CN102348475A - 具有用于对柔性管进行再成形的机构的蠕动式输液泵 - Google Patents
具有用于对柔性管进行再成形的机构的蠕动式输液泵 Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- 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
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/14212—Pumping with an aspiration and an expulsion action
- A61M5/14228—Pumping with an aspiration and an expulsion action with linear peristaltic action, i.e. comprising at least three pressurising members or a helical member
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- 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
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
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- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/08—Machines, pumps, or pumping installations having flexible working members having tubular flexible members
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- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/08—Machines, pumps, or pumping installations having flexible working members having tubular flexible members
- F04B43/084—Machines, pumps, or pumping installations having flexible working members having tubular flexible members the tubular member being deformed by stretching or distortion
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- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/08—Machines, pumps, or pumping installations having flexible working members having tubular flexible members
- F04B43/09—Pumps having electric drive
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T137/00—Fluid handling
- Y10T137/8593—Systems
- Y10T137/85978—With pump
- Y10T137/85986—Pumped fluid control
Abstract
输液泵包括:具有输出轴的致动器;泵致动器,该泵致动器包括彼此铰接连接的多个构件(30a,30b,30c,30d)以便形成平行四边形结构,所述多个构件被铰接到输出轴,并且具有由输出轴移动的长度l致动器且与管道接触,使得在输出轴致动距离x处的泵致动器与管道产生平坦的接触区域,且其中管道的其余非接触区域为至少基本上圆形的形状;以及逻辑执行器,其配置为使用至少两个关系,以求解相同数量的变量,从而计算在输出轴致动距离x处管道的横截面积。
Description
技术领域
本公开内容涉及医疗设备且更具体地涉及输液泵。
背景技术
输液泵或管式泵常用于将药物或药剂注入患者。管式泵相比隔膜泵来说较简单。而且,管式泵直接用管道操作且不需要用一次性泵送盒或柔性隔膜来操作。一次性处理成本相应地被降低。此外,管道对于消毒和保持无菌来说相对简单。
管式泵的一个问题是精确度。蠕动管式泵的体积控制通常由对泵辊子对着抵住蠕动泵沟槽(race)装载的管旋转的次数进行计数和对每一转的体积进行假设而组成。假定的体积基于由泵辊子接触的管的内部体积。假定的一个问题在于在泵辊子通过之后管不被解压缩到其初始的解压缩形状。该问题通常随着时间推移而变糟糕,因为泵管材料由于泵管道的不断的压缩和解压缩而变得弹性越来越小。
因此,需要提供一种具有增加的精确度的输液或管式类型的医用流体泵。
发明内容
本公开内容的输液泵用于向患者施用液体药物或药剂。泵供应来自药物或药剂源的液体,并经导管或其他注射设备将药物输送到患者。输液泵控制液体药物被输注到患者的方式。泵具有各种输注模式,比如:(i)连续模式,在该连续模式中,泵以单一的流率输送单一体积;(ii)自动斜坡(ramp)模式,在该模式中泵以逐渐增加到阀值速率并在一定时间段内保持该阀值速率然后逐渐减小的速率输送液体药物;(iii)间歇模式,在该模式中泵在较长的时间段内隔开地输送离散的液体体积,比如每三小时输送一定的液体体积;(iv)定制模式,在该模式中泵可被编程为在离散的时间段输送独特的输液流率;以及(v)自控镇痛(“PCA”)模式,在该模式中泵响应于患者的要求而周期性地输送大剂量止痛剂。
本公开内容提供具有泵致动器的输液泵,泵致动器在泵入冲程时帮助管道恢复到完美的或几乎完美的圆形形状,以改进泵的整体效率和精确度。而且,在泵送期间管道形状变化可以理论上被建模,因此,泵送精确度能基于在泵送循环内的理论模型而被控制,这也改进泵送精确度。泵送精确度在需要非常低的流率时甚至可能是更关键的。在其他泵中,依赖于管道的回弹性来在解压缩时将管道恢复到其圆形形状。然而,有时,尤其是在重复使用之后,管道仅部分地恢复到其原始圆形形状。这导致不精确且不完全的泵填充。而且,一些泵致动器使管扭曲或产生扭矩,这能随着时间推移而使管永久地扭曲。
本致动器与包括上游和下游阀的输液泵一起操作。在泵入冲程时,上游阀被打开而下游阀被闭合。这里,泵致动器被致动以便将管道有效地带回到其初始打开的且完美(或几乎完美)的圆形形状,且这样做而不会使管道扭曲或对管道产生扭力。这允许泵的控制器或逻辑执行器精确地假定泵填充体积等于管道的内直径面积乘以管道的被压缩和解压缩的段的长度。
在泵出冲程时,阀状态被切换,使得入口阀或闭塞器被夹紧,而出口阀或闭塞器被打开。泵致动器压缩管道以将一定体积的流体推到患者。在泵出冲程结束时留在管道段中的流体体积(其最佳地为零)被从在泵入冲程结束时吸入的流体体积减去,其为该冲程输送到患者的流体的量。冲程的总数量乘以该体积提供在治疗或治疗的一部分期间输送到患者的总体积。泵入冲程和泵出冲程被定序的频率确定了医用流体被输送到患者的流率。本公开内容的泵致动器被配置成实际上完全地压缩管道,使得冲程结束时泵出的体积为零或实际上为零。
在一个主要实施方式中,泵致动器包括四个铰接构件,四个铰接构件经安装联接件而铰接在一起。安装联接件之一连接到线性致动器的输出轴。其余三个安装联接件各自包括滑动件,滑动件以滑动方式配合到输液泵的主体中形成的狭槽中。该布置允许泵致动器通过将输出轴拉入或将输出轴推出来压缩管道。输出轴随后分别被推出或拉入,以将管道带回到其初始圆形形状。在两种情形中,铰接构件在泵入冲程和泵出冲程期间引导管道,以便不依赖于管道的回弹性。
在第一实施例中,通过四个构件铰接所得的组件来安装管道,使得管经受压缩但不扭曲或不产生能使管道扭曲的类扭矩力。在机器主体内布置了位置传感器,例如,在接纳连接到联接件的滑动件的狭槽中,以便感测滑动件来检测泵填充和泵排出冲程结束位置。冲程结束传感器可以是接近传感器,当达到泵出或泵入冲程结束位置时,该传感器电感地或电容地感测滑动件之一。
在第二主要实施例中,泵致动器仍包括铰接在一起的四个铰接构件。这里,铰接构件直接铰接在一起,不需要第一主要实施例的连接的联接件和相关的滑动件。第一主要实施例包括八个铰接点(每个联接件两个),而第二主要实施例包括四个铰接点。在第二主要实施例中,代替允许滑动构件在形成在输液泵主体中的狭槽内滑动,铰接点(与连接到线性致动器输出轴的铰接点相对)经轴承而固定到机器主体。两个其余铰接点自由移动。在机器主体处,线性致动器使铰接构件从金刚石形状移动到压缩形状,且随后将铰接构件拉回到金刚石形状。管道因此被压缩,实际上被完全地压缩,且随后被拉回到实际的完美圆形形状,其改进了泵效率和精确度。再次,通过金刚石形状铰接构件结构来安装管道,使得力被压缩地施加,例如在输出轴的方向上施加;而不是以切向类扭矩的方式来施加,所述方式能使管道扭曲。冲程结束传感器被放置在合适的位置,以便感测泵致动器何时处于泵入冲程结束位置或者泵出冲程结束位置。
在第一和第二主要实施例中,管道的横截面积对于驱动泵致动器的线性致动器的任何位置是已知的。例如,经编码器或传感器反馈,线性致动器的位置在任何给定时间点都已知。第一关系基于泵致动器的铰接构件是刚性的且恒定的事实而形成。第二关系基于在未压缩位置的管道直径是已知的且恒定的事实而形成。第三关系基于在结构由于泵送而塌陷(collapse)时,管道在铰接构件结构内尽可能多地扩展的假设而形成。三个关系允许在任何给定的距离x处横截面积所需的三个变量可以被求解。瞬时横截面积的解乘以泵致动器长度l致动器,允许求解出瞬时体积。在时间上对流量进行求导生成了流率,且因而通过线性致动器移动分布图(profile)而产生流率的控制。该分布图可以被形成使得流率是恒定的,这是理想的。
因此,本公开内容的优点是提供改进的医用输液泵。
本公开内容的另一优点是提供具有在泵入冲程和泵出冲程中辅助管道的泵致动器的输液泵。
本公开内容的又一优点是提供具有泵致动器的输液泵,其具有增加的效率和精确度。
而且,本公开内容的优点是提供具有泵致动器的输液泵,其辅助使泵管道解压缩而不对管道提供扭曲或扭转力。
此外,本公开内容的优点是提供用于控制输液泵流率的系统和方法。
在本文还对额外的特征和优点进行了描述,并且其从详细说明和附图中将变得显而易见。
附图说明
图1是用于本公开内容的医用流体泵致动器和相关输液泵的阀和医用流体流布置的示意图。
图2A至2C是示出包括多个铰接构件和联接结构(lineage)的、本公开内容的输液泵的输液泵致动器的一个实施例的操作的侧视图。
图3A和3B示出用于图2A至2C的输液泵牵引器的流动精确建模。
图4A和4B是示出包括多个直接铰接的构件的、本公开内容的输液泵致动器的另一实施例的操作的侧视图。
图5是用于铰接本公开内容的输液泵的图4A和4B的泵致动器的构件的一个实施例的顶部平面图。
图6是沿图5的线VI-VI截取的剖视图。
具体实施方式
图2A-2C显示了一个优选实施例,其具有以下优点:(i)控制管形状,以及(ii)允许在泵冲程的给定点处泵送管道段内的面积/容积被建模(允许计算流体流率)。图4A和4B显示了另一实施例,其也具有以下优点:(i)控制管形状,以及(ii)允许在泵冲程的给定点处泵送管道段内的面积/容积被建模。图5和6显示了用于图4A和4B的实施例的合适的铰接布置。
现在参考附图,尤其是参考图1,其示出了输液泵10的示意性图示。泵10将药物或药剂从供应源70,通过管18,经患者导管或插管82而泵送到患者80。管18如所示被装载到输液泵10内,使得泵能将流体从供应源70推出并以受控的方式使流体流过管18、导管或插管82,流到患者80。输液泵10包括逻辑执行器12。逻辑执行器12包括一个或多个处理器,比如控制一个或多个授权处理器的管理处理器,授权处理器则控制输液泵10的各个方面。例如,逻辑执行器12可以利用安全或监控处理器,其确保管理处理器和授权控制处理器正确地操作。处理器利用同样作为逻辑执行器12的一部分的一个或多个存储器来进行操作。如所示,逻辑执行器12与用户界面14一起来进行操作,或控制用户界面14。用户界面14向患者或操作者显示信息,并且还允许患者或操作者将信息从用户界面输入逻辑执行器12。为此,用户界面14可以利用触摸屏覆层,或利用诸如膜片开关的一个或多个机电输入设备来进行操作。
用户界面14使操作者能够命令逻辑执行器12,以控制输液泵10从而可以运行:(i)连续模式,在该连续模式中,泵10经管道18输送液体从而以单一流率实现期望的体积;(ii)自动斜坡模式,在该模式中,输液泵10以逐渐增加到阀值、在规定时间内保持该阀值速率、然后逐渐减小的速率从供应源70输送液体;(iii)间歇模式,在该模式中,输液泵10在较长的时间段内间隔地输送离散的液体体积,比如每三小时一大剂量(bolus)或一体积;(iv)定制模式,在该模式中输液泵10以不同的时间间隔输送独特的输液流率;以及(v)自控镇痛(“PCA”)模式,在该模式中,患者80按压按钮,使输液泵10周期性地将大剂量止痛剂注入患者。
为了提供各种输送模式,逻辑执行器12操作上游阀或闭塞器16a、下游阀或闭塞器16b和泵致动器20或40,如下面详细描述的。为了泵送已知体积的药物或药剂,逻辑执行器使阀或闭塞器16a挤压或压缩阀致动器20或40上游的管道18。逻辑执行器12还使阀或闭塞器16b打开,且同时或稍后使阀致动器20或40中的一个压缩管道18,迫使已知体积的流体沿管道向下朝向导管或插管82和患者80。流体的已知体积通过泵致动器20或40的夹紧部分的长度l致动器乘以管道18的内面积来设定。
在药物或药剂体积被输送到患者80之后,逻辑执行器12使下游阀或闭塞器16b关闭,并同时或稍后打开阀16a,使来自供应源70的医用流体能与阀致动器20或40的入口流体连通。逻辑执行器12导致阀致动器使管道18解压缩,产生真空,这在阀致动器20或40的夹紧部分的长度L内,将药物或药剂吸入管道18。
逻辑执行器12重复上述阀定序和泵致动,直到期望的药物流体总量经导管或插管82而输送到患者80。总体积等于各个泵体积乘以序列的数量。阀16a和16b与泵致动组合来进行切换的速度设定药物或药剂被输送到患者80的流率。
现参考图2A至2C,图1描述的用于输液泵10的泵致动器的一个实施例由泵致动器20来示出。比如致动器40一样,泵致动器20有助于在泵入冲程时使管道18解压缩到完全且完整的圆形形状,增加了泵致动器的效率和精确度,并且因而导致增加了输液泵10的效率和精确度。也就是说,管道18被控制成在泵出和泵入冲程中都改变形状,以便不依赖用于泵入冲程的管道18的弹性或回弹性。管道18可以由聚氯乙烯(“PVC”)或合适的非PVC材料,比如有机硅来制成。尽管这些材料具有回弹性,但是如果仅由管道自身,则管道可能不恢复到其全形状。该问题随时间推移以及使用而变得糟糕。而且,泵致动器20中的管道18不被扭弯,而是其经正常力而压缩,使得在泵致动器内的管道18段不随时间推移而扭曲。
图2A至2C的泵致动器20包括可与输出轴24一起操作的线性致动器22,其收缩到线性致动器22内或被推出线性致动器22(l致动器方向为进入或离开页面)。在一个实施例中,线性致动器包括马达,比如步进马达、或DC刷式或无刷马达,其耦接到导螺杆(未显示)。输出轴24直接或间接地螺接到导螺杆上,且根据步进或DC马达旋转的方向而往返移动。
输出轴24则连接到马达联接件26。马达联接件26包括第一和第二铰接销28a和28b,第一和第二铰接销28a和28b被分别插入铰接构件30a和30b的开口的圆形端部。泵致动器20还包括滑动联接件32a至32c,滑动联接件32a至32c各自包括第一铰接销28a和28b。滑动联接件32a至32c各自还分别包括滑动件34a至34c,滑动件34a至34c以可滑动方式接收到输液泵10的外壳固定器或主体36中的狭槽内。滑动联接件32a和32c分别包括铰接销28b和28a,其与位于铰接构件30a和30b的相对端部处的开口的圆形端部铰接地连接。滑动联接件32a至32c的铰接销28a和28b分别安装到铰接构件30c和30d的第一开口圆形端部。滑动联接件32b同样包括铰接销28b和28a,其铰接地且分别连接到构件30c和30d的第二或下端开口的圆形端部,从而完成泵致动器20的封闭夹紧结构。轴24和滑动件34a至34c将构件30a至30d、马达联接件26及相关的滑动联接件32a至32c维持在固定的但可打开且可闭合的状态。
马达联接件26和滑动联接件32a至32c(包括滑动件34a至34c、构件30a至30d以及所有的相关的铰接销28a和28b,其可以由金属比如钢、不锈钢或铝、或硬塑料比如聚碳酸酯制成)。构件30a至30d、联接件26和32a至32c以及相关的铰接销28a和28b如图2A至2C所示,具有进入或离开页面的深度,其至少大体等于图1所示的致动器长度l致动器。滑动件34a至34d还可以具有这样的深度或是一系列钉(peg)或板。在优选实施例中,滑动件34a至34c的材料和输液泵10的限制器36的表面被制成为限制在限制器36与滑动件34a至34c之间的摩擦的量。
图2A显示了具有完全延伸的或膨胀的管18的泵致动器20。这是当泵致动器已经将一定体积的药物或药剂拉入管道的对应于铰接构件30a至30d等的致动器长度l致动器的段时,泵致动器的位置。
图2B显示的是线性致动器22能将输出轴24向外推以压缩管道18。可选择地,线性致动器22可以将输出轴24向内拉动以如图2C所示压缩管道18。图2B和2C显示了局部压缩的管道18。考虑到输出轴24进一步在图2B的向外方向以及在图2C的向内方向移动,使得管道18至少基本上被压平以获得每冲程最大量的输送,并为了精确和效率目的而尝试使管道段具有尽可能接近0的内体积。也就是说,在一个实施例中,逻辑执行器12假定保留在管道18的段l致动器中的液体的体积在泵出冲程结束时是0。逻辑执行器12还假定管道18的段l致动器在泵入冲程结束时是图2A所示的精确圆。泵致动器20的构件和联接件有助于确保这些假设尽可能正确。
考虑到在由输液泵10的限制器36限定的狭槽38a至38c内放置传感器,比如电感或电容式接近传感器,以便感测各个滑动件34a至34c的末端,从而检测泵致动器20的冲程结束。例如,在图2B中的滑动狭槽38a中放置第一传感器,以便当构件30a至30d已经完全压缩管道18时感测到滑动件34a。在感测到滑动件34a的时刻,传感器向逻辑执行器12发送信号,逻辑执行器12停止输出轴24从线性致动器20的再进一步向外移动。可选择地,在狭槽38b中放入比如接近传感器的传感器以感测当管道18在图2C中完全压缩时滑动件34b的末端。如果管道压缩如图2B被执行,则用于填充泵管18的冲程结束传感器被放入图2A的滑动器狭槽38b中以便当滑动件34b被向外推到管道18变成理想圆的点处时感测滑动件34b。另一方面,如果如图2C所示完成压缩,则当泵入冲程完成时,传感器被放入图2A的狭槽38a或38c中。
在可选的实施例中,以与上面类似的方式用传感器经滑动件34a至34c进行电开关接触,以表明泵出或泵入冲程的结束。在逻辑执行器12处感测接触的结束,逻辑执行器12随后停止用于该冲程的致动器22的任何进一步致动。在进一步可选的实施例中,在滑动件狭槽38a至38c内放入硬停止器,硬停止器在冲程结束位置停止滑动件34a至34c并因此停止构件30a至30d和相关的联接件。这里,马达电流引出随马达试图继续转动而增加。逻辑执行器12立即感测到马达电流引出的增加,并确定泵致动器20处于泵入或泵出冲程的结束处。
在又一可选实施例中,如果马达为电旋转马达,则马达能装配有编码器,编码器告知逻辑执行器12马达进行了多少转(或子转),使得逻辑执行器可确定致动器24和相关的构件30a至30d联接件32a至32d已经移动了多远。在此,可设置(一个或多个)传感器以设定(一个或多个)“原位(home)”位置,该“原位”位置重置编码器以开始泵入和泵出冲程的计数。
现参考图3A至3B,泵致动器20被建模以形成输出轴24和马达联接件26移动的距离x与角度“θ”之间的关系,角度“θ”是构件30a至30d中的任何一个和水平中心线CL之间的角度,如图2A至2C、3A和3B所示。在图3A中,每个构件30a至30d具有长度L。lc是与输出轴24和马达联接件26的致动器移动距离x相关的、管道18与构件30a至30d的内表面之间的接触长度。
管道18具有外半径R,在图3A中其导致等于2∏R的初始外横截面积S0。图3B显示了当管道18由于轴24/联接件26的移动x而被压缩时,角度θ从45°改变到较小的角度θ(x)。r1(x)和r2(x)是四个接触角部的切向曲线的半径,即,对于给定的行进距离x,管道18与构件30a至30d接触以及管道不与构件30a至30d接触之间的断点。图3B显示的是圆形外横截面积S0改变到S(x),S(x)是对于轴24/联接件26的任何移动x来说的管道18的外横截面积。注意,外横截面积(|S(x)-S(0)|减去管道厚度的面积的恒定横截面积S厚度)的变化乘以泵致动器20的长度l致动器等于每移动x所泵送的流体体积。,在轴24/联接件26已经行进x的、从t0开始到时间t的瞬时流率因而等于每时间的流动体积差或(|V(x)-V(0)|)/(t-t0)。
外横截面积S(x)被认为包括三个子面积的总和:(i)由四个接触长度lc限定的内(主)子面积,由r2(x)和四个半径r1(x)限定的两个楔周长;加(ii)作为r1(x)和θ(x)的函数的两个外(端)子面积。
(i)知晓或测量x;(ii)假定(a)长度L不改变(其是正确的,因为构件30a至30d是刚性的)且(b)管道18的非接触长度(限定在l1或l2内)总是保持圆形且变成与构件30a至30d相切;以及(iii)由已知的距离L和x计算角度θ,使得在求解S(x)中留下三个变量,即r1(x)、r2(x)和lc或接触长度。关于r1(x)、r2(x)和lc(x)的三个方程式因此允许对S(x)进行计算。
在第一方程式中,根据已知距离L和x,角度θ可以计算如下:
已知L=l1+lc+l2,且
l1=r1(x)ctgθ
l2=r2(x)tgθ;得到关于r1(x)、r2(x)和lc(x)的第一表达式,即
方程式1
r1(x)ctgθ+lc(x)+r2(x)tgθ=L
关于r1(x)、r2(x)和lc(x)的第二方程式由如图3A所示的非压缩条件下管道18的初始已知半径R推导出,
方程式2
2(∏-2θ)r1(x)+4lc(x)+2(2θ)r2(x)=2∏R
第三关系式通过假设在泵送期间管道横截面积(S(x))由于管道18的材料的弹性性能而总是保持可能最大值而得到。也就是说,管道将扩展以始终接触构件30a至30d的内表面积。管道将尝试占据构件内的尽可能多的面积。然后,在数学上,S(x)对x求导将等于0:
θ=arcsin(cos45°-x/L)
S(x)=(π-2θ)r1 2+2l(x)r1+(2θ-2tgθ/cos2θ)r2 2+(4Ltg2θ-2l(x)sin2θ)r2+2Ltgθ1(x)-2L2sin2θtgθ
方程式3
泵致动器20内侧的几何形状因此能通过利用上述三个方程式求解任何给定值x的lc(x)、r1(x)和r2(x),从而被建模,这又产生S(x)、ΔS(x)、Q(x)和q(x,t)。这对于“梭”式泵(例如,包围管道18以挤压来泵送的细长泵致动器20)是非常有用的,因为“梭”式泵的输出流率和体积经梭移动循环和循环的频率来计算。循环的频率可表示流率,例如,1ml/hr、100ml/hr或1200ml/hr。随流率增加,频率精确度变得更重要。
循环内或梭移动内的流动对于精确度是重要的,尤其是对于低流率应用而言是重要的。理想地,泵致动器20移动以产生线性泵送输出,使得循环内的输出流率能被控制为是恒定的。如果每个循环内的流率是恒定的,则总体流率应更接近恒定,从而改进总体精确度。如上所述,对梭式泵送期间管道的形状进行几何建模允许循环内流率被控制为恒定。
上述模型在逻辑执行器12内被储存并处理。逻辑执行器12进而控制到致动器22的电子信号,使得瞬时流率q(x,t)被控制为恒定。具体地,考虑建立移动信号分布图,其基于下一时间段的横截面积ΔS(x)的改变来改变下一时间段的Δx,以实现在不同时间段上恒定的瞬时流率q(x,t)。ΔS(x)通过如上所示建模来确定。
现参考图4A和4B,致动器40示出泵致动器的可选实施例。致动器40在某些方面类似于致动器20,即,其使用四个铰接构件46a至46d以按金刚石形方式围绕管道18的段l。因此,构件46a至46d具有如图1所示的长度l。泵致动器40还包括如上述的线性致动器22和输出轴24。
输出轴24连接到轴承固定件42,轴承固定件42又连接到第一铰接销44a。铰接构件46a至46d和铰接销44a至44d的实施例如图5和6所示。铰接销44a铰接地连接铰接构件46a和46b。铰接销46b铰接地连接铰接构件46a和46c。铰接销44d铰接地连接到铰接构件46b和46d。铰接构件46c和46d经轴承销44c铰接地连接,轴承销44c则连接到在狭槽38内滑动的构件34。
图4A显示了处于完全收缩的泵入冲程结束位置的泵致动器40。为了将流体推出管道18,线性致动器22使输出轴24朝向固定器36延伸,压缩管道18的段l,从而迫使液体穿过而朝向患者80。图4B显示了处于中间位置,靠近完全泵出冲程结束位置的泵致动器40。在此处,再次地,泵致动器40尝试尽可能在泵出冲程上使管道18变平,以便使每冲程的泵送效率最大化,并增加泵送精确度(假定在管道18的段l中冲程结束泵出体积为0)。如果泵致动器40在其能使管道18的段l变得多平方面受限,则计算泵出冲程结束的面积S1,且外推体积(S1×l)被用作泵出冲程结束体积而不是0。
在图2A至2C和图4A和4B中,管道18的中心保持固定,如所示。也就是说,中心不随输出轴24上下移动而上下移动,因为当相关输出轴24移动时,致动器20和40的构件34b和34分别在各自狭槽38b和38内移动。管道18的泵送部分基本上与管道的周围部分位于相同的线上,如图1所示。这是有优势的,因为在管道18上不产生弯矩,这可以影响精确度。
由致动器40移动的管道的循环内管道几何能以与上面所示的致动器20相同的方式通过逻辑执行器12建模和实现。这允许将循环内流率控制为常数。
现参考图5和6,所示的是铰接地连接铰接构件46a至46d的一个实施例。铰接销44a至44d按降序显示。相应的铰接构件对,即铰接件46b和46a、46a和46c、46c和46d以及46d和46b以降序相应显示。如图5所示,铰接构件46a至46d各自在槽口52处开槽,使得一对构件能在由如图6所示的圆形轭环(collar)54形成的对准孔处配合在一起,。
图6的圆形轭环54为46a、46c、46d和46b顺序的铰接构件而被示出。然而,从图5应理解,46a至46d的每个铰接构件包括一对圆形轭环,其中之一显示在铰接构件的左下角且其中另一个显示在铰接构件的右上角。也就是说,在观看图5时,铰接构件46b实际上显现两次,一次与铰接构件46a组合,且在第二情形与铰接构件46d组合。在图5中的元件编号的对或顶部梯级(rung)中,当铰接构件46b与铰接构件46a一起显现时,用于铰接构件46b的圆形轭环54在铰接构件的右手上角显现。当在图5的元件编号中的最后或最下一对中,铰接构件46b替换地与铰接构件46d耦接时,用于铰接构件46b的第二圆形轭环54在铰接构件46b的左手下角部显现。这些铰接构件46a至46d中的每一个包括圆形轭环54的交替模式,使得每个构件能被铰接在一起以形成能完全压缩以将液体推出段l的四面闭合形状(参见图6,其显示了表面1和2能向上弯曲以彼此匹配)。四面形状则能被打开以使管道18解压缩以将流体吸入管道18的该段l内。
从图6应理解,铰链轭环54中的弯曲被置于相对于表面1和2的构件46a至46d的外侧(如箭头所示,在其中构件被弯曲),这允许表面1和2彼此对着一起变平,使得泵出冲程体积非常接近零。图5还显示了铰接销44a至44d的端部能连接到轴承56a和56b,轴承56a和56b则固定到任一轴承固定件42或机器主体36,如图4A和4B所示。轴承56a和56b用帽更换(未显示),其防止如图4A和4B所见的铰接销44b和44d从相关的铰接构件的邻接圆形轭环54变松。
图5显示了特氟纶或其他塑料、或低摩擦材料垫圈58能被夹在匹配的圆形轭环54之间。例如,如果构件46a至46d是金属,则垫圈58防止金属-金属接触,从而有助于减小摩擦和噪音。还考虑了使槽口52延伸离开圆形轭环54,如图5所示,使得槽口52的边缘不摩擦轭环54,从而再次减小摩擦和噪音。同样,在实施例中,铰接销44a至44d由具有低摩擦系数的光滑外部的合适强度的材料制成。如果需要,铰接销44a至44d能用润滑剂涂覆或浸渍。
应理解,此处描述的目前优选实施例的各种改变和修改对本领域技术人员来说是明显的。在不偏离本发明主题的范围和精神以及不减弱其预期的优势的情况下能做出这样的改变和修改。因此预期这样的改变和修改将由所附权利要求所涵盖。
Claims (22)
1.一种输液泵(10),包括:
致动器(22),其具有输出轴(24);
多个构件(30,30b,30c,30d),其与所述输出轴(24)铰接连接,所述构件(30,30b,30c,30d)彼此铰接连接,使得在所述输出轴(24)致动距离x处,所述构件(30,30b,30c,30d)与插入所述构件(30,30b,30c,30d)内的管道(18)产生平坦的接触区域,且其中,所述管道(18)的其余非接触区域为至少基本上圆形的形状;以及
逻辑执行器(12),其被配置为使用在所述输出轴(24)致动距离x处所计算的所述管道(18)的横截面积来控制所述致动器(22),从而获取所期望的流率。
2.如权利要求1所述的输液泵(10),其中,被配置为使用在所述致动距离x处的所述管道(18)的计算的横截面积包括使用基于横截面积的预期改变来改变距离x的变化的移动分布图来获得所期望的流率。
3.如权利要求1或2所述的输液泵(10),其中,在已知在所述输出轴(24)致动距离x处所述构件(30,30b,30c,30d)之一相对于所述管道(18)的理论水平中心线的角度θ的情况下,执行所述管道(18)的横截面积的计算。
4.如权利要求3所述的输液泵(10),其中,在所述输出轴(24)致动距离x处的所述角度θ为每个构件(30,30b,30c,30d)所共有。
5.如权利要求1至4中任一项所述的输液泵(10),其中,在已知所述构件(30,30b,30c,30d)中的至少一个的长度的情况下,执行对所述管道(18)的横截面积的计算。
6.如权利要求1至5中任一项所述的输液泵(10),其中,在已知所述管道(18)的标定的未压缩的半径或直径的情况下,执行所述管道(18)的横截面积的计算。
7.如权利要求1至6中任一项所述的输液泵(10),其中,所计算的所述管道(18)的横截面积中已经从其去除了所述管道(18)的横截面厚度面积。
8.如权利要求1至7中任一项所述的输液泵(10),其中,所期望的流率是恒定流率。
9.如权利要求1至8中任一项所述的输液泵(10),其中,所期望的流率基于期望的体积变化,所述期望的体积变化基于所述管道(18)的横截面积的期望的变化乘以所述构件(30,30b,30c,30d)的恒定长度l致动器。
10.一种输液泵(10),包括:
致动器(22),其具有输出轴(24);
泵致动器(20,40),其具有由所述输出轴(24)移动的长度l致动 器,并且与管道(18)接触,使得在输出轴(24)致动距离x处的所述泵致动器(20,40)与所述管道(18)产生平坦的接触区域,且其中所述管道(18)的其余非接触区域为至少基本上圆形的形状;以及
逻辑执行器(12),其被配置为使用至少两个关系以求解相同数量的变量,从而计算在所述输出轴(24)致动距离x处所述管道(18)的横截面积。
11.如权利要求10所述的输液泵(10),所述逻辑执行器(12)进一步被配置为使用在输出轴(24)致动距离x处的所计算的所述管道(18)的横截面积来控制所述致动器(22),从而获取所期望的流率。
12.如权利要求10或11所述的输液泵(10),其中所述关系之一基于所述泵致动器(20,40)的至少一个构件(30a,30b,30c,30d,46a,46b,46c,46d)的恒定长度L。
13.如权利要求10至12中任一项所述的输液泵(10),其中,所述关系之一基于所述管道(18)的已知的未压缩半径。
14.一种输液泵(10),包括:
致动器(22),其具有输出轴(24);
第一构件和第二构件(30a,30b,46a,46b),其与所述输出轴(24)铰接连接;
第三构件(30c,46c),其与第一构件(30a,46a)铰接连接;
第四构件(30d,46d),其与第二构件(30b,46b)铰接连接;并且
第三构件(30c,46c)和第四构件(30d,46d)被机械地保持使得当所述致动器(22)在第一方向上致动时,延伸穿过所述构件(30a,30b,30c,30d,46a,46b,46c,46d)的管段(18)被压缩以从管段(18)推出流体,且当所述致动器(22)在第二方向上致动时,所述管段(18)被解压缩以将流体吸入所述管段(18)。
15.如权利要求14所述的输液泵(10),其中,所述致动器(22)在所述第一方向上延伸而在所述第二方向上收缩。
16.如权利要求14或15所述的输液泵(10),所述第一构件(30a)经滑动构件(34a)与所述第三构件(30c)铰接连接,所述滑动构件(34a)以可滑动方式保持在限制器(36)内。
17.如权利要求14至16中任一项所述的输液泵(10),所述第二构件(30b)经滑动构件(34c)与所述第四构件(30d)铰接连接,所述滑动构件(34c)以可滑动方式保持在限制器(36)内。
18.如权利要求14至17中任一项所述的输液泵(10),所述第三构件(30c,46c)与所述第四构件(30d,46d)铰接连接。
19.如权利要求18所述的输液泵(10),所述第三构件(30c,46c)经滑动构件(34b,34)与所述第四构件(30d,46d)铰接连接,所述滑动构件(34b,34)以可滑动方式保持在限制器(36)内。
20.如权利要求14至19中任一项所述的输液泵(10),其中,所述构件(30a,30b,30c,30d,46a,46b,46c,46d)具有深度,所述深度至少基本上限定所述管段(18)的长度。
21.如权利要求14、15、18、19或20中任一项所述的输液泵(10),其中,以下至少一个成立:(i)所述第三构件(46c)直接铰接到所述第一构件(46a),(ii)所述第四构件(46d)直接铰接到所述第二构件(46b),以及(iii)所述第三构件(46c)直接铰接到所述第四构件(46d)。
22.如权利要求14、15、18、19、20或21中任一项所述的输液泵(10),其中,所述第三构件(46c)在固定到限制器(36)的位置处直接铰接到所述第四构件(46d)。
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US12/402,255 | 2009-03-11 | ||
US12/402,255 US8137083B2 (en) | 2009-03-11 | 2009-03-11 | Infusion pump actuators, system and method for controlling medical fluid flowrate |
PCT/US2010/026945 WO2010120416A1 (en) | 2009-03-11 | 2010-03-11 | Peristaltic infusion pump having mechanism for reshaping the flexible tube |
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- 2010-03-11 MX MX2011009516A patent/MX2011009516A/es not_active Application Discontinuation
- 2010-03-11 CN CN2010800117091A patent/CN102348475A/zh active Pending
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- 2010-03-11 KR KR1020117022826A patent/KR20110129933A/ko not_active Application Discontinuation
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Also Published As
Publication number | Publication date |
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KR20110129933A (ko) | 2011-12-02 |
US20100229978A1 (en) | 2010-09-16 |
MX2011009516A (es) | 2011-11-18 |
WO2010120416A1 (en) | 2010-10-21 |
CA2754911A1 (en) | 2010-10-21 |
EP2408492A1 (en) | 2012-01-25 |
US8137083B2 (en) | 2012-03-20 |
JP2012520139A (ja) | 2012-09-06 |
BRPI1011695A2 (pt) | 2016-03-22 |
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