CN1090485A - 椎间盘假体 - Google Patents
椎间盘假体 Download PDFInfo
- Publication number
- CN1090485A CN1090485A CN93118231A CN93118231A CN1090485A CN 1090485 A CN1090485 A CN 1090485A CN 93118231 A CN93118231 A CN 93118231A CN 93118231 A CN93118231 A CN 93118231A CN 1090485 A CN1090485 A CN 1090485A
- Authority
- CN
- China
- Prior art keywords
- plate
- granule
- prosthese
- vertebra
- ring
- 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.)
- Pending
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/02—Inorganic materials
- A61L27/10—Ceramics or glasses
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Abstract
本假体包括两块固定到相应脊椎(L4,L5)上的板
(1,2),和用于把板用关节互相连接的球连接器(3),
它的在前后平面(OX,OY)内的转动中心(C)是在板
的后面部分内向后偏置,在横向平面(OX,OY)内位
于各板的中间,在垂直平面(OX,OZ)内位于下脊椎
(L5)的板(1)的下面;该假体还包括用柔性材料制的,
装***的吸收冲击的环(10),环(10)具有一个用于球
连接器(3)的通道的开口(10a),并适合于在板和球连
接器周围之间被定界了的空间。曲率中心(C)的这
种定位防止在脊椎体运动时对关节骨突的应力,而柔
性环(10)使假体适合于腰脊椎的生理上脊柱前凸,并
吸收在运动时产生的大量的应力。
Description
本发明涉及椎间盘假体。
众所周知,椎间盘具有通过它的表面附着在脊椎体关节表面的双凸透镜的形状,它包括一个由同心纤维层组成的硬的边缘部份(环),和胶状的,软的中心部份(核髓样的),该部份是由通过用分沁粘液的组织充填空间所分离的细的纤维束组成。椎间盘是一个可变形的元件,它允许所有可能的相对运动(六个自由度),但又限制了这些运动的范围,特别是相对于椎间韧带和骨缓冲器的扭转运动。椎间盘是一种粘弹性的能吸收冲击的组织,当脊柱受载时,它为使脊柱保持直立提供强度和稳定性。
椎间盘可以由于各种原因受损,特别是随着年龄的增长和老化,它们可能导致使椎间盘滑脱。
椎间盘老化起初是椎间盘功能上的,而后是盘组织上的损坏,它们似乎是由于机械的应力对正变为紊乱结构的椎间盘的影响所引起的。椎间盘老化改变了它的机械性能,并造成体壁间隔(intersomatic)高度的减小,这将导致椎间盘/关节功能组合的失调。其结果是一种不稳定性,这种不稳定性可具有讨厌的临床后果,特别是腰痛。因此,体节的不稳定性导致异常的关节功能,引起关节炎,也是疼痛和骨赘突(osteophytic proceeses)的根源。
因此,有人提议用人造椎间盘替代受损的椎间盘,且已经设想了许多方案。由此,一些假体含不限制任何自由度的关节,而另一些,相比之下,完全不考虑某些运动,且至多只有一个自由度。第一种假体的设计者认为人造椎间盘应该在任何情况下都不规定一种运动,即功能单元的稳定性是通过保持剩余的韧带来保证,且非受压关节保证持久的骨/假体间的连接。
第二种类型假体设计者认为一些自由度在生理上是不需要的,且恢复一个被认为是紧要的自由度,因此,一种众所周知的假体形成允许只围绕横轴转动的活动关节。
有关节的假体可以是各种各样的,特别是,它可以由具一定柔性的材料组成,要不然,使用机械装置,如弹簧。
然而,这些已知的假体都不能够完全满足要求,例如,因为在关节处的摩擦太大(如在专利FR-2659226中所描述的假体),或者是因为在转动过程中所观察到的假体的不稳定性。况且,在上述专利中所描述的假体只允许一种倾斜,且在所有的平面内限于10°范围内的伸展弯曲,这比之脊椎的自然灵活性,姿态太低了。
目前,相对来说另外还有一个困难,就是对于椎间盘关节成形术如何确定指标,特别是推荐用于腰痛和坐骨神经痛的治疗的指标,而这些病是由于不稳定性,椎间盘切除术后的(post-discecfomg)腰坐骨痛和Ⅰ度脊椎前移所引起的。
按照本发明的建议,使用椎间盘假体所构成植入物的目的实际上是三种情况:
a)通过下述方式,亦即能够恢复到体壁间隔的正常高度来选择尺寸。实际上椎间盘老化,椎间盘机械功能的改变和引起体壁间隔在高度上的减少都会造成椎间盘/关节功能组合的失调。这种在高度上的减少导致关节小面的机械过载,和可能的腰痛根源,它可能引起下面的脊椎的上关节向上和向前位移,造成连接孔变窄,从而可能引起坐骨神经痛。
b)在配合的两个关节间允许生理上的可动性。
不稳定性可能是椎间盘老化或是由外科手术引起的结果,正常的和非正常的可动性间的界限至今不能精确的定义,体节的不稳定性引起关节的非正常功能,引起如已经指出的关节炎。
c)具有内在的稳定性并允许体壁间运动。
关节成形术用于迄今已经表明是关节固定(anthrodeses)的病例,它可以是一种有用的对于这种手术的可供选择的方法,这种手术对毗邻的区域并不是没有影响,实际上,所有的腰椎关节固定术在邻接体节中引起在应力上增加和转动中心位移,它们可能造成超可动性。
邻近关节固定区域的长期监视展现从第五年开始的椎间盘的恒定挤压、特别是滑脱或角位移,它的频率随时间增加。也能观察到实质上的关节病、滑脱的椎间盘或从这新的活动关节所获得的脊椎骨脱离。
按照本发明提出的椎间盘假体是由两块板组成,所说的板带有用来把它们固定到相应的脊椎上的装置,和用于把上述那些板用关节相连的装置。
按照本发明,关节装置是一个球连接器,它在前后面的平面内的转动中心是在板的后面部分和脊椎体的后面部分内向后偏移,在横向平面内,它实际上位于板和脊椎体的中点,而在垂直平面内,是位于下脊椎的板的下面;而且这种假体包括一个由柔性材料制造的可***的吸收冲击的环,所说的环具有用于球连接器的通道的开口,并形成所需的尺寸以便适应在板和球连接器周围之间被定界了的空间,并基本上匹配板的形状。
如本发明所确定的那样,球连接器的曲率中心的定位具有避免对关节骨突(apophyses)加压的优点,象在自然脊椎内那样,这是迄今已知的假体中所没有达到的。
因此,按照本发明的假体同时具有所需的机械强度,并在关节平面上借助于球连接器***相应的尺寸来减少摩擦。实际上,转动中心既不离关节太远,但也不是非常接近,因此,使它能够重现接近于自然可动性的可动性。
本发明的其它特征和优点通过下面说明并参照附图所示作为非限定例子的一个实施例的说明将更加清楚。
图1是一对装有按照本发明的一个实施例的椎间盘组成部件的脊椎的分解透视图;
图2是在图1中的椎间盘的下板的平面图;
图3是按照本发明的假体沿图2的3/3线的纵向剖面图,且是在两块板处于平行位置上的纵向剖面图;
图4是图1至图3所示的假体,且是在两块板彼此倾斜的位置上的正视图;
图5是沿在本发明的第二个实施例的图6中的5-5剖面线的纵向剖面图;
图6是在图5中的假体的平面视图;
图7是在图5和图6所示的假体且它的板是平行时的纵向正视图;
图8是类似于图7的视图,且在板之间形成一个角度;
图9、10、11和12是接照本发明的假体的四个可供选择的实施例。
图1所示是两个相邻的脊椎,例如,腰脊椎L5和L4,它们可以通过椎间盘假体连接,这个假体包括两个分别固定在下脊椎L5和上脊椎L4的板1和2,和一个把两块板1和2彼此用关节相连的球连接器3,和插在两块板1和2之间并通过球连接器3的柔性吸收冲击环10。
板1和2是类似的,具有基本上等于脊椎L5、L4的尺寸(它能够用于位于非L5-L4水平上的这些脊椎,包括非腰部水平),并大致上匹配相邻关节表面的形状,因此,每一块板1、2具有曲线形的边4,边4基本上是椭圆形或卵形的,它还有一个直线边5,打算使该边邻近脊柱管并与椭圆形4的两个截头端相连接,此外,每一块板1、2在其中心部分钻有一个通孔6,在该孔中,分别***一个小颗粒7、8,它们的尺寸是按下述方式确定,即,它可以与相应的孔6相啮合。后者优选的是成锥形,因为它可以成为小颗粒7、8附加的座,在这种情况下,可以按可移动的方式连接到相应的板1、2上。
小颗粒7、8一起构成球连接器关节3。***下面的板1的第一小颗粒7具有凸形球面9,它突出的装在板1的相应表面上,而它相反的表面11是平滑的,且与板1相反的向外的面齐平。上板2的小颗粒8也从它的面向板1的面突出,且具有凹的球形表面12。后者的曲率半径等于球面9的半径(r),以便能在后者上滑动,由此,形成球连接器关节。小颗粒8的相对的面14是平的,且与板2向外的面齐平。
通过曲率半径≤r远离表面9和12的球连接器3的曲率中心或转动中心c是按下列方法定位:
-该中心c是在前后平面(ox、oy)上,且是在板1、2和脊椎体的后面部份内向后偏离;
-在横向平面(ox、oz)内,转动中心c实质上位于板1、2和脊椎体的中间;
-在垂直平面(oy、oz)内,中心c恰好位于覆盖住下脊椎的上表面的板1的下面,如在图1中所示例子的L5。
该中心c的这种定位相应于大约处于假体高度之间的曲率半径r,当板1、2是平行的,它是该高度的一半。
实际上,转动中心c可以位于板1的下表面S1的下面(图3)(在0毫米亦即在表面S1本身上)和大约5毫米之间的距离d1,这决定于具体情况。
然而,转动的中心C被定位在从邻近的脊柱管的板1的直边5的中点M开始,距直边5为从中点M开始的板1的宽度L的大约1/3到1/2之间的距离上;因此,在图3中,中心C实际上位于距离d2=L/3和距离d3=L/2之间。
举一个非限制的数字例,d2=4毫米,d3=10毫米,L=20毫米,在该情况下,C位于大约宽为6毫米的区域中。
假体还包括用适当柔性材料制的被***的吸收冲击环10,它具有一个作为球连接器3的通道的开口10a。柔性环10的尺寸是按这样的方法确定,即可以适合在板1、2和球连接器3周围之间被定界定了的中间间隔,实际上与板的外形相匹配。
在自由的、未受压的状态下(图1),柔性环10具有从它的前面到后面可变的厚度。它的前面部份具有最大的厚度H,该厚度H从这前面部份棱边的中点到环10的后面部份一直是均匀地减小,因此,它的厚度h显然小于H。所以,环10具有一个非对称的形状,它的相对面彼此相对倾斜,且彼此靠近朝后面部份倾斜。
每一块板1、2在它的有相应的小颗粒7、8从它的面上突出的面上有一个环状的中心加厚部份14,15。后者邻接它环绕着的、所伴随的小颗粒7、8,后者围绕小颗粒与板的其余部分形成一个加强的整体。如图所示,加强部份14和15优选地具有圆锥形状的表面,其厚度在远离小颗粒7、8的方向上减少。
在每一块板1、2中形成一组小孔16,这些小孔适当地沿板的边分布。这些孔16设计来容纳用任何适当的方法固定在板1、2中的销钉17,例如,旋入它们的圆柱体状底部17a。钉入椎间盘软骨下的骨头的它们的尖端部份17b保证将板1、2固定到脊椎上,如L5L4,L5,……。
形成球连接器关节3的小颗粒7、8具有比板1、2小的尺寸,且通常是从具有可能是最好的摩擦学特征性(机械特性:静态的,动态的和耐磨损的),当然还是生物上稳定的材料中选取。它们的磨擦系数必须很低,且它们的使用寿命,以及板1、2的使用寿命样,必须是很长的(例如,40年)。
这些小颗粒7、8可以用适当的材料制造,例如陶瓷,特别是烧结氧化物,如氧化铝或者氧化锆,人造宝石、表面处理过的金属合金(金刚石)涂层,等等)。
柔性吸收冲击环10最好优选地由适当硬度的弹性材料构成。
设想的板1、2的标准号适合于所有可能的脊椎体的形态。可是球连接器3以较大号是适合于每个单个的形态和每个脊椎面的形态,因此,能够制造一定范围的适合于所有患者的椎间盘高度并允许以无限数目的组合适合于每一个特殊病例的另件(板1、2,球连接器3,柔性环10)。
除已提到的技术上的优点之外,按照本发明的椎间盘假体具有以下优点。
借助于适当的球连接器3的尺寸和如上所确定的它的关节c中心的位置,使摩擦表面减少,且由于板1、2彼此相对的倾斜所引起的摩擦将保持低水平(图4)。其结果是降低了小颗粒7、8的磨损,何况,关节表面9、12具有足以保证防止假体过份不稳定的曲率半径,且同时使它有适合的三维可动性,这种可动性实际上是与自然脊椎的可动性等同的。
板1、2和相应的脊椎三维运动时,柔性环10具有吸收大量应力、限制运动环10的对面在所有时间保持与相应的板1的面相接触的性能。高度上的或者环10从前面到后面的厚度上的变化具有使它适合于腰脊柱的生理脊柱前凸的优点。因此,H/h比适合于脊柱轮廓静力学,因为它是上述椎间盘水平的一种功能。环10两个面彼此的倾斜可以作为脊椎水平和病人形体的函数变化。举个例来说,它可以在L5/S1处达到15°。
应该注意到环10前面部份的厚度比它的后面部分要大得多这一事实,它考虑到如前所述构成这种环的柔性材料的困难(involuement)。由此,这导致了一发生与假体结合在一起的脊椎体的运动就产生吸收冲击作用。况且,适当的选择用于环10的柔性材料使它能达到最佳刚性,以便获得在不同应力下再现健康的椎间盘的转动倾斜。最后,按照本发明的假体使它能达到与自然的椎间盘非常类似、甚至完全等同的、一定的刚性和吸收冲击的能力。
上面所描述的假体是由外科大夫按下列方法植入就位。
首先,外科大夫在下脊椎上(例如L5)置入相应的板1,使它适当地与脊椎体对准中心,并用销钉17旋入脊椎把它固定。
然后,外科大夫在上脊椎(例如L4)装入上板2,使它适当地相对于下板1定位。
之后,外科大夫在板1、2之间装入组合的“夹层结构”该结构由柔性环10和由小颗粒7、8形成的球连接装置3的组合件所组成,他把这组合件装在板1、2之间的中间带内,且小颗粒7、8面向锥形孔6,然后,放松施加在接收板1、2的脊椎体上那点上的牵引。这样终于形成嵌入,所说的嵌入是通过对板1、2施力使小颗粒7、8的锥形座进入孔6并连接它们实现的。
按照本发明的假体能达到的角运动范围的量接近于健康的椎间盘的运动范围,列表如下:
L4/L5L5/S1
弯曲/伸展 24° 18°
倾斜 14° ≤14°
轴转动 4° 4°
由于它的紧实性,按照本发明的假体保证了体壁间间隔高度H的回复,且与此同时,它具有内在的稳定性,这也就是说防止了非生理的可动性,特别是平移运动。
当然,可以用于形成假体的材料应该是生物相容的,且必须是生物中性的,这就是说它必须是无毒的,不受腐蚀的。而且,它们必须不会引起炎症,且它们的机械和生物质量也不会由于所选择的消毒方法而受到改变,举例来说,板1、2可以用不锈钢、钛硬质合金或钛合金制造。
钛合金对于脊椎病理学的影像监视具有良好的放射和磁特性的优点,且也具有优良的生物耐受性(bictolerance)和良好的机械性能。
图5到图8所示是本发明的第二个实施例,每个小颗粒21、22分别接纳在相关联的支托板25、26上形成的接收座23、24中,小颗粒21、22部份地从它的接受座23、24中突出,在该座中,它们是自由地装入而不是压入配合。围绕每一个座和每个小颗粒,环形的加厚部件29、31是成圆锥形的,且在顶部的高度h1实际上等于板25、26的厚度。
小颗粒21、22是成锥形的,它的接收座23、24也是成锥形的,并具有约1°-7°的锥角,优选的是5°。
图5到图8所示的假体在其它方面与图1到图4所示的是类似的,特别要注意的是转动中心c的定位。然而,图中未示出柔性的吸收冲击的环10。
通过安置用于容纳小颗粒21、22的座,提供了一个明显的优点,即小颗粒21、22的外尺寸相应于座的内尺寸,它们不是固定在座内,且在一定时间之后,如果需要,可以很容易地从座中取出,也不需要从脊椎上拆下板25、26和替换它们。事实上,这能够使板避免在前个实施例的通孔6的平面上的局部柔性,由于小颗粒所受到的局部夹紧力,所说的柔性不是所需要的。
当然,后者也可以变换成圆柱形,同样,相应的座壁也应该是圆柱形的,但是,这种几何形状不能有利于定位,或者,其次,小颗粒可能脱开。事实上,已经发现,值得重视的是把小颗粒的壁明显地粘结到座的壁上可以产生一种性质,如防止脱开。
为此,已设想出小颗粒21、22和座23、24稍为有一点锥度较为有利,因为它防止了这种缺点。
由患者的身体施加到板25、26上的应力可以由于存在足够厚度e的底部27、28而减少,例如是每个板厚度d的3/4,或甚致等于d。因此,板不会出现任何局部机械强度的减弱而弯曲。
而且,每块板25、26加强的或环形加厚的部份29、31增加了座23、24的锥形壁和小颗粒21、22锥形壁之间的接触面的表面,这是借助于与前述实施例的加厚部份14、15相比增加它们的高度。这种增加的确是底部27、28的构造所必需的。
这样一种结构使它能用于要构成的假体,在参照患者局部脊椎***X射线的结果后,该假体的总高度可以适合于由外科大夫所要求的高度。
为了获得所需假体的总高度,外科大夫具有一组若干个递增高度的球连接器21、22,例如,11,13和15公分,对于这些组中的每一个,适合于形成球连接器的接触面9、12的曲率半径,因此,当板25、26是彼此平行(如图7所示),且是这个高度的一半时,这是接近于假体间的高度H1。
图8所示分别为在板25、26的最大角开口A(例如大约为32°)情况下的板25、26的位置。
图9至图12所示用于把板固定到脊椎体上替代销钉17的装置的各种可能的可供选择的实施例。因此,图9所示的板32、33,它面向脊椎的表面34是滚花的,图10所示的板35、36具有波纹表面37,而图11所示的板38、39包括凸出的表面41。
图12示出了板42,43,它们的压在脊椎体上的表面44已经受过适当的处理:按公知的方法固定金属织物,金属或陶瓷的喷涂,或粘结剂涂覆。
而且这种表面处理可以与图9到图11中的各种选择结合起来施加到表面34、37和41上。
销钉17也可以用螺纹或销子替代。
相反,用粘合剂(异丁烯酸甲酯)固定是不可想象的,因为靠近神经单元并在聚合时释放热量。对于非腰部区域,柔性环10不存在所描述的那种非对称性,因此,它可以有均匀的厚度。
应该注意到按照本发明的椎间盘假体不包含任何自由的另件,这与某些已知的椎间盘假体不同,正是由于这一点,它具有消除任何这样的另件对着主动脉或朝脊柱管挤出的危险的优点。
Claims (13)
1、一种椎间盘假体,包括两块板(1、2),所说的板具有用来把它们固定到相应脊椎(L4,L5)上的装置,和把板彼此用关节相连的装置(7、8),其特征在于所说的关节装置包括一个球连接器(3),它的在前后平面(ox,oy)中的转动中心(c)是在板和脊椎体的后面部份向后偏置,在横向平面(ox,oz)内实质上位于板和脊椎体的中间,在垂直平面(oy,oz)内位于下脊椎(L5)的板(1)的下面,且该假体还包括一个用柔体材料制造的***的吸收冲击的环(10),所说的环(10)具有一个用于球连接器(3)通道的开口(10a),所述环(10)形成所需的尺寸,以便适应各个板和所述球连接器周围之间的被定界了的空间,并基本上与板的形状匹配。
2、按照权利要求1所述的假体,其特征在于球连接器(3)包括具有凸球面(9)的第一小颗粒(7)和用于容纳该凸球面的凹球面(12)的第二小颗粒(8),这两个球面具有相同的曲率半径(r),所说的小颗粒装在各自板(1、2)的中心部位,且它们的突出的面是面对面的。
3、按照权利要求2所述的假体,其特征在于每一块板(1,22;25,26)具有一条靠近脊椎管位置上的直线边(5),且整个外形(4)实际上是椭圆形或卵形的,具有凸球面(9)的小颗粒(7;22)装在下脊椎的板(1,26)中,它的转动中心(c)位于起始于邻近脊椎管的板的直线边的中点(M),在距离上离所说的边大约为起始于所说的中点和下脊椎的板的下面的板的宽度(L)的近似三分之一(d2)和二分之一(d3)之间,所述转动中心位于距上述板为0和近似5mm之间处。
4、按照权利要求2或3的假体,其特征在于每块板(1,2;25,26)在小颗粒(7,8;21,22)突出的面上有一个毗邻小颗粒的中心环形的加厚部份(14,15;29,31),该部份围绕小颗粒并形成一个加强部份。
5、按照权利要求4所述的假体,其特征在于所说的加强部份(14,15;29,31)具有圆锥形的表面,其厚度在远离小颗粒(7、8)的方向上减少。
6、按照权利要求2至5中的一个所述的假体,其特征在于小颗粒(7,8;21,22)具有适配于相应的在板(1,2;25,26)上形成的锥形孔的锥形底座。
7、按照权利要求1至6中的一个所述的假体,其特征在于用于把板(1,2;25,26)固定到脊椎(L5,L4)上的装置包括旋入形成在板上并在整个板上适当分布的孔(16)中的锥形销钉(17),或压花表面(34),或波纹表面(37),或凸出的表面(41)。
8、按照权利要求1-7中的任一个所述的假体,其特征在于板(42,43)是通过金属组织(44)固定到脊椎上的,在板面对脊椎的表面上喷了金属或陶瓷,或者用粘合剂粘结,或也可以是这些方法之一与压花表面(34),或波纹表面(37)或凸出表面(41)之一结合。
9、按照权利要求1-8中的一个所述的假体,其特征在于板(1,2;25,26)具有实际上等于脊椎,特别是腰脊椎的相同的尺寸。
10、按照权利要求1-9中的一个所述的假体,其特征在于柔性吸收冲击环(10)具有最大厚度(H)的前面部份,这厚度(H)大于它后面部分的厚度(h),所说的厚度(h)是从前面部份的边的中心向后面部份规则递减,且在非压缩状态,环(10)的相对的面彼此相互倾斜。
11、按照权利要求1-10中的一个所述的假体,其特征在于球连接器(3)的小颗粒(7,8;21,22)是由下列材料之一制造:陶瓷,特别是烧结氧化物,如氧化铝或氧化锆、人造宝石,或任何表面处理过的金属合金。
12、按照权利要求1-11中的一个所述的假体,其特征在于柔性环(10)是由于适当硬度的弹性材料制成。
13、按照权利要求2-12中的一个所述的假体,其特征在于每个小颗粒(21,22)适合于在支撑板(25,26)中形成的接收座(23,24)内,所说的小颗粒部份地从该座内突出,且可自由地装入该座。
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FR9210232 | 1992-08-24 | ||
FR9210232A FR2694882B1 (fr) | 1992-08-24 | 1992-08-24 | Prothèse discale intervertébrale. |
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CN93118231A Pending CN1090485A (zh) | 1992-08-24 | 1993-08-24 | 椎间盘假体 |
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AU (1) | AU4964593A (zh) |
FR (1) | FR2694882B1 (zh) |
MX (1) | MX9305071A (zh) |
TR (1) | TR26927A (zh) |
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- 1993-08-23 ZA ZA936156A patent/ZA936156B/xx unknown
- 1993-08-24 WO PCT/FR1993/000825 patent/WO1994004100A1/fr active Application Filing
- 1993-08-24 TR TR00730/93A patent/TR26927A/xx unknown
- 1993-08-24 AU AU49645/93A patent/AU4964593A/en not_active Abandoned
- 1993-08-24 CN CN93118231A patent/CN1090485A/zh active Pending
- 1993-09-17 TW TW082107636A patent/TW280767B/zh active
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CN100574728C (zh) * | 2002-03-30 | 2009-12-30 | 无限整形外科有限公司 | 椎间盘置换装置及*** |
CN102028567B (zh) * | 2002-11-05 | 2013-09-11 | Ldr医学公司 | 椎间盘假体 |
CN100588380C (zh) * | 2003-07-22 | 2010-02-10 | 斯恩蒂斯有限公司 | 包括球缺形关节面的椎间植入物 |
CN1867304B (zh) * | 2003-10-17 | 2010-05-12 | 颈椎修复技术公司 | 成套颈椎骨间假体 |
CN1909856B (zh) * | 2004-01-09 | 2010-12-22 | 华沙整形外科股份有限公司 | 后植脊椎装置 |
CN101330886B (zh) * | 2005-12-13 | 2011-01-19 | 德鲁有限责任公司 | 小面关节假体 |
CN111821073A (zh) * | 2020-08-20 | 2020-10-27 | 四川大学华西医院 | 监测活动姿态及其应力变化的骨科内植物***及监测方法 |
CN111938881A (zh) * | 2020-08-20 | 2020-11-17 | 四川大学华西医院 | 可监测活动姿态及其应力的智能椎间盘***及监测方法 |
CN112535556A (zh) * | 2020-11-02 | 2021-03-23 | 淮阴工学院 | 一种气囊式人工颈椎间盘假体 |
Also Published As
Publication number | Publication date |
---|---|
TR26927A (tr) | 1994-08-24 |
TW280767B (zh) | 1996-07-11 |
MX9305071A (es) | 1994-04-29 |
WO1994004100A1 (fr) | 1994-03-03 |
ZA936156B (en) | 1994-09-19 |
FR2694882B1 (fr) | 1994-10-21 |
FR2694882A1 (fr) | 1994-02-25 |
AU4964593A (en) | 1994-03-15 |
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