WO2021261942A1 - Articulation artificielle du genou - Google Patents

Articulation artificielle du genou Download PDF

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Publication number
WO2021261942A1
WO2021261942A1 PCT/KR2021/007976 KR2021007976W WO2021261942A1 WO 2021261942 A1 WO2021261942 A1 WO 2021261942A1 KR 2021007976 W KR2021007976 W KR 2021007976W WO 2021261942 A1 WO2021261942 A1 WO 2021261942A1
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WO
WIPO (PCT)
Prior art keywords
axis
knee joint
artificial knee
shaft
joint
Prior art date
Application number
PCT/KR2021/007976
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English (en)
Korean (ko)
Inventor
김보일
Original Assignee
김보일
(주)보일랩스
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Application filed by 김보일, (주)보일랩스 filed Critical 김보일
Publication of WO2021261942A1 publication Critical patent/WO2021261942A1/fr

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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
    • A61F2/64—Knee 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
    • 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
    • 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
    • A61F2002/5007—Prostheses not implantable in the body having elastic means different from springs, e.g. including an elastomeric insert
    • 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
    • A61F2002/5016—Prostheses not implantable in the body adjustable
    • A61F2002/5018—Prostheses not implantable in the body adjustable for adjusting angular orientation
    • 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
    • A61F2002/5096—Ball-and-socket joints
    • A61F2002/5098—Ball-and-socket joints with rotation-limiting means
    • 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
    • A61F2002/6818—Operating or control means for braking
    • 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
    • A61F2002/6854—Operating or control means for locking or unlocking a joint

Definitions

  • the artificial knee joint is the most important component of the prosthetic leg, and in order to secure the wearer's safety and realize a natural gait, it should be able to provide an appropriate braking force according to each stage of the gait cycle. Accordingly, it is necessary to implement the movement of the artificial knee joint to which the prosthetic leg is mounted to be as similar as possible to the movement of the actual knee joint.
  • the artificial knee joint is configured to be fixed to the human body and is formed such that the upper joint member through which the first axis passes, the first axis, the A axis, and the third axis pass, and the first axis is the center of the artificial knee joint.
  • the T-shaped member includes a front portion to which the first elastic member is coupled and an A through portion through which the A axis passes, a second through portion through which the second axis passes, and a first protrusion protruding in the lateral direction. It further includes a rear portion formed.
  • the artificial knee joint is configured to be fixed to the human body and is formed so that the first axis passes through the upper joint member, the first axis passes through, and is rotatable with the upper joint member about the first axis a body portion connected to be connected to the prosthetic leg, and a lower joint member configured to be fixed to the prosthetic leg and connected to the body portion through a link member, the upper joint member having second protrusions on both sides, the body portion and the second protrusion are come into contact with each other in the process.
  • the first elastic member of the artificial knee joint when a load of the prosthetic wearer is applied, the first elastic member of the artificial knee joint is vertically compressed by the load, and the impact that can be applied to the artificial knee joint and the body of the prosthetic leg wearer and the It can distribute and/or absorb the load evenly. Accordingly, it is possible to protect the body of the prosthetic wearer and minimize fatigue that may occur during walking.
  • 1 is an exemplary diagram illustrating a gait cycle of a person.
  • Figure 4 is a side view of the artificial knee joint disclosed in Figure 3;
  • FIG. 5 is a perspective view of the main body illustrated in FIG. 3 .
  • FIG. 6 is a perspective view of the T-shaped member shown in FIG.
  • FIG. 7 is a perspective view of the upper joint member disclosed in FIG.
  • FIG. 8 is a side view showing the swing phase flexion state of the artificial knee joint disclosed in FIG. 3 .
  • FIG. 10 is a perspective view showing the configuration of the artificial knee joint except for the upper joint member disclosed in FIG.
  • FIG. 11 is a perspective view illustrating a support member to which a second elastic member is coupled according to an embodiment of the present disclosure
  • FIG. 14 is an exemplary view illustrating a process in which the T-shaped member and the first link member operate by eccentricity according to an embodiment of the present disclosure.
  • 15 is an exemplary view showing that the artificial knee joint according to an embodiment of the present disclosure is in a stance phase flexion state.
  • FIG. 17 is a side view of the artificial knee joint disclosed in FIG. 16 .
  • FIG. 18 is a perspective view of the upper joint member of the artificial knee joint disclosed in FIG. 16 .
  • the artificial knee joint is designed to generate a braking force in the knee extension direction when the leg to which the prosthetic is mounted is in a stance phase.
  • bending of the artificial knee joint is limited, and the artificial knee joint can support the weight of the prosthetic leg wearer by realizing the actual knee stance phase flexion.
  • the stance phase flexion means bending of the knee made in the stance phase process. As shown in Figure 1, stance phase flexion is made within a relatively small angle range compared to swing phase flexion.
  • the stance phase flexion at the beginning and/or the end of the stance phase may have a smaller angle compared to the middle phase of the stance phase.
  • the knee of the pedestrian moves in the walking direction You can see that it is bent.
  • the angle at which the knee is bent is smaller than the angle at which the knee is completely bent in the stance phase middle stage (b).
  • the artificial knee joint In the case of stance phase flexion at the initial stage (a) and/or the end stage (d) of the stance phase, the artificial knee joint has to be slightly bent with a predetermined angle in the walking direction, so it is difficult to implement naturally.
  • the wearer of the prosthetic leg puts the sole of the foot on the ground or pushes the ground for walking, abnormal motions such as excessive bending of the artificial knee joint or sudden knee bending unintentionally by the prosthetic leg wearer may occur.
  • the artificial knee joint 200 includes an upper joint member 210 , a lower joint member 220 , a main body 230 , a first link member 240 and a second link member 250 . can do.
  • the upper joint member 210 may be configured to be fixed to the human body.
  • the upper joint member 210 is, as shown, the coupling portion 212 is formed in the upper portion of the wearer's body (eg, not cut) and coupled to the socket (2) can be coupled. have.
  • the upper joint member 210 and the socket 2 may be integrally configured.
  • the upper joint member 210 and the lower joint member 220 are combined with the body portion 230 , the first link member 240 , and the second link member 250 to be folded to have a predetermined angle.
  • the artificial knee joint 200 is bent or stretched according to the gait cycle to provide an appropriate braking force.
  • the coupling structure of the artificial knee joint 200 will be described in detail with reference to FIGS. 3 and 4 .
  • FIG. 3 is a perspective view of the artificial knee joint 200 according to an embodiment of the present disclosure
  • FIG. 4 is a side view of the artificial knee joint 200 disclosed in FIG. 3
  • FIG. 5 is a perspective view of the main body 230 illustrated in FIG. 3
  • FIG. 6 is a perspective view of the T-shaped member 310 shown in FIG. 3
  • FIG. 7 is a perspective view of the upper joint member 210 shown in FIG. 3 .
  • the artificial knee joint 200 may include an upper joint member 210 , a lower joint member 220 , a main body 230 , a first link member 240 , and a second link member 250 .
  • the upper joint member 210, the first shaft 410 is passed.
  • the upper joint member 210 may be connected to the main body 230 through the first shaft 410 .
  • the upper joint member 210 is configured such that the first_3 through portion 710 is formed at a position corresponding to the 1_1 through portion 510 and the 1_2 through portion 512 of the body portion 230 . can be, and the 1_3 penetration part 710 of the upper joint member 210 and the 1_1 penetration part 510 and the 1_2 penetration part 512 of the body part 230 are rotated by the first shaft 410 possible to be connected.
  • Each of the T-shaped members 310 and 312 may be configured to be rotatably coupled to the main body 230 through the second shaft 420 and the A-axis 460 through the A-axis 460 .
  • the T-shaped members 310 and 312 may be formed in a T-shaped shape.
  • the T-shaped member includes a front portion 610 to which the first elastic member 470 is coupled, and a rear portion 620 in which the second through portion 622 , the A through portion 624 and the first protrusion 626 are formed.
  • the second shaft 420 may pass through the second through portion 622 .
  • a axis 460 may pass through A through portion 624 .
  • the upper surface of the front part 610 may be formed at an obtuse angle with the upper surface of the rear part 620 in order to prevent the artificial knee joint 200 from being excessively bent or sudden knee bending unintended by the prosthetic leg wearer. have.
  • the upper surface of the front part 610 may be formed to have an inclination from an upper direction to a lower direction.
  • a first elastic member 470 is coupled to the front part 610 to provide an elastic restoring force in a direction opposite to the direction in which the load is applied in order to disperse the impact caused by the load.
  • an opening 612 may be formed in the front portion 610 , and the first elastic member 470 may be coupled to the opening 612 by a screw method.
  • one end of the first elastic member 470 may be coupled to the opening 612 of the front part 610 in a screw form, and the other end may be in contact with the receiving part 520 of the body part 230 .
  • the first elastic member 470 may be coupled to the opening 612 by the fixing member 330 .
  • the main body 230 may further include accommodating parts 520 and 522 for accommodating at least a portion of the first elastic member 470 .
  • the accommodating parts 520 and 522 are the first accommodating part 520 and the second accommodating part 522 formed in a direction perpendicular to the upper surface direction of the front part 610 of the T-shaped member 310 .
  • each of the first elastic members 470 is disposed between the front portion 610 and the body portion 230 of the T-shaped member, and when a load is applied to the artificial knee joint 200, the shock caused by the load is distributed. In order to do this, it is possible to provide an elastic restoring force in a direction opposite to the direction in which the load is applied.
  • the first protrusion 626 formed on the rear part 620 of the T-shaped member 310 is a wire 340 to control the movement of the T-shaped member 310 when a load is applied to the artificial knee joint 200 . It may be connected to the first shaft 410 through . According to an embodiment, the first protrusion 626 may protrude from the inside to the outside and be connected to the end 320 of the first shaft 410 by the wire 340 . At this time, a locking groove may be formed on the outer peripheral surface of each of the first protrusion 626 and the end 320 of the first shaft 410 to catch the wire 340 .
  • the wire 340 may be, for example, a spring having an S-shape, as shown in FIGS. 3 and 4 .
  • the T-shaped member 310 may be rotatably coupled to the main body 230 about the A-axis 460 .
  • each T-shaped member 310 may be formed with an A through portion 624 through which the A axis 460 passes.
  • the A-axis 460 is more effective than the first protrusion 626 in the walking direction ( It may be disposed forward in the direction of the arrow shown in FIG. 6 .
  • the body portion 230 may have an A receiving portion formed at a position corresponding to the A through portion 624 formed in each T-shaped member 310 so as to be coupled to the T-shaped member 310 .
  • the A accommodating part may include an A_1 accommodating part 540 through which the A axis 460 passes, and an A_2 accommodating part (not shown) formed in a rear position corresponding to the A_1 accommodating part.
  • the A_1 accommodating part 540 and the A_2 accommodating part (not shown) may be formed on the outer surface of the main body 230 along the y-axis direction, as shown in FIG. 5 .
  • the A axis 460 passes through the A through portion 624 of the T-shaped member 310 and the A receiving portion of the body 230, and the T-shaped member 310 and the body portion ( 230) may be rotatably coupled to each other. Therefore, when each T-shaped member 310 is coupled with the main body 230 and an abnormal operation is about to occur in the stance phase, the T-shaped member 310 is rotated at a predetermined angle about the A-axis 460. By rotating, it is possible to prevent the movement of the second axis 420 and the third axis 430 to prevent the artificial knee joint 200 from being excessively bent, or from sudden knee bending unintended by the prosthetic leg wearer. have.
  • the main body 230 may be coupled to the lower joint member 220 through the first link member 240 and the second link member 250 to provide an appropriate braking force according to each stage of the gait cycle.
  • the second shaft 420 may pass through one end of the first link member 240 .
  • the second shaft 420 also passes through the second through portion 622 of the T-shaped member 310 of the body portion 230, whereby the first link member 240 and the T-shaped member 310 are They may be rotatably coupled to each other.
  • the third shaft 430 may pass through one end of the second link member 250 .
  • the third shaft 430 also passes through the third through portions 530 and 532 of the main body 230, whereby the second link member 250 and the main body 230 are rotatably coupled to each other. can be
  • the lower joint member 220 is configured such that the fourth shaft 440 and the fifth shaft 450 pass through to be coupled to the body portion 230 through the first link member 240 and the second link member 250 .
  • the fourth axis 440 is based on the walking direction rather than the first axis 410 in order to prevent the artificial knee joint 200 from being excessively bent or sudden knee bending unintended by the prosthetic leg wearer. It can be placed backwards.
  • the fourth shaft 440 may pass through the other end of the first link member 240 .
  • the fourth shaft 440 also passes through the lower joint member 220, whereby the first link member 240 and the lower joint member 220 may be rotatably coupled to each other.
  • the fifth shaft 440 may pass through the other end of the second link member 250 .
  • the fifth shaft 440 also passes through the lower joint member 220, whereby the second link member 250 and the lower joint member 220 may be rotatably coupled to each other.
  • FIG. 8 is a side view showing a swing phase flexion state of the artificial knee joint 200 according to an embodiment of the present disclosure. It is a side view showing a state in which the artificial knee joint 200 is bent in the walking direction.
  • the main body 230 of the artificial knee joint 200 has a first link member 240 and a second link member 250 .
  • the second axis 420 and the third axis 430 may rotate around the knee in a folded form.
  • the artificial knee joint 200 may implement actual swing phase flexion (bending) of the knee, and may provide an appropriate braking force according to the gait cycle.
  • the knee bending direction may mean a rotation direction in which the artificial knee joint 200 is bent.
  • FIG. 9 is an exemplary diagram illustrating the operation of the artificial knee joint 200 when a load is applied to the artificial knee joint 200 according to an embodiment of the present disclosure.
  • the load of the prosthetic leg wearer is applied to the artificial knee joint 200 in the direction of the arrow indicated at the top of FIG. 5 , the first protrusion 626 of the T-shaped member and the end 320 of the first shaft of the main body 230 are connected.
  • Tension is formed on the wire 340 (indicated by an arrow) to prevent the T-shaped members 310 and 312 from malfunctioning (eg, the T-shaped members 310 and 312 are separated from the main body 230).
  • the first elastic member 470 may be vertically compressed by the load. For this reason, the first elastic member 470 evenly distributes and/or absorbs the shock and load that can be applied to the artificial knee joint 200 and the body of the prosthetic leg wearer to protect the body of the prosthetic leg wearer, and may occur when walking. fatigue can be minimized.
  • FIG. 10 is a perspective view showing the configuration of the artificial knee joint except for the upper joint member disclosed in FIG. 11 is a perspective view illustrating a support member 1010 to which a second elastic member 1110 is coupled according to an embodiment of the present disclosure
  • FIG. 12 is an operation of the support member 1010 according to an embodiment of the present disclosure. It is an example diagram shown.
  • the main body 230 is coupled to the support member 1010 and the support member 1010 in contact with the second link member 250 during the standing period, and a second elastic member ( 1110) may be further included.
  • the second elastic member 1110 may be coupled to the lower portion of the support member 1010 as shown in FIG. 11 .
  • an opening 550 may be formed so that a portion of the support member 1010 to which the second elastic member 1110 is coupled is inserted.
  • the opening 550 may be formed to have a constant inclination.
  • the support member 1010 may be inserted into the opening so that a lower portion of the support member 1010 to which the second elastic member 1110 is coupled comes into contact with the second link member 250 may be disposed.
  • the opening 720 may be formed so that the position adjustment means that can change the position of the support member 1010 is inserted.
  • a screw thread is formed in the opening 720 , and the position of the support member 1010 may be adjusted by rotation of the screw.
  • FIG. 13 is a side view of the T-shaped member 1310 and the first link member 1340 of the artificial knee joint 1300 configured to have eccentricity according to an embodiment of the present disclosure
  • FIG. 14 is an embodiment of the present disclosure. It is an exemplary view showing the operation of the T-shaped member 1310 and the first link member 1340 by the eccentricity according to the.
  • the T-shaped member 1310 and the first link member 1340 may be configured to be rotatable through the centers 1320 and 1330 of the second axis.
  • the centers 1320 and 1330 of the second axis may correspond to the center 1320 at which the first link member 1340 rotates and the center 1330 at which the T-shaped member 1310 rotates.
  • a center 1330 at which the T-shaped member 1310 rotates may be different from a center 1320 at which the first link member 1340 rotates. That is, the center 1330 at which the T-shaped member 1310 of the main body 1350 rotates and the center 1320 at which the first link member 1340 rotates may be in an eccentric state that does not coincide with each other. Through this, the rotational motion of the first link member 1340 may be converted into a linear motion.
  • the operation process of the T-shaped member 1310 and the first link member 1340 for converting the rotational motion of the first link member 1340 into a linear motion will be described as follows.
  • the first operation step 1410 represents a state before the T-shaped member 1310 and the first link member 1340 are eccentrically rotated.
  • the first link member 1340 may be configured to be rotatable through the rotation center 1330 of the T-shaped member 1310 .
  • the first link member 1340 may be configured to be rotatable by ⁇ through the rotation center 1330 of the T-shaped member 1310 .
  • ⁇ may be 10°.
  • the second operation step 1420 represents a state after the first link member 1340 rotates through the center 1330 .
  • the center 1320 of the first link member 1340 moves to the left rather than the center 1320 shown in the first operation step, 1 It can be seen that the position of the link member 1340 moves to the left. For example, when the first link member 1340 rotates by 2°, it may move by 0.58 mm.
  • the position of the first link member 1340 is moved to the left by the rotational movement of the first link member 1340 through the eccentricity, thereby converting the rotational motion into a linear motion. Accordingly, when the prosthetic leg wearer intends to cause sudden knee bending, the rotational motion of the first link member 1340 is changed to a linear motion through eccentricity, thereby preventing the knee from being completely bent.
  • FIG. 15 is an exemplary view illustrating a stance phase flexion state of the artificial knee joint 1500 according to an embodiment of the present disclosure.
  • abnormal motions such as excessive bending of the artificial knee joint or sudden knee bending unintended by the prosthetic leg wearer may occur.
  • the artificial knee joint 1500 may be excessively bent, or sudden knee bending may occur unintentionally by the prosthetic wearer. This can be prevented and a natural stance phase bending state can be implemented as shown in FIG. 15 .
  • the upper joint member 1510 may have a stance phase flexion at an appropriate angle, and at this time, the second shaft 1570 and the third shaft 1580 may be fixed.
  • the first link member 1540 and the second link member 1550 also move while the artificial knee joint can be suddenly completely bent.
  • the artificial knee joint 1500 may prevent such a phenomenon by controlling the movement of the second axis 1570 and the third axis 1580 and maintain the stance phase flexion at an appropriate angle. .
  • the T-shaped member 1530 of the main body 1520 rotates clockwise by a predetermined angle from the main body 1520 about the A axis 1560 to rotate the second axis 1570 and the third axis 1580 . ) to prevent excessive movement.
  • the main body 1520 may be supported in a direction opposite to the direction in which the second shaft 1570 and the third shaft 1580 are going to move.
  • the second shaft 1570 passing through the T-shaped member 1530 of the main body 1520 has an eccentricity so that the rotational motion of the first link member 1540 is converted into a linear motion so that the knee is completely bent. loss can be prevented.
  • the second axis 1570 and the third axis 1580 move in the walking process through the T-shaped member 1530, the support member 1010, and the second axis 1570 configured to have eccentricity, so that the artificial knee It is possible to provide an artificial knee joint capable of securing safety by effectively preventing the joint from being excessively bent or from sudden knee bending unintended by the prosthetic leg wearer.
  • 16 is a perspective view of an artificial knee joint according to another embodiment of the present disclosure.
  • 17 is a side view of the artificial knee joint disclosed in FIG. 16 .
  • 18 is a perspective view of the upper joint member of the artificial knee joint disclosed in FIG. 16 .
  • the upper joint member 1610 has a second protrusion 1630 protruding to both sides.
  • the second protrusion 1630 is in contact with the upper surface of the T-shaped member 1640 .
  • An upper surface of the T-shaped member 1640 in contact with the second protrusion 1630 has a curvature.
  • the T-shaped member 1640 may have a depression in a portion in contact with the second protrusion 1630 . Since the A-axis 1660 is disposed backward with respect to the walking direction relative to the first protrusion 1650 , the T-shaped member 1640 may secure the recessed portion.
  • abnormal movements such as excessive bending of the artificial knee joint or sudden knee bending unintended by the prosthetic leg wearer may occur.
  • the artificial knee joint 1500 may be excessively bent, or sudden knee bending may occur unintentionally by the prosthetic wearer.
  • the second protrusion 1630 may apply a downward force while in contact with the upper surface of the T-shaped member 1630 .
  • abnormal motions such as excessive bending of the artificial knee joint or sudden knee bending unintended by the prosthetic leg wearer are prevented when the prosthetic leg wearer is walking, in the stance phase, or standing A bending state can be implemented.
  • the second protrusion 1630 presses the T-shaped member 1640 in the direction of the arrow 2 around the first shaft 1710 passing through the penetrating portion 1810 by the load. This limits the movement of the first link member 1670 in the direction of the arrow 3, so that when the load of the stance phase bending occurs, a natural stance bending (eg, 60 degrees) can be implemented.
  • the second protrusion 1630 may be configured in the form of a roller, and may press the T-shaped member 1640 while rotating.

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

Abstract

Articulation artificielle du genou selon un mode de réalisation de la présente invention comprenant : un élément supérieur d'articulation qui est formé de façon à pouvoir être fixé à un corps humain et à travers duquel passe un premier axe ; une partie de corps formée de telle sorte que le premier axe, un axe A, et un troisième axe la traversent, la partie corps étant reliée de manière rotative à l'élément supérieur d'articulation autour du premier axe et comprenant un élément en forme de T à travers duquel passe l'axe A et un deuxième axe ; un élément inférieur d'articulation formé de façon à pouvoir être fixé à une jambe artificielle et formé de telle sorte qu'un quatrième axe et un cinquième axe passent à travers celui-ci ; un premier élément de liaison ayant une extrémité couplée de façon rotative au deuxième axe, et l'autre extrémité étant couplée de façon rotative au quatrième axe ; et un second élément de liaison ayant une extrémité couplée de façon rotative au troisième axe, et l'autre extrémité étant couplée de façon rotative au cinquième axe, l'élément en forme de T pouvant tourner autour de l'axe A.
PCT/KR2021/007976 2020-06-24 2021-06-24 Articulation artificielle du genou WO2021261942A1 (fr)

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KR1020200100802A KR102260966B1 (ko) 2020-06-24 2020-08-11 인공무릎관절
KR10-2020-0100802 2020-08-11

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Publication number Priority date Publication date Assignee Title
KR102260966B1 (ko) * 2020-06-24 2021-06-04 (주)보일랩스 인공무릎관절
WO2022265464A1 (fr) * 2021-06-17 2022-12-22 (주)보일랩스 Articulation artificielle du genou
KR102661949B1 (ko) * 2021-06-17 2024-05-24 (주)보일랩스 인공무릎관절
KR102483561B1 (ko) * 2021-06-29 2023-01-02 (주)보일랩스 의족

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JPH10165430A (ja) * 1996-12-11 1998-06-23 Keiai Gishi Zairyo Hanbaishiyo:Kk 膝関節
JP2003514615A (ja) * 1999-11-23 2003-04-22 グラムテク インノボシューン アクチボラゲット 膝関節補綴装置
US20140188252A1 (en) * 2011-03-03 2014-07-03 D-Rev: Design For The Other Ninety Percent Polycentric knee joint prosthesis for extreme affordability
KR101897459B1 (ko) * 2018-07-17 2018-09-12 김보일 다축 인공무릎관절
KR101921607B1 (ko) * 2017-06-05 2018-11-23 김보일 다축 인공무릎관절
KR102260966B1 (ko) * 2020-06-24 2021-06-04 (주)보일랩스 인공무릎관절

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH10165430A (ja) * 1996-12-11 1998-06-23 Keiai Gishi Zairyo Hanbaishiyo:Kk 膝関節
JP2003514615A (ja) * 1999-11-23 2003-04-22 グラムテク インノボシューン アクチボラゲット 膝関節補綴装置
US20140188252A1 (en) * 2011-03-03 2014-07-03 D-Rev: Design For The Other Ninety Percent Polycentric knee joint prosthesis for extreme affordability
KR101921607B1 (ko) * 2017-06-05 2018-11-23 김보일 다축 인공무릎관절
KR101897459B1 (ko) * 2018-07-17 2018-09-12 김보일 다축 인공무릎관절
KR102260966B1 (ko) * 2020-06-24 2021-06-04 (주)보일랩스 인공무릎관절

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