodate the individual needs of the wearer.
- The present invention provides a prosthetic foot including: a frame having a first axis and a second axis; a connector connected to the frame, the connector being adapted to rotate about the first axis; and a footplate attached to the connector.
- Thus, it will be seen that according to principals of the present invention there is provided a prosthetic foot that provides both the energy storage capabilities of a high profile prosthesis with the stability of a multiaxial prosthesis. The high profile multiaxial prosthetic foot of the present invention provides medial-lateral rotation as compared to the slight medial-lateral tilting or rocking of the prior art devices. In a preferred embodiment, the medial-lateral rotation is controlled about a unitary axis. Furthermore, the high profile multiaxial prosthetic foot of the present invention provides a true hinge in the ankle joint region.
- Embodiments of the present invention further provide a high profile multiaxial prosthetic foot having an ankle joint wherein the axis of rotation lies along the longitudinal axis of the foot. The prosthetic foot of the present invention further provides the capability of free rotation about the ankle joint about its axis of rotation.
-
FIG. 1 is a side view of an embodiment of the high profile multiaxial prosthetic foot made in accordance with the principles of the present invention. -
FIG. 2 is a schematic showing an end view of the high profile multiaxial prosthetic foot ofFIG. 1 . -
FIG. 3 is a side view of the frame ofFIG. 1 . -
FIG. 4 is an end view of one embodiment of a frame/connector/footplate assembly made in accordance with the principles of the present invention. -
FIG. 5 is an end view of an alternative embodiment of a frame/connector/footplate assembly made in accordance with the principles of the present invention. -
FIG. 6 is another embodiment of a frame/connector/footplate assembly made in accordance with the principles of the present invention. -
FIG. 7 is an end cross-sectional view of another embodiment of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention. -
FIG. 8 is an end cross-sectional view of the high profile multiaxial prosthetic foot made in accordance with the principles of the present invention illustrating means for rotation control. -
FIG. 9 is an embodiment of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing alternate connector means and means for rotation control. -
FIG. 10 is a side view of still another embodiment of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention. -
FIG. 11 is a side view of still another embodiment of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention. -
FIG. 12 is an end view of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing rotation of the prosthetic foot about an axis aligned with the longitudinal axis of the foot. -
FIG. 13 is an end view of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing rotation of the prosthetic foot about an axis aligned with the longitudinal axis of the foot. -
FIG. 14 a is a side view of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing an adjustable displacement of a frame with respect to the foot. -
FIG. 14 b is a side view of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing an adjustable displacement of a frame with respect to the foot. -
FIG. 15 is an end view of a high profile multiaxial prosthetic foot made in accordance with the principles of the present invention showing the displacement of a frame with respect to the vertical alignment of a residual limb. - In
FIG. 1 , a high profile multiaxial prosthetic foot (“prosthetic foot”) made in accordance with the principles of the present invention is labeled 10. The prosthetic foot 10 includes aframe 12, aconnector 15 and afootplate 19. An upper portion of theframe 12 may be connected to socket (not shown) that is connected to a leg of the human wearer of the prosthetic foot 10 and a lower portion of theframe 12 is adapted to connect to thefootplate 19. In a preferred embodiment, theframe 12 has a generally circular cross-section. Of course, other suitable cross-sections may be used. Theconnector 15 is adapted to allow rotation of theframe 12 about an axis that is aligned with the longitudinal axis of thefootplate 19. As shown inFIG. 2 , an ankle joint 23 defines the connection between theframe 12 and theconnector 15. Thefootplate 19 is attached to theconnector 15, and, preferably, thefootplate 19 is rigidly attached to theconnector 15. Thus, it can be seen that thefootplate 19 is free to rotate about an axis defined by the ankle joint 23, the axis of rotation lying along the longitudinal axis of thefootplate 19 and the lower portion of theframe 12. The prosthetic foot 10 may also be adapted for anterior-posterior movement, by, for example, providing means for the elastic deformation of theconnector 15, theframe 12, and/or thefootplate 19. Thus, the prosthetic foot 10 may provide multiaxial movement. - The frame may be constructed of a high strength polymer or a composite material such as a carbon fiber laminate, for example. In a preferred embodiment, the frame is an L-shaped member. Being a generally L-shaped member, the frame defines a first axis and a second axis. The footplate may also be constructed of a high strength polymer or a composite material such as a carbon fiber laminate.
- In
FIG. 3 , theframe 12 is depicted removed from theconnector 15. Theframe 12 may be described as having a generally long axis L1 along the upper portion of theframe 12 and a generally short axis S1 along the lower portion of theframe 12, however, long axis L1 and short axis S1 may be of any length as required by a wearer of the prosthetic foot 10. The short axis S1 is connected to theconnector 15 through the ankle joint 23. In one embodiment, when the prosthetic foot 10 is assembled, the short axis S1 is aligned with the longitudinal axis of thefootplate 19. -
FIGS. 4, 5 and 6 show alternative embodiments of the present invention and more particularly, show alternative means for connecting a frame to a footplate. InFIG. 4 , aframe 42 is connected to aconnector 45 through an ankle joint 43. Theconnector 45 may be any general shape so long as it does not preclude the utility of the prosthetic foot 10. Theconnector 45 is generally configured so that it may provide an ankle joint 43 having an axis of rotation that lies along an anterior-posterior direction. Theconnector 45 is attached to thefootplate 49. In this embodiment, theconnector 45 is adapted to frictionally receive theframe 42. Thus, medial-lateral rotation of theframe 42 about its short axis is limited by the coefficient of friction existing between theconnector 45 and theframe 42 at the ankle joint 43. Theconnector 45 may be made of any suitable material that preserves the functionally of the prosthetic foot 10. For example, a high strength polymer, a carbon fiber laminate or a high modulus elastomeric material may be used for theconnector 45. A high modulus elastomeric material, for example, may allow movement of the footplate 49 in an anterior-posterior direction via compression of theconnector 45. - In
FIG. 5 , an alternative embodiment of the connector of the present invention is illustrated.Frame 52 is connected to aspring 55 through an ankle joint 53.Spring 55 is then attached to afootplate 59. In the embodiment depicted inFIG. 5 ,connector 55 is in the form of a torsional spring. However, other spring designs, such as a leaf spring, may be used. Thespring 55 is generally configured so that it may provide an ankle joint 43 having an axis of rotation that lies along an anterior-posterior direction. Thespring 55 may be constructed of a carbon fiber laminate or metal, for example. Thus, the amount of rotation of the footplate 59 about the ankle joint 53 may be limited by the spring constant for thespring 55. In this embodiment, it is preferred that theframe 52 be fixedly attached to thespring 55 at the ankle joint 53. However, it may possible to allow rotation of the short axis of theframe 52 within the ankle joint 53 with respect to thespring 55, by providing that thespring 55 is adapted to frictionally receive theframe 52. Thus, the amount of rotation of the footplate 59 about the ankle joint 53 is limited both by the coefficient of friction existing between the short axis of theframe 52 and thespring 55 at the ankle joint 53 and also the spring constant of thespring 55. - In
FIG. 6 , yet another embodiment of a frame/connector/footplate assembly made in accordance with the principles of the present invention illustrated. InFIG. 6 , aframe 62 is connected to aspring 65 at an ankle joint 63. In the embodiment depicted inFIG. 6 ,spring 65 is in the form of a torsional spring. However, other spring designs, such as a leaf spring, may be used. Thespring 65 is generally configured so that it may provide an ankle joint 63 having an axis of rotation that lies along the short axis of theframe 62. Thespring 65 may be constructed of a carbon fiber laminate or metal, for example. Thus, the amount of rotation of the footplate 69 about the ankle joint 63 may be limited by the spring constant for thespring 65. In this embodiment, aconnector 64 is also used. Thespring 65 and theconnector 64 are both attached to thefootplate 69. Rotation of theframe 62 within the ankle joint 63 may be constrained by providing that thespring 65 is adapted to frictionally receive theframe 62. Rotation of theframe 62 within theconnector 64 may be constrained by providing that theconnector 64 is adapted to frictionally receive theframe 62. The rotation of the footplate 69 may be limited by the coefficient of friction between theframe 62 and thespring 65, the coefficient of friction between theframe 62 and theconnector 64, or the spring constant of thespring 65, or combinations thereof. - In
FIG. 7 , a cross-sectional end view of a high profile multiaxialprosthetic foot 70 is shown. In this embodiment, theframe 72 is connected to aspring 74 by asetscrew 73. Thesetscrew 73 may fixedly attach thespring 74 to theframe 72 and limit or even prevent the rotation of theframe 72 within thespring 74. Aconnector 75 is adapted to rotationally receive theframe 72. Theconnector 75 is attached to thefootplate 79. Thespring 74 may abut thefootplate 79. - In
FIG. 8 , a cross-sectional end view of another embodiment of a prosthetic foot of the present invention is shown. In this embodiment, acontrol element 81 is adapted to receive aframe 82.Rotation stop control element 81. Also shown are aconnector 85 and afootplate 89. The rotation of the footplate 89 about its axis is limited by therotation stop footplate 89 may rotate either clockwise or counter-clockwise until reaching therotation stop rotation stop control element 81. The structure of therotation stop control element 81, and the related function of rotation control, are further described below with respect toFIG. 9 . - In
FIG. 9 , a side-view of a prosthetic foot incorporating aconnector 75, aspring 74 and acontrol element 81. Theframe 72 is connected to aspring 74 by asetscrew 73. Theconnector 75 is adapted to rotationally receive theframe 72. Theconnector 75 is also attached to the footplate 79 in a known manner. Thespring 74 may abut thefootplate 79. Thecontrol element 81 is adapted to receive theframe 72. In the preferred embodiment, thecontrol element 81 is rigidly attached to theframe 72. The control element includes arotation stop 87. The rotation of the footplate 89 about its axis is limited by therotation stop 87. A second rotation stop may be included as described above. Thefootplate 89 may rotate either clockwise or counter-clockwise until reaching a rotation stop. - In
FIG. 10 , yet another embodiment of a prosthetic foot of the present invention is illustrated. In this embodiment, aframe 112 is connected to aconnector 115, which in turn is attached to afootplate 119. In this embodiment, thefootplate 119 is formed to allow the use of aframe 112 wherein the angle between the short axis and the long axis of theframe 112 is greater than 90°. - In
FIG. 11 , yet another embodiment of a prosthetic foot of the present invention is illustrated. In this embodiment, aframe 112 is rotatably connected to aconnector 115, which in turn is fixedly attached to afootplate 119. Theframe 112 is connected to aspring 114. Thespring 114 may abut thefootplate 119. In this embodiment, thefootplate 119 is formed to allow the use of aframe 112 wherein the angle between the short axis and the long axis of theframe 112 is greater than 90°. -
FIG. 12 illustrates the ability of a prosthetic foot made in accordance with the principles of the present invention to provide medial-lateral rotation. InFIG. 12 , an end view of the prosthetic foot 10 is shown. As described in the previous embodiments, aframe 12 is connected to aconnector 15 at an ankle joint 13 with theconnector 15 being attached to afootplate 19. InFIG. 12 , the prosthetic foot is positioned on an inclined plane 11. This is analogous to a wearer of a prosthetic foot standing sideways on a hill. Thus, the longitudinal axis of thefootplate 19 is transverse to the direction of incline of the incline plane 11. It can be seen that the high profile multiaxial prosthetic foot of the present invention allows rotation in a medial-lateral direction, thus, stabilizing the footplate 19 in such a position. -
FIG. 13 likewise illustrates an embodiment of a prosthetic foot of the present invention positioned on an inclined plane 11. InFIG. 13 , there is further defined an angle θ. The angle θ is the angle formed between the plane of the incline and the long axis of theframe 12. Because of the orientation of the ankle joint 13, θ may effectively vary between 0 and 180°. - The prosthetic foot of the present invention may be adapted to provide adjustment of a frame with respect to a connector and a footplate. In
FIG. 14 a andFIG. 14 b, for example, aframe 112 is shown connected to aconnector 115. Theconnector 115 is attached to afootplate 119. One end of thefootplate 119 defines an imaginary vertical line v. A distance x1 is defined by the separation distance between v and the long axis of theframe 112. By positioning the long axis of theframe 112 closer to the connector 115 a second distance x2 may be defined between v and the long axis of theframe 112. The distance x1 is less than the distance x2. Thus, the position of the long axis of theframe 112 may be adjusted with respect to theconnector 115 and thefootplate 119. Along its longitudinal axis, thefootplate 119 defines a first end and a second end. Thus the position of the long axis of theframe 112 may be adjustably located with respect to the first end or the second end of thefootplate 119. The adjustable positioning of theframe 112 with respect to thefootplate 119 may accomplished, for example, by adjustably connecting theframe 112 to theconnector 115. Thus, the short axis of theframe 112 may be moved to a desired position along the longitudinal axis of thefootplate 119 and then fixed in position by theconnector 115 with respect to further movement along the longitudinal axis of the footplate. Referring toFIG. 7 , in one embodiment for example, theframe 72 may be adjustably positioned with respect to the footplate 79 as described above and this position fixed by tighteningsetscrew 73. - In
FIG. 15 , for example, aframe 112 is shown connected to aconnector 115. Theconnector 115 is attached to afootplate 119. Further illustrated is a residual limb 120. As known in the art, the residual limb is attached to a socket that is attached to theframe 112. The residual limb 120 defines a generally vertical axis v1. An angle θ1 is defined by the long axis of theframe 112 and v1. Thus it can be seen that θ1 may be varied to allow the residual limb 120 to be offset with respect to thefootplate 119. Thefootplate 119 can be seen to also define a top plane and a bottom plane. As illustrated inFIG. 15 , theconnector 115 is attached to thefootplate 119 at the top plane of thefootplate 119. Thus, the long axis of theframe 112 may be adjustably positioned with respect to the top plane so that the long axis defines an angle with respect to the top plane that is different than 90°. Referring toFIG. 7 , in one embodiment for example, theframe 72 may be adjustably positioned with respect to the footplate 79 as described above and this position fixed by tighteningsetscrew 73. - As is known in the art, the footplate of the prosthetic foot of the present invention may be covered with an anthropomorphic flexible polymer in the shape of a foot.
- The high profile multiaxial prosthetic foot made in accordance with the principles of the present invention allows free rotation of a prosthetic footplate about an axis that lies along the longitudinal axis of the footplate. Thus, such a prosthetic foot provides free rotation from 0 to 180° in a medial-lateral direction. A high profile multiaxial prosthetic foot made in accordance with the principles of the present invention further provides means to control the amount of rotation of the footplate. Thus, the present invention provides a high profile multiaxial prosthetic foot that allows true medial-lateral rotation as opposed to mere medial-lateral tilt.
- There has been provided in accordance with the present invention, a high profile multiaxial prosthetic foot providing stability for the user in conditions requiring medial-lateral rotation. While the invention has been described with specific embodiments, many alternatives, modifications and variations will be apparent to those skilled in the art in light of the forgoing description. Accordingly, it is intended to include all such alternatives, modifications and variations set forth within the spirit and scope of the appended claims.
Claims (20)
1. A prosthetic foot comprising:
a frame including an elongate, generally horizontal lower portion that extends along an axis;
a connector mounted to the lower portion, the connector being axially adjustable along the lower portion to a selected position along the lower portion;
and a footplate mounted to the connector to support the prosthetic on the ground.
2. The prosthetic foot of claim 1 , wherein the connector is mounted to the lower portion for rotation about said axis.
3. The prosthetic foot of claim 2 , further comprising a fastener to secure the connector at a selected axial position with respect to the lower portion of the frame.
4. The prosthetic foot of claim 3 , wherein the fastener is a set screw that extends through the connector and contacts the lower portion of the frame.
5. The prosthetic foot of claim 4 , wherein the lower portion is tubular, and wherein the connector includes at least one circular opening through which the lower portion extends.
6. The prosthetic foot of claim 2 , wherein the connector includes a spring that biases the connector toward a predetermined rotational position with respect to the lower portion.
7. The prosthetic foot of claim 1 , wherein the axis the lower portion and said footplate are generally oriented in a medial-lateral direction of the prosthetic foot.
8. A prosthetic foot comprising:
a frame including an elongate, generally horizontal lower portion that extends along an axis;
a connector mounted to the lower portion;
and a footplate mounted to the connector to support the prosthetic on the ground,
wherein the footplate is adjustable in an anterior-posterior direction relative to the lower portion.
9. The prosthetic foot of claim 8 , wherein the footplate is adjustable in an anterior-posterior direction relative to the connector.
10. The prosthetic foot of claim 8 , wherein the connector is adjustable in an anterior-posterior direction relative to the lower portion.
11. The prosthetic foot of claim 10 , further comprising a fastener to secure the connector at a selected axial position with respect to the lower portion of the frame.
12. The prosthetic foot of claim 11 , wherein the fastener is a set screw that extends through the connector and contacts the lower portion of the frame.
13. The prosthetic foot of claim 11 , wherein the lower portion is tubular, and wherein the connector includes at least one circular opening through which the lower portion extends.
14. The prosthetic foot of claim 8 , wherein the connector is mounted to the lower portion for rotation about said axis.
15. The prosthetic foot of claim 14 , wherein the connector includes a spring that biases the connector toward a predetermined rotational position with respect to the lower portion.
16. A prosthetic foot comprising:
a generally L-shaped frame;
a footplate;
a means for connecting the frame to the footplate,
wherein the connecting means keeps the frame at a substantially constant distance from the footplate while permitting the frame to pivot about an axis of rotation that is generally parallel to the longitudinal axis of the footplate; and
a means for varying the position of the frame along the axis of rotation.
17. The prosthetic foot of claim 16 ,
wherein the frame has an upper portion and a lower portion, and
wherein the connecting means has a bore defined therein, the lower portion of the frame being received into the bore.
18. The prosthetic foot of claim 16 , wherein the varying means is a set screw that inhibits the movement of the frame along the axis of rotation when tightened and that permits the movement of the frame along the axis of rotation when loosened.
19. The prosthetic foot of claim 16 ,
wherein the frame has an upper portion and a lower portion,
wherein the connecting means has a bore defined therein, the lower portion of the frame being received into the bore, and
wherein the varying means is a set screw that inhibits the movement of the frame along the axis of rotation when tightened and that permits the movement of the frame along the axis of rotation when loosened.
20. The prosthetic foot of claim 16 , further comprising a means for limiting the degree to which the frame pivots about the axis of rotation.
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US11/268,129 US20060064176A1 (en) | 2000-04-26 | 2005-11-07 | High profile multiaxial prosthetic foot |
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Cited By (1)
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---|---|---|---|---|
US8721737B2 (en) | 2011-02-03 | 2014-05-13 | Marquette University | Passive ankle prosthesis with energy return simulating that of a natural ankle |
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SE515958C2 (en) | 1999-06-10 | 2001-11-05 | Gramtec Innovation Ab | Device for a leg prosthesis provided with a foot |
US20080228288A1 (en) * | 2007-03-13 | 2008-09-18 | Ronald Harry Nelson | Composite Prosthetic Foot |
JP2008238711A (en) * | 2007-03-28 | 2008-10-09 | Fujifilm Corp | Hydrophilic member, and undercoating composition |
IT1393886B1 (en) * | 2009-05-04 | 2012-05-17 | Roadrunnerfoot Engineering S R L | PROSTHETIC FOOT TO WALK |
US8413313B2 (en) * | 2009-11-06 | 2013-04-09 | David Delon Williams | Divided-end artificial limb |
US20160175118A1 (en) * | 2014-12-18 | 2016-06-23 | Fountainhead, Llc | Prosthetic spacer devices, systems, and methods |
DE102017114892B3 (en) | 2017-07-04 | 2018-11-29 | Ottobock Se & Co. Kgaa | Prosthesis and prosthetic foot adapter |
Citations (28)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1334861A (en) * | 1919-02-11 | 1920-03-23 | Ole A Ingebrigtsen | Artificial ankle-joint |
US2692990A (en) * | 1953-09-29 | 1954-11-02 | Ernest R Schaefer | Ankle joint |
US4547913A (en) * | 1983-07-11 | 1985-10-22 | Flex Foot, Inc. | Composite prosthetic foot and leg |
US4822363A (en) * | 1985-08-01 | 1989-04-18 | Phillips L Van | Modular composite prosthetic foot and leg |
US4959073A (en) * | 1988-06-06 | 1990-09-25 | John Merlette | Foot prosthesis and method of making same |
US4994086A (en) * | 1989-08-09 | 1991-02-19 | United States Manufacturing Company | Universal modular frame for above-knee endoskeletal prosthesis |
US5116385A (en) * | 1991-05-06 | 1992-05-26 | Universite De Montreal | Medio-lateral control enhancing, cantilever-spring type prosthetic foot |
US5116383A (en) * | 1988-03-04 | 1992-05-26 | Chas. A. Blatchford & Sons Ltd. | Lowelimb prothesis |
US5116384A (en) * | 1990-08-31 | 1992-05-26 | Syncor, Ltd. | Prosthetic foot |
US5156631A (en) * | 1991-09-16 | 1992-10-20 | John Merlette | Foot and leg prosthesis and method of making same |
US5181933A (en) * | 1991-02-28 | 1993-01-26 | Phillips L Van | Split foot prosthesis |
US5201775A (en) * | 1990-04-20 | 1993-04-13 | Ohio Willow Wood Company | Adjustable lower limb prosthesis |
US5217500A (en) * | 1990-01-12 | 1993-06-08 | Phillips L Van | Prosthetic leg |
US5314499A (en) * | 1991-04-04 | 1994-05-24 | Collier Jr Milo S | Artificial limb including a shin, ankle and foot |
US5376141A (en) * | 1990-09-21 | 1994-12-27 | Phillips; Van L. | Low-profile symes foot prosthesis |
US5443527A (en) * | 1993-03-31 | 1995-08-22 | Wilson Michael T | Prosthetic food and three-way ankle joint |
US5486209A (en) * | 1989-04-13 | 1996-01-23 | Phillips; Van L. | Foot prosthesis having auxiliary ankle construction |
US5571212A (en) * | 1995-01-10 | 1996-11-05 | M+Ind (Model & Instrument Development Corporation | Prosthetic ankle joint for pivotally connecting a residual limb to a prosthetic foot |
US5593456A (en) * | 1994-05-17 | 1997-01-14 | Crp, Inc. | Foot and leg prosthesis and method of making same |
US5728176A (en) * | 1989-04-13 | 1998-03-17 | Flex-Foot, Inc. | Attachment construction for prosthesis |
US5766265A (en) * | 1985-08-01 | 1998-06-16 | Phillips; Van L. | Prosthetic foot having curved integral support |
US5800568A (en) * | 1996-02-16 | 1998-09-01 | Model & Instrument Development Corporation | Prosthetic ankle and walking system |
US5824112A (en) * | 1989-04-13 | 1998-10-20 | Phillips; Van L. | Prosthetic device incorporating low ankle design |
US6053946A (en) * | 1998-02-23 | 2000-04-25 | Wilkinson; Kerry E. | Flexible prosthetic foot apparatus |
US6206934B1 (en) * | 1998-04-10 | 2001-03-27 | Flex-Foot, Inc. | Ankle block with spring inserts |
US6228124B1 (en) * | 1997-09-08 | 2001-05-08 | Prosthetic Design, Inc. | Prosthetic foot with lateral and angular adjustability |
US6231618B1 (en) * | 1997-03-13 | 2001-05-15 | Prosthetic Design, Inc. | Prosthetic limb including an adjustable pyramidal link plate assembly |
US6261324B1 (en) * | 1999-05-26 | 2001-07-17 | Crp, Inc. | Foot prosthesis |
Family Cites Families (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB518258A (en) | 1939-04-26 | 1940-02-21 | J E Hanger And Company Ltd | An ankle joint for use in connection with an artificial foot |
FR2653327A1 (en) | 1989-10-23 | 1991-04-26 | Votrotto Remy | Prosthesis for a lower limb of the human body |
-
2000
- 2000-04-26 US US09/558,570 patent/US7044984B2/en not_active Expired - Fee Related
-
2001
- 2001-04-26 WO PCT/US2001/013364 patent/WO2001080787A1/en not_active Application Discontinuation
- 2001-04-26 EP EP01930764A patent/EP1276442A4/en not_active Withdrawn
- 2001-04-26 AU AU2001257269A patent/AU2001257269A1/en not_active Abandoned
-
2005
- 2005-11-07 US US11/268,129 patent/US20060064176A1/en not_active Abandoned
Patent Citations (32)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1334861A (en) * | 1919-02-11 | 1920-03-23 | Ole A Ingebrigtsen | Artificial ankle-joint |
US2692990A (en) * | 1953-09-29 | 1954-11-02 | Ernest R Schaefer | Ankle joint |
US4547913A (en) * | 1983-07-11 | 1985-10-22 | Flex Foot, Inc. | Composite prosthetic foot and leg |
US5766265A (en) * | 1985-08-01 | 1998-06-16 | Phillips; Van L. | Prosthetic foot having curved integral support |
US4822363A (en) * | 1985-08-01 | 1989-04-18 | Phillips L Van | Modular composite prosthetic foot and leg |
US5116383A (en) * | 1988-03-04 | 1992-05-26 | Chas. A. Blatchford & Sons Ltd. | Lowelimb prothesis |
US4959073A (en) * | 1988-06-06 | 1990-09-25 | John Merlette | Foot prosthesis and method of making same |
US5824112A (en) * | 1989-04-13 | 1998-10-20 | Phillips; Van L. | Prosthetic device incorporating low ankle design |
US5486209A (en) * | 1989-04-13 | 1996-01-23 | Phillips; Van L. | Foot prosthesis having auxiliary ankle construction |
US5728176A (en) * | 1989-04-13 | 1998-03-17 | Flex-Foot, Inc. | Attachment construction for prosthesis |
US5593457A (en) * | 1989-04-13 | 1997-01-14 | Phillips; Van L. | Foot prosthesis having auxiliary ankle construction |
US4994086A (en) * | 1989-08-09 | 1991-02-19 | United States Manufacturing Company | Universal modular frame for above-knee endoskeletal prosthesis |
US5217500A (en) * | 1990-01-12 | 1993-06-08 | Phillips L Van | Prosthetic leg |
US5201775A (en) * | 1990-04-20 | 1993-04-13 | Ohio Willow Wood Company | Adjustable lower limb prosthesis |
US5116384A (en) * | 1990-08-31 | 1992-05-26 | Syncor, Ltd. | Prosthetic foot |
US5376141A (en) * | 1990-09-21 | 1994-12-27 | Phillips; Van L. | Low-profile symes foot prosthesis |
US5776205A (en) * | 1991-02-28 | 1998-07-07 | Phillips; Van L. | Split foot prosthesis |
US5514185A (en) * | 1991-02-28 | 1996-05-07 | Phillips; Van L. | Split foot prosthesis |
US5181933A (en) * | 1991-02-28 | 1993-01-26 | Phillips L Van | Split foot prosthesis |
US5314499A (en) * | 1991-04-04 | 1994-05-24 | Collier Jr Milo S | Artificial limb including a shin, ankle and foot |
US5116385A (en) * | 1991-05-06 | 1992-05-26 | Universite De Montreal | Medio-lateral control enhancing, cantilever-spring type prosthetic foot |
US5156631A (en) * | 1991-09-16 | 1992-10-20 | John Merlette | Foot and leg prosthesis and method of making same |
US5443527A (en) * | 1993-03-31 | 1995-08-22 | Wilson Michael T | Prosthetic food and three-way ankle joint |
US5593456A (en) * | 1994-05-17 | 1997-01-14 | Crp, Inc. | Foot and leg prosthesis and method of making same |
US5571212A (en) * | 1995-01-10 | 1996-11-05 | M+Ind (Model & Instrument Development Corporation | Prosthetic ankle joint for pivotally connecting a residual limb to a prosthetic foot |
US5800568A (en) * | 1996-02-16 | 1998-09-01 | Model & Instrument Development Corporation | Prosthetic ankle and walking system |
US6231618B1 (en) * | 1997-03-13 | 2001-05-15 | Prosthetic Design, Inc. | Prosthetic limb including an adjustable pyramidal link plate assembly |
US6228124B1 (en) * | 1997-09-08 | 2001-05-08 | Prosthetic Design, Inc. | Prosthetic foot with lateral and angular adjustability |
US6053946A (en) * | 1998-02-23 | 2000-04-25 | Wilkinson; Kerry E. | Flexible prosthetic foot apparatus |
US6206934B1 (en) * | 1998-04-10 | 2001-03-27 | Flex-Foot, Inc. | Ankle block with spring inserts |
US6280479B1 (en) * | 1998-04-10 | 2001-08-28 | Flex-Foot, Inc. | Foot prosthesis having cushioned ankle |
US6261324B1 (en) * | 1999-05-26 | 2001-07-17 | Crp, Inc. | Foot prosthesis |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8721737B2 (en) | 2011-02-03 | 2014-05-13 | Marquette University | Passive ankle prosthesis with energy return simulating that of a natural ankle |
Also Published As
Publication number | Publication date |
---|---|
EP1276442A4 (en) | 2005-03-23 |
AU2001257269A1 (en) | 2001-11-07 |
WO2001080787A1 (en) | 2001-11-01 |
US7044984B2 (en) | 2006-05-16 |
US20020143407A1 (en) | 2002-10-03 |
EP1276442A1 (en) | 2003-01-22 |
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Legal Events
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STCB | Information on status: application discontinuation |
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