CN102239335A - 具有转子的流体泵 - Google Patents

具有转子的流体泵 Download PDF

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CN102239335A
CN102239335A CN2009801490081A CN200980149008A CN102239335A CN 102239335 A CN102239335 A CN 102239335A CN 2009801490081 A CN2009801490081 A CN 2009801490081A CN 200980149008 A CN200980149008 A CN 200980149008A CN 102239335 A CN102239335 A CN 102239335A
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rotor
blade
fluid pump
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CN102239335B (zh
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马里奥·谢科尔
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ECP Entwicklungs GmbH
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    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
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    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/13—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel by means of a catheter allowing explantation, e.g. catheter pumps temporarily introduced via the vascular system
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    • A—HUMAN NECESSITIES
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    • A61M60/237—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly axial components, e.g. axial flow pumps
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    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B63—SHIPS OR OTHER WATERBORNE VESSELS; RELATED EQUIPMENT
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    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
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    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/135—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
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    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B63—SHIPS OR OTHER WATERBORNE VESSELS; RELATED EQUIPMENT
    • B63H—MARINE PROPULSION OR STEERING
    • B63H1/00—Propulsive elements directly acting on water
    • B63H1/02—Propulsive elements directly acting on water of rotary type
    • B63H1/12—Propulsive elements directly acting on water of rotary type with rotation axis substantially in propulsive direction
    • B63H2001/122—Single or multiple threaded helicoidal screws, or the like, comprising foils extending over a substantial angle; Archimedean screws
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F05—INDEXING SCHEMES RELATING TO ENGINES OR PUMPS IN VARIOUS SUBCLASSES OF CLASSES F01-F04
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    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F05—INDEXING SCHEMES RELATING TO ENGINES OR PUMPS IN VARIOUS SUBCLASSES OF CLASSES F01-F04
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    • F05D2300/00—Materials; Properties thereof
    • F05D2300/50—Intrinsic material properties or characteristics
    • F05D2300/501—Elasticity
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F05—INDEXING SCHEMES RELATING TO ENGINES OR PUMPS IN VARIOUS SUBCLASSES OF CLASSES F01-F04
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    • F05D2300/505—Shape memory behaviour
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    • F05—INDEXING SCHEMES RELATING TO ENGINES OR PUMPS IN VARIOUS SUBCLASSES OF CLASSES F01-F04
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    • F05D2300/00—Materials; Properties thereof
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Abstract

本发明涉及一种流体泵，特别是用于输送流体的具有带至少一个转子叶片(20、21)的转子(18)的液体泵，转子在第一压缩状态和第二扩展状态之间其直径能变化。为了简单地产生泵的转子的可压缩性和可扩展性，根据本发明设置成，至少一个转子叶片在第一状态和第二状态之间能变形，在第一状态下，至少一个转子叶片呈现处于转子的压缩状态下，在第二状态下，至少一个转子叶片借助于在泵操作过程中转子转动期间的流体背压(23)而呈现处于转子的扩展状态下。

Description

具有转子的流体泵
本发明属于流体泵领域，并涉及一种泵，其转子直径可变，以能够被导引通过例如窄开口，譬如管，特别是血管，以及能够在被导引通过之后在扩展状态下操作。
本发明因此一方面可在医疗领域以微创方式例如作为血泵为心脏提供支持，然而，另一方面，在搅拌器中使用或用作船舶的推进元件也是可设想到的。
本发明由于可能的微型化而能够在医疗领域显示特别的优点。
在将流体泵通过大血管引入心室并随后在转子扩展后设置转子操作之后，可例如在人体中相当大地辅助心脏的泵血功率、或可部分地替换心脏的泵血功率。这种应用的治疗优点在于心脏肌肉的至少部分减负。
这种能扩展的流体泵已从现有技术中已知。例如，DE 10 059 714 C1公开一种泵，其可与泵驱动器一起被推动通过血管。血在那里流动通过插管，插管的直径可被扩展和压缩以改变流量比(flow ratio)。
从WO 03/103745 A2中已知一种血泵，其转子可被沿径向压缩和扩展，在该专利申请中建议了不同构造以实现可扩展性。例如借助于在引入之后导管的相互可移动的不同部件，可实现与此相关的泵壳体的压缩和径向变宽。另一方面，通过相对于位于导管内的线转动驱动轴，公开了产生线的螺旋结构的可能性，另外该线承载膜，该膜在呈现螺旋结构之后形成转子叶片。
另外，从该文献中已知具有多个本身是刚性并以可枢转方式铰接到中央部分上的叶片的转子结构，所述叶片在操作中展开并因此产生流体压力。
从EP 0 768 900 B1已知一种泵，其中转子叶片以如下方式铰接到泵壳体内的轴上，即它们可在不起作用的状态下合拢于轴，并在操作过程中可垂直于轴展开以输送流体。
从US 2006/0062672 A1已知一种流体泵的转子，所述转子具有叶片，所述叶片具有可挠曲地固定到毂部并借助于由转子初始转动而产生的流体背压而展开。
对已知现有技术而言，共同的是泵的转子叶片借助于枢转机构或者通过转动过程中的流体背压枢转而扩展、或者通过呈鲍登线方式的机械装置等形成以仅用于泵扩展。
在现有技术的背景上，本发明的目的是制造一种具有转子的流体泵，所述转子的直径可被压缩，其在结构方面尽可能简单地构造，其优选地包括与围绕转子的泵壳体类似的生物相容性材料，其壳体的扩展和压缩可被尽可能简单地实现并具有操作过程中必需的可靠性。
根据本发明，该目的由如权利要求1所述的特征实现。
另外，本发明涉及用于操作根据本发明的如权利要求16、17或18所述的流体泵的方法。
基于本发明的知识是可通过转子叶片本身的变形实现流体泵尽可能简单的结构。为此，流体泵的转子具有至少一个转子叶片，只要转子呈现第一压缩状态，所述至少一个转子叶片处于第一状态下，转子叶片在转子通过变形而转变到扩展状态的过程中呈现第二状态。
转子叶片由此通过在泵操作过程中在转子转动过程中出现的流体背压而从第一状态转变成第二状态。
本发明的特别优点在于：除了泵的实际驱动器外，不需要提供其它致动元件用于转子扩展之事实，以及由于转子叶片本身的可变形性，也不需要提供对泵的转子叶片或其它部件的以枢转方式的联接。
通过提供在输送操作过程中沿运动方向的叶片的工作侧和尾侧，便利并且同时也限定了叶片的变形，其中所述侧具有呈不同材料性质形式的不同构造和/或至少沿叶片的径向外末端与叶片的径向内端部之间距离的一部分的构造组件。
该限定应该因此有利地为采用了由于变形而允许最佳输送功率的转子形状。换言之，至少一个转子叶片的可变形性有利地以如下方式限定，即该变形不超过转子产生最大可能流体背压时的形状。
当流体泵被导引通过诸如血管的管时，没有外界影响转子也不会试图扩展。在医疗使用时不会期望这种试图，因为泵被导引通过的血管壁不应该被损坏。当施加通过管形人造通道(瓣膜)时，由于在人造管壁上将产生大摩擦力以及将需要显著大的力以将流体泵进给进本体内部，因此所述的恢复力将呈现特别大的困难。
只要泵不操作，即不在泵轴上转动，转子保持处于受压缩状态下，并可被进给通过血管。
如果泵被置于现场操作，则沿输送方向致动转子、以及转子叶片通过流体压力变形并因此被展开，其结果是实际大量的输送被设置成运行。如果转子叶片的变形是弹性的则是有利的，因为在很多应用情况下，流体泵必须在应用后再次被压缩以移出。
在这种情况下，在停止泵操作并停止转子之后，转子叶片再次呈现它们的第一状态，在该第一状态下转子被压缩。
通常，转子的在操作过程中在前的工作侧(高压侧)主要承受张力，而尾侧(吸引侧)承受压缩应力。工作侧和尾侧之间的界面可由此想象为在泵操作中呈现中性载荷之处。该界面必须吸收相应的横向的剪切应力。
可例如设置成，转子叶片的工作侧和尾侧在界面区域处彼此粘接，或者通过其它接合技术彼此连接。
对于本发明较为有利的转子叶片的性质例如可实现为至少一个转子叶片的工作侧包括第一材料且尾侧包括不同于第一材料的第二材料。两种材料均可为不同塑料，例如具有不同性质的聚合物，例如具有不同添加剂的不同塑料或它们中的一个由纤维增强。这些层之一——优选地在尾侧上——包括弹性体，且另一层包括聚合物，也是可以的。转子叶片也可由塑料材料形成的若干薄层制成，其中各层具有不同性质，例如第一层具有低参数，第二层具有高于第一层的参数，第三层具有高于第二层的参数等(该参数可为任何机械性质等)。如果这些层足够薄，关于叶片厚度的参数变化是(至少在宏观上)连续的。这种多个层可通过对每层喷射和/或喷溅等不同材料而制成。
证明了如果第一材料比第二材料易伸长，则是有利的。
第一材料应该由此具有固定伸长极限，使得在转子叶片变形过程中，在泵操作过程中实现尽可能精确限定的极限，并且在操作过程中设定该转子叶片的限定形状。这种固定伸长极限例如由材料的弹性系数的非线性范围提供，使得伸长所需的力从特定固定伸长极限超比例地(superproportionally)增加，且形状因此稳定。该性质可为第一材料固有的，但它可被辅助或大体产生，是因为将抗伸展纤维嵌入第一材料中，所述纤维比第一材料本身抗伸展性强得多，并且在转子叶片的第一状态下呈现未伸展，而在第一材料的第二状态下呈现伸展形式。这种纤维可例如由高强度塑料材料或玻璃或碳纤维形成。
位于转子叶片尾侧上的第二材料可为不能压缩的，或为仅能变形到特定压缩极限的。可变形性有利地为弹性。压缩极限可例如借助于压缩系数的非线性而形成，是因为压缩所需的力从特定压缩程度超比例地增加。
以下也可是有利的，如果提供位于工作侧上的第一材料层和位于尾侧上的第二材料层，其中第二材料层包括如下槽，所述槽容许所述第二层压缩至所述槽闭合的程度。
所述槽可与转子周向相切，以容许转子叶片沿着它们的径向长度弯曲。
也可有利地设置成，至少一个转子叶片在尾侧上具有成型元件，所述成型元件在第一状态下彼此间隔，而在第二状态下彼此抵靠。
这些成型元件可在第一状态下由槽缝彼此分离，或也嵌入能压缩材料中。它们以任何比率限定转子叶片的进一步可变形性，是因为它们在第二状态下彼此抵靠。
本发明的另一有利实施方式提供，至少一个止挡元件安装在至少一个转子叶片的一侧上，所述止挡元件穿过工作侧和尾侧之间的界面，并以有限方式在位于转子叶片另一侧上的凹槽内能移动。
止挡元件有利地由如下材料制成，所述材料与转子叶片的尾侧所包括的材料事实上一样不能压缩或精确地一样不能压缩，以实现有限的止挡位置。止挡元件可例如包括金属或硬塑料材料。
本发明除了流体泵外，还涉及一种用于操作上述形式的流体泵的方法，所述泵通过转子沿操作方向转动而起动，且转子通过流体背压而扩展。
另外也可设置成，为了减小转子直径，沿与操作方向相反的方向致动转子。
因此通过本发明而变得可行的是，当泵被导引通过开口时，特别是血管时，转子被沿与操作方向相反的方向致动并因此被压缩。
本发明也可包括：至少一个转子叶片包括用于最优化流体条件的至少一个翼板(参见图13/14，其中“W”指示翼板，“B”指示叶片)。图15示出一具有翼板“W’”的替代性实施方式，翼板“W’”仅位于叶片B’的工作侧上。
至少一个翼板自叶片的工作侧和/或自叶片的尾侧突伸，可为有利的。
通过将至少一个翼板定位于叶片末端，将转子与泵壳体内壁之间的流体条件最佳优化。这种翼板也可提供用于转子的轴承，只要在它在泵壳体内壁处滑行的范围内即可。然而，翼板也可设置在叶片的末端和径向内端部之间，在此处它们可影响流体流。
翼板可相对于叶片以可枢转方式固定，并可能通过在转子转动时产生的流体背压容易地枢转进它们的操作位置(参见图14和15)。
本发明也涉及一种用于制造如上所述的流体泵的方法。
本发明随后在参照实施方式的附图中例示并随后进行解释。
附图中：
图1示意性地示出流体泵在心脏中用于输送血的应用，
图2以纵剖图示意性地示出具有径向入流的泵头部，
图2a以纵剖图示意性地示出具有轴向入流的泵头部，
图3以平面图示意性地示出具有两个转子叶片的转子，
图4以侧视图示出转子，
图5示出贯穿转子叶片一部分的剖面图，
图6示出贯穿一不同实施方式中的转子叶片一部分的剖面图，
图7示出贯穿转子叶片一部分的剖面图，
图8示出图7中用VIII标示的细节的剖面放大图，
图9示出贯穿另一实施方式中的转子叶片的剖面图，
图10示出具有由成型元件支撑的螺旋形转子叶片的转子的一实施方式，
图11示出一转子，其螺旋形叶片由螺线形绕组支撑，
图12示出一转子，其螺旋形转子叶片由连接构件导引件支撑，
图13示出具有翼板的叶片的立体图，
图14示出图13的装置的剖视图，
图15示出叶片/翼板的一替代性设计的剖视图。
图1以剖视图示意性地示出心脏1，其中流体泵的头部3突伸进心室2。泵头部3设置在插管4的端部处，并具有在前部处圆化的泵壳体5。
泵的驱动借助于驱动轴6来实现，驱动轴6沿纵向延伸穿过插管4，并在外部连接到马达7。
可沿两个方向8、9致动马达7，而流体输送实际上仅沿一个转动方向进行。
在图2中以纵剖图示意性地示出具有泵壳体5的泵头部3、以及驱动轴6。驱动轴6在泵头部3的前端处借助于轴承11以可转动方式安装在轴承座10内。
图2示出呈扩展形式即相对于图1示图而言具有增大了的半径的泵头部。
为了将泵头部3穿过血管12引入心脏，通过使轴松弛(slack)或通过施加在轴上的轴向压力而沿径向压缩泵头部3，即使泵头部3处于其最小可能的径向伸长状态下。
如果泵头部已到达期望位置，则可通过沿箭头13方向施加张紧力而在轴向上一起拉曳泵壳体，因此泵壳体可沿径向扩展，如箭头14、15所示。
因壳体变形而引起的壳体压缩和扩展可想到通过利用形状记忆材料而实现。形状记忆材料在特定温度下的恢复原状性能因此得到利用。通过沿轴6的轴向延伸的槽缝16、17，流体——即本示例中的血——可通过泵壳体5朝泵的转子18流动，并可进一步输送通过转子18，例如沿轴向通过插管4。在图2中，转子的入流具有径向构造。在图2a中，示意性地呈现具有轴向入流和出流的一实施方式。
转子具有转子叶片载体19以及转子叶片20、21，在泵操作过程中即在转子的扩展状态下转子叶片20、21可折叠。
在转子扩展状态下，在操作过程中转子半径调整以适于泵壳体的内径。
如果泵头部意图移离心脏1，则泵操作停止，且转子叶片20、21抵靠转子叶片载体19以减小转子18的半径。这通过转子18沿与泵操作相反的转动方向转动而得到有利地辅助。
如果轴16以鲍登线方式朝泵头部3移动，则泵头部再次呈现其压缩形式并可移动通过血管12。
图3以平面图详细示出其上具有转子叶片载体19和转子叶片20、21的转子18，这些部件在它们的第一状态下即转子的压缩状态下以连续形状呈现。在第一状态下，转子叶片也可以紧密得多的方式抵靠转子叶片载体19。
重要的是，当泵操作和转子18的转动沿着输送操作所需的转动方向22起动时，沿朝向转子叶片的箭头23方向产生流体背压(fluid counterpressure)，且这些转子叶片由于扩大转子18半径而弯曲。如果泵设计为径向泵，则流体转移并因此沿箭头24方向沿径向向外输送。
如果转子叶片20、21沿轴向构形，则也可沿轴向输送流体，如图4中箭头25、26所标示的。
如果转子沿与输送所需的转动方向22相反的转动方向操作，则在转子叶片20、21上产生流体背压，所述背压与方向23反向，并引起转子叶片倚靠着转子叶片载体19折叠并引起转子直径相应的减小。在这种状态下，转子可随着相应压缩的泵壳体5穿过血管移出心脏。
通过选择转动方向和转动速度，一方面，转子直径因此可特定地改变，另一方面，泵的输送功率可按照期望调整。
图5举例示出具有在泵操作过程中在前的工作侧27以及尾侧28的转子叶片21，上述转子叶片沿着界面29在其两侧上具有不同性质。在操作过程中，流体背压沿箭头23方向作用在转子叶片上，并在转子扩展的第二状态下使转子叶片变形。为此目的，工作侧27必须能够在特定程度上伸长，且相应的第一材料层30具有为此原因的膜性质。该第一材料层可例如包括橡胶或弹性塑料材料，这些橡胶或弹性塑料材料能弹性变形至固定伸长极限并其后尽可能地抵抗进一步的伸长。
在尾侧21上，第二材料层31包括构造成例如如此硬以至于当力作用时仅发生最小程度的变形的抗压材料，使得借助于第一材料层30的伸长只能使转子叶片产生弯曲。
然而，可使第二材料层31具有一定程度的可压缩性。
图6示出适于转子叶片构造的另一示例，其中在第二材料层31中提供缺口32，这些缺口32容许尾侧压缩和弯曲，直到缺口32闭合且在这些缺口32之间所形成的各个片板以形状配合(form fit)方式彼此抵靠。在这种状态下，转子叶片的进一步弯曲将被阻止。
在这种情况下第二材料层31的材料可类似地为硬塑料材料，由这种硬塑料材料形成的部件以铸造或压印工艺被裁切或凹进。
并且，在这种情况下，第一材料层30的材料包括可在有限程度上伸长的材料。
在图7中，以剖面图呈现转子叶片，细节VIII在图8中更详细示出。细节VIII因此示出抗压第二材料层31a，抗压第二材料层31a就其而言具有三明治结构方式的多层构造，上述三明治结构包括抗拉伸和/或压缩外层33、34、35、36以及体积层(volumelayer)37。外层33、34、35、36可例如用纺织材料增强。
因此在尾侧上形成非常抗压的层，使得转子叶片的可变形能力基本上由工作侧27的伸长能力决定。
在图9中呈现一变型，其中止挡元件38例如借助于沉头螺钉39安装在第一材料层30内，止挡元件38突伸进第二层31的开口40。
如果转子叶片21变形，则第二材料层31内的开口40将趋于减小并移动，直到开口40的边缘抵靠止挡元件38为止。止挡元件包括与第二材料层31类似的硬材料，使得在抵靠之后，在尾侧上不可能有进一步的压缩，且桨形叶片(paddle blade)被增强以防进一步变形。
图10示出螺旋转子叶片，其中位于叶片尾侧上的一系列成型元件41、42彼此连接，例如粘接，或者以不同接合方法施加。在转子的压缩状态下，在这些成型元件之间分别存在间隔。在泵操作期间和展开叶片之后，这些成型元件彼此抵靠并增强为连续片板，上述连续片板支撑作为膜作用的叶片的平坦部件并阻止进一步变形。多个这种成行排列的成型元件可在轴向上沿着驱动轴6配置并沿角向偏移。
在图11中示出相似的构造，其中为加强转子叶片，由包括譬如包括塑料材料的线圈、弹簧丝或软管的绕组，来形成条板。各线圈分别形成一个成型元件，并通过粘接各自连接到转子叶片的类膜状表面。在转子压缩过程中，在叶片展开过程中绕组和开口之间的槽口闭合这些绕组和开口。为了稳定绕组，在绕组内提供连续核部，所述核部能够弯曲。
图12示出通过实心轨道/连接构件45提供对转子叶片的支撑，其中止挡元件以有限方式可移动。止挡元件连接到转子叶片。
轨道/连接构件45可构造为相对于按照期望作用的力和力矩而言抗弯和抗压的部件。在这种实施方式中，由于弯曲，产生了小的附加的恢复力。由于这种低材料厚度，就绝对方面，产生很小的恢复力。
在图12中，止挡元件位于下部位置。由于位于轴6上的连接构件收紧装置与位于轨道/连接构件45内的导引销的位置之间的小长度，向上弯曲到弯曲位置将需要在该位置施加较大作用力。
以上所述的转子叶片的构造仅是示例，借助于转子叶片的各侧的不同构造，能通过利用流体背压实现操作过程中的有限的可变形性。
在转子沿操作方向的反向转动的过程中，转子叶片的变形变得相反，且这些转子叶片抵靠转子，呈现第一状态并因此限定转子的压缩状态，在转子的压缩状态下，转子能容易地通过窄开口，例如血管或管形人造通道(瓣膜)。
因此，本发明容许以构造上特别简单的方式制造转子，上述转子的直径可改变以用于多种应用中，但特别有利地用于医疗领域。

Claims (29)

1.流体泵，特别是用于输送流体的具有带至少一个转子叶片(20、21)的转子(18)的液体泵，所述转子在第一压缩状态和第二扩展状态之间其直径能变化，其中所述至少一个转子叶片(20、21)在第一状态和第二状态之间能变形，在所述第一状态下，所述至少一个转子叶片(20、21)呈现处于所述转子的压缩状态下，在所述第二状态下，所述至少一个转子叶片(20、21)借助于在泵操作过程中转子转动期间的流体背压(23)而呈现处于所述转子的扩展状态下，其中所述至少一个转子叶片(20、21)具有在输送操作中沿运动方向的工作侧(27)和尾侧(28)，
其特征在于，所述侧具有呈不同材料性质形式的不同构造和/或至少沿所述叶片的径向外末端与所述叶片的径向内端部之间距离的一部分的构造组件。
2.如权利要求1所述的流体泵，其特征在于，所述至少一个转子叶片(20、21)能借助于所述流体背压(23)而弹性地变形。
3.如权利要求1或2所述的流体泵，其特征在于，所述至少一个转子叶片(20、21)的可变形性由材料性质和/或位于所述转子叶片一侧上的附加支撑元件限定。
4.如权利要求3所述的流体泵，其特征在于，所述至少一个转子叶片(20、21)的可变形性以如下方式限定，即所述变形不超出所述转子产生最大可能流体背压时的形状。
5.如权利要求4所述的流体泵，其特征在于，所述至少一个转子叶片(20、21)的工作侧(27)包括第一材料，所述尾侧(28)包括不同于所述第一材料的第二材料。
6.如权利要求4或5所述的流体泵，其特征在于，所述第一材料比所述第二材料更易伸长。
7.如权利要求6所述的流体泵，其特征在于，所述第一材料具有固定伸长极限。
8.如权利要求6或7所述的流体泵，其特征在于，纤维嵌入所述第一材料，并因此较大程度地比所述第一材料抗伸展。
9.如权利要求5或下述权利要求中之一所述的流体泵，其特征在于，所述第二材料是不能压缩的。
10.如权利要求5至9中任一项所述的流体泵，其特征在于，所述第二材料能被弹性压缩至压缩极限。
11.如权利要求5或下述权利要求中之一所述的流体泵，其特征在于，叶片包括位于所述工作侧的第一材料层和位于所述尾侧的第二材料层，以及所述第二层包括槽，所述槽容许所述第二层压缩至所述槽闭合的程度。
12.如权利要求1或下述权利要求中之一所述的流体泵，其特征在于，所述至少一个转子叶片(20、21)在其构造组件中包括位于所述尾侧(28)上的成型元件(31、41、42、43、44)或连接到成型元件，所述成型元件在所述第一状态下彼此间隔，而在所述第二状态下彼此抵靠。
13.如权利要求12所述的流体泵，其特征在于，所述成型元件(31、41、42、43、44)在所述第一状态下由槽缝(32)彼此分离。
14.如权利要求12或13所述的流体泵，其特征在于，所述成型元件(41、42)粘接或者通过其他接合方法施加在转子叶片的一侧特别是所述尾侧上。
15.如权利要求12、13或14所述的流体泵，其特征在于，所述成型元件(43、33)由绕组的各个线圈形成。
16.如权利要求12或下述权利要求中之一所述的流体泵，其特征在于，所述成型元件(31、41、42、43、44)嵌入到能压缩材料中。
17.如权利要求1或下述权利要求中之一所述的流体泵，其特征在于，至少一个止挡元件(38、39)安装在所述至少一个转子叶片的一侧上，所述至少一个止挡元件(38、39)穿过所述工作侧和所述尾侧之间的界面(29)，并能以有限的方式在所述转子叶片另一侧上在凹槽内移动。
18.如权利要求1或下述权利要求中之一所述的流体泵，其特征在于，所述至少一个转子叶片包括至少一个翼板。
19.如权利要求18所述的流体泵，其特征在于，所述至少一个翼板自所述叶片的工作侧突伸。
20.如权利要求18或19所述的流体泵，其特征在于，所述至少一个翼板自所述叶片的尾侧突伸。
21.如权利要求18、19或20所述的流体泵，其特征在于，所述至少一个翼板定位在所述叶片的末端处。
22.如权利要求17、18、19或20所述的流体泵，其特征在于，所述至少一个翼板相对于所述叶片能枢转。
23.如权利要求22所述的流体泵，其特征在于，所述至少一个能枢转翼板通过在转子转动时产生的流体压力而枢转到其操作位置。
24.制造如权利要求1至23之一所述的流体泵的方法，其特征在于，为了制造叶片，将两个不同材料层彼此固定到一起。
25.如权利要求24所述的制造流体泵的方法，其特征在于，将所述两个层彼此粘接或焊接到一起。
26.制造如权利要求1至23之一所述的流体泵的方法，其特征在于，为了制造叶片，将成型本体固定到层的一侧。
27.操作如权利要求1至23之一所述的流体泵的方法，其特征在于，所述泵通过所述转子(18)沿所述操作方向转动而起动，且所述转子通过流体背压(23)而扩展。
28.操作如权利要求1至15之一所述的流体泵的方法，其特征在于，为了减小转子半径，沿与操作方向相反的方向致动所述转子。
29.操作如权利要求1至23之一所述的流体泵的方法，其特征在于，当所述泵沿与操作方向相反的方向被导引通过开口、特别是血管或管形人造通道时，致动所述转子(18)。
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Publication number Priority date Publication date Assignee Title
CN108310496A (zh) * 2013-11-01 2018-07-24 Ecp发展有限责任公司 泵，特别是血液泵
CN108478891A (zh) * 2013-11-01 2018-09-04 Ecp发展有限责任公司 泵，特别是血液泵
CN108310496B (zh) * 2013-11-01 2021-06-25 Ecp发展有限责任公司 血液泵
US11679249B2 (en) 2013-11-01 2023-06-20 Ecp Entwicklungsgesellschaft Mbh Pump, in particular a blood pump
CN107530480A (zh) * 2015-04-30 2018-01-02 Ecp发展有限责任公司 用于流体泵的转子及其制造方法和模具
CN107548309A (zh) * 2015-04-30 2018-01-05 Ecp发展有限责任公司 用于流体泵的转子及其制造方法和模具
CN107530480B (zh) * 2015-04-30 2022-03-08 Ecp发展有限责任公司 用于流体泵的转子及其制造方法和模具
CN114470511A (zh) * 2015-04-30 2022-05-13 Ecp发展有限责任公司 用于流体泵的转子及其制造方法和模具
CN112399867A (zh) * 2018-07-30 2021-02-23 心血管系统股份有限公司 无诱导轮并且离心力驱动叶轮叶片的扩张的血管内泵和/或可扩张和可收缩的叶轮壳体

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US8721516B2 (en) 2014-05-13
US20150211542A1 (en) 2015-07-30
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US10662967B2 (en) 2020-05-26
US9964115B2 (en) 2018-05-08
EP3236079A1 (en) 2017-10-25
CN104141633B (zh) 2017-09-01
CA2745528C (en) 2022-03-08
US20140301822A1 (en) 2014-10-09
EP3825554A1 (en) 2021-05-26
US11852155B2 (en) 2023-12-26
EP2376788A1 (en) 2011-10-19
US20170356454A1 (en) 2017-12-14
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US10495101B2 (en) 2019-12-03
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US20110275884A1 (en) 2011-11-10
US20160106897A1 (en) 2016-04-21
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US20180291918A1 (en) 2018-10-11
HK1201899A1 (zh) 2015-09-11
EP2376788B1 (en) 2017-07-05
US8998792B2 (en) 2015-04-07
US9404505B2 (en) 2016-08-02
CN102239335B (zh) 2014-05-07
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US20240141913A1 (en) 2024-05-02
WO2010063494A1 (en) 2010-06-10

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