JPS6153061B2 - - Google Patents
Info
- Publication number
- JPS6153061B2 JPS6153061B2 JP57141584A JP14158482A JPS6153061B2 JP S6153061 B2 JPS6153061 B2 JP S6153061B2 JP 57141584 A JP57141584 A JP 57141584A JP 14158482 A JP14158482 A JP 14158482A JP S6153061 B2 JPS6153061 B2 JP S6153061B2
- Authority
- JP
- Japan
- Prior art keywords
- knee
- tightening
- fixed
- shaft
- thigh
- 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.)
- Expired
Links
- 210000003127 knee Anatomy 0.000 claims description 20
- 210000000689 upper leg Anatomy 0.000 claims description 8
- 238000005452 bending Methods 0.000 claims description 4
- 210000000629 knee joint Anatomy 0.000 claims description 4
- 210000002414 leg Anatomy 0.000 description 8
- 238000010586 diagram Methods 0.000 description 3
- 125000006850 spacer group Chemical group 0.000 description 3
- 230000007423 decrease Effects 0.000 description 2
- 230000006835 compression Effects 0.000 description 1
- 238000007906 compression Methods 0.000 description 1
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
- A61F2/68—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
- A61F2/60—Artificial legs or feet or parts thereof
- A61F2/64—Knee joints
- A61F2/642—Polycentric joints, without longitudinal rotation
- A61F2/644—Polycentric joints, without longitudinal rotation of the single-bar or multi-bar linkage 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
- A61F2002/5007—Prostheses not implantable in the body having elastic means different from springs, e.g. including an elastomeric insert
Description
【発明の詳細な説明】
図1は、人の歩行の際の右半身の姿勢の変化を
歩行の一周期の間、即ち、右足の着床Aから次の
着床Mの間にわたつて示したものであり、A−I
間が支持足期、I−M間が浮足期である。このよ
うな姿勢の変化を可能にする義足が理想的な義足
である。DETAILED DESCRIPTION OF THE INVENTION FIG. 1 shows changes in the posture of the right side of the body during one walking cycle, that is, from the landing A of the right foot to the next landing M. A-I
The period between I and M is the supporting phase, and the period between I and M is the floating phase. An ideal prosthetic leg would be one that allows such changes in posture.
図1に見られるように、健常者の歩行では浮足
期にはいる前から膝が大きく曲げられていき、浮
足期にはいると膝から下を前方に振り出す。これ
に近い動作のできる義足は、大腿と下腿が互いに
自由に回転できる構造のものである。しかし、そ
のような義足で、支持足期のA−G間のように膝
を曲げていこうとすると、膝が上体からの荷重で
急激に折れてしまうので、そうならないようにす
る歩行動作を訓練によつて習得しているのが現状
である。したがつて、膝折れの危険性を嫌つて、
歩行時には膝を伸ばした状態で固定してしまう義
足も多く用いられているが、これは坂道や階段で
は非常に歩き難い。また、膝にかかる荷重によつ
て膝折れを防止しようとする摩擦ブレーキ機構を
持つ義足も数種類あるが、これらのブレーキ力は
弱過ぎるので、これに頼ることはできない。これ
に対して、本発明の膝関節機構は膝をどのように
大きく曲げた状態でも支持できるブレーキ力を持
つている。 As can be seen in Figure 1, when a healthy person walks, the knees are greatly bent before entering the floating phase, and once the foot is in the floating phase, the legs below the knees are swung forward. A prosthetic leg that can perform movements similar to this has a structure that allows the thigh and lower leg to rotate freely relative to each other. However, with such a prosthetic leg, if you try to bend the knee like between A and G during the supporting leg phase, the knee will suddenly break due to the load from the upper body, so it is necessary to take steps to prevent this from happening. Currently, they are learned through training. Therefore, I don't like the risk of knee bending,
Prosthetic legs are often used that keep the knee extended when walking, but this makes it extremely difficult to walk on slopes or stairs. Additionally, there are several types of prosthetic legs that have a friction brake mechanism that attempts to prevent the knee from buckling due to the load applied to the knee, but the braking force of these is too weak to rely on. In contrast, the knee joint mechanism of the present invention has a braking force that can support the knee no matter how greatly it is bent.
図2に本発明の出発点になつた従来の摩擦ブレ
ーキ機構を示し、その原理を説明する。大腿接続
部3と締付部品5は軸1によつて連結され、該締
付部品5の左端の穴に嵌つている軸2は下腿6に
固定されている。軸2が膝関節軸になる。上体か
らの荷重が膝にかかつてくると、大腿接続部3は
軸1回りに回転しようとして、スペーサ4を介し
て締付部品5の上部を押さえ、その結果下部を引
上げようとする。これによつて該締付部品5は軸
2を締付ける。この力によつて生じる軸2回りの
ブレーキ力によつて膝折れを防止するのである。
ブレーキ力は締付力を大きくしても軸2の直径を
大きくしても増加する。しかし軸2を大きくする
と軸2の左方の点線部5aの断面積が小さくなつ
て破断する。また締付力を大きくしても同じく点
線部5aで破断する。それに対応するために点線
部5aの強度を上げると変形が小さくなつて締付
力が低下する。以上のような理由によつて、図1
の機構では十分なブレーキ力が得られないのであ
る。 FIG. 2 shows a conventional friction brake mechanism that is the starting point of the present invention, and its principle will be explained. The thigh connecting part 3 and the tightening part 5 are connected by a shaft 1, and the shaft 2, which is fitted into a hole at the left end of the tightening part 5, is fixed to the lower leg 6. Axis 2 becomes the knee joint axis. When a load from the upper body is applied to the knee, the thigh connecting part 3 tries to rotate around the axis 1, presses the upper part of the fastening part 5 via the spacer 4, and as a result tries to pull up the lower part. This causes the clamping part 5 to clamp the shaft 2. The braking force around axis 2 generated by this force prevents the knee from buckling.
The braking force increases regardless of whether the clamping force is increased or the diameter of the shaft 2 is increased. However, if the shaft 2 is made larger, the cross-sectional area of the dotted line portion 5a on the left side of the shaft 2 becomes smaller and breaks. Moreover, even if the tightening force is increased, it will break at the dotted line portion 5a. In order to cope with this, increasing the strength of the dotted line portion 5a reduces the deformation and reduces the tightening force. For the above reasons, Figure 1
This mechanism cannot provide sufficient braking force.
上記の欠点を無くしたのが本発明であり、その
構造を図3および図4に示す。締付部品は上下の
5.1と5.2に分けられて、軸10によつて連
結されている。軸2に換えて、膝の内側と外側に
直径の大きな2個の摩擦円板2aが置かれる。こ
の機構は図2の機構の10倍近いブレーキ力を持つ
ている。したがつて、どのように膝を大きく曲げ
ても膝折れは起こらなくなる。これによつて、ス
ペーサ4は弾性体4aに換えて、図1のA−E間
の膝の屈伸運動を近似することも可能になる。即
ち、着床時に上体からの荷重が急激に加わると、
大腿接続部3が軸2回りに回転して弾性体4aを
圧縮しながら下部締付け部品5.2を軸1を介し
て引上げようとする。同時に弾性体4aは上部締
付け部品5.1を上から押さえる。この結果軸1
0を支点として上下部締付け部品5.1と5.2
が下腿接続部6に固定されている摩擦円板2aを
狭んで締付ける。これによつて、上下部締付け部
品5.1および5.2と摩擦円板2aが固定され
た状態になり、結局、下腿に対して下部締付け部
品5.2が固定され、それに付いている軸2の位
置も固定されたことになる。その後は大腿接続部
は、上体からの荷重の増加に対応して弾性体4a
が圧縮される分だけ大腿接続部3が軸1回りに回
転し、荷重が減少すると弾性体4aの圧縮量が減
少するので、大腿接続部3は元にもどる。このよ
うな運動によつてA−E間の膝の屈伸運動が近似
できるのである。 The present invention eliminates the above drawbacks, and its structure is shown in FIGS. 3 and 4. The tightening parts are divided into upper and lower parts 5.1 and 5.2, which are connected by a shaft 10. Instead of the shaft 2, two friction disks 2a with large diameters are placed on the inside and outside of the knee. This mechanism has nearly 10 times the braking force of the mechanism shown in Figure 2. Therefore, no matter how much you bend your knees, your knees will not bend. Thereby, the spacer 4 can be used instead of the elastic body 4a to approximate the bending and stretching motion of the knee between A and E in FIG. In other words, if the load from the upper body is suddenly applied when landing on the floor,
The femoral connection 3 rotates around the axis 2 and tries to pull up the lower clamping part 5.2 via the axis 1 while compressing the elastic body 4a. At the same time, the elastic body 4a presses down on the upper clamping part 5.1 from above. This result axis 1
Upper and lower tightening parts 5.1 and 5.2 with 0 as the fulcrum
narrows and tightens the friction disk 2a fixed to the lower leg connection part 6. As a result, the upper and lower tightening parts 5.1 and 5.2 and the friction disk 2a are fixed, and the lower tightening part 5.2 is fixed to the lower leg, and the shaft attached to it is fixed. This means that position 2 is also fixed. After that, the thigh connection part is made of elastic body 4a in response to the increase in the load from the upper body.
The thigh connecting part 3 rotates around the axis 1 by the amount that is compressed, and when the load decreases, the amount of compression of the elastic body 4a decreases, so the thigh connecting part 3 returns to its original state. By such movement, the bending and stretching movement of the knee between A and E can be approximated.
また、I−M間の離床時には上体から荷重がか
かるのとは逆に軸1に弾性体4aを含めて上部締
付け部品5.1以下全体が釣り下げられる状態に
なるので、摩擦円板2aが締付けられることな
く、摩擦円板に接続している下腿の振れは自由に
なる。 In addition, when leaving the bed between I and M, the entire upper clamping part 5.1 and below, including the elastic body 4a, is suspended from the shaft 1, contrary to the case where the load is applied from the upper body, so the friction disc 2a The lower leg, which is connected to the friction disk, is free to swing without being tightened.
図1は人の歩行の一周期の間の右半身の姿勢の
変化の解説図、図2は従来の義足の膝関節機構の
解説図、図3は本発明の実施例を示す図、図4は
実施例の斜視図である。
1,2および10……軸、3……大腿接続部、
4……スペーサ、5……締付部品、6……下腿接
続部、7および8……ストツパー、2a……摩擦
円板、4a……弾性体、5.1……上部締付け部
品、5.2……下部締付け部品。
Fig. 1 is an explanatory diagram of changes in the posture of the right side of the body during one cycle of human walking, Fig. 2 is an explanatory diagram of the knee joint mechanism of a conventional prosthetic leg, Fig. 3 is a diagram showing an embodiment of the present invention, and Fig. 4 is a perspective view of an example. 1, 2 and 10...axis, 3...femoral connection part,
4... Spacer, 5... Tightening part, 6... Lower leg connection part, 7 and 8... Stopper, 2a... Friction disk, 4a... Elastic body, 5.1... Upper tightening part, 5. 2...Lower tightening parts.
Claims (1)
膝に弾力を与えるために、下腿に固定された摩擦
円板2a、該摩擦円板を上下から挾んで膝の後方
で軸によつて連結される上部および下部締付け部
品5.1,5.2、該下部締付け部品と膝の前方
で軸によつて連結され、大腿に接続固定される部
品3、および該大腿接続部3と上部締付け部品と
の間に挿入されている弾性体4aによつて構成さ
れる膝関節機構。1. In order to completely prevent the knee from bending when the foot lands on the floor and to give elasticity to the knee, a friction disk 2a is fixed to the lower leg, and the friction disk is held between the upper and lower sides and is attached to an axis behind the knee. an upper and a lower tightening part 5.1, 5.2 which are connected together, a part 3 which is connected to the lower tightening part by a shaft in front of the knee and is connected and fixed to the thigh, and a part 3 which is connected and fixed to the thigh; A knee joint mechanism constituted by an elastic body 4a inserted between the tightening parts.
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP57141584A JPS5932450A (en) | 1982-08-12 | 1982-08-12 | Knee joint mechanism of artificial leg |
PCT/JP1983/000266 WO1984000682A1 (en) | 1982-08-12 | 1983-08-12 | Knee joint mechanism for artificial leg |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP57141584A JPS5932450A (en) | 1982-08-12 | 1982-08-12 | Knee joint mechanism of artificial leg |
Publications (2)
Publication Number | Publication Date |
---|---|
JPS5932450A JPS5932450A (en) | 1984-02-21 |
JPS6153061B2 true JPS6153061B2 (en) | 1986-11-15 |
Family
ID=15295393
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP57141584A Granted JPS5932450A (en) | 1982-08-12 | 1982-08-12 | Knee joint mechanism of artificial leg |
Country Status (2)
Country | Link |
---|---|
JP (1) | JPS5932450A (en) |
WO (1) | WO1984000682A1 (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS63264263A (en) * | 1987-04-21 | 1988-11-01 | Mazda Motor Corp | Cold transfer device for castings |
Families Citing this family (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB8801278D0 (en) * | 1988-01-21 | 1988-02-17 | Hanger & Co Ltd J E | Knee prosthesis |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS5234875A (en) * | 1975-09-10 | 1977-03-17 | Grace W R & Co | Shock absorption device |
JPS5246432A (en) * | 1975-10-11 | 1977-04-13 | Fuji Electric Co Ltd | Electric equipment for oil-immersion type high voltge ac/dc converter |
Family Cites Families (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE2228391C3 (en) * | 1972-06-10 | 1975-09-11 | Otto Bock Orthopaedische Industrie Kg, 3428 Duderstadt | Knee joint for lower limb prostheses |
JPS5234875B2 (en) * | 1974-06-14 | 1977-09-06 |
-
1982
- 1982-08-12 JP JP57141584A patent/JPS5932450A/en active Granted
-
1983
- 1983-08-12 WO PCT/JP1983/000266 patent/WO1984000682A1/en unknown
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS5234875A (en) * | 1975-09-10 | 1977-03-17 | Grace W R & Co | Shock absorption device |
JPS5246432A (en) * | 1975-10-11 | 1977-04-13 | Fuji Electric Co Ltd | Electric equipment for oil-immersion type high voltge ac/dc converter |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS63264263A (en) * | 1987-04-21 | 1988-11-01 | Mazda Motor Corp | Cold transfer device for castings |
Also Published As
Publication number | Publication date |
---|---|
JPS5932450A (en) | 1984-02-21 |
WO1984000682A1 (en) | 1984-03-01 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
JP4550137B2 (en) | Long leg orthosis with load brake | |
US4446580A (en) | Prosthetic foot structure | |
Voigt et al. | Mechanical and muscular factors influencing the performance in maximal vertical jumping after different prestretch loads | |
US3488088A (en) | Therapeutic ambulatory and exercise aid | |
US3982280A (en) | Functional ankle for a prosthetic limb | |
CA2266572A1 (en) | Collapsible tactile support for body joints | |
CN102056579A (en) | External walking assist device for those with lower leg injuries | |
JPS61272048A (en) | Brake type knee joint | |
JP3002320U (en) | Long leg brace with knee joint angle adjustment mechanism | |
US979243A (en) | Apparatus for facilitating walking. | |
JP6197160B1 (en) | Leg assist device | |
JPS6153061B2 (en) | ||
EP1075237B1 (en) | Knee prosthesis | |
US4549318A (en) | Prosthetic device with a knee mechanism | |
CN114931483A (en) | Orthopedic traction bed | |
US1265609A (en) | Foot-rest. | |
US2575802A (en) | Knee joint of artificial legs | |
US6328707B1 (en) | Ankle restraining device | |
RU2200513C2 (en) | Artificial foot | |
CN210114544U (en) | Artificial limb foot plate | |
RU2053741C1 (en) | Femoral prosthesis | |
SU459221A1 (en) | Radiation arm for upper limb prostheses | |
RU2054906C1 (en) | Knee joint prosthesis | |
JP3968064B2 (en) | Prosthetic bounce device | |
RU2084209C1 (en) | Artificial knee joint |