CN101123920A - 三维可植入骨支撑 - Google Patents
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Abstract
本发明涉及一种可以用于治疗患病或损伤骨组织的可膨胀的半柔性装置及使用这种半柔性装置的方法。半柔性装置被***到松质骨组织的内部空间中,并填充适宜的材料以提供对骨头的内部结构性支撑。半柔性装置还可以充当用于药物治疗、放射性治疗或热治疗患病骨头的载体。
Description
相关申请的交叉引用
根据35 U.S.C.§119(e),本申请要求2005年1月7日提交的美国临时专利申请号60/641,968的优先权,其公开内容在此引入作为参考。
背景技术
当前,在现有技术中已知各种对哺乳动物的患病或损伤松质骨组织的治疗。松质骨或海绵状骨具有小梁(蜂窝状结构)和相对于皮层骨较高程度的多孔性。小梁之间的间距充满了包含营养海绵状骨的血管的红骨髓。海绵状骨在骨盆、肋骨、胸骨、椎骨、颅骨的骨头以及臂骨和股骨的端部可以找到。
所有的骨头都会受到外伤、疾病作用(processes)或破裂的损坏,例如,但不限于,骨质疏松症,疏松骨,骨质疏松破裂干骺端骨和骺骨,骨质疏松脊椎体,破裂骨质疏松脊椎体,由肿块、尤其是圆形单元肿块引起的脊椎体破裂,长骨骨端的无血管形成性坏死、尤其是近端股骨、远端股骨和近端肱骨的无血管形成性坏死,由内分泌情况引起的缺陷,以及转移性瘤。包括脊柱的骨头由于其解剖结构的复杂性而尤其难以治疗。椎骨的有效治疗由脊髓附近进一步加重到由此发源的神经。
在破裂骨或患病骨、尤其是椎骨的治疗中已经获得普及的两个最小侵入操作是经皮椎体成形术和椎体后凸成形术。美国专利号6,273,916描述了用于执行椎体成形术的方法和设备。椎体成形术是一种将接合剂类材料、例如聚甲基丙烯酸甲酯(“PMMA”)在高压下直接喷射到脊椎空腔内的操作。接合剂类材料能够固化,并且在***时提供对受影响的椎骨的结构性支撑。
在椎体后凸成形术中,在背部进行小的切入。利用荧光检查图像技术,外科医生将插管引导至所希望的位置,通过插管***钻头,穿过外皮壁钻入松质骨,以限定椎体内部的通道。移除钻头,并将气囊导管***该通道中。然后气囊导管膨胀,将松质骨压靠在外皮壁上,以在其中限定空腔。用于压缩破裂的这种操作的一个特殊的优点是,气囊导管的充气恢复了一部分脊椎高度。继放气和移除气囊导管之后,注射诸如在椎体成形术中使用的接合剂类材料以填充空腔。接合剂被容许固化,并封闭手术部位。
在先有技术中已知经皮椎体成形术和椎体后凸成形术的变形。例如,美国专利号5,827,289公开了,利用气囊形成或扩大骨头、尤其是但不限于脊椎体中的空腔或通道,并将治疗物质以改进的方式传送至骨头。美国专利号6,632,235公开了,利用充气装置,减少骨头中的破裂和治疗脊柱。美国专利申请公布号US 2003-0050644A1公开了,采用在引导金属丝上方***骨头中的可膨胀主体。美国专利申请公布号US 2005-0234456A1公开了,利用可植入医学装置支撑结构。美国专利号6,348,055公开了,利用一导管,将植入材料从高压敷料器传送至植入传送装置。美国专利号6,033,411公开了,利用精确深度引导仪器,执行硬组织植入材料的经皮植入。
虽然上述操作代表了在骨伤害和疾病治疗上的重要进步,但是,它们不是没有危险。两个操作共有的危险是,接合剂会从所治疗的骨头中的破裂部位渗出。虽然这些危险在椎体成形术中更明显,但是,由于高的注射压力,从破裂部位渗出的接合剂可以引起血栓形成,脊骨狭窄,或神经根压缩,偶尔可以引起肺栓子。
上述操作的另一个局限在于,一旦骨接合剂已经固化,就禁止随后从椎体移除接合剂,尤其是对脊柱中的椎骨来说。
同样,上述方法是修复性的,不能治疗所有的原发疾病状态,这可能引起或帮助需要应用早先的这些方法的破裂。
因此,尽管先有技术中有这些新近的进步,但是仍然继续需要用于治疗骨折和骨疾病状况的改善的装置和方法。
发明内容
本发明旨在一种治疗患病或损伤骨组织的方法,包括:选择要治疗的骨组织中的内部区域;将一装置***到要治疗的骨组织中的内部区域内;和治疗期间利用该装置在内部支撑骨组织。
本发明还旨在一种用于治疗患病或损伤骨组织的装置,包括:导管,其中所述导管包括限定至少一个贯穿的内部通道的主体;可膨胀的半柔性结构,其中所述半柔性结构限定一内部空间;和可移除的紧固件,其中所述紧固件将导管可释放地连接到半柔性结构上。
附图说明
图1是依照本发明一个实施例***到椎骨松质骨内限定的空腔中的可分离的半柔性结构和导管的侧视图。
图2是图1的可分离的半柔性结构和导管由骨支撑材料膨胀时的侧视图。
图3是断开图1的导管与图1的半柔性结构并密封半柔性结构的侧视图。
图4是半柔性结构植入椎骨以后的侧视图。
图5是脊骨椎骨和***在其中的关节内窥探针的横截面视图。
图6是具有半柔性结构的脊骨椎骨和部分地***椎体中的关节内窥探针的横截面视图。
图7是具有半柔性结构的脊骨椎骨和完全***椎体中的关节内窥探针的横截面视图。
具体实施方式
本发明涉及矫形外科装置和方法的技术领域。本发明的方法需要利用导管67,导管67通过可移除紧固件、优选螺旋装置连接到优选可分离的半柔性结构上。紧固件将导管67可释放地连接到半柔性结构49上,紧固件能够将半柔性装置49结合到导管67上,以及能够使半柔性装置49和导管67脱开结合。
导管67具有限定至少一个贯穿的内部通道的主体,半柔性结构限定一内部空间,半柔性结构包括允许导管的内部通道与半柔性结构的内部空间之间连通的可密封端口。
“半柔性结构”在此定义为有韧性的、可膨胀的非刚性结构。这与完全柔性结构或刚性的非柔性结构相对。更具体地说,半柔性结构定义为特定柔性比率在大约10%到大约30%的结构。应当理解,这样的比率不限于本发明的范围。半柔性结构的柔性比率定义为结构屈服于压力或力而没有断裂的比率,或者测量该能力、例如当该半柔性结构充满液体或其它材料时半柔性结构的膨胀性的每单位压力变化的体积变化单位的表示。
半柔性结构可以临时或永久地***到内部区域中,例如哺乳动物患病或损伤松质骨组织内部的空腔或其它空间中,以便在内部支撑骨头和/或治疗这样的疾病或损伤,以及减轻疾病或损伤症状,例如背痛。可分离的半柔性结构在穿过导管内部的通道导入、通常通过注射适宜的骨支撑材料时膨胀,半柔性结构提供了对其中的骨支撑材料的容纳和保持。可分离的半柔性结构的形状优选设计成,使得在膨胀时,该结构在三维尺寸上大体上适应和符合外部区域、例如在要治疗的骨头内部外皮壁内限定的空腔的尺寸。可分离的半柔性结构通过使用优选的半渗透薄膜防止骨支撑材料从破裂部位渗出,并便于控制从结构***,从而避免如上所述的有害影响。
为了提供对结构内的骨支撑材料的附加的容纳和保持,该结构可设置有可密封端口,通过所述可密封端口,导管与半柔性结构相连通。在分离导管时,可以密封该端口,以防止骨支撑材料从该结构内部流出。这种配置还便于提供对结构内的骨支撑材料的加压容纳和保持。该端口可以保持开启,但其中的骨支撑材料***,所以不会从该端口流出。在另一个实施例中,该端口临时被密封,这样,导管可以再次附着到该端口上,可以根据需要移除骨支撑材料。
半柔性结构可以由有韧性的、耐用的任何适宜的生物相容材料形成,例如,但不限于,不锈钢,钛,聚合物、例如诸如聚酯和聚乙烯的聚合材料和塑料,聚乳酸和这些聚合物彼此和其它单体的共聚物,再吸收合成材料、例如缝合材料,镍钛金属互化物,或者本领域技术人员所知的任何其它适宜的材料,包括这些材料的组合。适宜的生物相容材料优选是超弹性的并且拥有极好的类似橡胶的形状保持性的金属薄膜材料。镍钛金属互化物,镍和钛的金属合金,是一种尤其适宜的生物相容材料,因为镍钛金属互化物具有经受诸如松质骨组织内的生物环境的腐蚀作用的能力。另外,镍钛金属互化物还具有极好的耐磨性,在与镍钛金属互化物接触的组织中呈现最小的镍升高。Betz等,脊柱,28(20S)增补:S255-S265(2003年10月15日)。利用适宜的镍钛金属互化物作为可植入气囊中的优选生物相容材料公开在美国专利号6,733,513中,该专利在此引入作为参考。
半柔性结构优选是可膨胀的三维气囊的形式。在半柔性结构永久***到松质骨组织中的情况下,该结构的生物相容材料由适宜的表面材料制成,例如,但不限于如上所述的那些材料,以提供用于结合和愈合的骨亲和薄膜,以及帮助改善或促进健康骨细胞的吸引。
在疾病是骨折的原发(underlying)起因的应用中,本发明的目的还构思,半柔性结构充当用于治疗疾病或损伤的载体。在此构思的本发明包括用于原发疾病状态的药物治疗、放射性治疗和热治疗。这样的药物治疗可以包括,但不限于,包括药的治疗,例如,但不限于,顺铂,紫杉酚TM,亚德里亚霉素TM,阿霉素,美法仑,环磷酰胺,卡铂,氨甲喋呤,或者本领域技术人员所知的用于治疗骨疾病的类似的治疗。这样的放射性治疗可包括,但不限于,可以用于治疗恶性骨疾病以防止进一步破裂和疼痛的放射疗法,或者借助于栓塞(转移血管(transvascular)闭塞)应用于恶性骨疾病的介入操作。
骨支撑材料可包括根据治疗用途选择的若干材料。在治疗包含永久骨支撑的情况下,骨支撑材料包括骨接合剂,其作为液体注射进去,然后在较短时间内***。在治疗包含骨头的临时支撑的情况下,骨支撑材料可以作为液体注射进去,在需要支撑的时间期间保持液体形式。当治疗操作完成和/或需要附加治疗而更换时,则可以容易地抽出。在替换实施例中,骨支撑材料可以是柔韧的胶状材料的形式,以提供对骨骼构造的支撑和能量衰减。
参考各个附图可以看到,本发明包括具有至少一个内腔或其它长的延伸通道路径的导管67,优选为多内腔导管67,其带有用于临时或永久放置在诸如松质骨组织17的骨组织中限定的空腔74内的可分离的半柔性结构49。本发明还包括治疗通过外伤或通过疾病作用已经破裂的骨头的方法,例如,但不限于,骨质疏松症,骨质疏松破裂干骺端骨和骺骨,骨质疏松脊椎体,由肿块、尤其是圆形单元肿块引起的脊椎体破裂,长骨骨端的无血管形成性坏死、尤其是近端股骨、远端股骨和近端肱骨的无血管形成性坏死,由内分泌情况引起的缺陷,转移性瘤,长骨(即外伤或自发骨折或骨骼构造的其它局部畸变),例如颈、胸廓、腰椎和骶骨破裂,等等。
如图6和图7所示的可分离的半柔性结构49的形状设计成,使之大体上符合在松质骨组织17的内部外皮壁内所选择的空腔74的尺寸。空腔74可以仅仅通过本领域技术人员所熟知的任何适宜的操作来确定和/或限定在内部外皮壁内,例如,但不限于,对前体膨胀装置的钻孔、***,及其它相关方法。可以利用最小侵入图像引导技术预先确定空腔74的尺寸,例如,但不限于,X射线,CT扫描或手术CT图像,超声波,计算机断层,MR/CT图像重合,三维可视化,光定位,和核磁共振机(MRI),或任何其它适宜的图像技术。优选地,半柔性结构49的壁具有大约10%到大约30%之间的柔性比率,以提供该结构与包括松质骨17的壁或皮层骨内壁的空腔74的接合。
如图2所示,可分离的半柔性结构49在穿过多内腔导管67内部的内腔注射适宜的骨支撑材料时膨胀,该结构49提供对其中的骨支撑材料83的容纳和保持,以及提供对松质骨组织17的附加结构性支撑。根据该结构49是永久植入物,还是临时植入物,选择骨支撑材料83的特性,以便足够耐用以容许骨折愈合。
对于永久植入治疗,骨支撑材料83可以是在本领域中已知的或开发的配方设计制成的接合剂类材料,例如基于聚甲基丙烯酸甲酯(“PMMA”)的那些材料,或其它适宜的生物材料替换或组合,包括,但不限于,右旋糖酐,聚乙烯,碳纤维,聚乙烯醇(PVA),或多(对苯二甲酸亚乙酯)(PET),例如在传统椎体成形术或椎体后凸成形术操作中使用的那些材料。更优选地,接合剂类材料是PMMA。在本技术领域中,PMMA的具体配方设计是已知的,通常用于骨植入。这样的配方设计包括,但不限于,例如在美国专利号4,526,909和6,544,324中公开的那些配方设计,这些专利在此引入作为参考。
本发明的主要目的之一是,防止接合剂类材料从破裂部位渗出和防止引起的生理危险。由于接合剂类材料容纳和保持在半柔性结构49内部,所以这种预防是可能的。
为了提供对半柔性结构49内的骨支撑材料83的附加容纳和保持,该结构49可设置有可密封端口32,如图3和4所示,通过所述可密封端口32,导管67与半柔性结构49相连通。在与导管67分离时,可以密封该端口32,以防止骨支撑材料83从该结构49流出。这种配置还便于提供对结构49内的骨支撑材料83的加压容纳和保持。另外,可密封端口32还能够防止生物流体渗入半柔性结构49中,从而通过防止腐蚀和降解内部半柔性结构49的壁而改善结构的耐用性。作为选择,导管67可以保持与半柔性结构49的附着,直到骨支撑材料83已经固化的时刻。如果使用PMMA作为骨接合剂,固化时间一般在大约2分钟到大约10分钟。一旦PMMA固化,就可以在材料从可密封端口32最低危险地流出导管67的情况下分离导管67,如图3所示。图3中从骨组织17相反的箭头表示将骨支撑材料83注射到半柔性结构49内并由此脱离与导管67的结合之后导管67移动的方向。但是,因为这个操作潜在地使结构49临时开启,所以应当特别的小心,以避免生物流体渗入结构49内。
本发明的装置也可以用于松质骨17的临时植入,与当容许愈合破裂时依靠***金属杆、销或螺钉以保持骨头的结构的当前操作相比,其潜在地提供一种更有利的正骨技术。在这种情况下,半柔性结构49或许需要具有阀的口,以保持骨折愈合时结构的强度和刚度,但允许接近骨支撑材料83,以便以后抽空。在这种情况下,可密封端口32还提供了对导管67的再附着,以容许移除骨支撑材料83和使结构与骨头17分离。
选择骨支撑材料83的特性,使之在骨头愈合时呈现刚性或半刚性的状态,并且一旦愈合操作已经发展到不再需要内部支撑的程度,其能够从半柔性结构49分解、消融或其它取出。一旦骨支撑材料83从半柔性结构49抽空,那么结构49就可以从骨头脱离,以容许骨头17的最终愈合。半柔性结构49不同于金属杆或销的优点在于,当脱离时,它的柔性便于对松质骨17最低损伤地移除。
半柔性结构49可以由任何适宜的生物相容材料形成,例如,但不限于,不锈钢,钛,聚合物、例如诸如聚酯和聚乙烯的聚合材料和塑料,聚乳酸和这些聚合物彼此和其它单体的共聚物,再吸收合成材料、例如缝合材料,镍钛金属互化物,或者本领域技术人员所知的任何其它适宜的材料,包括这些材料的组合。优选地,半柔性结构49由生物相容的金属薄膜材料形成,其形状适当地设计成大体上符合或适合于所选择的用于治疗的骨头17的内部结构中限定的空腔74。镍和钛的合金,通常被称为镍钛金属互化物,非常适合于这个应用,因为它已证明的生物适应性和能够经受生物环境的腐蚀作用的能力。金属薄膜材料、尤其是镍钛金属互化物的其它所希望的性质是其超弹性和形状记忆能力,这便于将导管67***到松质骨17中限定的空腔74内。此外,镍钛金属互化物的应力-应变特性使其成为与骨支撑材料83共同提供对骨头17的附加结构性支撑的极好选择。
对于骨治疗包含结构49的永久放置,生物相容材料提供适当的表面处理,以提供用于结合和愈合松质骨17内部的骨亲和基体。在结构的植入是临时恢复测量的应用中,制备表面,以避免松质骨17与半柔性结构49的结合并减少两者的粘附,从而便于摆脱和最小化对松质骨组织17的损伤。
由于半柔性结构49的广泛应用,骨支撑材料83可包括根据治疗的原发用途选择的若干材料。在治疗针对永久骨支撑的情况,骨支撑材料83包括接合剂类材料,例如前述的PMMA配方设计,其可以作为液体、涂胶或凝胶注射,并且允许在短的时间内固化或***。因为接合剂类材料83容纳和保持在半柔性结构49内部,所以,更宽范围的接合剂类材料都是可以的,面对未包含的应用时,材料不会遇到相同的生物化学环境。
在治疗针对骨头17的临时支撑的情况,骨支撑材料83作为液体被注射,在需要支撑的时间期间仍然是液体,然后在操作已经完成时可以容易地抽出。在替换实施例中,骨支撑材料83可以是柔韧的胶状材料的形式,以提供对骨骼构造的支撑和能量衰减。
在疾病是骨折的贡献原因或原发原因的应用中,本发明的另一个目的构思是半柔性结构49充当治疗疾病的载体。在此构思的本发明的方面包括用于原发疾病状态的药物治疗、放射性治疗或热治疗。
在药物治疗方法的情况下,金属薄膜材料表面可以浸渍或涂敷以骨头本身内部的具体疾病状态为目标的定时释放的药物。作为选择,药物治疗也可以通过选择用于结构49的半渗透的生物相容材料扩散,以治疗骨头17的疾病或损伤。
在放射性治疗的情况下,放射性治疗通过将混合物导入半柔性结构49而与骨支撑材料83混合,以便它被容纳和保持在半柔性结构49内部。在这种情况下,在松质骨组织17已经适当暴露之后,放射性治疗可以从半柔性结构49取出。此外,由于本发明构思了结构49的临时植入,所以其也可以在放射性治疗期间或在完成所有的放射性操作之后更换。
在骨支撑材料83导入半柔性结构49内的第一种情况下,可以提供热治疗。骨支撑材料83的温度在导入半柔性结构49之前可以调节至所希望的水平。作为选择,也可以通过所选择的骨支撑材料83的催化反应获得适当的温度。骨组织17的再治疗可以通过后面的在此所述的所选择治疗方法的取出和再导入进行。
本领域技术人员应当明白,在不脱离主要发明构思的情况下,可以对如上所述的实施例作出各种变化。所以,应当理解,本发明不局限于公开的具体实施例,其意图是覆盖由附带的权利要求书所限定的本发明精神和范围之内的所有修改。
Claims (29)
1.一种治疗患病或损伤骨组织的方法,包括:
选择要治疗的骨组织中的内部区域;
将一装置***要治疗的骨组织的内部区域中;和
在治疗期间利用该装置在内部支撑骨组织。
2.如权利要求1所述的方法,还包括利用最小侵入图像引导技术选择内部区域。
3.如权利要求1所述的方法,其中,该装置是可更换的。
4.如权利要求3所述的方法,其中,该装置是具有能够支撑骨组织的结构的导管。
5.如权利要求4所述的方法,其中,导管包括可膨胀的三维半柔性结构和紧固件,并且紧固件将导管可释放地连接到半柔性结构上。
6.如权利要求5所述的方法,其中,导管可从半柔性结构上分离。
7.如权利要求6所述的方法,其中,导管具有限定至少一个贯穿的内部通道的主体,半柔性结构限定一内部空间,半柔性结构包括允许导管的内部通道与半柔性结构的内部空间之间连通的可密封端口。
8.如权利要求7所述的方法,还包括,通过导管内的通道将骨支撑材料注射到半柔性结构中,并通过可密封端口注射到该结构的内部空间中,从而膨胀骨组织内的三维半柔性结构。
9.如权利要求8所述的方法,其中,骨支撑材料能够***,以为骨组织提供永久骨支撑。
10.如权利要求8所述的方法,还包括:
将放射性治疗材料和骨支撑材料混合以形成混合物,将该混合物导入半柔性结构,其中半柔性结构能够便于将要治疗的区域暴露于放射性材料;和
暴露骨组织以放射性治疗。
11.如权利要求10所述的方法,还包括,当放射性治疗耗尽时,用第二、替换三维半柔性结构更换半柔性结构。
12.如权利要求10所述的方法,其中,放射性治疗是定时释放药物,药物可以渗出半柔性结构,并涂敷半柔性结构的表面。
13.如权利要求10所述的方法,其中,半柔性结构包括半渗透材料,药物通过半渗透材料扩散,以治疗疾病或损伤。
14.如权利要求13所述的方法,其中,半渗透材料选自包含聚合材料、再吸收合成材料、缝合材料、镍钛金属互化物及其组合的组。
15.如权利要求14所述的方法,其中,材料为生物相容的镍钛金属互化物。
16.如权利要求14所述的方法,其中,聚合材料选自包含聚酯、聚乙烯、聚乳酸及其组合的组。
17.如权利要求13所述的方法,其中,疾病或损伤选自包含骨质疏松症,骨质疏松破裂干骺端骨和骺骨,骨质疏松脊椎体,破裂骨质疏松脊椎体,由肿块、尤其是圆形单元肿块引起的脊椎体破裂,长骨骨端的无血管形成性坏死、近端股骨、远端股骨和/或近端肱骨的无血管形成性坏死,由内分泌情况引起的缺陷,转移性瘤,及其组合的组。
18.如权利要求8所述的方法,其中,半柔性结构可从导管上分离,所述方法还包括:
从半柔性结构分离导管;
密封可密封端口;和
在加压环境中将骨支撑材料保持在结构内,从而防止骨支撑材料从结构内流出,以提供对骨组织的临时支撑。
19.如权利要求8所述的方法,其中,骨支撑材料选自包含液体、涂胶、凝胶、接合剂及其组合的组。
20.如权利要求19所述的方法,其中,骨支撑材料是接合剂。
21.如权利要求20所述的方法,其中,接合剂包括选自聚甲基丙烯酸甲酯、右旋糖酐、聚乙烯、碳纤维、聚乙烯醇和多(对苯二甲酸亚乙酯)的组的材料。
22.如权利要求19所述的方法,其中,骨支撑材料是液体。
23.如权利要求18所述的方法,还包括:
将导管再附着到可密封端口上;和
抽出骨支撑材料。
24.一种用于治疗患病或损伤骨头的装置,包括:
导管,其中导管包括限定至少一个贯穿的内部通道的主体;
可膨胀的半柔性结构,其中半柔性结构限定一内部空间;和
可移除的紧固件,其中紧固件将导管可移除地连接到半柔性结构上。
25.如权利要求24所述的装置,还包括可密封端口,导管的内部通道通过所述可密封端口与半柔性结构的内部空间相连通。
26.如权利要求25所述的装置,其中,导管可从半柔性结构上分离。
27.如权利要求26所述的装置,其中,导管能够接收骨支撑材料。
28.如权利要求24所述的装置,其中,紧固件是螺旋装置。
29.如权利要求24所述的装置,其中,半柔性结构能够膨胀,以适应骨头中要治疗的区域。
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- 2006-01-06 AR ARP060100061A patent/AR055833A1/es unknown
- 2006-01-06 PE PE2006000048A patent/PE20060861A1/es not_active Application Discontinuation
- 2006-01-09 US US11/328,345 patent/US20060155296A1/en not_active Abandoned
- 2006-01-09 CA CA2592782A patent/CA2592782C/en active Active
- 2006-01-09 AU AU2006203902A patent/AU2006203902B2/en not_active Ceased
- 2006-01-09 EP EP06717700A patent/EP1833426A4/en not_active Withdrawn
- 2006-01-09 JP JP2007550516A patent/JP5159320B2/ja active Active
- 2006-01-09 TW TW095100736A patent/TW200640433A/zh unknown
- 2006-01-09 WO PCT/US2006/000534 patent/WO2006074410A2/en active Application Filing
- 2006-01-09 BR BRPI0606473-6A patent/BRPI0606473A2/pt not_active Application Discontinuation
- 2006-01-09 KR KR1020077015324A patent/KR101303583B1/ko active IP Right Grant
- 2006-01-09 CN CN2006800019105A patent/CN101123920B/zh not_active Expired - Fee Related
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CN107320146A (zh) * | 2011-01-17 | 2017-11-07 | 美它克医药公司 | 可脱离金属球囊递送装置和方法 |
CN108261250A (zh) * | 2016-12-30 | 2018-07-10 | 先健科技(深圳)有限公司 | 防内漏覆膜支架*** |
CN108261250B (zh) * | 2016-12-30 | 2019-12-10 | 先健科技(深圳)有限公司 | 防内漏覆膜支架*** |
Also Published As
Publication number | Publication date |
---|---|
AU2006203902B2 (en) | 2011-09-22 |
KR101303583B1 (ko) | 2013-09-11 |
AU2006203902A1 (en) | 2006-07-13 |
CN101123920B (zh) | 2012-09-26 |
WO2006074410A3 (en) | 2007-10-18 |
EP1833426A4 (en) | 2013-01-23 |
WO2006074410A2 (en) | 2006-07-13 |
BRPI0606473A2 (pt) | 2009-06-30 |
US20060155296A1 (en) | 2006-07-13 |
PE20060861A1 (es) | 2006-10-25 |
CA2592782A1 (en) | 2006-07-13 |
CA2592782C (en) | 2012-03-27 |
JP5159320B2 (ja) | 2013-03-06 |
KR20070114113A (ko) | 2007-11-29 |
EP1833426A2 (en) | 2007-09-19 |
AR055833A1 (es) | 2007-09-12 |
TW200640433A (en) | 2006-12-01 |
JP2008526372A (ja) | 2008-07-24 |
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