CN101583397A - 植入式心脏治疗装置中的信号分析 - Google Patents
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Abstract
植入式心脏治疗***中的心脏信号分析方法和装置。示出了几种信号处理和/或调节方法,包括R波检测实施例,这些实施例包括使用与在前峰值幅度相关的阈值。同样,一些实施例包括样本阈值处理以从采样信号中去除无关数据。一些实施例包括与采样心脏信号内的其他样本相比更大地对某些样本进行加权,以便进行分析。
Description
技术领域
本发明涉及植入式医疗装置领域。更特别地,本发明涉及分析心脏信号的方法。
背景技术
对于那些心脏功能不全的患者,起搏器和植入式心脏复律/除颤器(ICD)已经成为有用的治疗装置。这些装置提供有助于患者的心脏正确地工作的电刺激。这种装置的一方面期望精确地识别患者是否及何时正经受恶性心脏状况。然而,心脏可能不但经受正常的窦性心律,而且经受各种不同形式的心律失常,诸如心房纤维性颤动、房性心动过速、心室纤维性颤动、室性心动过速。并非所有的这些心律失常均是恶性的。因为心脏复律或除颤刺激的应用会令患者不安,应当避免非必要的刺激应用。另外,错误地应用刺激会导致患者的心脏进入诸如纤维性颤动的恶性心脏状况。因此需要提供区别恶性和非恶性心脏状况的附加途径的方法和装置。
发明内容
本发明在一个说明性实施例中包括一种心脏信号分析方法,该方法包括通过使用布置在患者内的第一和第二电极来采集心脏信号、检测心脏事件、调节与心脏事件相关的心脏信号的一部分、以及分析心脏信号的该部分以确定患者是否很可能正经受恶性心脏状况。调节与心脏事件相关的心脏信号的一部分的步骤可包括对心脏信号进行采样以产生多个样本,并将选定样本与样本阈值比较,以及如果样本的量值没有超出样本阈值,则用不同的值代替该样本。
在一些实施例中,样本至少临时以具有最小幅度及最大幅度的形式被存储,其中,如果样本的量值没有超出样本阈值,则该方法包括用对应于最小幅度的值代替选定样本。在另一个实施例中,样本至少临时以有符号的格式被存储,其中,如果样本的量值没有超出样本阈值,则该方法包括用对应于零的值以有符号的格式代替选定样本。如果样本的量值没有超出样本阈值,则该方法可包括用对应于样本阈值的值代替选定样本。
在一些实施例中,分析心脏信号的该部分的步骤包括将心脏信号的该部分与存储模板进行比较,其中所述存储模板包括多个模板样本,以及,如果模板样本中的一个或多个没有超出阈值,则标记那些模板样本,并且选择心脏信号的该部分的选定样本,以便当心脏信号的该部分与存储模板进行比较时该选定样本对应于模板的标记样本。该方法还可包括对样本向量进行加权以给予一些信号样本比其他信号样本更大的分析权重。在一些实施例中,分析心脏信号的该部分的步骤可包括将心脏信号的该部分与存储模板进行比较的步骤,并且该比较步骤包括与其他样本相比更大地对心脏信号的该部分的某些样本进行加权。
本发明在另一个说明性实施例中包括一种心脏信号分析方法,该方法包括通过使用布置在患者内的第一和第二电极来采集心脏信号、检测心脏事件、对心脏信号进行采样、将采样信号作为样本向量来处理、并将样本向量乘以加权向量以生成加权的样本向量、以及分析加权的样本向量以确定患者是否很可能正经受恶性心脏状况。在一些实施例中,加权向量可具有至少一些分量,这些分量大于加权向量内的至少一些其他分量。在又一方法中,样本向量包括被确定为样本向量的基准点的分量,并且加权向量具有对应于样本向量内的该基准点的峰值分量,该峰值分量具有比加权向量的其他分量更大的幅度。
另一个说明性实施例包括一种确定患者是否正遭受恶性心脏状况的方法,包括使用植入电极从患者采集具有心脏事件的心脏信号、对心脏信号进行采样以便其包括多个信号样本、以及将心脏信号与存储模板进行比较以生成一分值,该分值指示心脏信号和存储模板之间的相关性,其中在比较期间对信号样本中的至少一些提供较大的权重,而在比较期间对信号样本中的其他样本提供较小的权重。在一个实施例中,心脏信号包括基准点,并且对比其他样本更靠近基准点的样本给予更大的权重。在另一实施例中,心脏信号包括一个或多个斜坡,其中对沿着心脏信号的倾斜部分所取的样本给予较小的权重。
又一说明性实施例包括一种心脏信号分析方法,该方法包括通过使用布置在患者内的第一和第二电极来采集心脏信号、检测心脏事件、调节与心脏事件相关的心脏信号的一部分、以及分析心脏信号的该部分以确定患者是否很可能正经受恶性心脏状况。检测心脏事件的步骤可包括以下列方式观察采集的心脏信号是否超出阈值:在在前心脏事件之后,选择不应期;识别一个或多个在前心脏事件的峰值信号幅度并选择与峰值信号幅度相关的第一和第二阈值,第一阈值具有比第二阈值更大的值;以及在不应期之后以及在感测下一个心脏事件之前的时间上,生成具有连续下降的值的阈值,所述阈值具有等于第一阈值的第一值,且在稍后的时间点,具有接近第二阈值的值。
在一些实施例中,第一阈值至少为多个在前峰值信号幅度的平均值的50%。在又一另外的实施例中,第二阈值小于多个在前峰值信号幅度的平均值的10%。这些值可以是自适应的,例如如果识别出误检测,则可随着时间而改变一个百分比或其他百分比。分析步骤可包括将心脏信号与存储模板进行比较,以及对心脏信号与模板的第一对应部分的比较提供较大的权重,而对心脏信号与模板的第二对应部分的比较提供较小的权重。所述第一对应部分可对应于心脏信号的最大幅度部分。所述第二对应部分可对应于心脏信号的最大斜率区域。分析步骤可包括观察心脏信号的某些部分是否具有超出样本阈值的量值,并且,如果没有,则用预先选择的值代替心脏信号的那些部分。
附图说明
图1A和1B示出植入式心脏治疗装置的两个示例配置;
图2以块形式示出一个心脏信号分析范例;
图3以块形式示出心脏信号分析方法的一个说明性实施例;
图4图形化示出根据说明性方法的R波检测方法;
图5A-5C图形化示出调节所采集的心脏信号的说明性示例方法;
图6A-6B示出另一阈值操作;
图7以图形和数字格式示出一些用于加权向量的示例实施例;
图8示出使用加权矩阵的对样本的数学处理;以及
图9示出加权向量/操作的另一途径。
具体实施方式
应当参考附图阅读以下的详细描述。未必按比例的所述附图描绘说明性实施例,并且并非意欲限制本发明的范围。
迄今为止,植入式心脏治疗***是心外膜***或者经静脉***。例如,经静脉***可一般如图1B中所示被植入。然而,如在此将进一步描述的,本发明同样适用于与如图1A中所示的皮下植入式心脏治疗***共同运行。
图1A示出皮下放置的植入式心脏治疗***,特别地,为一个ICD***。在该说明性的实施例中,使用耦合到导联***14上的筒12监控心脏10。筒12可包括位于其上的电极16,同时导联***14连接到感测电极18、20,以及可用作冲击或刺激传输电极(shock or stimulus delivery electrode)和感测电极的线圈电极22。各种不同的电极规定多个感测向量V1、V2、V3、V4。可以看出每个向量提供心脏10电活动的不同的向量“视图”。该***可如例如在美国专利No.6,647,292和No.6,721,597中所示在皮下植入,所述两个专利的公开内容在此被引入作为参考。通过皮下放置,意味着电极的放置不要求将电极***到心室内、心肌内或上,或患者的脉管***。
图1B示出经静脉ICD***。通过包括耦合到导联***34上的筒32的***监控及治疗心脏30,所述导联***34包括心房电极36和心室电极38。可使用电极的多个配置,包括放置在心脏内、附着到心脏上或布置在患者的脉管***内。
图2以块形式示出一个心脏信号分析范例。从开始块50开始,如52所示采集心脏信号。采集步骤52可包括几个如图2的右边所示的子部分。第一步骤可接收信号54,这可例如使用如图1A-1B中所示布置在患者内的电极以及/或通过使用附加的或其他合适的植入电极配置来执行。然后该信号被放大至更适合于电处理的水平,如在56所示,并且被滤波以去除已知噪声(例如50/60Hz的噪声)及无关的数据(例如频率高于大约100Hz的信号),如在58所示。
在信号采集52之后,下一个步骤是检测是否已出现心脏事件,如在60所示。如果出现了,则进一步调节心脏信号,如在62所示,这可包括采样64以将模拟信号转变为数字信号。替代地,可使用数字化信号进行事件检测。在一些实施例中,信号也被调整66并被放入窗口格式中用于进一步分析。这种调整的一些说明性范例在2004年6月1日提交的并且名称为“METHOD ANDDEVICES FOR PERFORMING CARDIAC WAVEFORM APPRAISAL”的共同未决的美国专利申请No.10/858,598中示出,该申请的公开内容在此被引入作为参考。
一旦心脏事件已经被调节62,则分析信号,如68所示。分析可采取多种形式。速率测量是一种分析形式;在一些现有装置中速率测量是唯一的分析方法。本发明可包括使用形态分析,如共同未决的美国专利申请No.10/856,084中所阐明的,该申请于2004年5月27日提交,名称为“METHOD FORDISCRIMINATING BETWEEN VENTRICULAR AND SUPRAVENTRICULARARRHYTHMIAS”,该申请的公开内容在此被引入作为参考。
本发明在一些实施例中提供图2中所示的方法部分的附加细节。在一个示例实施例中,检测事件60的步骤可包括将接收信号与时间变化的事件阈值进行比较。用于改变事件阈值的方法可以以下面进一步阐明的方式执行。在另一个实施例中,调节信号62的步骤可包括抑制幅度不超出抑制阈值的信号区域的某些部分的附加步骤。在另一个实施例中,调节62和/或分析68的步骤可进一步包括为了分析或在分析期间加权心脏信号。例如,心脏信号可包括多个样本,其中在调节62或分析68期间给予一些样本较大的权重。
图3以块形式示出心脏信号分析方法的一个说明性实施例。图3的说明性方法包括上面提到的改进中的每一个,但应当理解,除非另有说明,在此公开的这些方法、子程序或子方法可以联合或单独使用。另外,根据需要,某些步骤可以被交换或以不同的顺序执行。
心脏信号分析的示例方法开始于开始块100,并且包括如102所示的采集信号。采集步骤102可包括如在104所示从植入电极接收信号,如在106所示放大该信号,并且如108所示对该信号进行滤波。放大和滤波步骤106、108可互换,并且可提供附加的滤波级。
一旦信号已在102被采集,该方法以检测事件继续,如在110所示。检测事件的步骤可包括一个子程序,如该图的左边所示。该子程序可包括,在感测到在前事件后,设定不应期,如在112所示。在此不应期期间,将不检测事件。同样在事件检测子程序中包括观察在前的峰值幅度的步骤,如在114所示。使用在前的峰值幅度设定第一和第二阈值,如在116所示。在一个说明性范例中,所述第一阈值为一个阈值水平,在该阈值水平之上在不应期结束之后不久进行检测,而第二阈值为一个阈值水平,在该阈值水平之上在稍后的时间进行检测。线性或指数曲线可用于规定所述阈值。在一些实施例中,第一阈值是至少两个在前峰值的平均值的相对较高的第一百分比,而第二阈值是至少两个在前峰值的平均值的相对较低的第二百分比。常数可被添加到任一阈值中。以下参考图4提供说明性阈值的进一步解释。
随着阈值设定,事件检测子程序随后包括将接收信号与阈值进行比较,如在118所示。当接收信号超出阈值时,可宣告一个事件。如果需要的话,除了所示的方法,事件或波形评价方法可被使用,例如确认方法,诸如在共同未决的美国专利申请No.10/858,598中所阐明的那些确认方法,该申请于2004年6月1日提交,并且名称为“METHOD AND DEVICES FOR PERFORMINGCARDIAC WAVEFORM APPRAISAL”,该申请的公开内容在此被引入作为参考。
在110检测到事件后,该方法通过如在120所示调节对应于所检测到的事件的接收信号来继续。调节步骤120可包括如该图左边所示的子程序。可对心脏信号进行采样,如在122所示,以数字化模拟信号。接下来,可对采样信号进行调整(align)以将该信号与所存储的心脏模板进行比较,如在124所示。
在调节步骤120中,采样心脏信号可经历抑制步骤,如在126所示。例如,可规定一个阈值,低于该阈值,样本被“清零”(“zeroed”out)。如果使用与模板的相关分析比较,则抑制步骤可减少噪声对分析的影响。接着,被采样、调整且抑制的心脏信号可进行加权步骤,如在128所示。在加权步骤128期间,某些样本被给予比其他样本更大的分析权重。
在调节步骤120之后,接下来该方法包括分析信号,如在130所示。分析可包括例如与所存储的模板或动态模板进行比较。分析还可包括其他形态或速率考虑,诸如R-R间隔或QRS宽度测量。然后处理和分析心脏信号的方法结束,如在132所示。根据图3的方法,可作出关于患者是否看来似乎正经历恶性心脏状况以及是否指示治疗的决定。
图4图形化示出根据一个说明性子方法的R波检测方法。该方法使用一个连续函数示出,但实际上有关的信号通常可能是离散的采样信号。在说明性的R波检测方法的过程中,不应期用块150表示,在该不应期期间R波检测器被禁用,或者在该不应期期间忽略通过R波检测器的检测。在时间t0后,规定并使用阈值152。该阈值152以第一阈值T1开始并根据如图中所示的对数公式渐近地接近第二阈值T2:
可以选择所述第一和第二阈值T1和T2作为在前峰值或在前峰值检测信号平均值的规定百分比。
在一个实施例中,第一阈值T1被设定在两个在前峰值的平均值的35-75%,而第二阈值T2被设定在两个在前峰值的平均值的2-20%。在另一个实施例中,第一阈值T1被设定在两个在前峰值的平均值的50-60%,而第二阈值T2被设定在两个在前峰值的平均值的2.5-7.5%。在又一实施例中,第一阈值T1被设定在两个在前峰值的平均值的55%左右,而第二阈值T2被设定在两个在前峰值的平均值的5%左右。第一和第二阈值可以例如根据患者的心脏活动或心脏信号特征、电极位置或其他合适的因素而改变。例如,第一和第二阈值百分比中的一个或另一个可以是自适应的并且可根据患者的检测事件速率、信噪比或另外的因素而改变。
通过将感测阈值设置在最新峰值的百分比的范围内,R波检测方法变为适应于患者心脏电活动的变化。
图5A-5C图形化示出调节所采集的心脏信号的说明性示例方法。参考图5A,对应于相对正常的具有QRS特征的心脏事件显示接收信号200。该信号200以模拟形式示出在基线202周围。采样阈值204、206显示在基线202周围。图5B示出对图5A的信号200的采样。可以看出样本210提供信号200的间歇表示,使得能够对信号进行数字处理。一些样本没有超出阈值204、206。参考图5C,仅示出采样表示210。样本中的一些已被“X”符号代替,诸如样本212。这些样本是没有超出阈值204、206的样本并且因而已使用说明性方法被基线值代替。
所述阈值204、206被显示为关于基线202对称的阈值。在其它实施例中,阈值204、206可以替代地是不对称的。在一些实施例中,可采取绝对值,而不是如所示的有符号的值,从而仅规定一个阈值。阈值204、206可被设定为一个值,该值足够低从而可以猜测落入阈值204、206范围内的样本主要是噪声而不是心脏信号。在一些实施例中,所述阈值被设定为恒定的水平。替代地,阈值204、206可被设定为在峰值信号幅度的1%至5%范围内的百分比,或者例如利用对接收心脏信号的认识而随着时间的推移自适应。在数字域中,一旦被采样,另一阈值水平就可利用信号的数字特征。例如,在具有256级分辨率的***(8位***)中,对绝对值操作,具有在00000000和00001000之间的值的样本可被设定为00000000。在另一个实施例中,落入阈值204之下且在基线202之上的信号可被设定为阈值204的值,并且落入阈值206之上且在基线202之下的信号可被设定为阈值206的值。
图6A-6B示出另一个阈值操作。图6A示出对模板执行的阈值处理(thresholding)。说明性地示出了模板信号250,其中样本252表示实际模板。模板可被用于与接收信号进行比较,以便确定接收信号是否很可能对应于恶性心脏事件。在根据参考图5A-5C所讨论的方法的方法中,一些样本254被显示为“清零”(“zeroed out”)到基线值。这些样本被标记,如阈值处理块256所显示的。
参考图6B,示出对接收信号258的处理。可以看出样本260落入样本阈值及基线之间。然而,样本260没有落入阈值处理块256内,并且因此不针对该样本执行阈值比较。替代地,针对在阈值处理块256中的样本执行阈值比较,并且将样本254清零。因此图6A-6B的方法要求标记哪些样本已在图6A的模板中遭受到阈值处理,以便在图6B中调节接收样本258。
图7以图形和数值格式示出用于加权向量的一些示例实施例。权向量W280在数值上被显示为包括多个值。在该说明性范例中,信号S包括多个样本282,其中选择权向量280的大小以对应于样本282的数目。在284显示了W的图形格式。可以看出对在信号S中间的样本给予了最大的权重。将较大的权重设置在信号S的该区域中的一个原因在于假定可检测QRS型心脏事件的一些表象(semblance),接收信号的中心部分很可能包含更显著的形态数据。此外,可加强该区域,因为它是与基线偏差最大的区域,并且能找到最可能包含最少相对数量的噪声的信号。
通过使用向量叉积,可使用权向量280来修改信号S。使用图7的方法,附加的分析可包括相关波形分析。用于这种分析的范例公式如下:
其中:ti为第i个模板样本的值,si为第i个信号样本的值,a为作为信号峰值与模板峰值的比率计算的标度因子,而i为模板和信号中的样本的数目。作为信号调节一部分的加权因子的使用基于如下公式的应用:
si=wi×ri
其中wi为第i个加权因子的值,而ri为第i个未加权或原始数据样本的值。同样对于模板:
ti=wi×tri
其中tri为原始模板值。
图8示出使用加权矩阵来数学处理样本。为了说明的目的,大大地简化了图8的数学操作。大体上,模板向量290与具有对应于加权向量的对角值的对角加权矩阵292交叉以产生加权模板向量294。同样,样本向量296和对角加权矩阵292的叉积产生加权的样本向量298。然后加权模板向量294和加权样本向量298可被用于进一步分析。
尽管图7-8假定信号调节是用于提供加权函数,但在分析期间可同样为信号提供附加的权重。返回到上述的CWA公式,可以在该公式中考虑加权向量:
再次,wi为第i个加权因子的值。使用上述公式,加权向量可被用于修改CWA分析。
图9图示加权向量/操作的另一个途径。示出了在多个样本块中对信号300采样。在峰值之后,信号300以大的向下斜率下降。信号300的一部分被放大显示在图9的上面部分中。在那里可以看出从信号300取出样本302和304。然而,由偏斜306指示的定时的轻微变化导致样本302’、304’,而不是样本302、304。这意味着,由于信号300的陡坡,采样的小的偏斜导致样本的明显改变,其中样本302’具有较小的量值和较低的值,而304’具有较大的量值和更负的值。样本的偏斜引起一个样本具有更小的幅度和更小的量值,而另一个具有更负的幅度和更大的幅值。然而,在308示出的加权向量可说明这种效应沿着最陡斜率区域的可能性。特别地,可以看出给予对应于陡坡的加权向量308的部分310最小的权重。同时,在逐渐更倾斜的位置,给予较大的权重。图9中示出的范例仅仅是接收信号可被加权的另一种说明性方式。
本领域的技术人员将认识到本发明可以以不同于在此描述和预期的特定实施例的多种形式来表明。相应地,可进行形式和细节的偏离而不脱离如随附权利要求中所述的本发明的范围和精神。
Claims (20)
1、一种心脏信号分析方法,该方法包括:
通过使用布置在患者内的第一和第二电极来采集心脏信号;
检测心脏事件;
调节与该心脏事件相关的所述心脏信号的一部分;以及
分析所述心脏信号的该部分的至少一些部分以确定患者是否很可能正经受恶性心脏状况;
其中调节与该心脏事件相关的所述心脏信号的一部分的步骤包括:对所述心脏信号进行采样以产生多个样本,并将选定样本与样本阈值进行比较,以及如果样本的量值没有超出样本阈值,则用不同的值代替该样本。
2、权利要求1的方法,其中样本至少临时以具有最小幅度及最大幅度的形式被存储,其中,如果样本的量值没有超出样本阈值,则该方法包括用对应于最小幅度的值代替选定样本。
3、权利要求1的方法,其中样本至少临时以有符号的格式被存储,其中,如果样本的量值没有超出样本阈值,则该方法包括用对应于零的值以有符号的格式代替选定样本。
4、权利要求1的方法,其中如果样本的量值没有超出样本阈值,则该方法包括用对应于样本阈值的值代替选定样本。
5、权利要求1的方法,其中分析所述心脏信号的该部分的步骤包括将所述心脏信号的该部分与存储模板进行比较,其中所述存储模板包括多个模板样本,以及如果所述模板样本中的一个或多个没有超出阈值,则标记那些模板样本,并且选择所述心脏信号的该部分的选定样本,以便当所述心脏信号的该部分与存储模板进行比较时该选定样本对应于模板的标记样本。
6、权利要求1的方法,进一步包括对样本向量进行加权以给予一些信号样本比其他信号样本更大的分析权重。
7、权利要求1的方法,其中分析所述心脏信号的该部分的步骤包括将所述心脏信号的该部分与存储模板进行比较的步骤,并且该比较步骤包括与其他样本相比更大地对所述心脏信号的该部分的某些样本进行加权。
8、一种心脏信号分析方法,该方法包括:
通过使用布置在患者内的第一和第二电极来采集心脏信号;
检测心脏事件;
对心脏信号进行采样,将采样信号作为样本向量进行处理,并将样本向量乘以加权向量以生成加权的样本向量;以及
分析加权的样本向量以确定患者是否很可能正经受恶性心脏状况。
9、权利要求8的方法,其中加权向量具有至少一些分量,这些分量大于加权向量内的至少一些其他分量。
10、权利要求8的方法,其中样本向量包括被确定为样本向量的基准点的分量,并且加权向量具有对应于样本向量内的基准点的峰值分量,该峰值分量具有比加权向量的其他分量更大的幅度。
11、一种确定患者是否正遭受恶性心脏状况的方法,该方法包括:
使用植入电极从患者采集具有心脏事件的心脏信号;
对心脏信号进行采样以便其包括多个信号样本;以及
将心脏信号与存储模板进行比较以生成一分值,该分值指示心脏信号和存储模板之间的相关性,其中在比较期间对所述信号样本中的至少一些提供较大的权重,而在比较期间对所述信号样本中的其他信号样本提供较小的权重。
12、权利要求11的方法,其中所述心脏信号包括基准点,并且对比其他样本更靠近基准点的样本给予更大的权重。
13、权利要求11的方法,其中所述心脏信号包括一个或多个斜坡,其中对沿着所述心脏信号的倾斜部分所取的样本给予较小的权重。
14、一种心脏信号分析方法,该方法包括:
通过使用布置在患者内的第一和第二电极来采集心脏信号;
检测心脏事件;
调节与该心脏事件相关的所述心脏信号的一部分;以及
分析所述心脏信号的该部分以确定患者是否很可能正经受恶性心脏状况;
其中:
检测心脏事件的步骤包括以下列方式观察采集的心脏信号是否超出阈值:
a)在在前心脏事件之后,选择不应期;
b)识别一个或多个在前心脏事件的峰值信号幅度并选择与该峰值信号幅度相关的第一和第二阈值,所述第一阈值具有比第二阈值更大的值;以及
c)在不应期之后以及在感测下一个心脏事件之前的时间上,生成具有连续下降的值的阈值,所述阈值具有等于第一阈值的第一值,且在稍后的时间点,具有接近第二阈值的值;并且分析步骤包括将心脏信号与存储模板进行比较,以及对心脏信号与模板的第一对应部分的比较提供较大的权重,而对心脏信号与模板的第二对应部分的比较提供较小的权重。
15、权利要求14的方法,其中第一阈值至少为多个在前峰值信号幅度的平均值的50%。
16、权利要求14的方法,其中第二阈值小于多个在前峰值信号幅度的平均值的10%。
17、权利要求14的方法,其中所述第一对应部分对应于心脏信号的最大幅度部分。
18、权利要求14的方法,其中所述第二对应部分对应于心脏信号的最大斜率区域。
19、权利要求14的方法,其中分析步骤包括观察心脏信号的某些部分是否具有超出样本阈值的量值,并且,如果没有,则用预先选择的值代替心脏信号的那些部分。
20、一种植入式心脏刺激装置(ICSD),包括:
壳体,包含用于ICSD的操作电路;以及
多个电极,耦合到所述操作电路上;
其中所述操作电路被配置用于执行如权利要求1-19之一中所述的方法。
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CN107847745A (zh) * | 2015-05-13 | 2018-03-27 | 阿库图森医疗有限公司 | 用于采集和分析心脏信息的定位***和方法 |
CN108136186A (zh) * | 2015-08-20 | 2018-06-08 | 心脏起搏器股份公司 | 用于医疗装置之间的通信的***和方法 |
CN108136186B (zh) * | 2015-08-20 | 2021-09-17 | 心脏起搏器股份公司 | 用于医疗装置之间的通信的***和方法 |
CN107582042A (zh) * | 2016-07-06 | 2018-01-16 | 韦伯斯特生物官能(以色列)有限公司 | 多个电解剖图的自动创建 |
CN107582042B (zh) * | 2016-07-06 | 2021-11-26 | 韦伯斯特生物官能(以色列)有限公司 | 多个电解剖图的自动创建 |
CN110769744A (zh) * | 2017-04-18 | 2020-02-07 | 波士顿科学医学有限公司 | 用于电生理学信号的注释直方图 |
CN110769744B (zh) * | 2017-04-18 | 2024-02-13 | 波士顿科学医学有限公司 | 用于电生理学信号的注释直方图 |
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US20080077030A1 (en) | 2008-03-27 |
AU2007300113A1 (en) | 2008-04-03 |
WO2008039841A8 (en) | 2008-09-25 |
CA2663756A1 (en) | 2008-04-03 |
US9042980B2 (en) | 2015-05-26 |
CN101583397B (zh) | 2013-11-06 |
US20110307024A1 (en) | 2011-12-15 |
EP2077889A2 (en) | 2009-07-15 |
WO2008039841A2 (en) | 2008-04-03 |
EP2077889B1 (en) | 2013-07-24 |
AU2007300113A2 (en) | 2009-05-28 |
US8014851B2 (en) | 2011-09-06 |
JP5095742B2 (ja) | 2012-12-12 |
JP2010504836A (ja) | 2010-02-18 |
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