WO1998056320A1 - Shock- and torque absorber in a leg prothesis - Google Patents
Shock- and torque absorber in a leg prothesis Download PDFInfo
- Publication number
- WO1998056320A1 WO1998056320A1 PCT/SE1998/001015 SE9801015W WO9856320A1 WO 1998056320 A1 WO1998056320 A1 WO 1998056320A1 SE 9801015 W SE9801015 W SE 9801015W WO 9856320 A1 WO9856320 A1 WO 9856320A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- resilient member
- telescopic
- parts
- telescopic part
- movement
- Prior art date
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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
- A61F2/76—Means for assembling, fitting or testing prostheses, e.g. for measuring or balancing, e.g. alignment means
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- A—HUMAN NECESSITIES
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2/60—Artificial legs or feet or parts thereof
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2/60—Artificial legs or feet or parts thereof
- A61F2/64—Knee joints
-
- A—HUMAN NECESSITIES
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/50—Prostheses not implantable in the body
- A61F2/78—Means for protecting prostheses or for attaching them to the body, e.g. bandages, harnesses, straps, or stockings for the limb stump
- A61F2/80—Sockets, e.g. of suction type
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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
- A61F2/02—Prostheses implantable into the body
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- A61F2002/30003—Material related properties of the prosthesis or of a coating on the prosthesis
- A61F2002/30004—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis
- A61F2002/30014—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis differing in elasticity, stiffness or compressibility
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- A—HUMAN NECESSITIES
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- A61F2002/30004—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis
- A61F2002/30016—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis differing in hardness, e.g. Vickers, Shore, Brinell
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- 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
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- 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
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- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2220/0033—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements made by longitudinally pushing a protrusion into a complementary-shaped recess, e.g. held by friction fit
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2220/0041—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements using additional screws, bolts, dowels or rivets, e.g. connecting screws
-
- 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
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0017—Angular shapes
- A61F2230/0021—Angular shapes square
-
- 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
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0018—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in elasticity, stiffness or compressibility
-
- 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
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0019—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in hardness, e.g. Vickers, Shore, Brinell
Definitions
- the present invention refers to a device in a leg prosthesis provided with a shock- and torque absorber intended to absorb shocks as well as rotational movements which occur when the foot hits the ground during walking, running, jumping etc. and comprising two parts which are telescopically displaceable and rotatable with respect to each other and provided with damping means.
- a shock absorber in a leg prosthesis should be able to absorb linear as well as rotational forces which occur at heel strik when the foor hits the ground during activities such as walking, running, jumping etc.
- the shock damping function of the artificial foot and sometimes also of the artificial knee is often unsufficient.
- Such shock absorbers which normally are placed in the lower leg part of the prosthesis often consist of hydraulic or pneumatic devices, which are relatively complicated and expensive.
- the object of the present invention is to provide a device of the kind mentioned above, which can absorb shocks as well as torques and which has a simple and reliable construction.
- the shock absorber should further be simple to adjust in order to exert different counter pressures depending on the weight of the prosthesis wearer and the type of activity that is carried out, e g the counter pressure should be higher at running than at walking.
- the first resilient member can be exchangeable and be of different hardness degrees. The same thing applies to the second resilient member.
- Fig. 1 is a vertical section through a first embodiment of the invention.
- Fig. 2 is a sction according th the line II-II in Fig. 1.
- Fig. 3 is a corresponding section as Fig. 2 but showing the device in a loaded position.
- Fig. 4 is a vertical section through a second embodiment of the invention.
- Fig. 5 is a vertical section through a third embodiment of the invention.
- Fig. 6 is a vertical section according to Fig. 5 but taken at an angle displaced
- Fig. 7 is a corresponding section as Fig. 6 but showing the device in a loaded position.
- Fig. 8a-c show schematically different disposals of the device according to the invention in leg prostheses.
- Fig. 9 illustrates schematically how a mechanic counter movement is created in the device which prevents obliqueness at an uneven load.
- the prosthesis comprises two telescopic parts 10 and 11 displaceable within each other and rotateable with respect to each other.
- a first resilient member 12 in the form of a block of rubber, polyurethane or similar material is clamped between the parts 10 and 11 and is arranged to be compressed when the parts 10 and 11 are displaced in a retracting direction.
- the first resilient member 12 is clamped between a nut 13 screwed into the upper outer telescopic part 10 and a support surface 14 on a housing member 15 formed in the lower inner telescopic mamber 11.
- the resilient member 12 extends through a tubular portion 16 of the telescopic member 11, said portion has a somewhat larger cross sectional area than the resilient member 12 in the unloaded position thereof (Fig. 1 and 2). By this a limited expansion of the resilient member 12 across the compression direction thereof is admitted when the telescopic parts 10 and 11 are pressed into each other (Fig. 3) upon an axial loading thereof. When the load is ceased the resilient member 12 returns to its initial position.
- the nut 13 can be tightened against the resilient member 12 in different degrees in order to vary the counter pressure exerted when the telescopic parts 10, 11 are pressed into each other when the prosthesis is exerted to shocks.
- the counter pressure can need to be varied depending on the weight of the prosthesis wearer and the type of activity that is carried out, e g the counter pressure should be higher at running than at walking.
- the housing member 15 of the telescopic part 11 is provided with a hollow space 17 extending across the housing member.
- the hollow space 17 has a larger extension in axial than in radial direction which can be seen from Fig. 2 and 3.
- a bolt 18 extends through this hollow space 17, said bolt is attached to the outer telescopic part 10.
- a resilient sleeve 19 is arranged about the bolt 18, said sleeve constituting a second resilient member.
- a metal sleeve 20 having a square outer cross section can possibly be arranged between the resilient sleeve 19 and the bolt 20.
- the hole for the bolt 18 in the wall of the outer telscopic member 10 is sufficiently large for the resilient sleeve 19 to be removed through said hole, e g in order to exchange it for another sleeve having a different degree of hardness.
- the relative displacement of the telescopic parts 10 and 11 is limited by the axial length of the hollow space 17.
- the second resilient member 19 has in unloaded position a very limited mobility in radial direction in the hollow space 17, which means that also rotational movements between the telescopic members 10 and 11 are elastically damped. At a torsional force right - left the resilient member 19 is compressed and admits depending on elastic stiffness and torsionla force a rotation of between 0-30° with a gradually increasing resistance. When the force ceases the resilient member 19 returns to its initial position and forces thereby the telescopic parts 10 and 11 to return to its initial position.
- the second resilient member 19 can be exchangeable for another member having a different elastic degree of stiffness and by that vary the resistance exerted against rotational movements between the telescopic parts 10 and 11.
- the first resilient member 12 is divided in two portions, an upper 12a and a lower portion 12b, separated by a disc 27 of a hard material, e g metal or nylon.
- the two portions 12a and b are of different elastic degrees of stiffness, at which the upper portion 12a preferably is of a harder and the lower portion 12b of a softer material.
- the lower softer portion 12b will be compressed first and expand in radial direction.
- the space in the tubular part 16 only admits a limited expansion of the lower part 12b for protecting this from being overcompressed.
- a compression of the upper harder portion 12a is started at a further compression to the end position where the movement is caught and limited by the second resilient member 19.
- the embodiment shown in Fig. 5-7 differs from the one described above through the way of adjusting the first resilient member 12. While in the above described embodiment this adjustment only can be made when the prosthesis has been taken off, it is in the embodiment shown in Fig. 4-6 possible to adjust the prestressing from the outside of the prosthesis also when this is on.
- the first resilient member 12 is in this case clamped between an end wall 21 of the outer telescopic part 10 and a plate 22 connected to a rod 23 which is axially displaceable in the inner telescopic part 11.
- the rod has a lower oblique surface 24, which cooperates with a corresponding oblique surface 25 of an adjustment screw 26 inserted in radial direction in the telescopic part 11. By tightening the adjustment screw 26 the rod 23 is pressed upwards at which the plate 22 is tightened against the first resilient member and increases the prestressing thereof.
- Fig. 8 a-c it is shown how the leg prosthesis part according to the invention can be palced in different types of leg prostheses.
- Fig. 8a is shown how it can be mounted in an upper leg prosthesis below the mechanic knee joint.
- Fig. 8b it is mounted in an upper leg prosthesis above the mechanic knee joint and in Fig. 8c it is mounted in a lower leg prosthesis.
- the leg prosthesis part consisting of the two telescopic parts 10 and 11 are at first hand intended to be mounted below the knee joint, which either is a mechanical or a natural knee joint, as is shown in Fig. 8b and c.
- the resilient members 12 and 19 can by this absorb shocks as well as torsional forces which occur at heel strike when walking, running, jumping etc.
- the two resilient members 12 and 19 keep in unloaded position the two telescopic parts 10 and 11 in a fixed position.
- the resilient members also act as energy ackumulators as the energy stored in them at the compression is returned at toe off when the foot leaves the ground, at which the shock absorbers expand to their initial position. The energy consumption when walking or running is by this minimized.
- a further advantage with the shock- and torque absorber according to the invention is that one obtains an automatic tilting compensation when the prosthesis is unevenly loaded.
- a problem always occurring in short telescopic elements is that they due to the short support bearing have a tendency to seize when the inner telescopic part is heavily loaded from the side and tilts in its bearings. Such a tendency to seizing is very . unpleasant in a leg prosthesis and gives a hard and jerky movement up and down.
- the critical moment is when the shock absorber is compressed and in a position with the loading on the toe section.
- the prosthesis wearer is in a position to unload the shock absorber by lifting the foot from the floor. Due to the lateral force in the loading there is a risk for seizing between the telescopic parts. At unloading the telescopic parts can be pushed apart with a sudden jerk when the lateral force is reduced and the resilient damping element momentaneously can overcome the friction in the seizing position.
- an autmatic mechanical counter movement which counteracts such an obliquity and which creates a force which all the time strives for maintaining the largest bearing surfaces of the inner telescopic member 11 in parallel.
- the hollow space 17 contributes to that the inner telescopic part 11 forms a flexible unit having two leg portions 11a, l ib on either side of the hollow space 17, which due to a certain resiliency in the material can be somewhat displaced with respect to each other at an uneven load.
- the force at the arrow a passes up through the inner telescopic part 11 and pushes the leg 11a upwards according to the arrow b.
- the second leg 1 lb is forced downwards according to the leg d.
- This displacement causes the part 16 to slightly tilt according to the arrow c.
- This tilting movement is counteracted by the small bearing 10a for the part 16 and forces the inner telescopic part 11 to straighten the obliquity in the big bearing 10b in the outer telescopic movement 10.
- the friction is somewhat increased in the small bearing 10a, but due to the considerably smaller diameter therein and by this a longer bearing surface with respect to diameter, this bearing is less sensitive to tiling.
- the total contact surface is also smaller and gives a considerably lower friction than the big bearing. 10b.
- Another important friction reducing function is also that the thin- walled big bearing 10b of the upper telescopic member 10 during lateral loading will circually shape itself after the inner telescopic part 11 and by this distributes the loading better and reduces the risk for a high surface pressure on the bearing.
Abstract
Description
Claims
Priority Applications (8)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP50109399A JP3987584B2 (en) | 1997-05-30 | 1998-05-28 | Shock / torque absorber on artificial leg |
CA002291629A CA2291629C (en) | 1997-05-30 | 1998-05-28 | Shock and torque absorber in a leg prothesis |
EP98926013A EP0984747B1 (en) | 1997-05-30 | 1998-05-28 | Shock- and torque absorber in a leg prothesis |
US09/424,827 US6302918B1 (en) | 1977-05-30 | 1998-05-28 | Shock-and torque absorber in a leg prothesis |
DK98926013T DK0984747T3 (en) | 1997-05-30 | 1998-05-28 | Shock and torsion damper in a leg prosthesis |
AU77941/98A AU7794198A (en) | 1997-05-30 | 1998-05-28 | Shock- and torque absorber in a leg prothesis |
AT98926013T ATE232705T1 (en) | 1997-05-30 | 1998-05-28 | SHOCK ABSORBER AND TORQUE LIMITER IN A PROSTHESIS LEG |
DE69811490T DE69811490T2 (en) | 1997-05-30 | 1998-05-28 | SHOCK ABSORBER AND TORQUE LIMITER IN ONE LEG PROSTHESIS |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
SE9702077-0 | 1997-05-30 | ||
SE9702077A SE514778C2 (en) | 1997-05-30 | 1997-05-30 | Shock and rotary damper for leg prosthesis |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1998056320A1 true WO1998056320A1 (en) | 1998-12-17 |
Family
ID=20407198
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/SE1998/001015 WO1998056320A1 (en) | 1977-05-30 | 1998-05-28 | Shock- and torque absorber in a leg prothesis |
Country Status (11)
Country | Link |
---|---|
US (1) | US6302918B1 (en) |
EP (1) | EP0984747B1 (en) |
JP (1) | JP3987584B2 (en) |
AT (1) | ATE232705T1 (en) |
AU (1) | AU7794198A (en) |
CA (1) | CA2291629C (en) |
DE (1) | DE69811490T2 (en) |
DK (1) | DK0984747T3 (en) |
ES (1) | ES2192326T3 (en) |
SE (1) | SE514778C2 (en) |
WO (1) | WO1998056320A1 (en) |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP1275355A1 (en) * | 2001-06-29 | 2003-01-15 | Otto Bock HealthCare GmbH | Torsion device for exoprosthesis |
US7169190B2 (en) * | 1998-04-10 | 2007-01-30 | Van L. Phillips | Active shock module prosthesis |
Families Citing this family (15)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6468315B1 (en) * | 2001-04-09 | 2002-10-22 | Kerry E. Wilkinson | Prosthetic apparatus with elastomeric shock absorber element |
US6820866B2 (en) * | 2001-08-10 | 2004-11-23 | Goodbar Llc | Attenuator apparatus |
US6488717B1 (en) | 2001-08-24 | 2002-12-03 | Mccoll Mack Edward | Prosthetic leg |
US6969408B2 (en) * | 2003-09-30 | 2005-11-29 | Ossur Engineering, Inc. | Low profile active shock module prosthesis |
GB2411841B (en) * | 2004-03-12 | 2006-08-09 | Univ London | Prosthetic limb attachment |
ATE402674T1 (en) * | 2004-04-22 | 2008-08-15 | Bock Healthcare Lp | VACUUM PUMP WITH SHOCK ABSORPTION AND CONTROLLED ROTATION FOR PROSTHETIC DEVICES |
US7101403B2 (en) * | 2004-05-28 | 2006-09-05 | Sen-Jung Chen | Vibration-absorbing device for an artificial lower limb |
ATE509598T1 (en) * | 2005-01-13 | 2011-06-15 | Oessur Hf | DAMPING DEVICE FOR A PROSTHESIS |
ATE529638T1 (en) * | 2007-08-01 | 2011-11-15 | Bock Healthcare Gmbh | VACUUM PUMP AND USE OF A VACUUM PUMP |
US8317877B2 (en) | 2008-08-18 | 2012-11-27 | The Ohio Willow Wood Company | Prosthetic foot |
US9265626B1 (en) | 2011-05-31 | 2016-02-23 | össur hf | Height-adjustable threaded shock absorbing module and associated coupling member |
US8915970B2 (en) | 2013-02-08 | 2014-12-23 | Biomet Manufacturing, Llc | Transdermal prosthesis |
US10531968B2 (en) * | 2014-05-23 | 2020-01-14 | Joseph Coggins | Prosthetic limb test apparatus and method |
US10898350B2 (en) | 2015-11-24 | 2021-01-26 | University Of South Carolina | Dynamic linear adjustable prosthetic |
US20220362040A1 (en) * | 2021-05-14 | 2022-11-17 | Willowwood Global Llc | Shock absorber system for a prosthesis |
Citations (4)
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US3842443A (en) * | 1972-08-30 | 1974-10-22 | Watkins L | Resilient pivot joint for an artificial leg |
US4186449A (en) * | 1977-04-04 | 1980-02-05 | Otto Bock Orthopadische Industrie Kg | Swivel joint |
EP0413450A1 (en) * | 1989-08-15 | 1991-02-20 | CHAS. A BLATCHFORD & SONS LIMITED | Artificial limb component |
DE19642719A1 (en) * | 1995-10-17 | 1997-04-24 | Goemed Orthopaedie Service Gmb | Insert piece for prosthesis |
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US3906552A (en) * | 1972-08-30 | 1975-09-23 | Watkins Lloyd J | Pivot joint adapter |
US4038705A (en) * | 1976-07-30 | 1977-08-02 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Rotational joint assembly for the prosthetic leg |
US4134159A (en) * | 1977-06-09 | 1979-01-16 | Wilson Michael T | Torque absorber for artificial limbs |
CA1246301A (en) * | 1985-11-15 | 1988-12-13 | Guy G. Martel | Above knee leg prosthesis |
CA2057108C (en) * | 1991-12-05 | 1996-12-31 | Kelvin B. James | System for controlling artificial knee joint action in an above knee prosthesis |
NL9400733A (en) | 1994-05-04 | 1995-12-01 | Ambroise Holland Bv | Prosthesis. |
GB2305363B (en) | 1995-09-22 | 1999-06-30 | Blatchford & Sons Ltd | Shin prosthesis |
US5961556A (en) | 1996-12-31 | 1999-10-05 | Lord Corporation | Prosthetic suspension unit having elastomeric energy storage units |
US5800562A (en) * | 1997-09-08 | 1998-09-01 | Wilkinson; Kerry E. | Prosthetic apparatus for absorbing shocks |
-
1997
- 1997-05-30 SE SE9702077A patent/SE514778C2/en unknown
-
1998
- 1998-05-28 WO PCT/SE1998/001015 patent/WO1998056320A1/en active IP Right Grant
- 1998-05-28 AU AU77941/98A patent/AU7794198A/en not_active Abandoned
- 1998-05-28 CA CA002291629A patent/CA2291629C/en not_active Expired - Fee Related
- 1998-05-28 EP EP98926013A patent/EP0984747B1/en not_active Expired - Lifetime
- 1998-05-28 AT AT98926013T patent/ATE232705T1/en not_active IP Right Cessation
- 1998-05-28 ES ES98926013T patent/ES2192326T3/en not_active Expired - Lifetime
- 1998-05-28 DK DK98926013T patent/DK0984747T3/en active
- 1998-05-28 JP JP50109399A patent/JP3987584B2/en not_active Expired - Fee Related
- 1998-05-28 DE DE69811490T patent/DE69811490T2/en not_active Expired - Lifetime
- 1998-05-28 US US09/424,827 patent/US6302918B1/en not_active Expired - Lifetime
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3842443A (en) * | 1972-08-30 | 1974-10-22 | Watkins L | Resilient pivot joint for an artificial leg |
US4186449A (en) * | 1977-04-04 | 1980-02-05 | Otto Bock Orthopadische Industrie Kg | Swivel joint |
EP0413450A1 (en) * | 1989-08-15 | 1991-02-20 | CHAS. A BLATCHFORD & SONS LIMITED | Artificial limb component |
DE19642719A1 (en) * | 1995-10-17 | 1997-04-24 | Goemed Orthopaedie Service Gmb | Insert piece for prosthesis |
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7169190B2 (en) * | 1998-04-10 | 2007-01-30 | Van L. Phillips | Active shock module prosthesis |
EP1275355A1 (en) * | 2001-06-29 | 2003-01-15 | Otto Bock HealthCare GmbH | Torsion device for exoprosthesis |
DE10131159A1 (en) * | 2001-06-29 | 2003-01-23 | Bock Healthcare Gmbh | Torsion device of an exoprosthetic system |
US6827343B2 (en) | 2001-06-29 | 2004-12-07 | Otto Bock Healthcare Gmbh | Torsion device of an exoprosthesis |
Also Published As
Publication number | Publication date |
---|---|
SE9702077L (en) | 1998-12-01 |
DE69811490T2 (en) | 2003-12-18 |
CA2291629C (en) | 2005-09-06 |
DE69811490D1 (en) | 2003-03-27 |
AU7794198A (en) | 1998-12-30 |
SE9702077D0 (en) | 1997-05-30 |
CA2291629A1 (en) | 1998-12-17 |
JP2002508683A (en) | 2002-03-19 |
ES2192326T3 (en) | 2003-10-01 |
SE514778C2 (en) | 2001-04-23 |
JP3987584B2 (en) | 2007-10-10 |
DK0984747T3 (en) | 2003-06-10 |
EP0984747B1 (en) | 2003-02-19 |
ATE232705T1 (en) | 2003-03-15 |
EP0984747A1 (en) | 2000-03-15 |
US6302918B1 (en) | 2001-10-16 |
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