CN1874821B - 用于控制搏动心脏辅助装置的操作的方法和装置 - Google Patents

用于控制搏动心脏辅助装置的操作的方法和装置 Download PDF

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CN1874821B
CN1874821B CN200480032592XA CN200480032592A CN1874821B CN 1874821 B CN1874821 B CN 1874821B CN 200480032592X A CN200480032592X A CN 200480032592XA CN 200480032592 A CN200480032592 A CN 200480032592A CN 1874821 B CN1874821 B CN 1874821B
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heart
digital signal
transmitter
signal processor
assist device
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CN1874821A (zh
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威廉·S·彼得斯
罗德尼·G·帕金
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Sunshine Heart Co Pty Ltd
Nuwellis Inc
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Abstract

一种控制病人(10)中的搏动心脏辅助装置(14)的操作的方法。该方法包括利用由心脏(12)产生的声音控制心脏辅助装置(14)的操作。

Description

用于控制搏动心脏辅助装置的操作的方法和装置
技术领域
本发明涉及控制搏动心脏辅助装置或心脏起搏器的操作的方法和装置。 
本发明主要被开发用于控制主动脉外反搏心脏辅助装置的操作，例如本申请人的名称为“心脏辅助装置、系统和方法”的国际PCT专利申请No.PCT/AU00/00654所公开的内容。不过，本发明也适于使用在控制其他心脏辅助装置，包括但不局限于，主动脉内气球反搏、动脉肌成形术、反和共搏装置、或心脏起搏器或去纤颤器或者左心室辅助装置或心脏循环监控。 
背景技术
反搏心脏辅助装置必需被控制以随着病人心脏的搏动按照预定时间关系进行操作。例如，公开于申请人上述PCT专利申请中的反搏心脏辅助装置用于与舒张期同步压缩主动脉，开始时间由主动脉瓣的关闭(产生已知为第二心音的可听声，或S2)进行标记，以减小舒张期过程中的主动脉的内部容积。该压缩可增加全身血压，增加通过冠状动脉的血液流动并且增加关闭的主动脉瓣的舒张输出。主动脉的压缩与主动脉压缩的周期性撤消(withdrawl)进行交换，按照公知为收缩前期的僧帽状和三尖瓣阀关闭(可听见地，第一心音，或S1)和主动脉瓣开启的时间(标记心脏收缩的开始)遵循ECG(表示心室去极化)的R波，从而允许主动脉返回至其正常内部容积。当心脏首先从左心室喷出血液时，该主动脉压缩的撤消使心脏负担减小，从而使心脏可更容易地从左心室喷血。该装置关联于R波或检测到的第一心音(S1)的放气(deflation)时间，以及关联于第二心音(S2)的进气(inflation)可根据特定病人的生理系统进行变化。 
本领域技术人员可知，由反搏心脏辅助装置提供的心脏辅助的程度取决于主动脉相对于本人心脏的压缩和解压的精确定时。在本发明关于心脏共搏动的实施例中，心脏压缩的定时必需调整至本人的节律。 
目前的装置依赖ECG，尤其是R波，从而定时套箍(cuff)的放气，并且套箍的进气可被定时至主动脉压力图线的二向性切迹，其表示主动脉瓣的 关闭。该方法由于下述原因而被严格地局限在控制心脏辅助装置等的应用中： 
1.ECG可良好地表示心室收缩的开始，但是无法表示心脏收缩的结束。此外，当T波表示心室的再极化时，其底部过宽并且用于定时目的不很精确； 
2.全身动脉血压可非常好地突出表示主动脉瓣关闭的时间，但是仅可以经由经皮动脉线进行临时使用，并不适于长期使用； 
3.动脉压力波形关联于由动脉瓣测量的更末梢的动脉压力，但是被延迟，并且无法精确地描述动脉瓣关闭的时间；并且 
4.随着心率的变化(尤其是如果病人突然进行锻炼，或者焦虑，或者节律处于心室纤维颤动，或者依赖心肌的收缩性状态等)，ECG的R波之后的动脉瓣的开启和关闭时间会明显变化，因此，当心脏收缩的开始可被相对安全地定时(并且气囊放气被开始)时，心脏舒张的开始定时在ECG单独的情况下是不可能的。 
不存在可靠和精确的方法以按照允许病人佩戴装置同时享受美好人生的方式长期详细地确定动脉瓣关闭的时间。 
转让给L.Vad Technology，Inc.的美国专利No.5,904,666和No.6,042,532中公开了下述方法，该方法通过测量主动脉压力图线的二向性切迹每两至三分钟转换动脉压力波形。不过，这需要装置功能性地每两至三分钟暂停以进行测量。这无法精确控制装置的功能适应特定的心脏跳动，并且在每两分钟内定时被设定，直到重新进行测量。而且，二向性切迹不可能总会被检测到。 
另一个与用于部分地控制可植入心脏辅助装置(即，具有外部驱动器/控制器)的部件相关联的问题在于，任何经皮管或线的尺寸、数量和硬度必需保持在最小，从而减小感染的机会并且增加装置的心理承受性。这可通过使用心动周期定时信号的无线传送而实现。不过，与心脏起搏器相关联的无线遥测通常是私人所有的，并且不必要的复杂，无法适合连续离散的信号输出。 
本发明的目的是提供一种通过使用检测到的心音确定并且调整反搏进气时间的方法和装置。在优选实施例中，心音被实时监控，从而为每个特定 心动周期形成精确的每次跳动的反搏定时，而不功能性地中断心脏辅助。心音也可间歇地、或者以固定的时间间隔、或者在心率中出现持续的变化时用于确定并且重设R波气球放气或进气之间的间隔。 
另一目的是至少在优选实施例中简单和经济地向外部装置提供检测到的信号的无线遥测。 
发明内容
在第一方面，本发明提供了一种控制病人体中的搏动心脏辅助装置的操作的方法，该搏动心脏辅助装置包括主动脉外气球泵，该主动脉外气球泵包括：泵；具有内腔的主动脉外气球；和从泵导引至主动脉外气球的流体管线，该方法包括使用心脏产生的声音控制所述心脏辅助装置的操作，用位于主动脉外气球的内腔中或位于导引至主动脉外气球的流体管线中的声音检测装置检测所述声音。 
优选地，本发明使用R波检测和心音检测的结合以控制心脏辅助装置的操作。或者，心脏辅助装置可通过利用心音S1和S2两者被完全控制从而停止和起动心脏辅助装置。 
在第二方面，本发明提供了一种控制病人体中的搏动心脏辅助装置的操作的方法，包括以电的方式检测病人心脏节律的R波并且产生信号以开始所述心脏辅助装置的搏动状态中的变化，并且检测由病人主动脉瓣的关闭产生的声音或压力波，并且产生信号从而使所述心脏辅助装置返回至其在上一个R波之前所具有的搏动状态。 
在第三方面，本发明提供了一种使用多通道数字信号处理器和发送器(DSPT)控制搏动心脏辅助装置的操作的方法， 
所述DSPT属于具有心电图(ECG)通道和心音图(PCG)通道的类型，所述DSPT至少适于正常地通过所述ECG通道传感表示心脏节律的电信号，正常地通过所述PCG通道传感心音，并且将信号发送至外部接收器， 
所述方法包括下述步骤： 
将所述DSPT双极ECG引线可操作地连接至病人的心脏；并且 
将所述DSPT麦克风可操作地连接至病人的心脏， 
由此，在经由所述ECG通道检测到R波之后，所述DSPT将R波信号发送至所述心脏辅助装置控制器从而控制所述心脏辅助装置的搏动的定时，并且 
由此，在经由所述PCG通道检测到心音之后，所述DSPT将心音信号 发送至所述心脏辅助装置控制器从而控制所述心脏辅助装置的搏动的定时。 
DSPT优选地适于正常地通过PCG通道传感20-500Hz范围内的心音。 
DSPT优选地能够接收和发送，更优选地，具有在范围内调整的参数设置，用于检测所述R波和心音，并且用于检测所述输出信号。 
连接于所述病人心脏的所述ECG引线处于心外膜或心内膜或者连接于植入心脏辅助装置本身。在另一实施例中，用于收集ECG信号的传感器嵌入心脏辅助装置的表面内，该装置应用于病人身体的心脏或另一部分，ECG信号从其中接收。 
DSPT麦克风可以在病人身体内部。在这种情况下，至病人心脏的连接处于心外膜或心内膜，采用起搏器电极线的方式，或者附着于所述植入装置本身，并且，在该实施例中，优选地位于所述心脏瓣膜的50mm范围内，或者更优选地，肺部不在所述麦克风与病人心脏之间。 
可选择地，麦克风位于病人体外。控制外部气体驱动的主动脉外气球泵的心音和ECG可以利用位于所述主动脉外气球的内腔或导引至主动脉外气球的气体管线中的外部麦克风。植入的气体管线和气球作为非常有效的“听诊器”，并且心音可被间歇地或连续地检测到，并且直接发送至位于病人体外的控制器。类似地，代替需要植入信号处理器和发送器，经皮ECG引线可直接将ECG信号发送至所述控制器。ECG引线可以与所述经皮气体管线相结合，或者可与所述经皮气体管线分离开。在任一实施例中，优选的是，具有用于皮肤下的经皮气体管线和ECG引线的可释放和可密封连接，从而在感染或没有使用的情况下可移除经皮线，同时使气体管线和ECG引线植入以在以后需要的情况下重新连接。 
DSPT优选地能够接收外部装置的信号，从而调节在用于检测R波和心音的DSPT中的数字信号处理变量。 
优选地，DSPT具有寿命足够长的电池，以使所述DSPT可独立于心脏传感引线而被移除和替换，或者DSPT具有可充电电池，其可通过感应或者经皮能量传送(TET)进行充电。 
而且，DSPT可以与植入控制器直接通信，诸如与植入的电液压主动脉外气球泵(EABi)协作-所述控制器和所述ECG和麦克风包含在所述泵中以限制对于任何引线的需要，并且所述泵按照要求定位于中右胸腔，并且所述泵的一个方面(包含密封麦克风和ECG电极)与所述右心脏结构相对。 
在第四方面，本发明提供了一种用于控制搏动心脏辅助装置的操作的双通道数字信号处理器和发送器(DSPT)，所述DSPT属于具有ECG通道和心音图(PCG)通道的类型，所述DSPT至少适于正常地通过所述ECG通道传感表示心脏节律的电信号，正常地通过所述PCG通道传感心音，并且将信号发送至外部接收器，从而控制所述心脏辅助装置的搏动的定时。可替换地信号可以直接发送至植入的控制器。 
DSPT优选地适于通过PCG通道正常传感在20-500Hz范围中的心音。 
DSPT优选地能够接收以及发送。更优选地，DSPT具有可在范围内调整的参数设置，用于检测所述R波和心音，并且用于检测所述输出信号。 
DSPT可以具有其他通道，用于检测主动脉和左心室的血压以及主动脉和心室壁的运动，来自这些通道的信号也可以被解读以控制心脏辅助装置的功能。 
心脏辅助装置可以是共搏装置(诸如LVAD或心脏压缩装置)，在这种情况下，搏动与心脏本身的节律同步，或者其可以是反搏装置，其中搏动与心脏本身的节律异相。在前一结构中，心脏辅助装置可以施加心脏本身的搏动压缩。在后一结构中，心脏辅助装置可以适于通过血管外部的压缩或者通过使管腔内装置扩张并且由此使血容量移动以及全身动脉系统压力变化从而向血管施加搏动压力。 
在第五方面，本发明提供一种用于控制共搏或反搏心脏辅助装置的装置，所述装置包括： 
共搏或反搏心脏装置； 
用于所述心脏辅助装置的控制器；和 
数字信号处理器和发送器(DSPT)至少适于通过心电图(ECG)通道正常地传感表示心节律的电信号并且通过PCG通道传感表示心音S1和/或S2的声音信号，并且向所述控制器发送可识别的信号，其中，所述DSPT设置成在主动脉电路不能传感病人心室的节律信号的情况下、以低于生理感觉速率的最小速率发送来自心室电路的起搏信号，所述控制器被设置成在所述控制器从所述DSPT接收的起搏信号处于低于预定速率的速率下的情况下关闭所述心脏辅助装置，所述预定速率高于最小速率。 
通过采用这种方法，如果控制器没有传感到任何信号，那么就意味着控制器与DSPT失去连接或者DSPT或控制器电池耗尽。由于后一种情况一般会被容易地检测到，所以前一种的信号缺少的原因通常可被迅速识别。可选择地，如果信号变为最小速率，此时装置将会已经停止，那么就表明在起搏器电极线中或心脏起搏器中出现错误状况，或者病人已经死亡。 
故障的原因的快速隔离有助于快速校正导致出现故障的情况。在病人死亡的情况下，可防止心脏辅助装置在病人死亡后继续运行。 
DSPT优选地适于通过PCG通道正常传感在20-500Hz范围中的心音。 
DSPT优选地能够接收以及发送，更优选地，DSPT具有在范围内调整的参数设置，用于检测所述R波和心音，并且用于检测所述输出信号。 
本方法优选地包括将DSPT植入在胸部三角区或腹部上方的肩部前方的皮肤下。 
附图说明
本发明的优选形式将通过实例并且参照附图进行描述，其中： 
图1是带有按照本发明第一实施例控制的心脏辅助装置的病人的剖视图； 
图2是带有按照本发明第二实施例控制的心脏辅助装置的病人的剖视图； 
图3是带有按照本发明第三实施例控制的心脏辅助装置的病人的剖视图；和 
图4是带有按照本发明第四实施例控制的心脏辅助装置的病人的剖视图；其中，局部地示出包括DSPT和泵以及控制器的外部安装壳。 
具体实施方式
根据背景，DSPT具有传感、发送的功能和可编程性。 
传感是检测并且解读病人本身心脏的心电图和心音图(分别为ECG的和PCG的)的能力。植入的传感引线检测病人本身的心脏电活动并且将其发送至DSPT电路。DSPT单元中的固件和/或软件解读病人的R波并且发送表示R波检测的信号。植入麦克风引线检测病人本身的心音并且将其发送至DSPT电路。DSPT单元中的固件和/或软件解读病人的心音并且发送表示S1和S2检测的信号。 
可编程性是允许医生按照病人个人的需要调整DSPT的传感和发送功能的能力。这是通过使用膝上型装置实现的，一般称为编程器，其具有位于病人的植入DSPT附近的皮肤上的输入装置。该编程器使用听觉(音调)或电磁脉冲透过皮肤与病人的DSPT通信，并允许医生按照需要调整DSPT的设置。 
ECG传感系统预期能够在具有双室心脏起搏器的情况下工作，该起搏器对病人的节律进行控制，因为他们本身的节律可能会不足或者缺乏。 
结合的心脏起搏器和内心脏电复律器/)去纤颤器(ICD)可在检测到心室性心动过速或VF时或者尝试“过激励”起搏病人的节律(即，以强脉冲起搏，使过激励病人本身的节律，然后缓慢降低比例以控制病人的节律)或者使心脏休克失去节律然后进行起搏。 
现在降参照图1描述本发明的第一实施例，该实施例示出了病人10和心脏12。心脏12的输出由搏动的、完全可植入的心脏辅助装置辅助，该装置一般由附图标记14表示。心脏辅助装置14在病人的升主动脉周围具有主动脉套箍16。套箍16基本上与申请人在先引用的国际PCT专利申请No.PCT/AU00/00654中的相同。套箍16由泵18驱动，该泵基本上与申请人的名称为“流体压力产生装置”的国际PCT专利申请No.PCT/AU02/00974中的相同。植入的DSPT 20也示出。泵18由外部电池/控制器22经由经皮电缆24提供动力/进行控制。DSPT 20向心脏辅助装置14的控制器22发送RF信号。 
DSPT 20具有连接于传感引线26的ECG通道和连接于麦克风引线28的PCG通道。 
DSPT ECG通道经由传感引线26连接于病人心脏12的心室的心外膜表面，并且DSPT ECG通道经由麦克风引线28连接于植入主动脉瓣附近主动脉根部之外的麦克风30。 
在运行过程中，DSPT 20检测通过ECG通道的R波(即，心室的R波)，然后等待预定时间(例如，0-30msec)之后将信号发送至控制器22，该控制器然后控制心脏辅助装置14的搏动。应该理解，在上述结构中，DSPT 20总是将信号发送至控制器22并且控制器可以根据接收该信号时将要采取的动作进行编程。如果需要的话，DSPT 20可在接收ECG通道中的传感信号时立刻从ECG通道发送信号。在这种情况下，可在控制器22中编入可变延迟从而确保心脏辅助装置14被致动的时间对该具体病人来说是正确定时的。 
而且，DSPT 20被设计成即使在存在电或压力或其他噪声干扰的情况下校正心脏活动的传感。其也设计成可无损害地经受去心脏纤颤脉冲。 
在所示的优选实施方式中，心脏辅助装置14是反搏装置，其中搏动与心脏本身的节律异相。 
控制器22用于在从心室电路中接收的起搏信号低于最小速率之下的速率情况下，例如每分钟40次跳动，关闭心脏辅助装置。如果控制器22示出其没有接收到任何起搏信号，那么这一般表示DSPT 20没有发送至控制器22或者DSPT 20或者其引线26或28的总体故障。 
下面将参照图2描述本发明的第二实施例，其中与第一实施例类似的部件将使用类似的附图标记表示。图2示出了病人10和心脏12。心脏12的输出由搏动的、部分可植入的心脏辅助装置辅助，该装置一般由附图标记14表示。心脏辅助装置14在病人的升主动脉周围具有主动脉套箍16。套箍16基本上与申请人在先提到的国际PCT专利申请中的相同。套箍16经由经皮气体管线23由外部泵和控制器22驱动。这些类型的泵和控制器对本领域技术人员来说是公知的并且不会在这里进行进一步地描述。电池(未示出)也安装在泵和控制器22的壳中。 
同样示出的是DSPT 20，其具有连接于传感引线26的ECG通道和连接于麦克风引线28的PCG通道。DSPT向心脏辅助装置14的控制器22发送信号。 
DSPT ECG通道经由传感引线26连接于病人心脏12的心室的心脏内表面，并且DSPT ECG通道经由麦克风引线28也经由心内膜连接于植入主动脉瓣附近的麦克风30。这些引线可经由锁骨下动脉或颈静脉放置并位于右心室内，或在右心房或在右室或在冠状穴中。 
在运行过程中，DSPT 20通过ECG通道检测R波(即，心室的R波)，然后等待预定时间(例如，0-30msec)之后将信号发送至控制器22，该控制器然后控制心脏辅助装置14的搏动。应该理解，在上述结构中，DSPT 20总是将信号发送至控制器22并且控制器可以根据接收该信号时将要采取的动作进行编程。如果需要的话，DSPT 20可在接收ECG通道中的传感信号时立刻从ECG通道发送信号。在这种情况下，可在控制器22中编入可变延迟从而确保心脏辅助装置14被致动的时间对该病人来说是正确定时的。 
DSPT 20植入皮肤下，优选地在肩部之前，在胸部三角区域，或者在腹部上的皮肤下。该位置使容易地定位电池充电线圈或编程器“读入器”(未示出)。 
下面将参照图3描述本发明的第三实施例，其中与第二实施例类似的部件将使用类似的附图标记表示。第三实施例与第二实施例非常类似并且操作 也类似，除了麦克风30在气体管线23中检测心音以及外部控制器22向植入DSPT 20的PCG通道发送对应的信号。 
下面将参照图4描述本发明的第四实施例，其中与第三实施例类似的部件将使用类似的附图标记表示。第四实施例与第三实施例非常类似，除了心脏辅助装置14仅使用由麦克风30检测到的气体管线23中的心音进行控制。(即，没有监控ECG信号)。在该实施例中，麦克风30位于外部定位的外壳32内，该外壳也包含泵和控制器22以及DSPT 20。麦克风30与气体管线23直接连通，气体管线用做“听诊器”，将心脏12的声音发送到外部安装的麦克风30。在运行过程中，随着主动脉瓣开启并且DSPT向控制器和泵22发送表示该接收的信号，麦克风30接收S1声音。心脏辅助装置14在接收到DSPT信号时被放气。当麦克风30接收表示主动脉瓣关闭的S2声音，DSPT向控制器和泵22发送信号从而使心脏辅助装置14重新充气。在本发明的该实施例中，DSPT可以包含软件从而过滤掉除了S1和S2声音之外的声音或者该系统可以是泵在每次心跳时被周期性地停止从而允许检测到S1和S2声音，然后控制器和泵22根据在泵不工作期间检测到的定时操作预定的时间。 
图4所示的结构可通过提供从心脏12延伸至外壳32的ECG引线而被改变。在这种情况下，DSPT将根据R波的ECG检测和S2声音的接收而进行操作。ECG引线将优选地设置在气体管线从病人身体离开的点处的内腔中或者连接于气体管线。这意味着进入病人体内的经皮路径只有一个点。ECG引线也可以邻近气体管线而引出。 
R波和心音二者的检测明显地改善了心脏辅助装置的精确定时，从每次跳动到心动周期的事件，诸如。脏收缩和心脏舒张的开始。而且，信号发送结构提供成本有效并且稳定的无线遥测系统，并且使病人的不舒服程度减小到最小。同样由于经皮气体管线不必带有任何内部引线，所以其可被制造得相对较小并且更柔软，从而增强病人的舒服感。 
本领域技术人员可知，可在不脱离本发明所广泛描述的精神和范围内对特定实施例中所示的发明进行无数的变化和/或改进。本实施例因此也被认为在所有方面是示意性的而不是限制性的。 
例如，虽然心外膜引线在图2中示出，但是一引线可以是心脏内的和其他是心外膜的，或者反之亦然。 

Claims (36)

1.一种控制病人体中的搏动心脏辅助装置的操作的方法，
该搏动心脏辅助装置包括主动脉外气球泵，该主动脉外气球泵包括：泵；具有内腔的主动脉外气球；和从泵导引至主动脉外气球的流体管线，
该方法包括使用心脏产生的声音控制所述心脏辅助装置的操作，用位于主动脉外气球的内腔中或位于导引至主动脉外气球的流体管线中的声音检测装置检测所述声音。
2.根据权利要求1所述的方法，其中，所述方法使用R波检测和心音检测的结合控制所述心脏辅助装置的操作。
3.根据权利要求1所述的方法，其中，所述心脏辅助装置完全通过利用心音S1和S2进行停止和开启所述心脏辅助装置。
4.一种控制病人体中的搏动心脏辅助装置的操作的方法，包括以电的方式检测病人心脏节律的R波并且产生信号以开始所述心脏辅助装置的搏动状态中的变化，并且检测由病人主动脉瓣的关闭产生的声音或压力波，并且产生信号从而使所述心脏辅助装置返回至其在R波之前所具有的搏动状态。
5.一种使用多通道数字信号处理器和发送器控制搏动心脏辅助装置的操作的方法，
所述数字信号处理器和发送器属于具有心电图通道和心音图通道的类型，所述数字信号处理器和发送器至少适于正常地通过所述心电图通道传感表示心脏节律的电信号，正常地通过所述心音图通道传感心音，并且将信号发送至外部接收器，
所述方法包括下述步骤：
将所述数字信号处理器和发送器的双极心电图引线可操作地连接至病人的心脏；并且
将所述数字信号处理器和发送器的麦克风可操作地连接至病人的心脏，
由此，在经由所述心电图通道检测到R波之后，所述数字信号处理器和发送器将R波信号发送至所述心脏辅助装置控制器从而控制所述心脏辅助装置的搏动的定时，并且
由此，在经由所述心音图通道检测到心音之后，所述数字信号处理器和发送器将心音信号发送至所述心脏辅助装置控制器从而控制所述心脏辅助装置的搏动的定时。
6.根据权利要求5所述的方法，其中，所述数字信号处理器和发送器适于正常地通过心音图通道传感20-500Hz范围内的心音。
7.根据权利要求5或6所述的方法，其中，所述数字信号处理器和发送器能够接收和发送信号。
8.根据权利要求7所述的方法，其中，所述数字信号处理器和发送器具有在范围内调整的参数设置，用于检测所述R波和心音，并且用于检测所述输出信号。
9.根据权利要求5或6所述的方法，其中，连接于所述病人心脏的数字信号处理器和发送器的所述双极心电图引线处于心外膜或心内膜或者附着于植入的心脏辅助装置本身。
10.根据权利要求5或6所述的方法，其中，用于收集心电图信号的传感器嵌入心脏辅助装置的表面内，该心脏辅助装置应用于病人身体的心脏或另一部分，心电图信号从其中接收。
11.根据权利要求5或6所述的方法，其中，所述数字信号处理器和发送器的麦克风在病人身体内部。
12.根据权利要求11所述的方法，其中，至病人心脏的连接处于心外膜。
13.根据权利要求11所述的方法，其中，至病人心脏的连接处于心内膜。
14.根据权利要求11所述的方法，其中，至病人心脏的连接采用起搏器电极线的方式。
15.根据权利要求11所述的方法，其中，至病人心脏的连接附着于所述植入的装置本身。
16.根据权利要求11所述的方法，其中，至病人心脏的连接位于所述心脏瓣膜的50mm范围内。
17.根据权利要求11所述的方法，其中，至病人心脏的连接中，肺部不在所述麦克风与病人心脏之间。
18.根据权利要求5或6所述的方法，其中，所述数字信号处理器和发送器的麦克风位于病人体外。
19.根据权利要求18所述的方法，其中，主动脉外气球泵在病人体外并由气体驱动，麦克风在病人体外，并且心音和心电图利用位于所述主动脉外气球的内腔或导引至主动脉外气球的气体管线中的外部麦克风控制主动脉外气球泵。
20.根据权利要求19所述的方法，其中，所述气体管线被植入，并且所述植入的气体管线和主动脉外气球起到听诊器的作用，并且心音可被间歇地或连续地检测到，并且经由植入的气体管线和气球直接发送至位于病人体外的控制器。
21.根据权利要求20所述的方法，其中，经皮心电图引线用于直接将心电图信号发送至所述控制器。
22.根据权利要求21所述的方法，其中，所述心电图引线与所述经皮气体管线相结合。
23.根据权利要求21所述的方法，其中，所述心电图引线与所述经皮气体管线分离开。
24.根据权利要求22或23所述的方法，还包括用于皮肤下的心电图引线和经皮气体管线的可释放和可密封连接。
25.根据权利要求5或6所述的方法，其中，所述数字信号处理器和发送器能够接收外部装置的信号，从而调节在用于检测R波和心音的数字信号处理器和发送器中的数字信号处理变量。
26.根据权利要求5或6所述的方法，其中，所述数字信号处理器和发送器具有寿命足够长的电池，以使所述数字信号处理器和发送器可独立于心脏传感引线而被移除和替换。
27.根据权利要求5或6所述的方法，其中，所述数字信号处理器和发送器具有可充电电池，其可通过感应或者经皮能量传送进行充电。
28.根据权利要求5或6所述的方法，其中，所述数字信号处理器和发送器与植入的控制器直接通信。
29.根据权利要求28所述的方法，其中，所述控制器和所述心电图和麦克风包含在所述泵中，所述泵位于中右胸腔，并且所述泵的包含密封麦克风和心电图电极的一个方面与所述右心脏结构相对。
30.一种用于控制搏动心脏辅助装置的操作的双通道数字信号处理器和发送器，所述数字信号处理器和发送器属于具有心电图通道和心音图通道的类型，所述数字信号处理器和发送器至少适于正常地通过所述心电图通道传感表示心脏节律的电信号，正常地通过所述心音图通道传感心音，并且将信号发送至外部接收器，从而控制所述心脏辅助装置的搏动的定时。
31.根据权利要求30所述的数字信号处理器和发送器，其中，信号被直接发送至植入的控制器。
32.根据权利要求30或31所述的数字信号处理器和发送器，其中，所述数字信号处理器和发送器适于正常传感在20-500Hz范围中的通过心音图通道的心音。
33.根据权利要求30或31所述的数字信号处理器和发送器，其中，所述数字信号处理器和发送器能够接收以及发送信号。
34.根据权利要求30或31所述的数字信号处理器和发送器，其中，所述数字信号处理器和发送器具有在范围内可调整的参数设置，用于检测所述R波和心音，并且用于检测所述输出信号。
35.根据权利要求30或31所述的数字信号处理器和发送器，其中，所述数字信号处理器和发送器具有用于检测主动脉和左心室血压以及主动脉或心室壁移动的通道，并且这些通道的信号也被解读以控制心脏辅助装置发挥作用。
36.一种用于控制共搏或反搏心脏辅助装置的装置，所述装置包括：
共搏或反搏心脏辅助装置；
用于所述心脏辅助装置的控制器；和
数字信号处理器和发送器至少适于通过心电图通道正常地传感表示心节律的电信号并且通过心音图通道传感表示心音S1和/或S2的声音信号，并且向所述控制器发送可识别的信号，其中，所述数字信号处理器和发送器设置成在主动脉电路不能传感病人心室的节律信号的情况下，以低于生理感觉速率的最小速率发送心室电路的起搏信号，所述控制器被设置成在所述控制器从所述数字信号处理器和发送器接收的起搏信号处于低于预定速率的速率下的情况下关闭所述心脏辅助装置，所述预定速率高于最小速率。
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US20140051909A1 (en) 2014-02-20
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US20150328466A1 (en) 2015-11-19
US8571658B2 (en) 2013-10-29
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US20100324354A1 (en) 2010-12-23
US9561375B2 (en) 2017-02-07

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