CN108245266A - 骨植入物 - Google Patents
骨植入物 Download PDFInfo
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- CN108245266A CN108245266A CN201611244802.2A CN201611244802A CN108245266A CN 108245266 A CN108245266 A CN 108245266A CN 201611244802 A CN201611244802 A CN 201611244802A CN 108245266 A CN108245266 A CN 108245266A
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- 210000000988 bone and bone Anatomy 0.000 title claims abstract description 245
- 239000007943 implant Substances 0.000 title claims abstract description 92
- 238000002513 implantation Methods 0.000 claims abstract description 58
- 238000011084 recovery Methods 0.000 claims description 110
- 230000003247 decreasing effect Effects 0.000 claims description 6
- 239000007787 solid Substances 0.000 claims description 5
- 230000001154 acute effect Effects 0.000 claims description 3
- 238000002474 experimental method Methods 0.000 description 6
- 108010048734 sclerotin Proteins 0.000 description 6
- 230000008468 bone growth Effects 0.000 description 4
- 230000008859 change Effects 0.000 description 3
- 238000005516 engineering process Methods 0.000 description 3
- 239000000463 material Substances 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- 230000037118 bone strength Effects 0.000 description 2
- 238000005520 cutting process Methods 0.000 description 2
- 230000012010 growth Effects 0.000 description 2
- 238000009940 knitting Methods 0.000 description 2
- 238000005457 optimization Methods 0.000 description 2
- 238000006243 chemical reaction Methods 0.000 description 1
- 239000004053 dental implant Substances 0.000 description 1
- 238000012938 design process Methods 0.000 description 1
- 230000004069 differentiation Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 230000009931 harmful effect Effects 0.000 description 1
- 210000004394 hip joint Anatomy 0.000 description 1
- 230000006872 improvement Effects 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
- 238000003475 lamination Methods 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 230000008569 process Effects 0.000 description 1
- 230000001737 promoting effect Effects 0.000 description 1
- 230000008439 repair process Effects 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
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- 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
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- 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
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- 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
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- A61C8/0018—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the shape
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Abstract
本发明公开一种骨植入物,具有一锁固段与一植入端。锁固段设有一螺纹与至少一骨复原腔。骨复原腔位于螺纹的螺根处。骨复原腔为从锁固段的表面向内凹陷的腔室。锁固段具有一中心轴。在锁固段的同一区段中,越接近植入端的骨复原腔在平行且通过中心轴的截面的面积越小。
Description
技术领域
本发明涉及一种植入物,且特别是涉及一种骨植入物。
背景技术
骨钉或人造牙根植入生物体内时,会对周遭组织施加应力,造成不同程度的影响。近年来皆使用参数化设计骨钉或人造牙根,并配合有限元素法,希望得到最佳化设计的骨钉或人造牙根。由于此方法须将所有可能的参数进行设计,才可能得到最佳化设计,过程中需耗费相当大量的时间。但是,不同患者的齿槽骨的骨质状况及咬合力皆不尽相同,不合适的骨钉或人造牙根将大幅减少骨整合率,进而衍生出较高的手术失败率,反而增加患者的负担。
若能以配合人体骨骼生长的方式,设计出可直接套用至各种齿槽骨大小、骨质以及咬合力的骨钉或人造牙根,将可避免参数化设计所需的大量时间,得到适合患者所需的骨钉或人造牙根,将可有效的提升骨整合率,以提高植牙手术的成功率,进而降低患者的负担。
发明内容
为解决上述问题,本发明的骨植入物具有一锁固段与一植入端。锁固段设有一螺纹与至少一骨复原腔。骨复原腔位于螺纹的螺根处。骨复原腔为从锁固段的表面向内凹陷的腔室。锁固段具有一中心轴。在锁固段的同一区段中,越接近植入端的骨复原腔在平行且通过中心轴的截面的面积越小。
基于上述,本发明的骨植入物的骨复原腔的截面的面积朝向植入端逐渐减少。这样的设计可加速骨头复原速度。
为让本发明的上述特征和优点能更明显易懂,下文特举实施例,并配合所附附图作详细说明如下。
附图说明
图1A是本发明一实施例的骨植入物的立体图及其局部剖视放大图;
图1B是图1A的骨植入物的局部剖视图;
图2A是本发明一实施例的骨植入物的立体图及其局部剖视放大图;
图2B是图2A的骨植入物的局部剖视图;
图3A是本发明另一实施例的骨植入物的立体图;
图3B是图3A的骨植入物的局部放大图;
图4A是本发明再一实施例的骨植入物的局部放大图;
图4B是图4A的骨植入物的局部剖视图;
图5与图6是本发明一实验例的骨植入物经动物试验后的切片照片;
图7是本发明又一实施例的骨植入物的立体图及其局部剖视放大图;
图8是本发明更一实施例的骨植入物的立体图及其局部剖视放大图。
符号说明
100、200、300、400、500、600:骨植入物
110、210、310、410、510、610:锁固段
110A:柱状本体
112:螺纹
112A:螺根
114、214、314、414、514、614:骨复原腔
114A、114B、114C、214A、214B、214C:骨复原腔的截面
116:表面
120、220、320、420、520、620:植入端
L12:中心轴
A12、A22、A32:顶角
A14、A24、A34、A16、A26、A36:夹角
E12、E22、E32:第一边
E14、E24、E34:第二边
210A、310A、410A:第一段
210B、310B、410B:第二段
C30、C40:中心腔
P30、P40:孔隙
具体实施方式
骨生长需有适当应力,过与不及均有不良影响。当骨植入物植入骨组织后,骨组织会根据受力大小的不同而产生不同的反应。当骨头受力较小时,部分小梁骨及内层密质骨将被移除以降低骨骼强度。当骨头受力稍大时,骨骼强度会提升。当骨头受力更大而略微超过负载,骨骼可健康的修复。当骨头受力远超过负载时,骨骼将会被破坏而无法修复。根据上述原则,发明人分析并计算各空间单元是否适合骨组织生长。适合骨组织生长的空间单元会被设定为空腔以留给骨组织生长,不适合骨组织生长的空间单元则被设定为由骨植入物占据。经过上述的设计过程后,最终得到骨植入物的适当外型。其中,包含了由骨植入物的材料占据的空间,用于确保有足够的支撑强度,同时也包含了至少一骨复原腔以供骨组织复原生长。因此,发明人得出兼顾骨长入比例以及周围健康骨头比例的骨植入物的适当外型。以下,参考附图说明本发明的骨植入物的数个实施例。
图1A是本发明一实施例的骨植入物的立体图及其局部剖视放大图。请参考图1A,本实施例的骨植入物100具有一锁固段110与一植入端120。锁固段110设有一螺纹112与至少一骨复原腔114。骨复原腔114位于螺纹112的螺根112A处。本实施例的螺纹112是单一条的脊状结构,斜向环绕于锁固段110的表面116上,以使锁固段110可与骨头紧密结合。然而,在其他实施例中,螺纹可以是斜向环绕于锁固段的表面上且彼此平行的多条脊状结构,螺纹也可以是环绕于锁固段的表面上的多个封闭环状的脊状结构,或者螺纹也可以是其他可使锁固段与骨头紧密结合的结构。本实施例的骨复原腔114是单一条型态,与螺纹112平行地斜向环绕于锁固段110的表面116上而位于螺纹112的螺根112A处。然而,在其他实施例中,骨复原腔114也可以是多个。此外,这些骨复原腔114加总后例如大致与图1A的骨复原腔114相似,只是各个骨复原腔114之间可能是分离的。
骨复原腔114为从锁固段110的表面116向内凹陷的腔室。举例而言,在一种区分方式下,锁固段110可分成柱状本体110A以及螺纹112。柱状本体110A的表面就是前述的锁固段110的表面116,且螺纹112环绕于柱状本体110A的表面上116,而螺根112A也位于柱状本体110A的表面上。若未形成骨复原腔114,则柱状本体110A的表面116原本的位置可由图1A中的虚线表示。从图1A中的虚线表示的位置朝骨植入物100的内部凹陷而成的腔室就是骨复原腔114。相较于传统的具有螺纹的骨植入物而言,本实施例的骨植入物100在螺纹112的螺根112A处凹陷有骨复原腔114。
锁固段110具有一中心轴L12,中心轴L12平行于图1A中的Y轴,沿着柱状本体110A的轴向延伸。以平行且通过中心轴L12的切面切过骨复原腔114,会得许多骨复原腔114的截面。在锁固段110的同一区段中,越接近植入端120的骨复原腔114的截面的面积越小。从另一角度来看,骨复原腔114越接近植入端120的区段的体积越小。本实施例中,同一区段是表示在该区段中锁固段110的半径没有剧烈的变化。例如,骨复原腔的截面114A最远离植入端120,骨复原腔的截面114C最接近植入端120,而骨复原腔的截面114B的位置介于骨复原腔的截面114A与骨复原腔的截面114C之间。因此,骨复原腔的截面114A的面积大于骨复原腔的截面114B的面积,而骨复原腔的截面114B的面积大于骨复原腔的截面114C的面积。如下表一所示,将图1A中骨复原腔114的七个截面从远离植入端120向接近植入端120开始编号,依序编号为R1~R7。以编号R1的骨复原腔114的截面114A的面积为100%,可发现本实施例的骨复原腔114的截面的面积确实在越接近植入端120越小。最接近植入端120的编号R7的骨复原腔的截面114C的面积仅为编号R1的骨复原腔的截面114A的面积的59.2%。
表一
截面编号 | 腔室截面的面积变化 |
R1 | 100% |
R2 | 96.2% |
R3 | 88.8% |
R4 | 81.4% |
R5 | 77.7% |
R6 | 70.3% |
R7 | 59.2% |
经过实验后发现,本实施例的骨植入物100可同时兼顾骨长入比例以及周围健康骨头比例,加速复原并降低手术失败率,进而减轻患者的负担。后续将以实验例说明本发明的骨植入物相较于现有技术促进骨愈合的效果上的改进。
图1B是图1A的骨植入物的局部剖视图。请参考图1A与图1B,本实施例的骨植入物100的锁固段110是以实心的设计为例,可给予骨植入物100较强的刚性,但本发明不局限于此。请再参照图1A,本实施例的锁固段110具有一中心轴L12,中心轴L12平行于图1A中的Y轴。以平行且通过中心轴L12的切面切过骨复原腔114,则得到骨复原腔114的多个截面的轮廓在靠近中心轴L12的一侧分别具有一顶角。越接近植入端120的顶角越大。例如,以XY平面为切面通过中心轴L12切过骨复原腔114时,骨复原腔的截面114A在切面上的轮廓在靠近中心轴L12的一侧具有顶角A12。类似的,骨复原腔的截面114B具有顶角A22,骨复原腔的截面114C具有顶角A32。骨复原腔的截面114C的顶角A32大于骨复原腔的截面114B的顶角A22,而骨复原腔的截面114B的顶角A22大于骨复原腔的截面114A的顶角A12。经过实验后发现,骨复原腔114的截面的顶角采用上述安排时,可同时兼顾骨长入比例以及周围健康骨头比例,加速复原并降低手术失败率,进而减轻患者的负担。此外,距离植入端120最远的骨复原腔114的截面的顶角为锐角,即骨复原腔的截面114A的顶角A12为锐角。距离植入端120最近的骨复原腔114的截面的顶角为钝角,即骨复原腔的截面114C的顶角A32为钝角。在一实施例中,骨复原腔114的截面的顶角范围可介于15°~160°之间。
从另一观点来看,本实施例的骨复原腔114的各个截面的顶角是由一第一边与一第二边构成。这些第一边与中心轴L12的多个夹角以5°~45°的范围由远离植入端120处朝接近植入端120的方向递减。这些第二边与中心轴L12的多个夹角以15°~120°的范围由远离植入端120处朝接近植入端120的方向递减。具体而言,骨复原腔114的截面114A的顶角A12由第一边E12与第二边E14构成,骨复原腔114的截面114B的顶角A22由第一边E22与第二边E24构成,骨复原腔114的截面114C的顶角A32由第一边E32与第二边E34构成。
图1A中,为了方便说明中心轴L12与顶角的两边的夹角,将中心轴L12平移至通过各顶角的顶点的位置做表示。各顶角的两边中,是以较靠近正Y轴方向(即远离值入端120的中心轴L12方向)的一边为第一边,并以另一边为第二边。骨复原腔114的截面114A的顶角A12的第一边E12与中心轴L12的夹角A14是指,从第一边E12逆时针转至中心轴L12时的角度。骨复原腔114的截面114B的顶角A22的第一边E22与中心轴L12的夹角A24是指,从第一边E22逆时针转至中心轴L12时的角度。骨复原腔114的截面114C的顶角A32的第一边E32与中心轴L12的夹角A34是指,从第一边E32逆时针转至中心轴L12时的角度。第一边E12与中心轴L12的夹角A14大于第一边E22与中心轴L12的夹角A24,而第一边E22与中心轴L12的夹角A24大于第一边E32与中心轴L12的夹角A34。在一实施例中,第一边E12与中心轴L12的夹角A14为45°,第一边E32与中心轴L12的夹角A34为5°。此外,这些第一边(包含但不限于第一边E12、E22、E32)与中心轴L12的多个夹角(包含但不限于夹角A14、A24、A34)的范围可以是5°~45°。
骨复原腔114的截面114A的顶角A12的第二边E14与中心轴L12的夹角A16是指,从第二边E14顺时针转至中心轴L12时的角度。骨复原腔114的截面114B的顶角A22的第二边E24与中心轴L12的夹角A26是指,从第二边E24顺时针转至中心轴L12时的角度。骨复原腔114的截面114C的顶角A32的第二边E34与中心轴L12的夹角A36是指,从第二边E34顺时针转至中心轴L12时的角度。第二边E14与中心轴L12的夹角A16大于第二边E24与中心轴L12的夹角A26,而第二边E24与中心轴L12的夹角A26大于第二边E34与中心轴L12的夹角A36。在一实施例中,第二边E14与中心轴L12的夹角A16为120°,第二边E34与中心轴L12的夹角A36为15°。此外,这些第二边(包含但不限于第二边E14、E24、E34)与中心轴L12的多个夹角(包含但不限于夹角A16、A26、A36)的范围可以是15°~120°。
本实施例的骨植入物100可藉积层制造方法制造出一体成型的结构,例如是3D打印技术,但本发明不局限于此。
图2A是本发明一实施例的骨植入物的立体图及其局部剖视放大图,而图2B是图2A的骨植入物的局部剖视图。请参照图2A与图2B,本实施例的骨植入物200的锁固段210包含一第一段210A与一第二段210B,第二段210B位于第一段210A与植入端220之间。第一段210A为实心且第二段210B为空心。第二段210B的一外壁厚度在100μm以上,可维持适当的强度。第二段210B的空心部分的体积例如可以占第二段210B的整体体积的60%以下,但本发明不局限于此。如同前一实施例所述,在锁固段210的同一区段中,越接近植入端220的骨复原腔214的截面的面积越小。如下表二所示,将图2A中的骨复原腔214的七个截面从远离植入端220向接近植入端220开始编号,依序编号为R1~R7。以编号R1的骨复原腔214的截面214A的面积为100%,可发现本实施例的骨复原腔214在第一段210A的的截面的面积越接近植入端220越小。另外,骨复原腔214在第二段210B的截面的面积也是越接近植入端220越小。然而,骨复原腔214在第一段210A中最接近植入端220的编号R3的骨复原腔214的截面的面积小于第二段210B的骨复原腔214中最远离植入端220的编号R4的骨复原腔214的截面的面积。在一实施例中,编号R4的骨复原腔214的截面的面积还大于第一段210A的骨复原腔214中最远离植入端220的编号R1的骨复原腔214的截面的面积,空心的第二段210B可以提供适合骨组织生长的环境,故第二段210B的骨复原腔214的截面的面积较大。
表二
截面编号 | 腔室截面的面积变化 |
R1 | 100% |
R2 | 96.9% |
R3 | 93.8% |
R4 | 135.4% |
R5 | 125.8% |
R6 | 109.6% |
R7 | 102.4% |
图3A是本发明另一实施例的骨植入物的立体图,图3B是图3A的骨植入物的局部放大图。图3A的骨植入物300与图2A的骨植入物200相似,相同处在此不再赘述。图3A的骨植入物300的第一段310A为实心,且骨植入物300的第二段210B为空心而存在如虚线所示的中心腔C30。骨复原腔314至少部分连通中心腔C30,例如是骨复原腔314位于骨植入物300的第二段210B的部分连通中心腔C30。在本实施例中,第二段210B的骨复原腔314具有多个孔隙P30,以与中心腔C30连通。在一实施例中,单一孔隙P30的截面积例如介于2500μm2~90000μm2,但本发明不局限于此。如下表三所示,将图3A中的骨复原腔314的七个截面从远离植入端320向接近植入端320开始编号,依序编号为R1~R7。以编号R1的骨复原腔314的截面的面积为100%,可发现本实施例的锁固段310的第一段310A的骨复原腔314的截面的面积越接近植入端320越小。另外,锁固段310的第二段310B的骨复原腔314的截面的面积也是越接近植入端320越小。然而,在第一段310A的骨复原腔314的截面中最接近植入端320的编号R3的骨复原腔314的截面的面积小于第二段310B的骨复原腔314的截面中最远离植入端320的编号R4的骨复原腔314的截面的面积。骨复原腔314连通中心腔C30的设计可增加骨长入的比例。
表三
截面编号 | 腔室截面的面积变化 |
R1 | 100% |
R2 | 90.9% |
R3 | 72.7% |
R4 | 81.8% |
R5 | 72.7% |
R6 | 72.7% |
R7 | 63.6% |
图4A是本发明再一实施例的骨植入物的局部放大图,而图4B是图4A的骨植入物的局部剖视图。图4A的骨植入物400与图3A的骨植入物300相似,相同处在此不再赘述。本实施例的骨植入物400的锁固段410包含第一段410A与第二段410B,第二段410B位于第一段410A与植入端420之间。其中,第一段410A与第二段410B皆为中空,且第一段410A的半径与第二段410B的半径不同。在一实施例中,第二段410B的半径为第一段410A的半径的30%~99%。骨复原腔414的截面的面积仍遵照递减规则由远离植入端420至靠近植入端420渐渐变小,最下层几乎没有腔室。此外,骨复原腔414的一部分经由孔隙P40与中心腔C40连通。
图5与图6是本发明一实验例的骨植入物经动物试验后的切片照片。图5与图6的骨植入物的设计大致与图4A的骨植入物类似。发明人将本发明的实验例的骨植入物植入动物体内,观察其促进骨组织生成的情形。本实验例的骨植入物的表面在第一个月时有微量新生骨质贴附,同时有微量骨质进入中心腔。第二个月时,已可见新生骨质生长于骨植入物周围及骨复原腔中,增加其稳固性,如图5的横向切面与图6的纵向切面。本实验例的骨植入物的内部与表面均被新生骨覆盖,且新生骨组织紧密贴合于骨植入物的表面。在植入一个月时,采用现有骨植入物的骨质量密度(bond mass density,BMD)为0.88±0.48,而采用本实验例的骨植入物的骨质量密度可达1.14±0.48。采用现有骨植入物的骨体积比(BV/TV)约为66.79%,而采用本实验例的骨植入物的骨体积比可达85.15%。采用现有骨植入物的骨表面密度约为6.47/单位面积,而采用本实验例的骨植入物的骨表面密度可达7.25/单位面积。此外,采用本实验例的骨植入物的实验在植入两个月后的扭力测试表现优于采用现有骨植入物的实验。由此可证明,本发明的骨植入物具有良好的骨愈合率。
上述各实施例的骨植入物都以应用于牙床为例,但本发明不局限于此。
图7是本发明又一实施例的骨植入物的立体图及其局部剖视放大图。请参照图7,本实施例的骨植入物500与图1A的骨植入物100相似,相同处在此不再赘述。图7的骨植入物500是应用于椎弓根钉,锁固段510的骨复原腔514的截面的面积同样是越接近植入端520越小。如下表四所示,将图7中的骨复原腔514的十三个截面从远离植入端520向接近植入端520开始编号,依序编号为R1~R13。以编号R1的骨复原腔514的截面的面积为100%,可发现本实施例的骨复原腔514的截面的面积在越接近植入端520时越小。
表四
图8是本发明更一实施例的骨植入物的立体图及其局部剖视放大图。请参照图8,本实施例的骨植入物600与图1A的骨植入物100相似,相同处在此不再赘述。图8的骨植入物600是应用于髋关节,锁固段610的螺纹是环绕于锁固段610表面上的多个封闭环状的脊状结构,使固锁段610可具有多个骨复原腔室614。所述多个骨复原腔614的截面的面积同样是越接近植入端620越小。图8中以虚线表示锁固段610的柱状本体的表面116原本的位置,从图8中的虚线表示的位置朝骨植入物600的内部凹陷而成的腔室就是骨复原腔614,而所述多个骨复原腔614的截面的面积也是依此原则计算。如下表五所示,将图8中的六个骨复原腔614从远离植入端620向接近植入端620开始编号,依序编号为R1~R6。以编号R1的骨复原腔614的截面的面积为100%,可发现本实施例的骨复原腔614的截面的面积确实在越接近植入端620越小。
表五
综上所述,本发明的骨植入物在螺根处有至少一骨复原腔,且位于同一区段上的骨复原腔的截面面积朝向底部逐渐减少。这样的设计不仅可调整骨植入物的整体刚性,更增加了骨整合率,加速骨头复原速度。
虽然结合以上实施例公开了本发明,然而其并非用以限定本发明,任何所属技术领域中熟悉此技术者,在不脱离本发明的精神和范围内,可作些许的更动与润饰,故本发明的保护范围应以附上的权利要求所界定的为准。
Claims (13)
1.一种骨植入物,具有锁固段与植入端,其中该锁固段设有螺纹与至少一骨复原腔,该至少一骨复原腔位于该螺纹的螺根处,该至少一骨复原腔为从该锁固段的表面向内凹陷的腔室,该锁固段具有中心轴,且在该锁固段的同一区段中,越接近该植入端的该至少一骨复原腔在平行且通过该中心轴的截面的面积越小。
2.如权利要求1所述的骨植入物,其中该至少一骨复原腔于平行且通过该中心轴的多个截面的轮廓在靠近该中心轴的一侧分别具有顶角,越接近该植入端的该些顶角越大。
3.如权利要求2所述的骨植入物,其中距离该植入端最远的该顶角为锐角,且距离该植入端最近的该顶角为钝角。
4.如权利要求2所述的骨植入物,其中各该顶角由第一边与第二边构成,该些第一边与该中心轴的多个夹角由远离该植入端处朝接近该植入端的方向递减。
5.如权利要求4所述的骨植入物,其中各该夹角的范围为5°~45°。
6.如权利要求2所述的骨植入物,其中各该顶角由第一边与第二边构成,该些第二边与该中心轴的多个夹角由远离该植入端处朝接近该植入端的方向递减。
7.如权利要求6所述的骨植入物,其中各该夹角的范围为15°~120°。
8.如权利要求1所述的骨植入物,其中该锁固段包含第一段与第二段,该第二段位于该第一段与该植入端之间,该第二段的半径为该第一段的半径的30%~99%。
9.如权利要求1所述的骨植入物,其中该锁固段包含第一段与第二段,该第二段位于该第一段与该植入端之间,该第一段为实心且该第二段为空心,该第二段的外壁厚度在100μm以上。
10.如权利要求9所述的骨植入物,其中该至少一骨复原腔在该第一段中平行且通过该中心轴的截面的面积越接近该植入端越小,且该至少一骨复原腔在该第二段中平行且通过该中心轴的截面的面积越接近该植入端越小。
11.如权利要求10所述的骨植入物,其中该至少一骨复原腔在该第一段中最接近该植入端的平行且通过该中心轴的截面的面积小于该至少一骨复原腔在该第二段中最远离该植入端的平行且通过该中心轴的截面的面积。
12.如权利要求1所述的骨植入物,其中该锁固段为空心而具有中心腔,该至少一骨复原腔至少部分连通该中心腔。
13.如权利要求12所述的骨植入物,其中该至少一骨复原腔具有多个孔隙,以与该中心腔连通,每一该些孔隙的截面积介于2500μm2~90000μm2。
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