JP2004166802A - Artificial knee joint - Google Patents

Artificial knee joint Download PDF

Info

Publication number
JP2004166802A
JP2004166802A JP2002333917A JP2002333917A JP2004166802A JP 2004166802 A JP2004166802 A JP 2004166802A JP 2002333917 A JP2002333917 A JP 2002333917A JP 2002333917 A JP2002333917 A JP 2002333917A JP 2004166802 A JP2004166802 A JP 2004166802A
Authority
JP
Japan
Prior art keywords
knee joint
portion
artificial knee
guide surface
bending angle
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.)
Granted
Application number
JP2002333917A
Other languages
Japanese (ja)
Other versions
JP4148316B2 (en
Inventor
Kenji Doi
Masahiro Kurosaka
Takahisa Takano
Shinichi Yoshiya
晋一 吉矢
憲司 土居
恭寿 高野
昌弘 黒坂
Original Assignee
Kobe Steel Ltd
New Industry Research Organization
株式会社神戸製鋼所
財団法人新産業創造研究機構
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 Kobe Steel Ltd, New Industry Research Organization, 株式会社神戸製鋼所, 財団法人新産業創造研究機構 filed Critical Kobe Steel Ltd
Priority to JP2002333917A priority Critical patent/JP4148316B2/en
Publication of JP2004166802A publication Critical patent/JP2004166802A/en
Application granted granted Critical
Publication of JP4148316B2 publication Critical patent/JP4148316B2/en
Application status is Expired - Fee Related legal-status Critical
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/02Prostheses implantable into the body
    • A61F2/30Joints
    • A61F2/38Joints for elbows or knees
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/02Prostheses implantable into the body
    • A61F2/30Joints
    • A61F2002/30001Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof

Abstract

<P>PROBLEM TO BE SOLVED: To provide an artificial knee joint smoothly bent to a high bending angle by guiding a winding angle corresponding to the bending angle in the artificial knee joint constituted to make a thighbone component to roll and slide on a tibia component. <P>SOLUTION: The thighbone component 1 is formed by connecting mutually rear parts of a pair of condyloid projecting members 2a and 2b laterally provided at some interval apart therefrom with a cam 3. The tibia component 11 is formed with a spine 4 and, at least, a guide surface out of mutual guide surfaces 3a and 4s where the cam 3 and the spine 4 contact with each other when the bending angle of the knee joint increases, is formed by twisting. <P>COPYRIGHT: (C)2004,JPO

Description

【0001】 [0001]
【発明の属する技術分野】 BACKGROUND OF THE INVENTION
本発明は、慢性関節リウマチ、変形性膝関節症などによる高度に変形した膝関節あるいは交通事故、災害等により破壊された関節を正常な機能に回復させるために用いられる人工膝関節に関するものである。 The present invention relates to rheumatoid arthritis, highly deformed knee or traffic accidents due to osteoarthritis of the knee, the knee prosthesis used to restore the destroyed joints normal function due to a disaster or the like .
【0002】 [0002]
【従来の技術】 BACKGROUND OF THE INVENTION
従来から、図6に示すように、疾患や事故により変形・破壊された膝関節の大腿骨Aの遠位部と脛骨Bの近位部の骨切りを行い大腿骨コンポーネント1と脛骨コンポーネント11をそれぞれ挿入固定する人工膝関節置換手術が行われており、人の正常な関節運動を再現するものとして、脛骨コンポーネント11の上面(「関節面」という)12に接しつつ大腿骨コンポーネント1の下面の凸面部8が転動及び/又は滑動することにより、屈曲可能となるような構造の人工膝関節が用いられてきた(汎用品)。 Conventionally, as shown in FIG. 6, the femoral component 1 and tibial component 11 performs osteotomy of the proximal portion of the distal portion and the tibia B of the femur A knee joint that has been deformed or broken by disease or accident It is performed knee replacement surgery to insert respectively fixed, as to reproduce the normal articulation of the human, the tibial component 11 top (called "joint surfaces") 12 to the lower surface of the femoral component 1 while being in contact by convex section 8 rolls and / or sliding, artificial knee joint of the structure so as to allow bending has been used (general-purpose products).
【0003】 [0003]
ところで現在、日本で使用されている人工膝関節は、欧米で開発されたものが95%近くを占め(例えば、特許文献1〜3参照)、したがってその人工膝関節は、欧米の椅子、ベッドを利用した生活に必要な屈曲角度(前後方向の曲げ角度)を重視して開発されたため、臨床的には120度程度までの屈曲角度しか得られないものが多かった。 However currently, the artificial knee joint which is used in Japan, was developed in Europe accounted for nearly 95% (e.g., see Patent Documents 1 to 3), therefore the knee prosthesis, Western chair, a bed because it was developed with an emphasis on the bending angle necessary for utilizing life (bend angle in the front-back direction), clinically it was often not obtained only bending angle of up to about 120 degrees.
【0004】 [0004]
しかし、日本人の高齢者などは日常的に正座することが多く、そのため150度以上の屈曲角度まで可能な人工膝関節が望まれている。 However, such Japanese elderly be routinely sit many artificial knee joint has been desired that can to the bending angle of the order or 150 degrees.
【0005】 [0005]
また実際の生体膝関節では、屈曲に際して、関節面に対して水平方向への回転(「回旋」という)も同時に生じており、屈曲角度に対応した回旋角度が誘導されることにより滑らかに屈曲できるものである。 In the actual biological knee joint, during flexion, rotation in the horizontal direction with respect to the articular surface (referred to as "rotation") also occurs at the same time, it can smoothly bend by the rotation angle corresponding to the bending angle is derived it is intended. そして150度以上の高屈曲角度において、より自然で滑らかな屈曲を実現するためには、10度以上の回旋角度を確保することが望ましい。 And at high flexion angles of 150 degrees or more, in order to achieve a more natural and smooth flexion, it is desirable to ensure a rotation angle of 10 degrees or more.
【0006】 [0006]
特許文献4に開示された人工関節(図7、8参照)は、160度の高屈曲角度を実現すべく提案されたものである(従来例1)。 Disclosed in Patent Document 4 a prosthesis (see FIGS. 7 and 8) is the one proposed in order to achieve high bending angle of 160 degrees (Conventional Example 1). この人工関節を構成する大腿骨コンポーネント1は、図7に示すように、上記汎用品と同様、一対の顆状突起部材2a、2bを所定の間隔9(図示せず)をあけて横(水平方向)に設け、それらの後部6同士を結合部材(「カム」という)3で結合して一体としたものであるが、その後部6を汎用品より後方に膨らませ、その後部6の上部に前部5側に巻き込まれるように凸面部7が形成されている。 Femoral component 1 constituting the prosthesis, as shown in FIG. 7, similarly to the above general-purpose products, laterally spaced pair of condylar members 2a, 2b by a predetermined distance 9 (not shown) (the horizontal provided in a direction), but is obtained by integrally attached to their rear 6 together with the coupling member (referred to as "the cam") 3, the rear 6 inflated behind the generic products, before the top of the rear 6 convex portions 7 are formed so as to be involved in section 5 side. 一方、脛骨コンポーネント11には、図8に示すように、汎用品と同様、関節面12と突起部(「スパイン」という)4とが形成されている。 On the other hand, the tibial component 11, as shown in FIG. 8, similarly to the general-purpose product, and the protruding portion articular surface 12 (referred to as "spine") 4 and is formed. これにより、図8に示すように、屈曲角度が130度を超えたときにも、カム3がスパイン4に接触し支持される一方、凸面部7が関節面12に滑らかに接触しつつ摺動するので、大腿骨コンポーネント1が脛骨コンポーネント11から脱落することなく160度まで高屈曲角度が得られるとしている。 Thus, as shown in FIG. 8, when the bending angle exceeds 130 degrees, while the cam 3 is in contact with the spine 4 support, while the convex portion 7 is smoothly in contact with the articular surface 12 slides because, the high bending angle up to 160 degrees without the femoral component 1 from falling off from the tibial component 11 is to be obtained.
【0007】 [0007]
ところが、この提案の人工関節では回旋については全く考慮されておらず、単に前後方向への屈曲のみが可能となるものである。 However, not taken into consideration at all for rotation in the joint of this proposal, in which merely bent in the longitudinal direction is possible. そして、このような屈曲のみが可能な人工関節を施術した場合、靭帯を含む軟部組織がある程度健全な症例に対しては、軟部組織による回旋が幾分確保され屈曲もある程度確保され得るが、軟部組織の状態が悪い症例に対しては、回旋は生じ難く屈曲の点で改良の余地があった。 Then, when the treatment of such bending only the possible artificial joint, relative to a certain extent healthy cases soft tissue including ligaments, but convoluted by soft tissue may be secured to some extent also somewhat reserved bent, soft for conditions are poor cases organizations rotation had hardly room for improvement in terms of the bending occurs.
【0008】 [0008]
一方、特許文献5には、図9に示すような人工膝関節が開示されている(従来例2)。 On the other hand, Patent Document 5, an artificial knee joint is disclosed as shown in FIG. 9 (prior art 2). 上記従来例1と同様、大腿骨コンポーネント1と脛骨コンポーネント11とから構成されるものであるが、上記従来例1と異なりスパインおよびカムを用いていない。 Similarly to the conventional example 1, it is those composed of femoral component 1 and tibial component 11 Metropolitan but not with spine and cam unlike the conventional example 1. 脛骨コンポーネント11の関節面12に設けられた一対の凹面部12a、12bのうち、一方の凹面部12aの有意の部分の曲率と、大腿骨コンポーネント1を構成する一対の顆状突起部材2a、2bのうち凹面部12aと接する方の顆状突起部材2aの凸面部8aの有意の部分の曲率とを概ね等しくし、他方の凹面部12bの有意の部分の曲率をこの凹面部12bと接する方の顆状突起部材2bの凸面部8bの有意の部分の曲率より小さくした(言い換えると、なだらかにした)ことにより、前者の凹面部12aに一方の顆状突起部材2aの凸面部8aが嵌まり込んでここを支点として他方の顆状突起部材2bが水平方向に回転でき、すなわち回旋が可能となるものである。 A pair of concave portions 12a provided on the joint surface 12 of the tibial component 11, among 12b, a curvature of a significant part of one of the concave portion 12a, a pair that constitute the femoral component 1 condyles member 2a, 2b of the curvature of the significant portion of the convex surface portion 8a of the condyles member 2a towards contact with the concave portion 12a and substantially equal, the curvature of a significant portion of the other of the concave portion 12b of the direction in contact with the concave portion 12b of the condylar made smaller than the curvature of a significant portion of the convex surface portion 8b of the projection member 2b (in other words, was gently) by, elaborate convex portion 8a is fits in one of the condyles member 2a to the former of the concave portion 12a in rotatable here the other condyles member 2b is the horizontal direction as a supporting point, that is, what becomes possible rotation. しかし、この人工膝関節は、歩行時の比較的小さな屈曲角度の範囲で必要な回旋角度を確保することを目的としており、高屈曲角度にまで適用できるものではない。 However, the artificial knee joint is intended to ensure a rotation angle necessary in a relatively range of small bending angles during walking, not be applied to a high bending angle. また、屈曲角度に応じて回旋角度が誘導されるものではない。 Also it does not have rotation angle is derived in accordance with the bending angle.
【0009】 [0009]
【特許文献1】 [Patent Document 1]
特公昭61−50625号公報【特許文献2】 JP-B-61-50625 [Patent Document 2]
特公昭62−36696号公報【特許文献3】 JP-B-62-36696 [Patent Document 3]
特公平2−45456号公報【特許文献4】 JP Kokoku 2-45456 [Patent Document 4]
特開平11−313845号公報【特許文献5】 JP 11-313845 [Patent Document 5]
米国特許第5,219,362号明細書【0010】 US Pat. No. 5,219,362 [0010]
【発明が解決しようとする課題】 [Problems that the Invention is to Solve
以上のような状況に鑑み、本発明の課題は、屈曲角度に対応した回旋角度が誘導されることにより高屈曲角度まで円滑に屈曲できる人工膝関節を提供することにある。 In view of the above circumstances, an object of the present invention is to provide an artificial knee joint can be smoothly bent to high flexion angle by the rotation angle corresponding to the bending angle is derived.
【0011】 [0011]
【課題を解決するための手段】 In order to solve the problems]
請求項1の発明は、大腿骨の遠位部に装着される大腿骨コンポーネントと脛骨の近位部に装着される脛骨コンポーネントとからなる人工膝関節において、該人工膝関節の屈曲角度の変化に対応して該人工膝関節の回旋角度が変化するように構成された人工膝関節である。 The invention of claim 1, in the artificial knee joint comprising a tibial component to be attached to the proximal portion of the femoral component and the tibial mounted on the distal portion of the femur, the change in the bending angle of the knee joint corresponding to a configuration prosthetic knee joint so as to change the rotation angle of the artificial knee joint.
【0012】 [0012]
請求項2の発明は、大腿骨の遠位部に装着される大腿骨コンポーネントと脛骨の近位部に装着される脛骨コンポーネントとからなる人工膝関節において、前記大腿骨コンポーネントが、互いに間隔をあけて横に設けられた一対の顆状突起部材と、該一対の顆状突起部材の互いの後部を結合する、概ね前方に向かう案内面を有する結合部材とを備え、前記脛骨コンポーネントが、前記各顆状突起部材の凸面部が摺動及び/又は転動する一対の凹面部と、前記一対の顆状突起部材の間隔に嵌入され該間隔の長手方向に可動自在となるように形成された、概ね後方に向かう案内面を有する突起部とを備え、該人工膝関節の屈曲角度が変化したとき、前記突起部と前記結合部材との互いの案内面の接触部位の位置が変化することにより、該人工膝関節 A second aspect of the present invention, in the artificial knee joint comprising a tibial component to be attached to the proximal portion of the femoral component and the tibial mounted on the distal portion of the femur, the femoral component, spaced apart from one another a pair of condyles members provided laterally Te, couples the rear of each other of the pair of condyles member, generally a coupling member having a guide surface towards the front, the tibial component, each a pair of concave portions convex surface portions of the condyles member slides and / or rolls, is fitted to the spacing of the pair of condyles member is formed so as to be freely movable in the longitudinal direction of the spacing, generally a protrusion having a guide surface towards the rear, when the bending angle of the knee joint is changed, by the position of the contact portion of the guide surface of each other and the coupling member and the projections is changed, the artificial knee joint 回旋角度が変化するように構成された人工膝関節である。 Is rotation angle is configured knee joint so as to change.
【0013】 [0013]
請求項3の発明は、前記結合部材の案内面と前記突起部の案内面のうち少なくとも一つが、捩じれた形状である請求項2に記載の人工膝関節である。 A third aspect of the present invention, at least one of the guide face of the guide surface and the projecting portion of the coupling member, an artificial knee joint according to claim 2, wherein a shape twisted.
【0014】 [0014]
〔作用〕 [Action]
以下において、大腿骨コンポーネントと脛骨コンポーネントとの相対的な動きや位置関係の把握を容易にするため、脛骨コンポーネントは、その関節面を水平にした状態で固定されたものとみなし、大腿骨コンポーネントのみが屈曲・回旋するものとして説明する。 In the following, for ease of understanding of the relative movement and the positional relationship between the femoral component and the tibial component, the tibial component, deemed to be fixed to the articular surface in a state of being horizontal, the femoral component only but it is described as bent-rotation.
【0015】 [0015]
本発明の人工膝関節は、屈曲角度の変化に対応して該人工膝関節の回旋角度が変化するように構成しているので、屈曲角度に応じて回旋角度が誘導され円滑な屈曲が可能となる。 Knee prosthesis of the present invention, since the rotation angle of the knee joint in response to changes in the bending angle is configured to vary, can smoothly bend is induced rotation angle according to the bending angle and Become.
【0016】 [0016]
例えば、屈曲角度が変化したときに前記突起部と前記結合部材との互いの案内面の接触部位の位置が変化することにより該人工膝関節の回旋角度が変化するように構成すれば、屈曲角度に応じて回旋角度が誘導され円滑な屈曲が可能となる。 For example, if constructed as torsion angle of the artificial knee joint is changed by the position of the contact portion of each other of the guide surfaces of the coupling member and the protruding portion when the bending angle is changed is changed, the bending angle is turning degree becomes possible induced smooth bends in response to.
【0017】 [0017]
また例えば、前記結合部材の案内面を捩じった形状に形成すれば、屈曲角度を変化させたときに、その屈曲角度の変化量に対応して前記突起部の案内面と接触する、前記結合部材の案内面の接触部位の高さ方向の位置が移動することによりその接触部位の水平方向の位置も移動し、その水平方向への移動量分だけ脛骨コンポーネントに対して大腿骨コンポーネントが水平方向(関節面方向)に回転(回旋)する。 Further, for example, be formed into a shape twisted guide surface of the coupling member, when changing the bending angles, in contact with the guide surface of the protrusion in response to the variation of the bending angle, the horizontal position of the contact portion by the height position of the contact portion of the guide surface of the coupling member is moved also moves, the femoral component is horizontal relative movement amount by the tibial component to the horizontal direction It rotates in the direction (the joint plane direction) (rotation). したがって屈曲角度に対応する回旋角度が生じることになる。 Hence that the rotation angle corresponding to the bending angle occurs.
【0018】 [0018]
上記において、前記結合部材の案内面に替えて、前記突起部の案内面の方を捩った形状に形成しても同様の作用効果を奏することは明らかである。 In the above, instead of the guide surface of the coupling member, it is apparent that the same effects even when formed in a shape twisted towards the guide surface of the protrusion.
【0019】 [0019]
さらに上記において、前記結合部材の案内面と前記突起部の案内面との両方を捩った形状に形成すれば、上記と同様の作用により屈曲角度に対応する回旋角度が生じることに加え、双方の案内面の捩りの度合いをそれぞれ単独で捩った場合に比べて小さくできるので、大腿骨コンポーネントと脛骨コンポーネントとの間に生じる集中応力が前記結合部材と前記突起部とに分散され、各コンポーネントの疲労寿命が延長される。 In addition above, if formed in a shape twisted both the guide surface and the guide surface of the protrusion of the coupling member, in addition to the rotation angle corresponding to the bending angle caused by the action similar to the above, both since the degree of twisting of the guide surface can be reduced as compared with the case where the twisted singly respectively, stress concentration occurs between the femoral component and the tibial component is dispersed in said coupling member and the projections, the components fatigue life of is extended.
【0020】 [0020]
さらに、前記一対の凹面部のうち、一方の凹面部の有意の部分の曲率をこの凹面部に接する前記顆状突起部材の凸面部の有意の部分の曲率と概ね等しくし、他方の凹面部の有意の部分の曲率をこの凹面部と接する前記顆状突起部材の凸面部の有意の部分の曲率より小さくすることにより、前者の凹面部に一方の顆状突起部材の凸面部が嵌まり込んでここを支点として他方の顆状突起部材が後者の凹面部上を摺動し得るので、回旋がより滑らかに行われる。 Furthermore, the pair of the concave portion, and substantially equal to the curvature of a significant part of one of the concave portion and the curvature of the significant portion of the convex surface portion of the condyle member in contact with the concave portion, the other concave portion by smaller than the curvature of a significant portion of the convex surface portion of the condyle member contacting the curvature of the significant portion and the concave portion, crowded convex portion fits in one of the condyles member to the concave portion of the former since the other condylar member here as a fulcrum can slide over the latter of the concave portion, rotation is performed more smoothly.
【0021】 [0021]
【発明の実施の形態】 DETAILED DESCRIPTION OF THE INVENTION
以下、本発明に係る人工膝関節の実施の形態について図面を参照しながら説明する。 It will be described below with reference to the accompanying drawings, embodiments of the artificial knee joint according to the present invention.
【0022】 [0022]
図1は本発明の実施に係る人工膝関節の斜視図である。 Figure 1 is a perspective view of the artificial knee joint according to an embodiment of the present invention. 図2〜4は本発明の実施に係る人工膝関節の動作状態を説明する図であり、図2は屈曲角度0度、図3は屈曲角度90度、図3は屈曲角度150度の状態を示す。 2-4 is a diagram illustrating the operation state of the artificial knee joint according to an embodiment of the present invention, FIG 2 is bent angle of 0 °, 3 bending angle 90 °, the state of FIG. 3 is bent angle of 150 degrees show. なお、図2〜4の各(a)は図1における関節面12より上方はAA断面、関節面12より下方はCC断面を繋ぎ合わせた断面図であり、各(b)は図1における関節面12より上方はBB断面、関節面12より下方はDD断面を繋ぎ合わせた断面図である。 Each (a) in 2-4 above the articular surface 12 in FIG. 1 AA section, is below the articular surface 12 is a sectional view of joining the CC cross section, each (b) is the joint in FIG. 1 above the plane 12 BB section, below the articular surface 12 is a sectional view of joining the DD cross section.
【0023】 [0023]
図1において、本発明の人工関節は大腿骨コンポーネント1と脛骨コンポーネント11とからなる。 In Figure 1, the prosthesis of the present invention consists of a femoral component 1 and tibial component 11 Prefecture. 大腿骨コンポーネント1は、一定の間隔9をあけて横(水平方向)に設けた一対の顆状突起部材2a、2bを、これらの互いの前部を一体に結合して膝蓋を形成するとともに、互いの後部を結合部材であるカム3により結合して形成されている。 The femoral component 1, a pair of condyles member 2a provided in the lateral (horizontal direction) at regular intervals 9, a 2b, to form a patellar front of each other and coupled together, are formed by combining the cam 3 is a coupling member to the rear of each other. 一方、脛骨コンポーネント11は、関節面12に一対の凹面部12a、12bと、突起部であるスパイン4とが形成されており、このスパイン4を大腿骨コンポーネントの間隔9に嵌入するとともに、各凹面部12a、12bそれぞれに各顆状突起部材2a、2bの各凸面部8a、8bそれぞれを当接させた状態で用いられる。 On the other hand, tibial component 11 includes a pair of concave portions 12a to the joint surface 12, and 12b, a spine 4 is a projection portion is formed, with fitted the spine 4 to the interval 9 of the femoral component, the concave parts 12a, 12b each condyle member 2a respectively, the convex portions 8a of 2b, 8b used being in contact, respectively.
【0024】 [0024]
間隔9に嵌入されたスパイン4が、膝関節の屈曲にしたがって前後方向に自在に動くように、間隔9の横(水平方向)の幅は突起部4の横方向の幅より少しだけ広目とし、間隔9の空間部の前後方向(長手方向)の長さは、関節面12の高さレベルでの突起部4の前後方向の長さ(すなわち裾部の長さ)より長くしておく。 Spine 4 which is fitted into the gap 9, to move freely in the longitudinal direction in accordance with flexion of the knee joint, the width of the lateral (horizontal) gap 9 and only wide eyes slightly than the lateral width of the protruding portions 4 , the length of the longitudinal direction of the space interval 9 (longitudinal direction), longitudinal length of the protrusion 4 in the height level of the articular surface 12 (i.e. the length of the skirt portion) than keep longer.
【0025】 [0025]
そしてスパイン4の、概ね後方に向かう案内面4sを左右対称の形状でなく、捩った形状、例えば、案内面4sを水平に切断したときの切断線が、スパイン4の下端(裾部)から上端(頂部)に向かうにしたがって、上方から見て反時計方向に回転するような形状に形成しておく。 The spine 4, generally not in the form of symmetrical guide surface 4s towards the rear, twisted shapes, for example, section line when the guide surface 4s were horizontally cut from the lower end of the spine 4 (skirt) toward the upper end (top), keep shaped to rotate as viewed from above in a counterclockwise direction.
【0026】 [0026]
あるいは、上記スパイン4の案内面4sを捩った形状とする替わりに、カム3の、概ね全周に亘る案内面3sを左右対称の形状でなく、捩じった形状としてもよい。 Alternatively, instead of a shape twisted guide surface 4s of the spine 4, the cam 3, generally not in the form of symmetrical guide surface 3s over the entire circumference, it may have a shape which is twisted. 案内面3sを捩った形状とするためには、例えば、横に寝かせた円柱の中心軸を湾曲させたものをカム3として用いればよい。 To a shape twisted guide surface 3s, for example, those obtained by bending the center axis of the cylinder like a laid may be used as a cam 3. もしくは、カム3の中心軸は左右方向に真っ直ぐでカム3の左右の径を変化させ円錐台状にして捩りを加えてもよい。 Or it may be added torsional center axis of the cam 3 in the lateral direction frustoconical changing the diameter of the left and right cam 3 in straight.
【0027】 [0027]
あるいは、図1に示すように、スパイン4の案内面4sとカム3の案内面3sの双方ともを捩った形状とすると、より一層回旋角度が得られさらに好ましい。 Alternatively, as shown in FIG. 1, when a shape twisted the both guide surfaces 3s guide surface 4s and the cam 3 of the spine 4, more preferably more obtained more rotation angles.
【0028】 [0028]
まず、スパイン4の案内面4sを捩った形状とするためには、図2に示すように、スパイン4の案内面4sについて、その上部(近位部)においては右側(内側)が左側(外側)より前方に位置するようにし、その下部(遠位部)においては右側(内側)が左側(外側)より後方に位置するようにするとよい。 First, in order to shape twisted guide surface 4s of the spine 4, as shown in FIG. 2, the guide surface 4s of the spine 4, in its upper (proximal portion) of the right side (inside) left ( so as to be positioned in front of the outside), may in its lower part (distal portion) so that the right side (inside) is located behind the left side (outside). なお、上部(近位部)と下部(遠位部)のうち一方のみを上記の位置関係としてもよい。 Incidentally, only one may be a positional relationship of the of the upper (proximal portion) and the lower (distal portion). 次に、カム3の案内面3sを捩った形状とするためには、図2に示すように、カム3の案内面3sについて、その上部(近位部)と下部(遠位部)の右左側(内外側)が前後方向にほぼ等しい位置に位置するようにし、かつ右側(内側)の半径が左側(外側)の半径より小さくするとよい。 Next, in order to shape twisted guide surfaces 3s of the cam 3, as shown in FIG. 2, the guide surface 3s of the cam 3, and its upper (proximal) the lower portion of the (distal portion) as right left (out side) is positioned at a position substantially equal to the longitudinal direction, and may radius of the right side (inside) is less than the radius of the left side (outside).
【0029】 [0029]
なお、一般的な膝の回旋は、大腿骨と脛骨の内側を軸として外側が回旋(外旋)する。 Note that rotation of a typical knee, outside swirling (lateral rotation) inside the femur and tibia as an axis. しかし、本発明は、回旋の制御を外旋のみに限定するものではなく、カム3とスパイン4の形状を適切に設計することにより、大腿骨と脛骨の外側を軸として内側が回旋する内旋を制御することも可能である。 However, the present invention is not intended to limit the control of the rotation only in external rotation, by suitably designing the shape of the cam 3 and the spine 4, the inner as an axis outside of the femur and tibia to rotation Uchi旋it is also possible to control the.
【0030】 [0030]
このように、案内面3sと4sのうちの少なくとも一つの案内面を捩った形状としておくと、屈曲にしたがって回旋が誘導される。 Thus, the keep a shape twisted at least one guide surface of the guide surface 3s and 4s, rotation is induced in accordance with bending. 例えば図2〜4に示すように、案内面3sと4sの双方ともを捩った形状とした場合において、膝関節の屈曲角度が0度のとき(図2)には、カム3とスパイン4とは接触せず、顆状突起部材2aと2bとは前後方向にずれがなく(δ=0)、回旋は生じていない。 For example, as shown in FIGS. 2-4, in the case of a shape twisted the both guide surfaces 3s and 4s, when the bending angle of the knee joint of 0 degrees (FIG. 2), the cam 3 and the spine 4 not in contact with, no shift in the longitudinal direction of the condyles member 2a and 2b (δ = 0), rotation does not occur. 屈曲角度を増加させていくと、やがてカム3とスパイン4とが互いの案内面同士(3sと4s)で接触するが、案内面3s、4s双方が捩られた形状をしているので、図3の(a)、(b)で示すように、図1のAA断面およびBB断面における前後方向の接触位置が異なり、顆状突起部材2aと2bとの前後方向のずれδが生じ、回旋が生じ始める(図3)。 As you increase the bending angle, although the cam 3 and the spine 4 eventually contacted with one another the guide faces (3s and 4s), the guide surfaces 3s, since 4s both have a twisted shape, FIG. of 3 (a), as shown in (b), different from the direction of the contact position before and after the AA section and BB cross section in FIG. 1, resulting longitudinal displacement of the condyles member 2a and 2b [delta] is, rotation is It begins to occur (Fig. 3). そして、さらに屈曲角度が増大すると、前記接触位置が上方に移動し、ずれδの量が増加して回旋角度も増加する(図4)。 Then, further when the bending angle is increased, the contact position is moved upward, also increases turning angle increases the amount of shift [delta] (FIG. 4). このようにして、屈曲にしたがって回旋が誘導される。 In this way, rotation is induced in accordance with bending. なお、上記図2〜4の場合において、案内面3s、4sのうち一方のみを捩った形状とし、他方を左右対称の形状としても、上記と同様の機構で回旋が誘導されることは明らかである。 Incidentally, in the case of FIG. 2 to 4, the guide surfaces 3s, a shape twisted only one of 4s, have a shape symmetrical to the other, clear that induces rotation in the same above mechanism it is. ただし、一方のみを捩った形状として、上記双方を捩った形状とする場合と同程度の回旋を生じさせるためには、その捩りの度合いを、双方を捩った形状とする場合に比べ大きくする必要があり、接触部位への応力集中が増加するおそれがある。 However, a shape twisted only one, in order to cause rotation of the same extent as if a shape twisted the two sides, as compared with the case where the degree of twisting, a twisted both shape should be larger, there is a possibility that stress concentration on the contact portion is increased.
【0031】 [0031]
なおカム3およびスパイン4の断面形状は、図2〜4に示すものに限られるものではなく、屈曲角度の変化によって旋回角度が変化するように構成されれば、どのような形状であってもかまわないが、荷重による応力に耐える形状とすることが好ましい。 Note sectional shape of the cam 3 and the spine 4 is not limited to those shown in FIGS. 2-4, if the turning angle is configured to vary with changes in the bend angle, be any shape may not, but is preferably a shape to withstand the stresses due to the load. 例えば、カム3の断面形状は、図2〜4の円形の他に楕円形等であってもよく、スパイン4の断面形状は、図2〜4のような略三角形の他に、略四角形等であってもよい。 For example, the cross-sectional shape of the cam 3 may have an elliptical shape or the like in addition to the circular 2-4, the cross-sectional shape of the spine 4, in addition to the substantially triangular as shown in FIG. 2-4, substantially square, etc. it may be.
【0032】 [0032]
また、案内面3sと4sとは、互いに接触したときに集中荷重を生じさせず、また摩耗をできるだけ少なくするため、角のない滑らかな表面形状としておくことがよい。 Further, the guide surfaces 3s and 4s, without causing concentrated load upon contact with each other, and in order to minimize wear, it is possible to keep a smooth surface shape with no corners.
【0033】 [0033]
また、図1に示すように、膝関節ができるだけ滑らかに屈曲するよう、顆状突起部材2a、2bの凸面部8a、8bは球面状とし、これらが当接しつつ摺動/転動する凹面部12a、12bも、集中荷重を生じさせず摩耗をできるだけ小さくするため、球面状とすることがよい。 Further, as shown in FIG. 1, so that the knee joint is as smooth as possible flexion, the condyles members 2a, 2b of the convex portion 8a, 8b is a spherical, concave portion to which they are sliding / rolling while contact 12a, 12b is also used to minimize the wear without causing the concentrated load may be a spherical shape.
【0034】 [0034]
さらに、凹面部12a、12bのうち一方の凹面部(図1では12a)の有意の部分の曲率をこれと接する凸面部(図1では8a)の有意の部分の曲率と概ね等しくし、他方の凹面部(図1では12b)の有意の部分の曲率をこれと接する凸面部(図1では8b)の有意の部分の曲率より小さくする(言い換えると、なだらかにする)ことが好ましい。 Further, the concave portion 12a, one of the concave portion of 12b was substantially equal to the curvature of the portion of significant convex portion in contact with this curvature of the significant part of (in FIG. 1 12a) (in FIG. 1 8a), the other concave portion is smaller than the curvature of a significant portion of the convex portion in contact with this curvature of the significant part of (in FIG. 1 12b) (in FIG. 1 8b) (in other words, be gently) is preferred. ここに「有意の部分」とは、当該人工膝関節の屈曲角度および回旋角度の範囲で凸面部12a(または12b)と凹面部8a(または8b)とが互いに接触し得る部分を意味する。 Here, the "portion of significant" means that portion in the range of flexion and torsion angle of the knee joint and the convex portion 12a (or 12b) and the concave portion 8a (or 8b) may contact each other. これにより、凹面部12aに凸面部8aが嵌まり込んでここを支点とする一方、凹面部12b内を凸面部8bが前後方向に摺動し得るので、回旋がより滑らかに行われる。 Thus, while a fulcrum here fits the convex portion 8a in the concave portion 12a, since the inside of the concave portion 12b is convex portion 8b can slide in the longitudinal direction, rotation is carried out more smoothly. なお凹面部12bの有意の部分の曲率は、案内面3s、4sの形状との組み合わせに応じて、より円滑な回旋が可能となるよう適宜調整すればよい。 Note curvature of the significant portion of the concave portion 12b, the guide surfaces 3s, depending on the combination of the shape of 4s, may be appropriately adjusted so as to be capable smoother rotation is.
【0035】 [0035]
なお、本発明に係る人工膝関節は、生体適合性、機械的強度、耐摩耗性等を考慮して、この分野で通常用いられている公知の材料で通常行われている公知の加工法により形成すればよい。 Incidentally, the artificial knee joint according to the present invention, the biocompatible, in view of mechanical strength, abrasion resistance, etc., by known processing method which is usually carried out in known materials commonly used in this field it may be formed. すなわち材料としては、例えばチタン、チタン合金、ステンレス鋼、Co−Cr合金等の金属材料、あるいはセラミックス素材、超高分子量ポリエチレン等の合成樹脂材料等を用い、各部材の表面(凸面部8a、8b、凹面部12a、12b)を鏡面・研磨加工等しておくことが好ましい。 That is, as the material, such as titanium, titanium alloy, stainless steel, Co-Cr metallic material such as alloy or ceramic material, a synthetic resin material such as ultra high molecular weight polyethylene, the surface of each member (convex portion 8a,, 8b it is preferable that the concave portions 12a, 12b) to keep the mirror-polishing or the like.
【0036】 [0036]
また、本発明の人工膝関節を実際に患者体内に埋設・装着するにあたっては、ポリメタクリル酸メチル等の骨セメントを用いて残存生体骨と接着する方法、あるいは骨セメントを用いずに人工膝関節の表面に凹凸をつけて生体骨を侵入させ固着する方法等、従来の人工膝関節に用いられている公知の技術を適宜採用すればよい。 Further, when actually embedded, attached to the patient an artificial knee joint of the present invention, a method for bonding the remaining living bone using bone cement poly methyl methacrylate or knee joint without the use of bone cement, and a method of fixing with a unevenness of the surface to penetrate the living bone, a known technique used in the conventional artificial knee joint may be employed as appropriate.
【0037】 [0037]
【実施例】 【Example】
図1に示した形状と同様の人工関節(カム3とスパイン4との双方を捩った形状とし、凹面12aは凸面8aと互いの有意の部分を略合同とし、凹面12bは凸面8bよりなだらかな形状としたもの)を3種類のサイズについて製作し、それぞれのサイズごとに屈曲角度を0度から150度まで順次増加させ、各屈曲角度における回旋角度を実測し、屈曲角度と回旋角度との関係を求め、その結果を図5に示した。 And both the twisted shape of the shape and the same prosthesis (cam 3 spine 4 shown in FIG. 1, the concave 12a is a significant portion of the convex surface 8a with each other and substantially congruent, concave 12b is gently than convex 8b shape and the one) were fabricated on three different sizes, a bending angle for each size successively increasing from 0 ° to 150 °, actually measured rotation angle at each flexion angle, the bending angle and the torsion angle obtained relation, the results are shown in Figure 5.
【0038】 [0038]
図5に示すように、各サイズの人工膝関節(図5の折れ線a、b、c)とも屈曲角度約70度までは回旋が生じないが、屈曲角度約90度に達すると回旋が生じ始め、以後、屈曲角度の増加とともに回旋角度も増加し、屈曲角度150度において回旋角度18〜22度が得られ、屈曲角度150度以上の高屈曲角度においてより自然で滑らかな屈曲を実現できる10度以上の回旋角度を確保できることを確認した。 As shown in FIG. 5, the artificial knee joint of each size (line a in FIG. 5, b, c) both to the bending angle of about 70 degrees is rotation does not occur, rotation reaches the bending angle of about 90 degrees begins to occur hereafter, torsion angle also increases with increasing bending angle, bending angle 150 rotation angle 18-22 degrees in degrees is obtained, 10 degrees can achieve more natural and smooth bending at the bent angle of 150 degrees or more high flexion It was confirmed to be able to ensure the rotation angle of the above.
【0039】 [0039]
なお、一般的な歩行に必要な最大屈曲角度は約60度でそのときの回旋角度は約3度である。 The maximum bending angle required for typical gait rotation angle at that time is about 60 degrees is about 3 degrees. したがって、歩行時に必要な屈曲角度の範囲においても回旋角度を制御することが好ましいが、スパインにカムが常に接触しつづけると、スパインの摩耗および破損、カムの折損等の危険性が増す。 Therefore, it is preferable to control the rotation angle also in bending angle of the range required during walking, when the cam continues always in contact with the spine, wear and damage to the spine, the risk of breakage or the like of the cam increases. そのため、本実施例では屈曲角度約70度まではスパインとカムとを接触させず回旋が生じない構造とした。 Therefore, to the bending angle of about 70 degrees in this embodiment has a structure in which rotation does not occur without contacting the spine and the cam.
【0040】 [0040]
【発明の効果】 【Effect of the invention】
以上説明したように、本発明によれば、屈曲角度に対応した回旋角度が誘導され150度以上の高屈曲角度まで円滑に屈曲できる人工膝関節を提供できるようになった。 As described above, according to the present invention, it becomes possible to provide an artificial knee joint can be smoothly bent to high flexion angles above the turning angle is derived 150 degrees corresponding to the bending angle.
【図面の簡単な説明】 BRIEF DESCRIPTION OF THE DRAWINGS
【図1】本発明の実施に係る人工膝関節の斜視図である。 1 is a perspective view of the artificial knee joint according to an embodiment of the present invention.
【図2】本発明の実施に係る人工膝関節の、屈曲角度0度における動作状態を説明する図である。 [Figure 2] of the knee prosthesis according to an embodiment of the present invention, is a diagram illustrating the operation state in the bending angle of 0 °.
【図3】本発明の実施に係る人工膝関節の、屈曲角度90度における作動状態を説明する図である。 [Figure 3] of the artificial knee joint according to an embodiment of the present invention, is a diagram for explaining the operating state in the bending angle of 90 degrees.
【図4】本発明の実施に係る人工膝関節の、屈曲角度150度における作動状態を説明する図である。 [Figure 4] of the artificial knee joint according to an embodiment of the present invention, is a diagram for explaining the operating state in the bending angle of 150 degrees.
【図5】実施例の人工膝関節における、屈曲角度と回旋角度との関係を示す図である。 In artificial knee joint of Figure 5 embodiment, and shows the relationship between the bending angle and rotation angle.
【図6】人工膝関節を生体に取り付けた状態を説明する図である。 6 is a diagram for explaining a state in which the artificial knee joint attached to a living body.
【図7】従来例1の人工膝関節の大腿骨コンポーネントの側面図である。 7 is a side view of a femoral component of a conventional example 1 of the artificial knee joint.
【図8】従来例1の人工膝関節の屈曲角度約130度における側面図である。 8 is a side view of the bending angle of about 130 degrees of the conventional example 1 of the artificial knee joint.
【図9】従来例2の人工膝関節の斜視図である。 9 is a perspective view of the artificial knee joint of a conventional example 2.
【符号の説明】 DESCRIPTION OF SYMBOLS
1…大腿骨コンポーネント2a、2b…顆状突起部材3…結合部材(カム) 1 ... femoral component 2a, 2b ... condyles member 3 ... coupling member (cam)
3s…案内面4…突起部(スパイン) 3s ... guide surface 4 ... protrusions (spine)
4s…案内面5…前部6…後部7…凸面部8、8a、8b…凸面部9…間隔11…脛骨コンポーネント12…関節面12a、12b…凹部A…大腿骨B…脛骨 4s ... guide surface 5 ... front 6 ... rear 7 ... convex portion 8, 8a, 8b ... convex portion 9 ... gap 11 ... tibial component 12 ... articular surfaces 12a, 12b ... recess A ... femoral B ... tibia

Claims (3)

  1. 大腿骨の遠位部に装着される大腿骨コンポーネントと脛骨の近位部に装着される脛骨コンポーネントとからなる人工膝関節において、該人工膝関節の屈曲角度の変化に対応して該人工膝関節の回旋角度が変化するように構成された人工膝関節。 In the artificial knee joint comprising a tibial component to be attached to the proximal portion of the femoral component and the tibial mounted on the distal portion of the femur, the knee joint in response to changes in the bending angle of the knee joint configured knee joint so that the turning degree change.
  2. 大腿骨の遠位部に装着される大腿骨コンポーネントと脛骨の近位部に装着される脛骨コンポーネントとからなる人工膝関節において、 In the artificial knee joint comprising a tibial component to be attached to the proximal portion of the femoral component and the tibial mounted on the distal portion of the femur,
    前記大腿骨コンポーネントが、互いに間隔をあけて横に設けられた一対の顆状突起部材と、該一対の顆状突起部材の互いの後部を結合する、概ね全周に案内面を有する結合部材とを備え、 The femoral component, and a pair of condyle members provided laterally spaced from each other, coupling the rear portion of each other of the pair of condyles member, a generally binding member having a guide surface in entire periphery equipped with a,
    前記脛骨コンポーネントが、前記各顆状突起部材の凸面部が摺動及び/又は転動する一対の凹面部と、前記一対の顆状突起部材の間隔に嵌入され該間隔の長手方向に可動自在となるように形成された、概ね後方に向かう案内面を有する突起部とを備え、 The tibial component, a pair of concave portions convex surface portions of the respective condyle member slides and / or rolls, freely longitudinally movable of said pair of condylar is fitted to the spacing of the projecting member said spacing becomes so formed, and a protruding portion having a generally guide surface towards the rear,
    該人工膝関節の屈曲角度が変化したとき、前記突起部と前記結合部材との互いの案内面の接触部位の位置が変化することにより、該人工膝関節の回旋角度が変化するように構成された人工膝関節。 When the bending angle of the knee joint is changed, by the position of the contact portion of the guide surface of each other and the coupling member and the projections is changed, configured as torsion angle of the artificial knee joint is changed artificial knee joint.
  3. 前記結合部材の案内面と前記突起部の案内面のうち少なくとも一つが、捩じれた形状である請求項2に記載の人工膝関節。 Wherein at least one of the guide surface of the guide surface of the coupling member and the protrusion, twisted shape an artificial knee joint according to claim 2.
JP2002333917A 2002-11-18 2002-11-18 Artificial knee joint Expired - Fee Related JP4148316B2 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP2002333917A JP4148316B2 (en) 2002-11-18 2002-11-18 Artificial knee joint

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
JP2002333917A JP4148316B2 (en) 2002-11-18 2002-11-18 Artificial knee joint

Publications (2)

Publication Number Publication Date
JP2004166802A true JP2004166802A (en) 2004-06-17
JP4148316B2 JP4148316B2 (en) 2008-09-10

Family

ID=32698492

Family Applications (1)

Application Number Title Priority Date Filing Date
JP2002333917A Expired - Fee Related JP4148316B2 (en) 2002-11-18 2002-11-18 Artificial knee joint

Country Status (1)

Country Link
JP (1) JP4148316B2 (en)

Cited By (36)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2007007841A1 (en) * 2005-07-14 2007-01-18 Saga University Artificial knee joint
JP2010012262A (en) * 2008-06-30 2010-01-21 Depuy Products Inc Tibial bearing having increased axial-rotation
JP2010188051A (en) * 2009-02-20 2010-09-02 Japan Medical Materials Corp Artificial knee joint
JP2012513254A (en) * 2008-12-23 2012-06-14 エースキュラップ インプラント システムズ, エルエルシー Knee prosthesis
JP2013513435A (en) * 2009-12-09 2013-04-22 ザ・ジエネラル・ホスピタル・コーポレーシヨン・ドウーイング・ビジネス・アズ・マサチユセツツ・ジエネラル・ホスピタル Implants that repair the normal range of knee flexion and movement
US8551179B2 (en) 2011-06-16 2013-10-08 Zimmer, Inc. Femoral prosthesis system having provisional component with visual indicators
US8690954B2 (en) 2011-11-18 2014-04-08 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
JP2014510562A (en) * 2011-01-27 2014-05-01 スミス アンド ネフュー インコーポレーテッド Restraint knee prosthesis
WO2014208687A1 (en) 2013-06-27 2014-12-31 京セラメディカル株式会社 Artificial knee joint implant
US8932365B2 (en) 2011-06-16 2015-01-13 Zimmer, Inc. Femoral component for a knee prosthesis with improved articular characteristics
JP2015512762A (en) * 2012-04-13 2015-04-30 コンフォーミス・インコーポレイテッドConforMIS, Inc. Devices and methods for additive manufacturing of implant components
US9060868B2 (en) 2011-06-16 2015-06-23 Zimmer, Inc. Femoral component for a knee prosthesis with bone compacting ridge
US9132014B2 (en) 2010-04-13 2015-09-15 Zimmer, Inc. Anterior cruciate ligament substituting knee implants
US9173744B2 (en) 2010-09-10 2015-11-03 Zimmer Gmbh Femoral prosthesis with medialized patellar groove
US9220600B2 (en) 2008-12-23 2015-12-29 Aesculap Implant Systems, Llc Knee prosthesis
US9301845B2 (en) 2005-06-15 2016-04-05 P Tech, Llc Implant for knee replacement
US9308095B2 (en) 2011-06-16 2016-04-12 Zimmer, Inc. Femoral component for a knee prosthesis with improved articular characteristics
US9408686B1 (en) 2012-01-20 2016-08-09 Conformis, Inc. Devices, systems and methods for manufacturing orthopedic implants
US9517134B2 (en) 2007-02-14 2016-12-13 Conformis, Inc. Implant device and method for manufacture
JP2017501837A (en) * 2014-01-08 2017-01-19 デピュイ・(アイルランド)Depuy (Ireland) System for use in knee surgery
US9579110B2 (en) 2001-05-25 2017-02-28 Conformis, Inc. Patient selectable joint arthroplasty devices and surgical tools
US9592127B2 (en) 2005-12-15 2017-03-14 Zimmer, Inc. Distal femoral knee prostheses
US9615929B2 (en) 2009-01-23 2017-04-11 Zimmer, Inc. Posterior-stabilized total knee prosthesis
US9636229B2 (en) 2012-09-20 2017-05-02 Conformis, Inc. Solid freeform fabrication of implant components
US9662217B2 (en) 2011-07-13 2017-05-30 Zimmer Gmbh Femoral knee prosthesis with diverging lateral condyle
US9700971B2 (en) 2001-05-25 2017-07-11 Conformis, Inc. Implant device and method for manufacture
US9849019B2 (en) 2012-09-21 2017-12-26 Conformis, Inc. Methods and systems for optimizing design and manufacture of implant components using solid freeform fabrication
KR20180115533A (en) * 2017-04-13 2018-10-23 주식회사 티제이씨라이프 Artificial Knee Joint Having Enhanced Physical Property, And Design Method
US10130375B2 (en) 2014-07-31 2018-11-20 Zimmer, Inc. Instruments and methods in performing kinematically-aligned total knee arthroplasty
US10136997B2 (en) 2015-09-29 2018-11-27 Zimmer, Inc. Tibial prosthesis for tibia with varus resection
US10188530B2 (en) 2010-12-17 2019-01-29 Zimmer, Inc. Provisional tibial prosthesis system
US10195041B2 (en) 2010-07-24 2019-02-05 Zimmer, Inc. Asymmetric tibial components for a knee prosthesis
US10265181B2 (en) 2011-11-21 2019-04-23 Zimmer, Inc. Tibial baseplate with asymmetric placement of fixation structures
US10278827B2 (en) 2015-09-21 2019-05-07 Zimmer, Inc. Prosthesis system including tibial bearing component
US10413415B2 (en) 2010-09-10 2019-09-17 Zimmer, Inc. Motion facilitating tibial components for a knee prosthesis
US10470889B2 (en) 2017-11-30 2019-11-12 Zimmer, Inc. Asymmetric tibial components for a knee prosthesis

Cited By (64)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9700971B2 (en) 2001-05-25 2017-07-11 Conformis, Inc. Implant device and method for manufacture
US9579110B2 (en) 2001-05-25 2017-02-28 Conformis, Inc. Patient selectable joint arthroplasty devices and surgical tools
US9301845B2 (en) 2005-06-15 2016-04-05 P Tech, Llc Implant for knee replacement
US9750612B2 (en) 2005-06-15 2017-09-05 P Tech, Llc Methods and systems for providing gender specific pharmaceuticals
WO2007007841A1 (en) * 2005-07-14 2007-01-18 Saga University Artificial knee joint
JP4887292B2 (en) * 2005-07-14 2012-02-29 国立大学法人佐賀大学 Artificial knee joint
US7955394B2 (en) 2005-07-14 2011-06-07 Saga University Artificial knee joint
US10433966B2 (en) 2005-12-15 2019-10-08 Zimmer, Inc. Distal femoral knee prostheses
US9592127B2 (en) 2005-12-15 2017-03-14 Zimmer, Inc. Distal femoral knee prostheses
US9517134B2 (en) 2007-02-14 2016-12-13 Conformis, Inc. Implant device and method for manufacture
JP2010012262A (en) * 2008-06-30 2010-01-21 Depuy Products Inc Tibial bearing having increased axial-rotation
US9220600B2 (en) 2008-12-23 2015-12-29 Aesculap Implant Systems, Llc Knee prosthesis
JP2012513254A (en) * 2008-12-23 2012-06-14 エースキュラップ インプラント システムズ, エルエルシー Knee prosthesis
US9615929B2 (en) 2009-01-23 2017-04-11 Zimmer, Inc. Posterior-stabilized total knee prosthesis
US10076420B2 (en) 2009-01-23 2018-09-18 Zimmer, Inc. Posterior-stabilized total knee prosthesis
JP2010188051A (en) * 2009-02-20 2010-09-02 Japan Medical Materials Corp Artificial knee joint
JP2013513435A (en) * 2009-12-09 2013-04-22 ザ・ジエネラル・ホスピタル・コーポレーシヨン・ドウーイング・ビジネス・アズ・マサチユセツツ・ジエネラル・ホスピタル Implants that repair the normal range of knee flexion and movement
US9861484B2 (en) 2010-04-13 2018-01-09 Zimmer, Inc. Anterior cruciate ligament substituting knee implants
US9132014B2 (en) 2010-04-13 2015-09-15 Zimmer, Inc. Anterior cruciate ligament substituting knee implants
US10195041B2 (en) 2010-07-24 2019-02-05 Zimmer, Inc. Asymmetric tibial components for a knee prosthesis
US10413415B2 (en) 2010-09-10 2019-09-17 Zimmer, Inc. Motion facilitating tibial components for a knee prosthesis
US10322004B2 (en) 2010-09-10 2019-06-18 Zimmer Gmbh Femoral prosthesis with lateralized patellar groove
US9867708B2 (en) 2010-09-10 2018-01-16 Zimmer Gmbh Femoral prosthesis with lateralized patellar groove
US9173744B2 (en) 2010-09-10 2015-11-03 Zimmer Gmbh Femoral prosthesis with medialized patellar groove
US10188530B2 (en) 2010-12-17 2019-01-29 Zimmer, Inc. Provisional tibial prosthesis system
JP2014510562A (en) * 2011-01-27 2014-05-01 スミス アンド ネフュー インコーポレーテッド Restraint knee prosthesis
JP2016163771A (en) * 2011-01-27 2016-09-08 スミス アンド ネフュー インコーポレーテッド Constrained knee prosthesis
US9993345B2 (en) 2011-06-16 2018-06-12 Zimmer, Inc. Femoral prosthesis system
US10441429B2 (en) 2011-06-16 2019-10-15 Zimmer, Inc. Femoral component for a knee prosthesis with improved articular characteristics
US8932365B2 (en) 2011-06-16 2015-01-13 Zimmer, Inc. Femoral component for a knee prosthesis with improved articular characteristics
US9308095B2 (en) 2011-06-16 2016-04-12 Zimmer, Inc. Femoral component for a knee prosthesis with improved articular characteristics
US8551179B2 (en) 2011-06-16 2013-10-08 Zimmer, Inc. Femoral prosthesis system having provisional component with visual indicators
US9629723B2 (en) 2011-06-16 2017-04-25 Zimmer, Inc. Femoral component for a knee prosthesis with improved articular characteristics
US10045850B2 (en) 2011-06-16 2018-08-14 Zimmer, Inc. Femoral component for a knee prosthesis with improved articular characteristics
US9060868B2 (en) 2011-06-16 2015-06-23 Zimmer, Inc. Femoral component for a knee prosthesis with bone compacting ridge
US10070966B2 (en) 2011-06-16 2018-09-11 Zimmer, Inc. Femoral component for a knee prosthesis with bone compacting ridge
US9662217B2 (en) 2011-07-13 2017-05-30 Zimmer Gmbh Femoral knee prosthesis with diverging lateral condyle
US9655729B2 (en) 2011-11-18 2017-05-23 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
US9655728B2 (en) 2011-11-18 2017-05-23 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
US9788954B2 (en) 2011-11-18 2017-10-17 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
US9295558B2 (en) 2011-11-18 2016-03-29 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
US9204970B2 (en) 2011-11-18 2015-12-08 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
US9186255B2 (en) 2011-11-18 2015-11-17 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
US9072607B2 (en) 2011-11-18 2015-07-07 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
US8858643B2 (en) 2011-11-18 2014-10-14 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
US9925050B2 (en) 2011-11-18 2018-03-27 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
US8764838B2 (en) 2011-11-18 2014-07-01 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
JP2017221732A (en) * 2011-11-18 2017-12-21 ジンマー,インコーポレイティド Tibial bearing component for knee prosthesis with improved articular characteristics
US8690954B2 (en) 2011-11-18 2014-04-08 Zimmer, Inc. Tibial bearing component for a knee prosthesis with improved articular characteristics
US10265181B2 (en) 2011-11-21 2019-04-23 Zimmer, Inc. Tibial baseplate with asymmetric placement of fixation structures
US9408686B1 (en) 2012-01-20 2016-08-09 Conformis, Inc. Devices, systems and methods for manufacturing orthopedic implants
US10456261B2 (en) 2012-01-20 2019-10-29 Conformis, Inc. Devices, systems and methods for manufacturing orthopedic implants
JP2015512762A (en) * 2012-04-13 2015-04-30 コンフォーミス・インコーポレイテッドConforMIS, Inc. Devices and methods for additive manufacturing of implant components
US9636229B2 (en) 2012-09-20 2017-05-02 Conformis, Inc. Solid freeform fabrication of implant components
US9849019B2 (en) 2012-09-21 2017-12-26 Conformis, Inc. Methods and systems for optimizing design and manufacture of implant components using solid freeform fabrication
WO2014208687A1 (en) 2013-06-27 2014-12-31 京セラメディカル株式会社 Artificial knee joint implant
US9839520B2 (en) 2013-06-27 2017-12-12 Kyocera Corporation Artificial knee joint implant
JP2017501837A (en) * 2014-01-08 2017-01-19 デピュイ・(アイルランド)Depuy (Ireland) System for use in knee surgery
US10130375B2 (en) 2014-07-31 2018-11-20 Zimmer, Inc. Instruments and methods in performing kinematically-aligned total knee arthroplasty
US10278827B2 (en) 2015-09-21 2019-05-07 Zimmer, Inc. Prosthesis system including tibial bearing component
US10136997B2 (en) 2015-09-29 2018-11-27 Zimmer, Inc. Tibial prosthesis for tibia with varus resection
KR101941701B1 (en) * 2017-04-13 2019-04-11 주식회사 티제이씨라이프 Artificial Knee Joint Having Enhanced Physical Property, And Design Method
KR20180115533A (en) * 2017-04-13 2018-10-23 주식회사 티제이씨라이프 Artificial Knee Joint Having Enhanced Physical Property, And Design Method
US10470889B2 (en) 2017-11-30 2019-11-12 Zimmer, Inc. Asymmetric tibial components for a knee prosthesis

Also Published As

Publication number Publication date
JP4148316B2 (en) 2008-09-10

Similar Documents

Publication Publication Date Title
US7261740B2 (en) Tibial knee prosthesis
EP0449391B1 (en) Tool assembly for a prosthetic knee
JP4296091B2 (en) Posterior spinal joint prosthesis
US8337564B2 (en) Total knee replacement prosthesis
AU2016200458B2 (en) Posterior cruciate-retaining orthopaedic knee prosthesis having controlled condylar curvature
EP2878283B1 (en) Orthopaedic prosthesis
US9642711B2 (en) High flexion articular insert
US5964808A (en) Knee prosthesis
ES2205003T3 (en) Fermoral condyle design component for knee replacement.
DE60125620T2 (en) Posterior stabilized knee replacement for knees with preserved lateral ligaments
JP5528690B2 (en) Fixed-bearing knee prosthesis
JP3862358B2 (en) Elbow joint - artificial skull
CN101351172B (en) Modular fixed and mobile bearing prosthesis system
DE69835704T2 (en) Knee prosthesis with movable insert and metal-metal contact surface
EP2149353B1 (en) Orthopaedic Knee Prosthesis
JP4159256B2 (en) Articulating artificial spinal disc
EP0732091B1 (en) Mobile bearing total joint replacement
US5507820A (en) Fixed bearing joint endoprosthesis
AU746243B2 (en) Femoral component for knee endoprosthesis
CN102058448B (en) Fixed-bearing knee prosthesis assembly having interchangeable
ES2218097T3 (en) Prosthesis mono-knee.
EP0781117B1 (en) Prosthetic knee joint device
ES2343007T3 (en) Knee protesis with mobile support.
US5219362A (en) Knee prosthesis
JP3738221B2 (en) Knee prosthesis

Legal Events

Date Code Title Description
A621 Written request for application examination

Free format text: JAPANESE INTERMEDIATE CODE: A621

Effective date: 20051021

A521 Written amendment

Free format text: JAPANESE INTERMEDIATE CODE: A821

Effective date: 20051021

A977 Report on retrieval

Free format text: JAPANESE INTERMEDIATE CODE: A971007

Effective date: 20071227

A131 Notification of reasons for refusal

Free format text: JAPANESE INTERMEDIATE CODE: A131

Effective date: 20080325

A521 Written amendment

Free format text: JAPANESE INTERMEDIATE CODE: A523

Effective date: 20080509

TRDD Decision of grant or rejection written
A01 Written decision to grant a patent or to grant a registration (utility model)

Free format text: JAPANESE INTERMEDIATE CODE: A01

Effective date: 20080610

A01 Written decision to grant a patent or to grant a registration (utility model)

Free format text: JAPANESE INTERMEDIATE CODE: A01

A61 First payment of annual fees (during grant procedure)

Free format text: JAPANESE INTERMEDIATE CODE: A61

Effective date: 20080617

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20110704

Year of fee payment: 3

R150 Certificate of patent or registration of utility model

Free format text: JAPANESE INTERMEDIATE CODE: R150

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20110704

Year of fee payment: 3

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20120704

Year of fee payment: 4

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20130704

Year of fee payment: 5

R250 Receipt of annual fees

Free format text: JAPANESE INTERMEDIATE CODE: R250

R250 Receipt of annual fees

Free format text: JAPANESE INTERMEDIATE CODE: R250

S533 Written request for registration of change of name

Free format text: JAPANESE INTERMEDIATE CODE: R313533

S531 Written request for registration of change of domicile

Free format text: JAPANESE INTERMEDIATE CODE: R313531

S111 Request for change of ownership or part of ownership

Free format text: JAPANESE INTERMEDIATE CODE: R313117

R350 Written notification of registration of transfer

Free format text: JAPANESE INTERMEDIATE CODE: R350

R350 Written notification of registration of transfer

Free format text: JAPANESE INTERMEDIATE CODE: R350

R250 Receipt of annual fees

Free format text: JAPANESE INTERMEDIATE CODE: R250

R250 Receipt of annual fees

Free format text: JAPANESE INTERMEDIATE CODE: R250

R250 Receipt of annual fees

Free format text: JAPANESE INTERMEDIATE CODE: R250

LAPS Cancellation because of no payment of annual fees