CN101683290B - 具有可控骨节曲率的后固定膝关节矫形假体 - Google Patents
具有可控骨节曲率的后固定膝关节矫形假体 Download PDFInfo
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Abstract
本发明公开一种具有可控骨节曲率的后固定膝关节矫形假体,包括胫骨轴承和股骨组件,所述股骨组件构造成与胫骨轴承铰接。股骨组件包括后凸轮,所述后凸轮构造成与胫骨轴承的隆凸接触,股骨组件还包括在矢状面中弯曲的骨节表面。骨节表面的曲率半径在早期屈曲和中期屈曲之间逐渐变小。此外在一些实施例中,骨节表面的曲率半径可在中期屈曲过程中增加。
Description
相关美国专利申请的交叉引用
交叉引用:序列号为12/165,579,题目为《具有可控骨节曲率的股骨矫形组件》(″Orthopaedic Femoral Component Having Controlled CondylarCurvature″),由John L.Williams等在2008年6月30日申请的美国实用专利申请;序列号为12/165,574,题目为《具有可控骨节曲率的后十字保持膝关节矫形假体》(″Posterior Cruciate-Retaining Orthopaedic Knee Prosthesis HavingControlled Condylar Curvature″),由Christel M.Wagner在2008年6月30日申请的美国实用专利申请;序列号为12/165,582,题目为《后部固定的矫形假体》(″Posterior Stabilized Orthopaedic Prosthesis″),由Joseph G. Wyss在2008年6月30日申请的美国实用专利申请;以及序列号为61/077,124,题目为《具有可控骨节曲率的膝关节矫形假体》(″Orthopaedic Knee Prosthesis Having ControlledCondylar Curvature″),由Joseph G. Wyss在2008年6月30日申请的美国临时专利申请,上述全部中的每一个在此结合作为参考。
技术领域
本发明的公开内容通常涉及矫形假体,特别涉及用于膝关节置换手术的矫形假体。
背景技术
关节成型术是公知的用关节假体置换患病的和/或损伤的天然关节的外科手术过程。经典的膝关节假体包括胫骨盘、股骨组件以及在胫骨盘和股骨组件之间的聚合体插入件或固定轴承。根据患者关节的损伤严重性,可采用灵活性可变的矫形假体。例如,在例如出现了重大软组织损伤或流失的时候,膝关节假体可包括“固定的”胫骨轴承,这种情况下就需要限制膝关节假体的运动。可选地,膝关节假体可包括“活动的”胫骨轴承,这种情况下会需要较大程度的运动自由度。另外,膝关节假体可以是整个的膝关节假体,它设计用于替换患者股骨双骨节的股骨-胫骨界面,或是单侧的(或单骨节)膝关节假体,设计用于替换患者股骨的单个骨节的股骨-胫骨界面。
用于替换患者天然膝关节的膝关节矫形假体的种类还要看手术过程中是否将患者的后十字韧带保留或者牺牲掉了(也就是去掉了)。例如,如果患者的后十字韧带受损,坏了,和/或在手术过程中被去除了,就需要使用后固定的膝关节假体来提供额外的支撑和/或之后的屈曲度。可选地,如果后十字韧带是完好的,就会用到十字保持膝关节假体。
典型的膝关节矫形假体通常设计为复制患者关节的自然运动。随着膝关节的屈曲和伸展,股骨和胫骨部件铰接并进行相对的前后运动和相对的内外侧旋转运动的组合。然而,患者的周围软组织也会贯穿整个关节运动范围对膝关节矫形假体的运动及稳定性产生影响。那就是说,由患者软组织外加于假体组件的作用力可能会引起膝关节矫形假体发生不希望或不必要的运动。例如,膝关节矫形假体随着股骨组件在屈曲范围内移动会表现出一定量不自然的(不合理的)前向平移。
在典型的膝关节矫形假体中,不合理的前向平移会发生在几乎任意角度的屈曲过程中,但特别是发生在屈曲角度的中后位置。不合理的前向平移可以通常被定义成股骨组件在胫骨轴承上的异常相对运动,其中股骨组件和胫骨轴承之间的接触“点”相对于胫骨轴承向前“滑动”了。这种不合理的前向平移会导致关节稳定性流失,加速磨损,膝关节异常运功,和/或引起患者在一些活动过程中经历不稳的感觉。
发明内容
依照一个方面,后固定膝关节矫形假体包括股骨组件和胫骨轴承。股骨组件可包括一对间隔分开的骨节,这对骨节在它们之间限定了骨节内凹槽。该对间隔分开的骨节中的至少一个可具有在矢状面中弯曲的骨节表面。股骨组件还可包括定位在骨节内凹槽中的后凸轮。胫骨轴承可包括平台和从平台向上延伸的隆凸,平台具有轴承表面,所述轴承表面构造成与股骨组件的骨节表面铰接。
在一些实施方式中,股骨组件的骨节表面:可与轴承表面以第一屈曲角度在骨节表面上的第一接触点接触;可与轴承表面以第二屈曲角度在骨节表面上的第二接触点接触;以及可与轴承表面以第三屈曲角度在骨节表面上的第三接触点接触。另外,股骨组件的后凸轮可与胫骨轴承的隆凸在第四屈曲角度接触。
第二屈曲角度可以比第一屈曲角度更大,并且在一些实施例中可处于约为0度到约为50之间的范围内。例如,在一个实施例中,第二屈曲角度可不大于约30度。第三屈曲角度可以比第二屈曲角度大并小于约90度。例如,例如,在一个实施例中,第三屈曲角度至少是30度。在另一个实施例中,第三屈曲角度至少是50度。在又一个实施例中,第三屈曲角度至少是70度。在一些实施例中,第四屈曲角度比第三屈曲角度大不超过10度。例如,在一个特定的实施例中,第四屈曲角度不大于第三屈曲角度。另外地,在一些实施例中,第四屈曲角度至少是50度。在另一个实施例中,第四屈曲角度至少是70度。
矢状面中的骨节表面可在第一接触点具有第一曲率半径,在第二接触点具有第二曲率半径,以及在第三接触点具有第三曲率半径。在一些实施例中,第三曲率半径比第二曲率半径大至少0.5毫米。例如,在一些实施例中,第三曲率半径比第二曲率半径大至少2毫米,或在另外的实施例中大5毫米。另外,在一些实施例中,第二半径与第三半径的比率处于0.75到0.85的范围内。
在一些实施方式中,股骨组件在矢状面内的骨节表面可包括第一弯曲表面部和第二弯曲表面部。第一弯曲表面部可被限定在第一接触点和第二接触点之间。第二弯曲表面部可被限定在第二接触点和第三接触点之间。在这样的实施例中,第一弯曲表面部具有基本不变的曲率半径,它基本等于第二曲率半径。另外,第二弯曲表面部具有基本不变的曲率半径,它基本等于第三曲率半径。
依照另一方面,后固定膝关节矫形假体可包括股骨组件和胫骨轴承。股骨组件可包括一对间隔分开的骨节,这对骨节在它们之间限定了骨节内凹槽。这对间隔分开的骨节中至少一个可具有在矢状面中弯曲的骨节表面。股骨组件还可包括定位在骨节内凹槽中的后凸轮。胫骨轴承可包括平台和从平台向上延伸的隆凸,平台具有轴承表面,所述轴承表面构造成与股骨组件的骨节表面铰接。
在一些实施方式中,股骨组件的骨节表面可与轴承表面以第一屈曲角度在骨节表面上的第一接触点接触。第一屈曲角度可小于约30度。另外,骨节表面与轴承表面以第二屈曲角度在骨节表面上的第二接触点接触。第二屈曲角度可处于35度到90度的范围内。股骨组件的骨节表面还与轴承表面以第三屈曲角度在骨节表面上的第三接触点接触。第三屈曲角度可以大于第二屈曲角度。另外,当股骨组件从第一屈曲角度移动到第二屈曲角度时,骨节表面与轴承表面在第一接触点和第二接触点之间的多个接触点上接触。进一步说,在一些实施例中,股骨组件的后凸轮可与胫骨轴承的隆凸以第四屈曲角度接触。第四屈曲角度可小于,或基本等于,或略大于第三屈曲角度,其中,后凸轮与隆凸在所述角度接触。例如,在一个实施例中,第四屈曲角度比第三屈曲角度大不超过大约10度。
在一些实施例中,这多个接触点中的每一个接触点由从共同起点延伸到这多个接触点的相应接触点的射线限定。每条射线可具有由下列多项式定义的长度:rθ=(a+(b*θ)+(c*θ2)+(d*θ3)),其中,rθ为在θ度屈曲时接触点限定的射线的长度,a为处于20-50之间的系数值,b为处于从由-0.30<b<0.0,0.00<b<0.30和b=0组成的组中选择的区间中的系数值。如果b处于-0.30<b<0.00区间,则c为在0.00到0.012间的系数值,而d为在-0.00015到0.00之间的系数值。可选择地,如果b处于0<b<0.30的区间中,则c为在-0.010到0.00之间的系数值,而d为在-0.00015到0.00之间的系数值。还可选择,如果b等于0,则c为处于从由-0.0020<c<0.00和0.00<c<0.0025组成的组中选择的区间中的系数值,且d为在-0.00015到0.00间的系数值。在一些实施例中,第一曲率半径的起点和射线的共同起点之间的距离在0到10毫米的范围内。
在一些实施例中,第一屈曲角度可处于0度到10度的范围内,第二屈曲角度可处于45度到55度的范围内,并且第三屈曲角度可处于约65度到约75度的范围内。例如,在一个特定的实施例中,第一屈曲角度约为10度,第二屈曲角度约为50度,而第三屈曲角度约为70度。另外,第四屈曲角度约为70度。
在一些实施例中,矢状面中的骨节表面可在第一接触点具有第一曲率半径,在第二接触点具有第二曲率半径,以及在第三接触点具有第三曲率半径。在这样的实施例中,第三曲率半径比第二曲率半径大至少0.5毫米。在一些实施例中,第三曲率半径比第一曲率半径大至少2毫米。另外,在一些实施例中,第三曲率半径比第一曲率半径大至少5毫米。
另外,在一些实施例中,股骨组件在矢状面内的骨节表面可包括限定在第二接触点和第三接触点之间的弯曲表面部。在这样的实施例中,弯曲表面部具有基本不变的曲率半径,该曲率半径基本等于第三曲率半径。
根据又另一方面,后固定膝关节矫形假体可包括含有股骨组件和胫骨轴承的后固定膝关节矫形假体。股骨组件可包括一对间隔分开的骨节,这对骨节在它们之间限定了骨节内凹槽。这对间隔分开的骨节中至少一个可具有在矢状面中弯曲的骨节表面。股骨组件还可包括定位在骨节内凹槽中的后凸轮。胫骨轴承可包括平台和从平台向上延伸的隆凸,平台具有轴承表面,所述轴承表面构造成与股骨组件的骨节表面铰接。
在一些实施例中,股骨组件的骨节表面可与轴承表面以第一屈曲角度在骨节表面上的第一接触点接触。第一屈曲角度可小于约30度。另外,骨节表面与轴承表面以第二屈曲角度在骨节表面上的第二接触点接触。第二屈曲角度可处于35度到90度的范围内。股骨组件的骨节表面还与轴承表面以第三屈曲角度在骨节表面上的第三接触点接触。第三屈曲角度可以大于第二屈曲角度。在一些实施例中,股骨组件的后凸轮可与胫骨轴承的隆凸以第四屈曲角度接触。另外,当股骨组件从第一屈曲角度移动到第二屈曲角度时,骨节表面与轴承表面在第一接触点和第二接触点之间的多个接触点上接触。进一步说,在一些实施例中,股骨组件的后凸轮可与胫骨轴承的隆凸以第四屈曲角度接触。第四屈曲角度可小于或等于第三屈曲角度。
在一些实施例中,矢状面中的骨节表面可在第一接触点具有第一曲率半径,在第二接触点具有第二曲率半径,以及在第三接触点具有第三曲率半径。在这样的实施例中,第三曲率半径比第二曲率半径大至少2.0毫米。
仍进一步说,这多个接触点中的每个接触点是由从各个接触点的共同起点延伸到该多个接触点的对应接触点的射线。每条射线可具有由下列多项式定义的长度:rθ=(a+(b*θ)+(c*θ2)+(d*θ3)),其中,rθ为限定θ度屈曲处的接触点的射线的长度,a为处于20-50之间的系数值,以及b为处于从由-0.30<b<0.0,0.00<b<0.30和b=0组成的组中选择的区间中的系数值。如果b处于-0.30<b<0.00区间,则c为在0.00到0.012之间的系数值,而d为在-0.00015到0.00之间的系数值。可选择地,如果b处于0<b<0.30区间,则c为在-0.010到0.00之间的系数值,而d为在-0.00015到0.00间的系数值。还可选择,如果b等于0,则c为处于从由-0.0020<c<0.00和0.00<c<0.0025组成的组中选择的区间中的系数值,且d为在-0.00015到0.00间的系数值。在一些实施例中,第一曲率半径的起点和射线的共同起点之间的距离在0到10毫米内。
另外,在一些实施例中,每对间隔分开的骨节的每一个可包括骨节表面。在这样的实施例中,骨节表面可以为大致对称的或者不对称的。
附图说明
具体描述特别参考下面的附图,其中:
图1是膝关节矫形假体的一个实施方式的分解透视图;
图2是图1的股骨组件和胫骨轴承大致沿剖面线2-2的横截面视图,其中股骨组件铰接到第一屈曲角度;
图3是图2的股骨组件和胫骨轴承的横截面视图,其中股骨组件铰接到第二屈曲角度;
图4是图2的股骨组件和胫骨轴承的横截面视图,其中股骨组件铰接到第三屈曲角度;
图5是图1的股骨组件一个实施方式的横截面视图;
图6是图1的股骨组件另一个实施方式的横截面视图;
图7是图1的股骨组件另一个实施方式的横截面视图;
图8是图1的股骨组件另一个实施方式的横截面视图;
图9是模拟位于各种不同屈曲角度下具有递增的曲率半径的股骨组件的前后平移图;
图10是另一个模拟位于各种不同屈曲角度下具有递增的曲率半径的股骨组件的前后平移图;
图11是另一个模拟位于各种不同屈曲角度下具有递增的曲率半径的股骨组件的前后平移图;
图12是另一个模拟位于各种不同屈曲角度下具有递增的曲率半径的股骨组件的前后平移图;
图13是图1的股骨组件另一个实施方式的横截面视图;
图14是针对股骨组件尺寸分类的限定图13的股骨组件曲率的多项式的系数值一个实施方式的表格;
图15是针对股骨组件尺寸集合的曲率半径长度值和比值的一个实施方式的表格;以及
图16是图1的股骨组件另一个实施方式的另一骨节的横截面视图。
具体实施方式
本发明公开的概念允许多种变型和替换形式,而在附图中则以示例的形式示出了其特别实施例并将在此详细描述。然而应理解的是,这并不是将本发明公开的概念限定为公开的特殊形式,相反的,其目的在于覆盖所有的变型、类似物、替换物,使其落入由所附权利要求书限定的本发明的精神和范围内。
本发明通篇采用的表示解剖参照的术语,诸如:前、后、内侧、外侧、上、下等等,将参考此处描述的矫形植入物和患者的自然解剖结构两者。这些术语具有在解剖学和矫形领域内所有公知的含义。并认为在说明书和权利要求书中采用的这些解剖相关术语与其公知含义一致,除非标明其它含义。
现在参见图1,在一个实施例中,后固定膝关节矫形假体10包括股骨组件12、胫骨轴承14以及胫骨盘16。股骨组件12和胫骨盘16示例性地由诸如钴铬合金或钛的金属材料构成,但在其它实施例中也可由其它材料构成,诸如:陶瓷材料、聚合物材料、生物工程材料或其它类似物。胫骨轴承14示例性地由诸如超高分子量的聚乙烯(UHMWPE)的聚合物材料构成,但在其它实施例中也可由其它材料构成,诸如:陶瓷材料、金属材料、生物工程材料或其它类似物。
如下面将详细介绍的,股骨组件12设置为与胫骨轴承14铰接,该胫骨轴承设置为与胫骨盘16联接。画出的胫骨轴承14具体为可旋转或活动的胫骨轴承并被设置为在应用时相对胫骨盘16旋转。然而,在其它实施例中,胫骨轴承14可具体为固定的胫骨轴承,其被限制或禁止相对胫骨盘16旋转。
胫骨盘16设置为固定在经过外科处理的患者胫骨的近端(未示出)。胫骨盘16可通过采用骨胶或其它附着工具固定在患者的胫骨上。胫骨盘16包括具有顶面20和底面22的平台18。示意性的,顶面20通常是平的,在一些实施例中,可经过高度抛光。胫骨盘16还包括从平台18的底面22向下延伸的柄杆24。洞或孔26限定在平台18的顶面20中并向下延伸到柄杆24。如下文详细介绍的,孔26被形成用于接收胫骨插入物14的互补柄杆。
如上所述,胫骨轴承14设置为与胫骨盘16联接。胫骨轴承14包括具有上轴承表面32和底面34的平台30。在画出的实施例中,胫骨轴承14体现为旋转或移动的胫骨轴承,轴承14包括从平台30的底面32向下延伸的柄杆36。当胫骨轴承14联接至胫骨盘16时,柄杆36被胫骨盘16的孔26接收。在使用中,胫骨轴承14设置为绕由柄杆36限定的轴线相对胫骨盘16旋转。在胫骨轴承14配置为固定的胫骨轴承的实施方式中,轴承14可包括或不包括柄杆36和/或可包括其它设备或特征从而将胫骨轴承14以非旋转方式固定到胫骨盘18上。
胫骨轴承14的上轴承表面32包括内侧轴承表面42和外侧轴承表面44,以及从平台16向上延伸的隆凸60。内侧和外侧轴承表面42、44设置为接收或以其它形式接触股骨组件14的相应的内侧和外侧骨节52,54,将在下文对此进行详细的介绍。这样,每一个轴承表面42、44可具有内凹的轮廓。隆凸60位于轴承表面42,44之间并包括前侧62和后侧64,所述后侧具有凸轮表面66。在画出的实施方式中,凸轮表面66具有基本内凹的曲率。然而,包括具有其他几何形状的凸轮表面66的隆凸60可以在其他实施方式中用到。例如,胫骨轴承,它包括具有基本为“S”形横截轮廓的隆凸,可以在其他实施方式中用到,比如在序列号为12/165,582,题目为《后部固定矫形假体》(″Posterior StabilizedOrthopaedic Prosthesis″),由Joseph G. Wyss等申请的美国专利申请中介绍的胫骨轴承,其中全文通过引用结合于此。
股骨组件12设置为与患者股骨末端经外科预处理的表面(未示出)联接。股骨组件12可通过应用骨胶或其它附着工具固定在患者股骨上。股骨组件12包括外侧的铰接表面50,铰接表面50具有一对内侧和外侧骨节52、54。在使用时,骨节52、54替代患者股骨的天然骨节并且设置为与胫骨轴承14的平台30的相应轴承表面42、44活动连接。
骨节52、54间隔分开,从而在它们之间限定出骨节内凹槽或凹进56。后凸轮80和前凸轮82(看图2)布置在内凹槽56中。后凸轮80朝向股骨组件12的后侧定位并包括凸轮表面86,该凸轮表面被构造成在屈曲过程中与胫骨轴承12的隆凸60的凸轮表面66接合或其他方式的接触,这在图2-4中画出并在接下来会详细介绍。
应理解的是,画出的膝关节矫形假体10设置为替换患者的右膝关节,照此,认为轴承表面42和骨节52是位于内侧,而认为轴承表面44和骨节54是位于外侧。然而,在其他实施例中,膝关节矫形假体10可被设置为替换患者的左膝关节。在这样的实施例中,应理解为,轴承表面42和骨节52是位于外侧,而轴承表面44和骨节54是位于内侧。不管怎样,此处描述的特征和概念应结合设置为替换患者的两个膝盖关节中的哪一个的膝关节矫形假体。
现在参见附图2-4,股骨组件12被构造成在使用中与胫骨轴承14铰接。股骨组件12的每个骨节52,54包括骨节表面100,所述骨节表面在矢状面中外凸弯曲并与各自的轴承表面42,44接触。另外地,在预定的屈曲范围之内,股骨组件12的后凸轮80与胫骨轴承14的隆凸60接触。例如,图2中所示的一个实施例中,当膝关节矫形假体10处于伸展状态或不处于屈曲状态(如屈曲约0度角)时,骨节52的骨节表面100与轴承表面42(或对骨节54来说的轴承表面44)在骨节表面100上的一个或多个接触点100接触。另外地,在这个特定的屈曲角度处,后凸轮80不与隆凸60接触。然而,在之后的(也就是更大的)屈曲角度处,后凸轮80被构造成与隆凸60接触,从而对矫形假体的运动进行一定量的控制。
随着膝关节矫形假体10在中间屈曲角度中发生铰接,股骨组件12与胫骨轴承14在骨节表面100上的一个或多个接触点接触。例如,在图3中所示的一个实施方式中,当膝关节矫形假体10通过中间屈曲角度(如在约45度处)发生铰接时,骨节表面100与轴承表面42在骨节表面100上的一个或多个接触点104接触。如下面针对特定实施方式所详细讨论到的,后凸轮80在特定的屈曲角度处与隆凸60可能发生接触也可能不发生接触。无论如何,随着膝关节矫形假体10在稍后的屈曲角度(如,在约70度屈曲角度处)发生铰接,如图4中所示,骨节表面100与轴承表面42在骨节表面100上的一个或多个接触点106接触。另外地,后凸轮80现在与隆凸60相接触。当然,这应当理解为,股骨组件12与胫骨轴承14可以以任意一个特定屈曲角度在骨节表面100上的多个接触点接触。然而,为了说明清楚,在图2-4中,仅分别画出了接触点102,104,106。
后凸轮80开始接触隆凸60的特定屈曲角度是由股骨组件12的骨节表面100的特定几何形状决定的。例如,在图2-4画出的实施例中,膝关节矫形假体10被构造成使得后凸轮80开始与隆凸60接触的屈曲角度约为70度。然而,在其他实施方式中,后凸轮80开始接触隆凸60的屈曲角度可以是其他角度,如下详述。
膝关节矫形假体10被构造成使得股骨组件12相对于胫骨轴承14的不合理前向平移量减小或拖延到之后的(也就是较大的)屈曲角度。特别地,如下详述,骨节52,54之一或两者的骨节表面100都具有特定的几何形状或曲率,能够减小和/或拖延前向平移,并且在一些实施方式中还能够促进股骨组件12发生“回滚”(roll-back)或后向平移。应当理解,通过将股骨组件12的不合理前向平移的开始拖延至较大的屈曲角度,在患者进行那些不涉及深度屈曲的活动时不合理前向平移的整体发生情况就会减少。
在典型的膝关节矫形假体中,不合理的前向平移可能在膝关节假体定位于大于0度的屈曲角度的任意时刻发生。前向平移的可能性随着膝关节矫形假体铰接的屈曲角度变大而增加,特别是在中期屈曲角度下。在这种定位下,股骨组件在胫骨轴承上不合理的前向平移会出现在以下任意时刻,该时刻即在股骨组件和胫骨轴承之间的切线(牵引)力未能满足下列等式的任意时刻,等式为:
T<μN (1)
其中,“T”为切线(牵引)力,“μ”为股骨组件和胫骨轴承的摩擦系数,“N”为股骨组件和胫骨轴承之间的法向力。作为普遍原则,股骨组件和胫骨轴承之间的切线(牵引)力定义为:
T=M/R (2)
其中,“T”为股骨组件和胫骨轴承之间的切线(牵引)力,“M”为膝关节力矩,“R”为在特定屈曲角度下与胫骨轴承接触的骨节表面的矢状面内的曲率半径。应理解的是,等式(2)是支配实际情况等式的简化,其不考虑诸如惯性和加速度的其他因素。不管怎样,等式(2)提供了下列见解,即通过控制股骨组件的骨节表面的曲率半径,可减少或者延迟膝关节矫形假体的不合理的前向平移。也就是说,通过控制骨节表面的曲率半径(如,增加或保持曲率半径),等式(2)的右手边可被减少,从而降低切线(牵引)力的值并满足等式(1)。如上论述的,通过确保切线(牵引)力满足等式(1),司减少股骨组件在胫骨轴承上的不合理前向平移或以其他方式将股骨组件在胫骨轴承上的不合理前向平移延迟至较大的屈曲角度。
基于上述分析,为了减少或拖延不合理前向平移的发生,要对股骨组件12的骨节52,54之一或两者的骨节表面100的几何形状进行控制。例如,在一些实施方式中,通过控制骨节表面100的曲率半径,使得曲率半径在一定的屈曲角度范围内保持恒定不变和/或在早期到中期屈曲的范围内增加。与之对照地,典型的股骨组件具有从远端曲率半径(也就是处于屈曲角度约为0度处)开始递减的曲率半径。然而,已经确定的是,通过在早期到中期屈曲角度的预定范围内保持曲率半径的相对恒定(也就是曲率半径不减小)和/或在屈曲角度的预定范围内增加曲率半径,会减小或拖延股骨组件12发生不合理的前向平移。
另外地,在一些实施方式中,骨节表面100构造或设计成使得骨节表面100离散的曲率半径之间的转变是渐变的。那就是说,通过渐变地在离散曲率半径之间变换,而不是突变,可减小或拖延股骨组件12发生的不合理前向平移。进一步说,在一些实施方式中,骨节表面在早期到中期屈曲范围(例如,从约0度到约90度)内曲率半径的变化率受到控制,从而使得变化率小于预定阈值。那就是说,已经确定的是如果骨节表面100曲率半径的变化率大于预定阈值,就可能发生不合理的前向平移。
相应地,在图5-8中画出的一些实施例中,股骨组件12的骨节表面100在早期到中期屈曲角度中具有增加的曲率半径。通过增加曲率半径,就将不合理的前向平移减小或拖延到了之后的屈曲角度,如下详述。特别地,不合理的前向平移可被拖延到一屈曲角度或超过该屈曲角度,该屈曲角度为股骨组件12的后凸轮80开始与胫骨轴承14的隆凸60接触的屈曲角度。一旦后凸轮80接触到隆凸60,不合理的前向平移就受到后凸轮80与隆凸60接合情况的控制。那就是说,后凸轮80可被隆凸60限制不能向前移动。
曲率半径R2和曲率半径R3之间的增加量,以及所述增加发生的位于骨节表面100上的屈曲角度,都已经被确定为能够影响到不合理前向平移的发生。在序列号为12/165,579,题目为《具有可控骨节曲率的股骨矫形组件》(″Orthopaedic Femoral Component Having Controlled Condylar Curvature″),与本发明同时申请并通过引用结合于此的美国专利申请中更详细地介绍过,采用LifeMOD/Knee Sim,1007.1.0Beta16版本的软件程序实现对各种股骨组件设计的多种仿真,该软件程序可从加利福利亚的San Clemente公司,LifeModeler供应的市场上买到,用来分析股骨组件在早期和中期屈曲时增加股骨组件的骨节表面的曲率半径的效果。基于这一分析,其能确定通过下列方式增加骨节表面的曲率半径,可以减少或者以其他方式延迟股骨组件相对胫骨轴承的不合理的向前平移,下列方式为更多地处于约30度屈曲到约90度屈曲的范围中的屈曲角度下以增长约0.5毫米到约5毫米范围内的量增加骨节表面的曲率半径。
例如,图9中画出的曲线图200代表使用股骨组件的深度屈曲的膝关节模拟的结果,其中,骨节表面的曲率半径在屈曲30度、屈曲50度、屈曲70度以及屈曲90度下增加0.5毫米(如,从25.0毫米到25.5毫米)。类似地,图10所示的曲线图300代表使用股骨组件的深度屈曲的膝关节模拟的结果,其中,骨节表面的曲率半径在屈曲30度、屈曲50度、屈曲70度以及屈曲90度下增长1.0毫米(如,从25.0毫米到26.0毫米)。图11所示的曲线图400代表使用股骨组件的深度屈曲的膝关节模拟的结果,其中,骨节表面的曲率半径在屈曲30度、屈曲50度、屈曲70度以及屈曲90度下增加2.0毫米(如,从25.0毫米到27.0毫米)。再者,图12所示的曲线图500代表使用股骨组件的深度屈曲的膝关节模拟的结果,其中,骨节表面的曲率半径在屈曲30度、屈曲50度、屈曲70度以及屈曲90度下增加5.0毫米(如,从25.0毫米到26.0毫米)。
在曲线图200、300、400、500中,股骨组件的内侧骨节(“med”)和外侧骨节(“lat”)的关节最低或者最远的点(CLP)是以图形的方式表示股骨组件对于胫骨轴承的相关定位。照此,下滑的线表示股骨组件在胫骨轴承上的滚回,而上升的线表示股骨组件在胫骨轴承上的向前平移。
如曲线图200、300、400、500所示,在每个实施例中股骨组件的向前滑动被延迟至约100度屈曲,而向前平移的总量被限定小于约1毫米。特定的,通过在早期屈曲角度下较大地增加骨节表面的曲率半径,可促进股骨组件在胫骨轴承上的回滚。当然,引导曲率半径和屈曲角度以这种增长的增加总量受到其他因素的限制,诸如患者膝关节的天然关节间隙、胫骨轴承的尺寸以及类似物。不管怎样,根据曲线图200、300、400、500中记录的模拟,在早期到中期屈曲过程中,通过增加股骨组件的骨节表面的曲率半径,能减少或以其他方式延迟股骨组件在胫骨轴承上的不合理的向前平移。
因此,回头参见图5-8,矢状面中的骨节表面100部分地由许多弯曲表面部102,104,106,108形成,其中所述每个表面部的矢状端部与骨节表面100的相邻弯曲表面部的矢状端部正切。每个弯曲表面部102,104,106,108由曲率半径限定。具体地,弯曲表面部102由曲率半径R2限定,弯曲表面部104由曲率半径R3限定,弯曲表面部106由曲率半径R4限定。
股骨组件12的骨节表面100构造成使得弯曲表面部104的曲率半径R3大于弯曲表面部102的曲率半径R2。在一个实施例中,曲率半径R3比曲率半径R2大0.5毫米或更多。在另一个实施例中,曲率半径R3比曲率半径R2大2毫米或更多。在特定的实施例中,曲率半径R3比曲率半径R2大至少5毫米或更多。然而,应当理解的是,在一些实施方式中,R2和R3之间曲率半径的特定增加量是由股骨组件12的特定尺寸大小决定,或与之成比例的。
弯曲表面部102,104,106,108中的每一个在贯穿屈曲角度的不同范围中接触胫骨轴承14的轴承表面42(或44)。例如,弯曲表面部102从较早的屈曲角度θ1延伸到之后的屈曲角度θ2。弯曲表面部104从屈曲角度θ2延伸到之后的屈曲角度θ3。弯曲表面部106从屈曲角度θ3延伸到之后的屈曲角度θ4。
例如,在一个实施例中,如图5中所示,弯曲表面部102从约0度屈曲的屈曲角度θ1延伸到约50度屈曲的屈曲角度θ2。弯曲表面部104从约50度屈曲的屈曲角度θ2延伸到约70度屈曲的屈曲角度θ3。弯曲表面部106从约70度屈曲的屈曲角度θ3延伸到约120度屈曲的屈曲角度θ4。在图5画出的实施例中,股骨组件12的后凸轮80构造成与胫骨轴承14的隆凸60在约70度屈曲的屈曲角度θC处接合或接触。然而,在其他实施方式中,后凸轮80可构造成与隆凸60在早于或晚于70度的屈曲角度处接合。为了确保后凸轮80在曲率半径从R3减小到R4之前或之后马上与隆凸60接合或接触,对矫形假体运动的控制可从骨节表面100的几何形状转变成后凸轮80与隆凸60的相互作用,这可进一步减少股骨组件12的前向平移量。例如,在一个特定的实施例中,后凸轮80可构造成与隆凸60在屈曲角度θC处接合或接触,所述屈曲角度θC比屈曲角度θ3大不超过10度,在该角度骨节表面100的曲率半径从曲率半径R3减小到曲率半径R4。
在另一个实施例中,如图6中所示,弯曲表面部102从约0度屈曲的屈曲角度θ1延伸到约10度屈曲的屈曲角度θ2。弯曲表面部104从约10度屈曲的屈曲角度θ2延伸到约30度屈曲的屈曲角度θ3。弯曲表面部106从约30度屈曲的屈曲角度θ3延伸到约120度屈曲的屈曲角度θ4。在图6画出的实施例中,股骨组件12的后凸轮80构造成与胫骨轴承14的隆凸60在约30度屈曲的屈曲角度θC处接合或接触。又然而,在其他实施方式中,后凸轮80可构造成与隆凸60在早于30度(也就是早于将曲率半径R3减小到R4)或晚于30度不久(例如,0-10度以内)的屈曲角度处接合。
在另一个实施例中,如图7中所示,弯曲表面部102从约0度屈曲的屈曲角度θ1延伸到约30度屈曲的屈曲角度θ2。弯曲表面部104从约30度屈曲的屈曲角度θ2延伸到约50度屈曲的屈曲角度θ3。弯曲表面部106从约50度屈曲的屈曲角度θ3延伸到约120度屈曲的屈曲角度θ4。在图7画出的实施例中,股骨组件12的后凸轮80构造成与胫骨轴承14的隆凸60在约50度屈曲的屈曲角度θC处接合或接触。又然而,在其他实施方式中,后凸轮80可构造成与隆凸60在早于50度(也就是早于将曲率半径R3减小到R4)或晚于50度(例如,0-10度以内)不久的屈曲角度处接合。
在另一个实施中,如图8中所示,弯曲表面部102从约0度屈曲的屈曲角度θ1延伸到约70度屈曲的屈曲角度θ2。弯曲表面部104从约70度屈曲的屈曲角度θ2延伸到约90度屈曲的屈曲角度θ3。弯曲表面部106从约90度屈曲的屈曲角度θ3延伸到约120度屈曲的屈曲角度θ4。在图8画出的实施例中,股骨组件12的后凸轮80构造成与胫骨轴承14的隆凸60在约90度屈曲的屈曲角度θC处接合或接触。又然而,在其他实施方式中,后凸轮80可构造成与隆凸60在早于90度(也就是早于将曲率半径R3减小到R4)或晚于90度(例如,0-10度以内)不久的屈曲角度处接合。
应当理解的是,图5-8的实施例是示意性的实施例,而在其他实施方式中,弯曲表面部102,104,106中的每一个可以不同于图5-8中所示的屈曲角度延伸。例如,在图5-8的每一个实施例中,尽管弯曲表面部102是从屈曲约0度开始画的,在其他实施方式中,弯曲表面部102可以位于屈曲0度之前的屈曲角度(也就是伸展过度)。
另外地,应当理解的是,后凸轮80与隆凸60接触的屈曲角度θC可小于,基本等于,或略大于屈曲角度θ3,曲率半径R3在屈曲角度θ3处减小到曲率半径R4。在一些实施方式中,屈曲角度θC在屈曲角度θ3的预定阈值内。例如,在一个具体的实施例中,屈曲角度θC处于约10度的屈曲角度θ3内。例如,曲率半径R3可在约为70度的屈曲角度θ3处减小到曲率半径R4,后凸轮80可构造成在屈曲角度θC处于屈曲约60度到约80度的范围内开始接触隆凸60。
现在参见图13-15,在一些实施方式中,骨节表面100包括在早期到中期曲率范围中的离散曲率半径之间的渐变过渡,使得骨节表面在屈曲角度范围内的曲率半径改变量变小。例如,如图13中所示,一些实施方式中的弯曲表面部102设计成具有从第一曲率半径R1到第二曲率半径R2的渐变过渡。为了做到这种效果,弯曲表面部102是由多条射线120而非恒定不变的曲率半径限定而成,如图5-8中所画出和如上所述。多条射线120的每一条都从公共起点O起始。另外,多条射线120的每一条都在弯曲表面部120限定出各自的接触点130。尽管为了附图清晰,仅在图13中示出了三条射线120,但应理解的是,可采用无穷多条射线120来限定弯曲表面部102。
集合限定出弯曲表面部102的每个接触点130的位置可由在每个屈曲角度下的每条射线120的长度来决定。特别地和意外地,已经确定出股骨组件12在胫骨轴承14上的不合理前向平移可通过依照下面的多项式限定弯曲表面部102而减小或拖延:
rθ=(a+(b*θ)+(c*θ2)+(d*θ3)), (3)
其中,“rθ”为在屈曲“θ”度下界定弯曲表面部104上接触点130的射线120(十进制单位)的长度,“a”是20至50间的标量值,“b”是系数值,其被选择成使得:
-0.30<b<0.00, (4)
0.00<b<0.30,或者
b=0
如果选择的系数“b”在-0.30<b<0.00范围内,则系数“c”和“d”如比选择,即:
0.00<c<0.012,以及 (5)
-0.00015<d<0.00。
可选择地,如果选择的系数“b”在0.00<b<0.30范围内,则系数“c”和“d”如此选择,即:
-0.010<c<0.0,以及 (6)
-0.00015<d<0.00。
再者,如果选择的系数“b”等于0,则系数“c”和“d”如此选择,即:
-0.0020<c<0.00,或者 (7)
0.00<c<0.0025,以及
-0.00015<d<0.00。
应理解的是,标量“a”和系数“b”、“c”和“d”的值的范围是针对多项式(3)的无穷多个可能解的子集。即,可从无穷多个可能解中确定上面提供的特定集合范围从而得出曲线集合(如,弯曲表面部102),其具有从曲率半径R1到曲率半径R2的骨节表面100的渐变过渡,这样可减少或延迟股骨组件12相对胫骨轴承14的向前平移。此外,应理解的是,参考以上实施例指定的数值,是利用十进制单位提供每个系数“a”、“b”、“c”和“d”的数值范围。然而,可采用诸如英制单位系统的其他单位系统将系数值的上述范围转换为在实施例中所使用的系数值范围。
还可通过多条射线120的共同起点O的设置来改变弯曲表面部102的整个形状。通过限制多条射线120的共同起点O和曲率半径R1的起点122之间的距离124,可以减少或者拖延股骨组件12在胫骨轴承14上发生的不合理前向滑动。另外,可通过确保多条射线120的公共起点O与远端曲率半径R1的起点122之间的距离在预定距离124之内,改进膝关节矫形假体10的稳定性。这样,在一个实施例中,多条射线120的共同起点O的位置选择成使得共同起点O和曲率半径R1的起点120之间的距离124小于大约10毫米,从而减小或拖延股骨组件前向平移的发生和/或为膝关节矫形假体10提供改进的稳定性。
应理解的是,共同起点O和曲率半径R1的起点122之间的距离124以及特定的系数值依赖于一些实施例中股骨组件12的特定尺寸。例如,如图14所示,表格700示出了对于上面定义的多项式(3)的一个特定实施例的系数值以及对于共同起点O和曲率半径R1的起点122之间的距离124的一个特定实施例的数值。如表格700所示,共同起点O和曲率半径R1的起点122之间的距离124和标量“a”的数值相对股骨组件尺寸而变化。然而,在这个特定的实施例中,相对股骨组件尺寸,系数“b”、“c”和“d”的数值是恒定的。然而,应理解的是,在其他的实施例中,系数值“b”、“c”和“d”可相对股骨组件的尺寸而变化。
如上所述,在一些实施方式中,骨节表面100进一步设计或构造成使得骨节表面100在早期和中期的屈曲范围内曲率半径的变化不太大或不太剧烈(如曲率半径变化程度与屈曲角度变化量之比过大)。也就是说,如果曲率半径R1与曲率半径R2,R3,或R4的比率过大,股骨组件12就可能发生不合理的前向平移。这样,通过将股骨组件12的骨节表面100设计成使得远端曲率半径R1与(i)弯曲表面部102的曲率半径R2的比率,与(ii)弯曲表面部104的曲率半径R3的比率,以及与(iii)之后屈曲的弯曲表面部106的曲率半径R4的比率,都小于预定的阈值,就能意外地减小或拖延不合理前向平移的发生。
相对应地,在一个特定的实施方式中,股骨组件12的骨节表面100设计成使得曲率半径R1与曲率半径R2的比率处于约1.10到约1.30之间,曲率半径R1与曲率半径R3的比率处于约1.001到约1.100之间,而曲率半径R1与曲率半径R4的比值处于约1.25到约2.50之间。进一步说,在一些实施方式中,曲率半径R2与曲率半径R3的比值处于约0.74到约0.85之间。
应理解到,股骨组件12的骨节表面100的曲率半径R2到R3的具体增长量和/或确定所述增长在骨节表面100上的定位还可由股骨组件12的尺寸大小决定,与之成比例,或受其影响。也就是说,应理解到,与尺寸较大的股骨组件相比,骨节表面100的曲率半径R2到R3这0.5毫米的增长量在小尺寸的股骨组件中是相对较大的增长量。这样,股骨组件12的骨节表面100的曲率半径R2到R3增长的幅度可根据股骨组件的大小而改变。然而,在一个实施例中,贯穿股骨组件尺寸的集合,曲率半径R1与曲率半径R2、R3和R4的比率保持在基本恒定的数值。
例如,如图15中所示,表格800定义了对于股骨组件尺寸集合1到10的每个曲率半径R1、R2、R3、R4的长度。如表格800中所示,对于股骨组件12的每个尺寸1-10的每个曲率半径R1、R2、R3、R4的长度可选择成使得R1/R2及R1/R3的比率相对于贯穿股骨组件的尺寸基本恒定。在画出的实施方式中,如前所述,针对股骨组件大小从1到10,曲率半径R1与曲率半径R2的比率维持在大约1.25到大约1.27的数值,而针对股骨组件大小从1到10,曲率半径R1与曲率半径R3的比率保持在大约1.005的数值。
股骨组件12的骨节表面100的整体形状和设计已经在上面相对于股骨组件12的单骨节52,54介绍过了。应当理解在一些实施方式中股骨组件12的两个骨节52,54可以是对称的并具有相似的骨节表面100。然而,在其他的实施方式中,股骨组件12的骨节52,54可以是不对称的。例如,如图16中所示,股骨组件12可包括具有骨节表面300的第二骨节52,54,所述骨节表面部分地由多个弯曲表面部302,304,306所限定。弯曲表面部302从较早的屈曲角度θ5延伸到之后的屈曲角度θ6。弯曲表面部304从屈曲角度θ6延伸到之后的屈曲角度θ7。弯曲表面部306从屈曲角度θ7延伸到之后的屈曲角度θ8。骨节表面300还包括远端半径R5,该远端半径R5经由弯曲表面部302渐变过渡到曲率半径R6。另外地,弯曲表面部304由曲率半径R7限定,而弯曲表面部306由曲率半径R8限定。
这样,在骨节52,54对称的实施方式中,屈曲角度θ5基本等于屈曲角度θ1,屈曲角度θ6基本等于屈曲角度θ2,屈曲角度θ7基本等于屈曲角度θ3,以及屈曲角度θ8基本等于屈曲角度θ4。另外地,曲率半径R5基本等于曲率半径R1,曲率半径R6基本等于曲率半径R2,曲率半径R7基本等于曲率半径R3,曲率半径R8基本等于曲率半径R4。进一步说,对于两个骨节,上述的等式(4)的系数值“a”、“b”、“c”和/或“d”的集合是基本相同的。
然而,在其他实施例中,骨节52、54是不对称的。这样,屈曲角度θ5可能会不同于屈曲角度θ1。另外,屈曲角度θ6可能会不同于屈曲角度θ2。这就是说,曲率半径在R2和R3之间的增加可能发生于骨节52,54之间的不同屈曲角度。进一步说,屈曲角度θ8可能会不同于屈曲角度θ4。然而,应当理解到,屈曲角度θ7可能会基本等于屈曲角度θ3,从而使后凸轮80恰当地定位于骨节内凹槽56内。
另外,在骨节52、54不对称的那些实施例中,曲率半径R5可以不同于曲率半径R1,曲率半径R6不同于曲率半径R2,曲率半径R7不同于曲率半径R3,和/或曲率半径R8不同于曲率半径R4。进一步说,上述的等式(3)的系数值“a”、“b”、“c”和/或“d”的集合在骨节表面100和300之间是不同的。
虽然在附图和前面的描述中对本发明做了详细的图示和描述,但这些图示和描述应理解作为范例而不对特征有限定作用,应当理解到所画出和介绍的仅是示意性实施方式,并且所有本发明公开内容的精神以内的改变和变型都应得到保护。
本发明的多个优点来自于在此描述的设备和组件的各种特征。需要说明的是本发明的设备和组件的替换实施例可不包括所描述的全部特征,虽然仍然得益于至少这些特征的部分优势。本领域技术人员可结合本发明的一个或多个特征实现他们自己的设备或组件的发明,这些发明都落入附加权利要求书所限定的本发明的精神和范围内。
Claims (10)
1.一种后固定膝关节矫形假体,包括:
股骨组件,包括(i)一对间隔分开的骨节,在这对骨节之间限定了骨节内凹槽,该对间隔分开的骨节中的至少一个具有在矢状面中弯曲的骨节表面以及(ii)定位在骨节内凹槽中的后凸轮;以及
胫骨轴承,包括(i)平台,所述平台具有轴承表面,所述轴承表面构造成与股骨组件的骨节表面铰接以及(ii)从平台向上延伸的隆凸;
其中,股骨组件的骨节表面(i)与轴承表面以第一屈曲角度在骨节表面上的第一接触点接触,第一屈曲角度小于30度,(ii)与轴承表面以第二屈曲角度在骨节表面上的第二接触点接触,第二屈曲角度处于35度到90度的范围内,(iii)与轴承表面以第三屈曲角度在骨节表面上的第三接触点接触,所述第三屈曲角度大于第二屈曲角度,以及(iv)当股骨组件从第一屈曲角度移动到第二屈曲角度时,与轴承表面在第一接触点和第二接触点之间的多个接触点上接触,
股骨组件的后凸轮与胫骨轴由承的隆凸以第四屈曲角度接触,第四屈曲角度比第三屈曲角度大不超过10度,
所述多个接触点中的每个接触点由从共同起点延伸至该多个接触点的对应点的射线限定,每条射线具有由下列多项式定义的长度:
rθ=(a+(b*θ)+(c*θ2)+(d*θ3)),
其中,rθ为在θ度屈曲时限定接触点的射线的长度,a为处于20-50间的系数值,以及b为处于从由-0.30<b<0.00,0.00<b<0.30和b=0组成的组中选择的范围内的系数值,
其中,如果b处于-0.30<b<0.00区间,则(i)c为在0.00到0.012之间的系数值,而(ii)d为在-0.00015到0.00间的系数值,
其中,如果b处于0<b<0.30区间,则(i)c为在-0.010到0.00之间的系数值,而(ii)d为在-0.00015到0.00之间的系数值,
其中,如果b等于0,则(i)c为处于从由-0.0020<c<0.00和0.00<c<0.0025组成的组中选择的范围内的系数值,且(ii)d为在-0.00015到0.00之间的系数值。
2.如权利要求1所述的后固定膝关节矫形假体,其特征在于:
矢状面中的骨节表面在第一接触点具有第一曲率半径,所述第一曲率半径具有起点,以及
第一曲率半径的起点和射线的公共起点之间的距离处于0到10毫米的范围内。
3.如权利要求1所述的后固定膝关节矫形假体,其特征在于:第一屈曲角度处于0度到10度的范围内,第二屈曲角度处于45度到55度的范围内,而第三屈曲角度处于65度到75度的范围内。
4.如权利要求1所述的后固定膝关节矫形假体,其特征在于:
(i)矢状面中的骨节表面在第一接触点具有第一曲率半径,在第二接触点具有第二曲率半径,且在第三接触点具有第三曲率半径,以及
(ii)第三曲率半径比第二曲率半径大至少0.5毫米。
5.如权利要求4所述的后固定膝关节矫形假体,其特征在于:第三曲率半径比第一曲率半径大至少2毫米。
6.如权利要求4所述的后固定膝关节矫形假体,其特征在于:第一曲率半径与第三曲率半径的比率小于第一曲率半径与第二曲率半径的比率。
7.如权利要求4所述的后固定膝关节矫形假体,其特征在于:第一曲率半径与第二曲率半径的比率在1.10到1.30之间。
8.如权利要求4所述的后固定膝关节矫形假体,其特征在于:第一曲率半径与第三曲率半径的比率在1.001到1.100之间。
9.如权利要求4所述的后固定膝关节矫形假体,其特征在于:矢状面中的股骨组件的骨节表面包括限定在第二接触点和第三接触点之间的弯曲表面部,所述弯曲表面部具有基本恒定不变的曲率半径,所述弯曲表面部的曲率半径基本上与第三曲率半径相等。
10.一种后固定膝关节矫形假体,包括:
股骨组件,包括(i)一对间隔分开的骨节,在这对骨节之间限定了骨节内凹槽,该对间隔分开的骨节中的至少一个具有在矢状面中弯曲的骨节表面以及(ii)定位在骨节内凹槽中的后凸轮;以及
胫骨轴承,包括(i)平台,所述平台具有轴承表面,所述轴承表面构造成与股骨组件的骨节表面铰接以及(ii)从平台向上延伸的隆凸;
其中,股骨组件的骨节表面(i)与轴承表面以第一屈曲角度在骨节表面上的第一接触点接触,第一屈曲角度小于30度,(ii)与轴承表面以第二屈曲角度在骨节表面上的第二接触点接触,第二屈曲角度处于35度到90度的范围内,(iii)与轴承表面以第三屈曲角度在骨节表面上的第三接触点接触,所述第三屈曲角度大于第二屈曲角度,以及(iv)当股骨组件从第一屈曲角度移动到第二屈曲角度时,与轴承表面在第一接触点和第二接触点之间的多个接触点上接触,
股骨组件的后凸轮与胫骨轴承的隆凸以第四屈曲角度接触,第四屈曲角度不大于第三屈曲角度,
所述多个接触点中的每个接触点由从共同起点延伸至该多个接触点的对应点的射线限定,每条射线具有由下列多项式定义的长度:
rθ=(a+(b*θ)+(c*θ2)+(d*θ3)),
其中,rθ为在θ度屈曲时限定接触点的射线的长度,a为处于20-50间的系数值,以及b为处于从由-0.30<b<0.00,0.00<b<0.30和b=0组成的组中选择的范围内的系数值,
其中,如果b处于-0.30<b<0.00区间,则(i)c为在0.00到0.012之间的系数值,而(ii)d为在-0.00015到0.00间的系数值,
其中,如果b处于0<b<0.30区间,则(i)c为在-0.010到0.00之间的系数值,而(ii)d为在-0.00015到0.00之间的系数值,
其中,如果b等于0,则(i)c为处于从由-0.0020<c<0.00和0.00<c<0.0025组成的组中选择的范围内的系数值,且(ii)d为在-0.00015到0.00之间的系数值。
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CN101683290A (zh) | 2010-03-31 |
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JP2010012255A (ja) | 2010-01-21 |
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AU2009202626B8 (en) | 2015-07-30 |
US20090326665A1 (en) | 2009-12-31 |
AU2009202626A1 (en) | 2010-01-14 |
US20190247194A1 (en) | 2019-08-15 |
AU2009202626A8 (en) | 2015-07-30 |
US20120296437A1 (en) | 2012-11-22 |
US20150005888A1 (en) | 2015-01-01 |
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