EP2091473A2 - Tige de prothèse à expulsion d'air active - Google Patents

Tige de prothèse à expulsion d'air active

Info

Publication number
EP2091473A2
EP2091473A2 EP07846339A EP07846339A EP2091473A2 EP 2091473 A2 EP2091473 A2 EP 2091473A2 EP 07846339 A EP07846339 A EP 07846339A EP 07846339 A EP07846339 A EP 07846339A EP 2091473 A2 EP2091473 A2 EP 2091473A2
Authority
EP
European Patent Office
Prior art keywords
prosthesis
shaft
pump
chamber
stump
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.)
Withdrawn
Application number
EP07846339A
Other languages
German (de)
English (en)
Inventor
Felix Carstens
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Otto Bock Healthcare GmbH
Original Assignee
Otto Bock Healthcare GmbH
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Otto Bock Healthcare GmbH filed Critical Otto Bock Healthcare GmbH
Publication of EP2091473A2 publication Critical patent/EP2091473A2/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/78—Means for protecting prostheses or for attaching them to the body, e.g. bandages, harnesses, straps, or stockings for the limb stump
    • A61F2/80—Sockets, e.g. of suction type
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/68—Operating or control means
    • A61F2/74—Operating or control means fluid, i.e. hydraulic or pneumatic
    • A61F2/742—Low pressure systems, e.g. vacuum pump
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/68—Operating or control means
    • A61F2/74—Operating or control means fluid, i.e. hydraulic or pneumatic
    • A61F2/748—Valve systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/78—Means for protecting prostheses or for attaching them to the body, e.g. bandages, harnesses, straps, or stockings for the limb stump
    • A61F2/7812—Interface cushioning members placed between the limb stump and the socket, e.g. bandages or stockings for the limb stump
    • A61F2/7843—Inflatable bladders
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • A61F2/60—Artificial legs or feet or parts thereof
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50—Prostheses not implantable in the body
    • 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
    • A61F2002/802—Suction sockets, i.e. utilizing differential air pressure to retain the prosthesis on the stump
    • A61F2002/805—Suction sockets, i.e. utilizing differential air pressure to retain the prosthesis on the stump having an air valve

Definitions

  • the invention relates to a prosthesis socket for use in an artificial replacement of an amputated limb according to the preamble of claim 1
  • a cup-shaped container of substantially rigid material is molded into the stump and shaped according to the rules of the prosthetic technique such that a painless transfer of forces on the amputation stump by this so-called prosthesis stem is possible.
  • the forces to be transmitted through the shaft generally consist of compressive and tensile forces as well as moments such as occur when using an arm on the hand. If the prosthesis replaces the loss of a portion of the lower limb, the forces are primarily due to the static and dynamic transmission of body weight during locomotion. In addition to these compressive forces as well as bending and rotational moments, but also in leg prostheses tensile forces that try to pull the prosthesis from the stump. This results already alone from the weight of the prosthesis, which triggers a pull on the leg stump when lifting the pothesis from the ground. In addition, there are the dynamic forces that arise when walking and running to a considerable extent.
  • the prosthetic stems Whenever possible, adjust the volume and the anatomical shape of the stump, taking into account the known knowledge of suitably modeled stem shapes, so that the pressure of the prosthesis stem is distributed under load to the largest possible area of the stump, and if possible no air gap between the stump and the stump Inner surface of the shaft is present.
  • the volume of an amputation stump can change significantly due to displacement of body fluid.
  • the otherwise so advantageous full contact stems mentioned above cause it by the desired uniform pressure on the stump during the loading phase, which is naturally higher because of the transfer of body weight forces higher than the normal ambient pressure, to considerable displacement of fluid in the stump and thus the stump volume decreases.
  • stump-shaft pseudarthroses Such reduced in volume stump not only allows unwanted movements between stump and shaft, so-called stump-shaft pseudarthroses, but can very quickly lead to significant problems for the prosthesis wearer, because the desired uniform pressure distribution is no longer guaranteed and the movement between stump and shaft can lead to rubbing and bruising.
  • the loss means of stump volume very often also the loss of the secure airtight connection to the shaft.
  • the present invention relates specifically to the prosthesis connection by suction, wherein the principle of the invention is independent of the nature of the proximal prosthesis seal, so the invention can be used in principle for all types of suction prostheses at different amputation heights.
  • the principle of the invention is independent of the nature of the proximal prosthesis seal, so the invention can be used in principle for all types of suction prostheses at different amputation heights.
  • prostheses to an amputation stump by negative pressure
  • a thermoplastic or a fiber composite plastic is usually used today.
  • the shanks are thermally molded onto a positive model of the prosthetic socket or cast over such a model with liquid plastic and fibrous layers between foils. The result is a substantially dimensionally stable cup-shaped shaft, which is airtight, or can be equipped airtight.
  • the shaft When the stump is inserted into such a shaft, it naturally displaces the air in the shaft. If it is ensured by suitable measures that no air can flow into the shaft, the shaft thus sucks like a suction cup on the stump, so can not readily, d. H. For example, not without opening a distally mounted in the shaft valve, be removed again.
  • the seal against unwanted ingress of air can be produced by various measures. For stumps with a large soft tissue portion, such as in many thigh stumps, often the uninterrupted contact of the skin with the inner wall surface of the prosthesis socket is sufficient.
  • the suction effect of the negative pressure results in a reduced relative movement between the shaft and skin (reduced stump-shaft pseudarthrosis), improved rotational stability of the prosthesis, a more precise guidance possibility of the prosthesis and, last but not least, improved proprioception for the prosthesis wearer correspondingly reduced foreign body sensation and increased safety.
  • Caspers describes the use of an active vacuum pump which is fluidly connected to the prosthesis stem to create a vacuum between the skin of the denture wearer and the interior of the stem.
  • Mechanical pumps are either incorporated into the prosthetic tube which establishes the connection of the prosthetic socket and artificial foot, or a mechanical pump is integrated into a resilient part of an artificial foot.
  • the pump is provided in any case outside the interior of the shaft and is connected by a flow channel, in the simplest case by a hose, with said interior of the prosthesis shaft.
  • the pumps are actuated by the fact that when walking the cyclic loading and discharge of the prosthesis is able to perform an active pumping work. For this purpose, a relative movement between at least two parts of such a mechanical pump is required.
  • a further disadvantage of the prior art systems is that in certain embodiments only certain components for constructing the prosthesis, for example only a very specific embodiment of the artificial foot, can be used, which considerably restricts the design possibilities of the prosthesis constructor.
  • All pumps which are used on the outside of a prosthesis stem, must overcome the forces to increase the volume, which act by the built-Druclcunter Kunststoff on the mutually movable parts of the pump.
  • the achievable vacuum is essentially dependent on the force with which the pump resets after a reduction in volume.
  • a typical ball pump will no longer return to its initial state in such use for sucking from a certain pressure difference but it will remain collapsed due to the suction forces.
  • the arrangement of the pump according to the invention erfhidungshunt in the interior of the prosthetic esophagus of great advantage because the volume-increasing force only compensate for flow pressure losses and not work against the pressure difference between the shaft interior and atmosphere, since the outside of the flexible wall of the pumping chamber is not of the higher atmospheric pressure is applied.
  • This force can be applied for example with a simple foam insert, a small spring, a flexible chamber material with restoring force or a Velcro connection for the transmission of tensile forces.
  • the pump can be designed very thin application of very light materials without high mechanical requirements, which is a great advantage for use in prostheses. Since in the opposite direction, ie in the direction of volume reduction of the pump chamber, both the pressure difference, to be pumped against, and against the restoring spring forces must be worked, the forces required for pumping in the inventive arrangement are correspondingly smaller, which is a further advantage and avoiding printing problems at the stump.
  • the object of the invention is achieved by the features mentioned in claim 1, wherein one or the combination of several subclaims represent different embodiments.
  • inventive measures a system for lowering the pressure in Gap space between an amputation stump and the stump receiving prosthesis shaft created under the level of atmospheric pressure, without the need for complex and heavy additional components outside of the prosthesis shaft are required.
  • the energy required to displace gas (air) against a higher pressure is derived from the momentum during use of the prosthesis.
  • the components of the present invention consist, for the most part, of either airtight film and open-cell foam, or are formed by two layers (63, 64) of an elastic die coating (55) which form a chamber (34) in the wall of the die coating.
  • the prosthesis according to the invention differs cosmetically hardly from conventional prostheses in a known design, and no voluminous additional parts must be integrated into the cosmetic appearance. Except the check valve (16) with the connecting element (14) and the flow channel (15) and possibly a second discharge valve (52) no additional components outside the shaft (2) are necessary for the realization of the invention. Accordingly, a prosthesis having the characteristics of the present invention can be constructed with all known combinations of adapters and other components, and the prosthesis builder is not dependent on using components specially adapted to the vacuum system, for example special artificial feet. All of these features provide significant advantages over the prior art.
  • the chamber can also be made of a flexible material with restoring force, which then can be dispensed with the foam insert.
  • a second, smaller in volume air chamber can be used to generate the necessary restoring forces. If the filling volume and thus the pressure in this second chamber is formed variable, the restoring force can be changed by changing the filling pressure of the second chamber.
  • the chamber (13) is fluidly connected via a second one-way valve (16) to the atmosphere.
  • the volume of the pump chamber (34) decreases as the chamber (13) is compressed. This increases the pressure in the chamber and air is blown off via the second one-way valve (16) into the atmosphere, whereby the gas volume and thus the pressure in the shaft is reduced.
  • the above-mentioned Puinphunt (13) is integrated into a shaft belonging to the elastic die coating, a so-called liner.
  • the elastically-restoring element can therefore be made significantly weaker and thus less expensive and lighter with the teachings of the present invention.
  • both the prosthesis stem must be impermeable to air, and that additional measures, which are known per se and not the subject of the present invention, must be taken to prevent air from entering through the Proximal open side of the prosthetic socket to prevent.
  • this can be achieved with lower leg prostheses, for example, by pulling a tubular elastic covering of an airtight material with elastic pretension from the outside of the prosthesis shaft over the knee onto the skin of the thigh and resting there without a gap.
  • Thigh stumps with naturally large soft tissue portion can seal without additional measures by appropriate shaft design against air ingress, the suction effect is highly dependent on the constancy of the stump volume.
  • Fig. 1 an amputation stump in the region of the lower leg in a corresponding lower leg prosthesis with the features of claim 1 of the invention consisting of a prosthesis stem with an adapter connected via an adapter and an extension element artificial foot, the pump according to the invention with one-way valves and an airtight coating from the outside of the shaft to the thigh.
  • the shaft and the tubular cover are cut sagittally to show the pump.
  • the stump fits into the prosthetic socket without gaps.
  • FIG. 2 shows the prosthesis from FIG. 1 in the sagittal section, wherein the stump is wrapped in a known cup-shaped elastic coating, a so-called liner.
  • FIG. 6 A preferred embodiment of the prosthesis stem with ejection pump.
  • the pumping bladder and its interacting components are shown in section. Of the prosthesis stem is only a section through the part of the shaft wall shown in the pumping bladder is installed.
  • Fig. 6 A preferred embodiment of the prosthesis stem with ejection pump.
  • the pumping bladder and its interacting components are shown in section. Of the prosthesis stem is only a section through the part of the shaft wall shown in the pumping bladder is installed.
  • FIG. 5 A sectional view of an embodiment of a one-way valve, as provided in the pumping bladder of Fig. 5 in the interior of the Einsaugöffhung.
  • Fig. 1 shows the invention using the example of a cut in the sagittal plane lower leg prosthesis (1).
  • the shank (2) which receives and is adapted to the stump (3), is substantially cup-shaped with an open-topped end (4) and a bottomed closed bottom end (5).
  • the shaft (2) has an inwardly directed inside (6) and an outwardly directed outside (7).
  • the inside (6) forms a cup-shaped space (8), which receives the stump (1).
  • the shaft (2) is connected via an adapter (9) attached thereto with a tubular extension part (10) with an artificial foot (11).
  • the bulge (12) is certainly not necessary in all cases, but is to avoid / on pressure points advantageous. It is just so deep that the flexible pumping bladder (13), which will be described in more detail below, in the compressed state, fills the space formed by the bulge (12) and thus does not enter the interior space (8). it protrudes shank (2) and causes pressure points on the stump (3).
  • the pumping bladder (13) is connected airtight with a tubular channel (14) which breaks the wall of the shaft (2) and which in this way forms a flow passage from the interior of the pumping bladder through the shaft wall.
  • an elastic coating (20) of a cuddly aterial for example, silicone, PUR or TPE provided, which with its inner side (22) m on the outside (7) of the shaft (2) rests and with this a sealing surface forms, on the other hand forms a second sealing surface in that the coating (20) fits snugly against the skin (24) of the thigh (25) and conforms to this sealing.
  • a cuddly aterial for example, silicone, PUR or TPE provided, which with its inner side (22) m on the outside (7) of the shaft (2) rests and with this a sealing surface forms, on the other hand forms a second sealing surface in that the coating (20) fits snugly against the skin (24) of the thigh (25) and conforms to this sealing.
  • the exemplary embodiment of the invention shown relates to a prosthesis for treatment after a lower leg amputation.
  • the invention is not limited to a certain amputation level, but is analogously applicable to prosthetic restorations other amputation heights.
  • the stump with bare skin is inserted into the stem, or whether the stump has a protective or cushioning liner 17 of a conformable material, for example of an elastomer, advantageously of silicone , PUR or TPE, as shown in Fig. 2 - also in a section in the sagittal plane - shown.
  • a protective or cushioning liner 17 of a conformable material for example of an elastomer, advantageously of silicone , PUR or TPE, as shown in Fig. 2 - also in a section in the sagittal plane - shown.
  • Such liners are known to the expert in various designs. Since these elastic liners closely conform to the skin of the stump and, as a result of the system, there is no air gap between the skin of the stump and the inside (18) of the liner (17), the negative pressure generated in the shaft interior (8) by the pump (13) transfer the stump even if the liner (17) is not gas-permeable.
  • FIG. 3 shows such a situation with reference to the prosthesis already shown in FIG. 1 in a sagittal section. Between the skin (21) of the stump (3) and the inside (6) of the shaft (2) is shown a gap (26) filled with air.
  • Fig. 4a and Fig. 4b the two load situations of a step cycle are shown in Fig. 4a and Fig. 4b shortly before lifting the toe (27) (Fig. 4a) and shortly after placing the heel (28).
  • a reaction moment M VF which acts as a bending moment on the system stump prosthesis and which causes the proximal edge of the prosthesis (4) to be strongly pressed against the tibia (30) in the area of the knee, whereby the pressure on the calf decreases.
  • Fig 4a this is indicated by the fact that in the dorsal region of the shaft, ie between calf (29) and rear shaft inner wall (6), a gap (26) is drawn.
  • the pumping bladder (13) is not compressed and inflated due to the elastic insert to a maximum possible volume.
  • stump-shaft pseudarthrosis a position at which the relative movements between the stump and shaft, referred to by those skilled in the art as stump-shaft pseudarthrosis, as they arise through the use of the prosthesis are greatest, so that the actuation of the pump, as below is explained in more detail, as large as possible.
  • a lower leg prosthesis this is easily seen, as in the embodiment of the invention from Figs. 4a and 4b, the proximal shaft region.
  • a pumping bladder 13 is provided by way of example in the dorsal and proximal shaft region.
  • one or more pump bubbles in the shaft at other locations.
  • an elongated pumping bladder of approximately 5 cm to 12 cm in length and approximately 4 cm to 8 cm in width on both sides of the tibial bone in the shaft.
  • pump bubbles can all work independently of one another, or they can co-operate in a cascade. The latter arrangement is not sketched and will only be described here. It is useful if the pump bubbles due to design a certain dead space, ie a volume that can not be further reduced, have.
  • the dead space limits according to the laws of gas physics the maximum possible pressure difference between the suction side of the pump and the discharge side, which in the pumps in connection with the present invention, the side with the higher pressure, characterized in that the air volume in the pump bubble at the initial pressure after whose operation fills the dead space at a pressure which is at most equal to the pressure on the outside, in the present case, therefore, the atmospheric pressure.
  • the air in the pump is so in this state when they are actuated so only cyclically compressed and relaxed again.
  • At least two pumping bubbles (13) are connected in series in such a way that the one-way valve (16) at the outlet of the first pumping bladder (13), which is arranged, for example, in the region of the calf (29), at the same time as an inlet valve (37) at the inlet opening (36) of an at least second pumping bladder (13), which is arranged, for example, opposite in the tibial region (30). Only the outlet opening (38) of this second pumping bladder is then connected in the manner described with a flow channel (14) through the skirt wall (51) to the outside via a hose (15) and an outflow valve (16) to the atmosphere.
  • This arrangement has the advantage that the amount of air in the second pumping bladder is increased by the displaced air from the first pump bladder. As a result, the possible pressure difference is greater by the pumping action at a fixed dead space.
  • the object of the invention is to transport existing air out of the shaft in a gap between the outside of an amputation stump and the inside of a prosthesis shaft and, if appropriate, a buffer volume in fluid communication therewith, and in the mentioned gap a negative pressure to create.
  • a buffer volume in fluid communication therewith, and in the mentioned gap a negative pressure to create.
  • a system which is able to compress gas molecules via a force that is exerted over a certain actuation path, ie to increase the pressure in order to counteract the molecules to shift the atmospheric pressure from a lower pressure level into the atmosphere.
  • a chamber-shaped pumping bladder (13) which encloses a pumping space (34).
  • the pumping bladder (13) is made of flexible, air-impermeable membrane and possible embodiments and preferred arrangements will be described in more detail with reference to FIGS. 5, 6 and 7 or FIGS. 10 and 11.
  • the pumping bladder (13) has an elongated oval shape in the embodiments shown in FIGS. 1-4, the longer side being approximately parallel to the vertical axis of the prosthesis.
  • the short side measures about 5 to 8 cm and the longer side about 8 to 12 cm.
  • Fig. 5 shows the pump from the preceding figures enlarged in a section.
  • the pump consists of an inwardly facing layer (31) and an outwardly facing layer (32) of flexible film, which at the edge over the entire Circumferentially welded airtight or materially connected, which is indicated in Fig. 5 with (33).
  • suitable film materials would include, but are not limited to, PUR or PVC, which are known to be readily joined by HF or thermal welding techniques.
  • the two welded foils (31 and 32) must enclose a space (34) whose content is greater than zero and here referred to as the pumping space. For this it is necessary that the two films are brought into a certain distance from each other. This is achieved in the simplest way, that the pump space (34) is at least partially filled with a foam material (35).
  • the above-described stump shaft non-union in this embodiment can exert only a compressive force FD in the arrow direction and not in the opposite direction, a resilient element must be provided to return the pump bubble back into your Strukturforrn ,
  • the foam (35) is also provided, which is suitably open-cell, so that air can flow through.
  • an opening (36) is provided, which in the example shown consists only of a hole in the film, through which air from the interior of the shaft (8) via a one-way valve (37), which is even more accurate below is described in the interior (34) of the pumping bladder (13) can flow.
  • a channel (54) is provided as a flow channel, so that the opening can not be blocked unintentionally.
  • a second opening (38) is provided, through which air from the interior space (34) can reach the flexible film bubble into a flow channel (39) when the volume of this space is reduced due to a force F D.
  • This channel (39) consists in the example shown of a tube (14) which airtight manner with the shaft wall (51), for example, by lamination so connected, so that no air can pass between the outside of the tube and the shaft wall.
  • the tube (14) protrudes about 5 mm into the interior (8) of the shaft (2).
  • a ring (40) made of an elastic material, such as rubber, airtight, for example by gluing with the film (32) is provided.
  • the inner diameter (42) of the ring (40) is aligned with the opening (38) in the pumping bladder and is slightly smaller than the outer diameter of the tubular flow channel (14).
  • the pumping bladder (13) by simply plugging on the inwardly projecting part of the tube (41) fixed frictional and positive and are connected airtight when the surface pairing suitable and the elastic bias due to the differences in diameter large enough is.
  • the ring (40) with the pipe end (41) in a manner shown materially connected, for example by gluing, airtight.
  • a protective coating (74) is provided which, for example, consists of an air-permeable textile which spans the entire pump bladder (13) in terms of surface area and which overlies the skirt wall in the area (75). material or form-fitting, for example, by gluing, is connected.
  • the coating has the task of protecting the pump bladder from mechanical damage, and at the same time acts as a dust filter and thus prevents a functional impairment of the one-way valves (37) and (16) due to contamination.
  • the protective cover is not shown in the other figures. Fig.
  • FIG. 6 shows an exemplary embodiment of a one-way valve (37), as in the interior (34) of the pumping bladder (13) in the region of the inlet opening (36) is mounted such that a flow connection from the shaft interior (8) through the opening (36). in the foil of the pumping bladder through the one-way valve (37) and through at least one further opening (45) on the one-way valve.
  • the flow direction is illustrated in Fig. 6 by an arrow (StR).
  • the housing (46) of the one-way valve (37) is connected to the inside of the film (32), for example by gluing or welding in the edge region (47).
  • a membrane (48) for example made of silicone foil, covers the opening (36) and is pressed lightly onto the opening (36) by an open-cell flexible foam insert (49).
  • a per se known one-way valve is formed.
  • the membrane (48) is pressed even more firmly against the opening (36), so that no air can pass through.
  • the one-way valve (37) must be such that the smallest possible pressure difference Ap for opening in the flow direction (StR) is sufficient. This can be achieved by measures known per se for one-way valves.
  • the embodiment shown in Fig. 6 is only one embodiment for a one-way valve may, but in no way limits the present invention to this embodiment.
  • Fig. 7 essentially shows the one-way valve of Fig. 6 with a hose connection (50) for use as a discharge valve (16) in communication with the flow channel (15).
  • Fig. 8 shows the inside (6) facing side of the prosthesis stem (2) of an embodiment of the erfmdungs proper pumping bubble (13) with the above-described sealing ring (40) to the opening (38), and the opening (36) with the Inner side directed one-way valve (37), which is shown as dashed lines in this view invisible element.
  • the opening (36) is in this embodiment, as already shown in Fig. 5, not directed directly to the inside of the shaft (8) but to the inside (6) of the skirt wall (51) out. This has proved to be advantageous because it avoids that the opening is accidentally closed by the skin of the stump (21) or its coating (17).
  • FIG. 9 shows a frontal view of a section of the inside (6) of the skirt wall (51) in the region of the position of the pump bladder (13), which is outlined by the outline (53).
  • the channel (54) extends in the region where the Einsaugöffhung (36) of the pumping bladder (13) comes to lie and it protrudes beyond the extension region (53) of the pumping bladder (13). This ensures that the suction opening (36) of the pump bladder can not be covered and sealed by the otherwise smooth inner wall (6) of the shank (2).
  • other measures such as an intermediate layer of a coarse textile between the pump (13) and shaft inner wall (6) are possible in order not to block the flow opening (36) unintentionally.
  • FIG. 10 shows a further embodiment of the invention. It is merely a section through the shaft with the stump therein. The presentation of the remaining components of a prosthesis has been omitted since these are not essential for the understanding of the invention.
  • a pumping plunger made of an elastic and flexible material, for example of silicone, TPE or PUR, together with a connecting device (56) and an airtight cup-shaped container (58) of a substantially rigid material, which is similar to the embodiment of Figs. 1 to 5 the type of amputation and the stump conditions is adapted according to the known rules of prosthesis construction, a unit as a prosthesis stem according to the invention (57).
  • the detachable connection between the stiff shaft portion and the flexible elastic portion is necessary for applying the prosthesis.
  • the flexible pump plunger (55) before getting into the stiff shaft portion as a conventional liner in a known manner rolled up the stump.
  • the connecting device (56) serves to connect the flow channel (60) or (77) of the pumping line with the atmosphere, but at the same time to prevent air from entering the interior (8) of the cup-shaped container (58).
  • the pumping coupler (55) is selected such that it is always somewhat smaller in circumference than the stub (3), so that it must be rolled up onto the stump (3) with elastic prestressing and become gripped Stump (3) snuggles over the entire surface.
  • the stump is inserted into the rigid shaft portion (58) after application of the pumping fin (55).
  • a tubular Pin (76) is provided, which forms a flow channel (77) which is sketched via a one-way valve (59), which is sketched in the drawing as a spring-loaded ball in a valve seat and is not described in detail as a known element, with a further flow channel (60). connected is.
  • the example tubular flow channel (60) opens with the one-way valve (59) opposite end in the pump chamber (34) of a variable in volume pumping bladder (13).
  • the pumping bladder (13) and the flow channel (60) are located within the wall (62) of the pumping fin (55).
  • the wall (62) is divided in the region of the pumping space (34), so that in each case approximately half the wall thickness forms the inside (63) or the outside (64) of the pumping space (34).
  • the flow channel (60) is formed, for example, by inserting a placeholder that does not adhere to the base material during the vulcanization of the pumping line. The placeholder can be pulled out after vulcanization, creating a tubular channel. The insertion of a hose would be another way to form the flow channel (60) in the wall of the pump cleaner.
  • the canal is tubular and should always be consistent with normal use of the prosthesis. A lumen of 1 to 3 mm in diameter is sufficient.
  • the liner from a plurality of layers, wherein the layers are materially bonded there, where no cavities or flow channels are desired.
  • Another manufacturing variant would be to insert the pumping chamber and the necessary flow channels prefabricated in a tool for producing the Pupliners and thus vulcanize or embed in plastic.
  • a rigid part (65) is cast at the distal end, through which the flow channel (60) leads, which receives the one-way valve (59) and in which the tube (76) is fixed.
  • the Verbmdungs learned (56) is arranged centrally as possible at the closed end (5) of the cup-shaped container (58) and consists of the tubular flow channel (76) and the seal (66), which is designed here as an O-ring, and an airtight Connection between the hard adapter (65) at the distal end of the pumping fin (55) and the shaft bottom (5) produces.
  • the opening (78) in the shaft bottom is sealed with this arrangement against ingress of air as soon as the stump (3) with the pumping plunger (55) is fully inserted in the container (58)
  • the air gap (26), which is exaggerated for clarity in the drawing, is thus sealed from the outside of the prosthesis, and it can not penetrate air.
  • a flexible tubular coating (20) for sealing the outer side (7) of the shaft (58) with the Skin of the thigh (24) provided.
  • an elastically resilient element for example an open-cell foam (35) is provided, which elastically resets the pump chamber as described above. Accordingly, the function of this embodiment of the invention is analogous to the embodiment shown above.
  • a further one-way valve (67) which is formed in the simplest way from a membrane (68), which in front of an opening (69) which in turn connects the pumping space (34) with the interior of the shaft (8), allows the refilling of Pump space (34) with air from the shaft interior (8) then to whom the elastic insert (35) again pushes the elastic and flexible walls of the pump chamber and thus increases the volume of the pump chamber. If necessary, for example, by a recess (54) in the surface of the inner side (6) of the skirt wall (51) as already described in Fig. 5, to ensure that the opening (69) is not laid by the shaft wall. By cyclic repetition of the air pressure in the interior (8) of the shaft (57) is lowered further and further.
  • the above explanations apply to this embodiment of the invention in full analog.
  • several pumping chambers can be provided with corresponding valves and channels in this embodiment, working individually or in cascade.
  • An additional buffer volume can also be provided as described above.
  • FIG. 11 shows an embodiment of the invention similar to that of FIG. 10.
  • the pump chamber (34) for the return of the pump no elastically resilient element is provided, but the outside (70) of the outwardly facing wall (FIG. 31) of the pumping bladder in the pumping plunger (55) is equipped with a self-adhesive means (71, 72)) whereby a detachable connection to the inside (6) of the dimensionally stable shaft portion (58) can be produced.
  • the pumping pump in the pump chamber consists of a flexible material with restoring force, or that in the pump chamber (34) of the pumping bladder (13) a chamber-shaped molding of appropriate flexible material Resetting force is located.
  • the pump chamber deforms again after deformation by external forces solely by the restoring force of the material after removing the deforming forces back to their initial state, can on a foam insert or on a Verbmdungs observed for transmitting tensile forces, as shown in FIG 11 described, be waived.
  • the elastic return of the pumping space (34) of the pumping chamber (13) of the pumping fin (55) can be achieved by an inserted air chamber of smaller volume analogous to the above.
  • FIGS. 10 and 11 additionally show a flow channel (73) which balances the pressure between the space delimited by the inside (18) of the liner and the skin (21) of the stump and the space between the outside (19) of the liner, the inside (6) of the rigid shaft portion (58) and the inside (22) of the coating (20) permits.

Landscapes

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

Abstract

L'invention concerne une tige de prothèse en forme de cuve, réalisée en matériau étanche à l'air et essentiellement rigide, comportant des éléments d'étanchage contre l'entrée d'air depuis le côté proximal ouvert, ladite tige étant destinée à l'emploi dans des prothèses pour le remplacement de membres. L'intérieur de la tige comporte au moins un système de pompe de telle manière que des mouvements relatifs entre le moignon et la tige, produits lors de l'utilisation de la prothèse, provoquent une expulsion d'air hors de l'espace intérieur de la tige de prothèse au moyen de canaux d'écoulement et de soupapes unidirectionnelles, vers le côté extérieur de la tige de prothèse. L'effet de pompe est obtenu par variation de volume d'une chambre composée de feuilles flexibles ou élastiques, se trouvant à proximité du moignon dans son extension maximale. La chambre est fixée à la paroi intérieure d'une tige de prothèse rigide, ou intégrée à la paroi d'un revêtement de moignon amovible, flexible et élastique, disposé en tant que partie de la tige de prothèse entre le moignon et une structure rigide.
EP07846339A 2006-11-20 2007-11-15 Tige de prothèse à expulsion d'air active Withdrawn EP2091473A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102006054891A DE102006054891A1 (de) 2006-11-20 2006-11-20 Prothesenschaft mit aktivem Luftausstoß
PCT/DE2007/002064 WO2008061500A2 (fr) 2006-11-20 2007-11-15 Tige de prothèse à expulsion d'air active

Publications (1)

Publication Number Publication Date
EP2091473A2 true EP2091473A2 (fr) 2009-08-26

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EP07846339A Withdrawn EP2091473A2 (fr) 2006-11-20 2007-11-15 Tige de prothèse à expulsion d'air active

Country Status (6)

Country Link
US (1) US20100070051A1 (fr)
EP (1) EP2091473A2 (fr)
CN (1) CN101594837A (fr)
DE (2) DE102006054891A1 (fr)
RU (1) RU2009123469A (fr)
WO (1) WO2008061500A2 (fr)

Families Citing this family (40)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8034120B2 (en) 2002-12-20 2011-10-11 Ossur Hf Suspension liner system with seal
US11523917B2 (en) 2002-12-20 2022-12-13 Ossur Hf Suspension liner system with seal
US10322016B2 (en) 2002-12-20 2019-06-18 Ossur Iceland Ehf Adjustable seal system, seal component and method for using the same
US9877851B2 (en) 2002-12-20 2018-01-30 Ossur Hf Adjustable seal system, seal component and method for using the same
US7927378B2 (en) * 2007-03-05 2011-04-19 Scussel Sbj Systems, Llc Vacuum assisted prosthetic sleeve and socket
US10842653B2 (en) 2007-09-19 2020-11-24 Ability Dynamics, Llc Vacuum system for a prosthetic foot
US8382852B2 (en) 2008-06-10 2013-02-26 Alps Intellectual Property Management, Llc Prosthetic liner with perspiration elimination mechanism
US8808394B2 (en) * 2008-06-10 2014-08-19 Alps South, LLC Prosthetic liner with perspiration elimination mechanism
US8113235B2 (en) 2008-10-03 2012-02-14 David Robert Bogue Apparatus and methods for facilitating prosthesis donning, doffing, retention, and fit
GB0822590D0 (en) * 2008-12-11 2009-01-21 Materialise Nv Orthotic prosthetic cushioned device and method of making the same
WO2010085336A1 (fr) 2009-01-21 2010-07-29 Craig Mackenzie Gaine d'étanchéité pour revêtement intérieur prothétique et procédés apparentés
US8679194B2 (en) 2009-01-21 2014-03-25 Evolution Industries, Inc. Expulsion liner for prosthetic or orthotic devices and associated methods
US9017420B1 (en) * 2010-01-08 2015-04-28 Frederick S. Bernhardt Inflatable interface for use between a limb liner and a limb prosthesis
RU2458609C1 (ru) * 2011-03-04 2012-08-20 Игорь Николаевич Васянин Искусственная мышца, способ ее изготовления и компенсирующий костюм
EP2726025B1 (fr) * 2011-07-01 2019-03-27 Orthocare Innovations Llc Système d'emboîture d'équilibre
US8956422B2 (en) 2011-08-22 2015-02-17 Ossur Hf Suspension liner with seal component
DE102011119591B3 (de) * 2011-11-29 2013-05-29 Otto Bock Healthcare Gmbh Prothese mit einer peristaltischen Pumpe
US9198780B2 (en) 2012-02-14 2015-12-01 Ossur Hf Vacuum assisted suspension system
EP2844195B1 (fr) 2012-04-30 2019-03-20 Össur HF Dispositif prothétique, système et procédé pour accroître une attache de mise au vide
DE102012017214A1 (de) * 2012-08-31 2014-05-15 Otto Bock Healthcare Gmbh Prothesenliner und Prothesenschaftsystem mit Prothesenliner und Prothesenschaft
WO2014134381A1 (fr) * 2013-03-01 2014-09-04 Ossur Hf Système de suspension à vide
DE102013009196A1 (de) 2013-06-03 2014-12-04 Otto Bock Healthcare Gmbh Prothesenliner und Prothesenschaftsystem mit Prothesenliner und Prothesenschaft
WO2016003711A1 (fr) 2014-07-01 2016-01-07 Ossur Hf Mécanisme de pompe pour système de suspension sous vide
DE102014010683B4 (de) 2014-07-22 2021-08-19 Ottobock Se & Co. Kgaa Liner für eine Prothese
US10028845B2 (en) 2015-01-08 2018-07-24 Ossur Iceland Ehf Pump mechanism
CN104771252A (zh) * 2015-04-14 2015-07-15 江先利 一种假肢装置
WO2016187608A1 (fr) 2015-05-21 2016-11-24 Ossur Iceland Ehf Système de pompe
WO2016196081A1 (fr) 2015-05-29 2016-12-08 Ossur Iceland Ehf Système de pompe destiné à être utilisé avec un dispositif prothétique
EP3340941B1 (fr) 2015-08-27 2021-11-10 Ossur Iceland EHF Système de pompe
EP3824851A1 (fr) 2015-10-15 2021-05-26 Össur Iceland EHF Système d'étanchéité réglable
US10517746B2 (en) 2016-03-21 2019-12-31 Comfort Products, Inc. Air control system for enhancing a connection between a limb liner and a limb prosthesis
EP3238667B1 (fr) 2016-04-25 2018-10-10 Össur Iceland EHF Enveloppe destinee a recouvrir un moignon
US10512554B2 (en) 2016-08-26 2019-12-24 Ossur Iceland Ehf Pump system
DE102017106903B3 (de) * 2017-03-30 2018-07-19 Otto Bock Healthcare Gmbh Liner für eine Prothese
US10945865B2 (en) 2017-11-01 2021-03-16 Ossur Iceland Ehf Prosthetic socket sealing system
US11510793B2 (en) 2017-11-28 2022-11-29 Ossur Iceland Ehf Adjustable seal system, seal component and method for using the same
US11224527B2 (en) * 2018-01-30 2022-01-18 Alps South Europe, S.R.O. Interchangeable pump-lock for prosthetic socket and method of use
US20190298553A1 (en) * 2018-03-29 2019-10-03 Open Bionics Ltd Prosthetic limbs
DE102018131550A1 (de) * 2018-12-10 2020-06-10 Ottobock Se & Co. Kgaa Orthopädietechnische Einrichtung
DE102021107816A1 (de) * 2021-03-29 2022-09-29 Ottobock Se & Co. Kgaa Orthopädietechnischer Schaft und Verfahren zu dessen Einstellung

Family Cites Families (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1893853A (en) * 1931-12-15 1933-01-10 Amos E Tullis Artificial limb
DE2127269A1 (de) * 1971-06-02 1972-12-14 Helfrecht, Manfred, 8591 Poppenreuth Einlage fur Kunstgheder
DE2729800A1 (de) * 1977-07-01 1979-01-04 Walter Dr Med Surerus Doppelventil zum einbau in prothesensaugschaefte mit ringfoermiger stuetzeinlage
US6149691A (en) * 1998-06-26 2000-11-21 Fay; John N. Self-inflating socket having encased gel
US6926742B2 (en) * 1999-06-03 2005-08-09 Otto Bock Healthcare Lp Plate/socket attachment for artificial limb vacuum pump
DE10142492A1 (de) * 2001-08-30 2003-04-03 Carstens Orthopaedie Und Mediz Prothesenschaft mit Dichtung
US6544292B1 (en) * 2002-04-08 2003-04-08 Aldo A. Laghi Prosthetic liner with integral air expulsion valve

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO2008061500A2 *

Also Published As

Publication number Publication date
WO2008061500A2 (fr) 2008-05-29
WO2008061500A3 (fr) 2008-07-31
RU2009123469A (ru) 2010-12-27
DE112007003292A5 (de) 2009-10-22
DE102006054891A1 (de) 2008-06-05
CN101594837A (zh) 2009-12-02
US20100070051A1 (en) 2010-03-18

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