CN1078136A - 一种体外反搏装置的控制方法 - Google Patents
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Abstract
本发明属于控制体外反搏装置的一种方法,通过
采用点状电极技术和自适应滤波技术获得在反搏状
态下波形稳定、特征点明显的心阻抗血流图,并对心
阻抗血流图中主动脉瓣关闭点检测或计算,及反搏血
流波起点的检测,调整反搏装置充排气时间,使反搏
血流波起点逐渐向主动脉关闭点靠近并重合;由对心
阻抗血流图中心脏收缩波和反搏波的波峰高度和波
形持续时间的检测获得反搏疗效的依据,从而使对反
搏装置的控制更为合理,反搏疗效和安全性得以提
高。
Description
本发明属于控制体外反搏装置工作的一种方法,主要是利用心阻抗血流图作为反搏时主动脉血流状态的反馈信息,调整反搏装置的充气、排气时间,从而达到控制目的。
目前国内外的各类体外反搏装置采用耳垂脉搏波、指脉波或颞动脉压力脉搏波作为反搏时主动脉血流状态的反馈信息,控制反搏装置的工作,耳脉、指脉和颞动脉均属于微动脉和终末小动脉的范畴,在反映主动脉血流状态、心脏收缩舒张状态方面无法与主动脉区直接检出的血流信号相比。
1.利用脉搏波中降中峡作为反搏充气定时控制存在的问题
心脏的间歇性射血,将产生从主动脉根部出发沿着脉管系传播的脉搏波。在主动脉脉搏波中存在一个小切迹-主动脉瓣关闭切迹,将脉搏波分成收缩和舒张两部分,主动脉瓣关闭切迹是由于心室收缩末期,心室内压力下降,主动脉瓣关闭的一瞬间,充盈于动脉中的血液向心室方向倒流,引起主动脉和血柱的后振动,后振动与脉搏波的反射回波合并在一起而形成主动脉瓣关闭切迹,它标志着主动脉瓣的关闭,也是心脏收缩和舒张期的分界线。
沿着动脉系统传播的脉搏波随着离心脏的距离增大其峰值的时间和波形的形状都将发生变化(峰化和陡化)。使脉搏波波形变化的因素是多方面的,其中主要的原因:
(1)管壁弹性对压力变化的阻尼作用,一些快速而细小的振动逐渐衰减,以至消失,如主动脉瓣关闭切迹一般只能用心导管插至主动脉根附近测定其压力曲线而录出。
(2)大的压力变化向外周传播到狭小的分枝时,遇到阻碍,一部分沿动脉壁反射回来,在逐渐衰减的过程中,同时也与向外周传播的后继脉搏波相干涉,引起波形的变化。
因此,微动脉和小动脉脉搏波中的降中峡不能等同于主动脉脉搏波的主动脉瓣关闭切迹。利用其作为心脏收缩舒张的特征点进行反搏充排气定时控制是不可靠的。
2.利用脉搏波中反搏波与叩击波的峰值比和面积比作为反搏充气定时控制存在的问题
从理论上说,反搏充气时间应选定在肢体受压引起血流返流回主动脉根部时正好落在主动脉瓣关闭的瞬间。从反搏控制系统发出充气信号到气囊加压作用于肢体,然后在脉搏波上看到反搏波的出现,这期间存在二方面的延时,(1)充气阀开通到压力作用于肢体的延时,这部分延时主要受充气阀到气囊之间管道的长度、管道的弹性、管道的内径、充气的压力和气囊容积的大小影响,这部分延时对于一台反搏装置来说是基本不变的。(2)肢体受压后下半身血液返流到达主动脉瓣,即在主动脉区录得的脉搏波中见到反搏波的开始出现,这部分延时因人而异,取决于下列因素:人体的胖瘦、四肢的长短、血管的口径、血管的弹性和血液的粘滞度等等,这部分延时大约在50ms~200ms之间。考虑到这二方面的延时,反搏的充气定时一般提前到T波的顶点或上升枝,然后观察脉搏波中收缩波和反搏波,使收缩波波峰后100~120ms出现反搏波的起点为最佳。这种方法是不可能保证反搏波紧接在主动脉瓣关闭后这一时刻到达主动脉瓣,如果充气时间调得过前,在心脏尚在射血期,反搏波头就到达主动脉瓣,必然加重心脏的射血阻力,增大心脏的后负荷,使心肌的耗氧增大。充气时间调得过后,反搏波到达主动脉瓣的时间过迟,反搏波出现晚,振幅低,保持时间短,反搏的疗效将减小。因此,利用脉搏波进行反搏的充气时间控制很难保证反搏获得最佳疗效,也很难保证反搏对病人的安全性。
3.反搏排气定时控制存在的问题
反搏排气时间的确定目前一般考虑二方面的因素,(1)保证在下一个心缩期之前解除对肢体的压迫,减轻心脏的射血阻力。(2)充分利用心舒期的整个时间,使施加于肢体的压力保持时间足够长。这两方面的考虑一是降低收缩波的起点和峰值,二是增加反搏波的面积,使脉搏波中反搏波与收缩波的峰值比和面积比增加,使反搏疗效增加。从减轻心脏的射血阻力角度来说,心脏射血时反搏气囊的排气应使主动脉内的压力减小,然而,从反搏气囊的排气,解除对肢体的压迫,到主动脉内血液充盈挤压排空的肢体动脉血管,使主动脉内压力减小,存在一段的延时,这与反搏气囊的充气到主动脉瓣处压力增加的延时有一定的相关性。与人体的四肢长短、血管的口径、血管的弹性和血液的粘滞度有关,这一部分延时在脉搏波上是无法体现的,且是因人而异的。因此,以降低脉搏波中收缩波的起点及峰值和增加反搏波的面积作为反搏排气的控制同样是不准确和不可靠的。
本发明的目的就是针对上述问题,提出采用心阻抗血流图作为反搏时主动脉血流状态的反馈信息和反搏控制的依据。
本发明的任务是这样完成的:采用合理安排检测心阻抗血流图的点状电极位置和采用自适应滤波技术,获得反搏状态下波形稳定、特征点明显的心阻抗血流图波形,通过对心阻抗血流图中主动脉瓣关闭点和反搏血流波起点的检测,调整反搏充气排气时间,使反搏血流波起点逐渐向主动脉瓣关闭靠近并重合,通过对心阻抗血流图中收缩波和反搏波的波峰高度和波形持续时间的检测,获得反搏疗效的依据,从而实现对体外反搏装置的合理控制,提高反搏的疗效和使用的安全性。
图1是本发明的原理框图,并作为摘要附图。
下面结合附图和实施例对本发明作进一步说明。
本发明主要包括以下步骤:A.采用检测电极(1)、高频恒流源(2)、心电信号和阻抗信号滤波装置(3)、(4)、(5),获得在反搏状态下波形稳定、特征明显的心阻抗血流图;B.计算机系统(6)、(7)对自适应滤波处理后的心阻抗血流图进行检测,获取控制反搏装置充气排气时间的数据;C.对心阻抗血流图中心脏收缩波和反搏波的波形峰值和持续时间进行检测,获取反映反搏疗效的客观指标;D.计算机控制体外反搏装置的充气排气时间。
检测电极(1):由五个点状电极组成,分别置于如附图1所示的位置,即:电极①位于左或右耳根部、或额头,④位于胸骨剑突,均为阻抗电流电极,从这两个电极施加高频恒定电流到人体,电极②位于锁骨下胸骨旁线上,③位于第四、五肋间胸骨旁线上,均为心阻抗测量的探测电极。从这两个电极获得主动脉中心区胸腔内的血流阻抗信号,同时从这两个电极还获得人体心电信号。自适应滤波将探测电极测量的血流阻抗信号作为原始输入信号。自适应滤波处理的阻抗参考输入信号从电极③和位于胸骨旁线腹缘处的电极⑤之间获得。
高频恒流源(2):由晶体振荡器、限幅放大器带通滤波器和电压-电流转换器组成,获得频率稳定度高、稳度恒定的高频电流。由电极①施加于人体,以进行阻抗的测量。
心电信号放大滤波电路(3):由低通差分放大器、带通滤波放大器组成,对从电极②、③中获得的人体心电信号进行放大滤波。
心阻抗信号放大滤波电路(4)及自适应处理参考阻抗信号放大滤波电路(5):由带通滤波放大器、检波器、低通滤波器、微分电路构成,对从电极②、③中获得心阻抗血流信号和从电极③、⑤中获得自适应处理的阻抗参考信号进行放大滤波。
模数转移器(6)和个人微型计算机(7)组成计算机系统,模数转换器将心电信号、心阻抗血流信号和阻抗参考信号转换为数字信号并输入计算机,计算机完成波形的显示、心电QRS波检测、心率上下限告警、心阻抗血流信号与阻抗参考信号的自适应处理及其波形特征点和峰值的测量和体外反搏装置(8)充气、排气时间的控制。
计算机完成体外反搏的闭环控制过程如下:反搏开始时,计算机自动将反搏充气时间设置在心电T波结束。由于反搏波到主动脉的延迟,此时在心阻抗血流图中可以通过计算机检测出主动脉关闭点和反搏波的起始点。计算机根据这两点的时间差,调节反搏装置的充气时间,使反搏波的起始逐渐向主动脉关闭点移动。在两点逐渐重合过程中,由于反搏影响到主动脉关闭点的自动检测,计算机转为由Bazett公式(
)计算的主动脉关闭时间进行控制,即在检测到心电Q波后,由Bazett公式计算的QT时间作为主动脉瓣关闭时刻,使反搏波的起始点,落在主动脉瓣关闭时刻的左右一个范围内。如果两点逐渐重合过程中,由于心脏的射血和胸腔内血流的变化影响到反搏波起始点的检测,计算机根据检测到的反搏波起始点与充气时间的时间差,获得对于此病人下肢加压开始形成反搏波后,反搏波到达主动脉中心区的延迟时间。计算机调节反搏充气时间,使在这一延迟时间后形成的反搏波的起始点落在主动脉瓣关闭时刻的左右一个范围内,并由计算机控制,使其在反搏过程中保持在这个范围内,从而实现了闭环控制。
相对于用心电、指脉或颞动脉的脉搏波等方法控制体外反搏装置,本发明有如下优点:①采用心阻抗血流图获得主动脉中心区的血流状态,没有指脉或颞动脉脉搏波波形的峰化和陡化,作为反搏的控制更为直接,可靠;②心阻抗血流图中获得的反搏血流波的起始点,反映了反搏对主动脉血流形成影响的开始,调节充气排气时间使此起始点与主动脉瓣关闭点重合,并通过计算机闭环调节保持这一状态,使反搏的控制更为直观,安全性提高;③心阻抗血流图中获得的收缩波和反搏波的峰值和持续时间,是反搏疗效的客观依据,为反搏的控制和疗效的观察提供了方便。
Claims (2)
1、一种体外反搏装置的控制方法,它包括:
A.采用点状电极和自适应滤波技术获得在反搏状态下波形稳定、特征点明显的心阻抗血流图。
B.计算机对自适应滤波处理后的心阻抗血流图进行检测,获得主动脉关闭点和反搏波的起始点,两点的时间差作为反搏装置充气排气时间控制的依据,若主动脉瓣关闭点的检测受反搏波影响,则计算机根据Bazett公式计算QT时间作为主动脉瓣的关闭时间,由该时间和反搏波起始的时间差作为充气时间的控制依据。
C.对心阻抗血流图中心脏收缩波和反搏波的波形峰值和持续时间进行检测,获取反映反搏疗效的客观指标。
D.计算机控制体外反搏装置的充气、排气时间。
2、根据权利要求1所述方法,其特征在于电极的设置为:阻抗电流电极一个位于左或右耳根部、或额头,一个位于胸骨剑突,阻抗探测电极一个位于锁骨下胸骨旁线上,一个位于第四、五肋间胸骨旁线上,自适应滤波将探测电极测量的血流阻抗信号作为原始输入信号,并在位于胸骨旁线腹缘处的一个新增电极与位于第四、五肋间处的阻抗探测电极之间获得阻抗参考输入信号。
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CA002095690A CA2095690C (en) | 1992-05-07 | 1993-05-06 | High efficiency external counter pulsation apparatus and method for controlling same |
EP93420182A EP0569308B1 (en) | 1992-05-07 | 1993-05-06 | A high efficiency external counter pulsation apparatus |
DE69333949T DE69333949D1 (de) | 1992-05-07 | 1993-05-06 | Hochleistungs-Gegenpulsationsapparat |
FI932059A FI110754B (fi) | 1992-05-07 | 1993-05-06 | Ulkoinen vastasykelaite sekä menetelmä tämän ohjaamiseksi |
AU38394/93A AU3839493A (en) | 1992-05-07 | 1993-05-06 | A high efficiency external counterpulsation apparatus and method for controlling same |
NO93931649A NO931649L (no) | 1992-05-07 | 1993-05-06 | Pulsator for aa utoeve mottrykk ved hjertepulsrytmen, og fremgangsmaate for reguleringen |
JP5131447A JPH06292721A (ja) | 1992-05-07 | 1993-05-07 | 高効率の外部カウンタパルセーション装置及びその制御方法 |
IL105633A IL105633A (en) | 1992-05-07 | 1993-05-07 | High efficiency external counterpulsation apparatus |
KR1019930007860A KR100274697B1 (en) | 1992-05-07 | 1993-05-07 | A high efficiency external counter pulsation apparatus and method for controlling same |
US08/396,261 US5554103A (en) | 1992-05-07 | 1995-02-27 | High efficiency external counterpulsation apparatus and method for controlling same |
AU10068/97A AU682647B2 (en) | 1992-05-07 | 1997-01-02 | A high efficiency external counterpulsation apparatus and method for controlling same |
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KR1019980016219A KR100274696B1 (ko) | 1992-05-07 | 1998-05-07 | 외부 카운터펄세이션 장치와 그 제어방법 |
US09/435,583 US6572621B1 (en) | 1992-05-07 | 1999-11-08 | High efficiency external counterpulsation apparatus and method for controlling same |
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CN 92209813 CN2138495Y (zh) | 1992-05-08 | 1992-05-08 | 一种体外反搏气源装置 |
CN92209589.2U CN2146246Y (zh) | 1992-05-08 | 1992-05-08 | 一种体外反搏囊套 |
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- 1993-05-06 FI FI932059A patent/FI110754B/fi not_active IP Right Cessation
- 1993-05-06 EP EP93420182A patent/EP0569308B1/en not_active Expired - Lifetime
- 1993-05-06 CA CA002095690A patent/CA2095690C/en not_active Expired - Fee Related
- 1993-05-06 DE DE69333949T patent/DE69333949D1/de not_active Expired - Lifetime
- 1993-05-06 NO NO93931649A patent/NO931649L/no not_active Application Discontinuation
- 1993-05-07 KR KR1019930007860A patent/KR100274697B1/ko not_active IP Right Cessation
- 1993-05-07 JP JP5131447A patent/JPH06292721A/ja active Pending
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1995
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1997
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1998
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1999
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Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
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WO2006114055A1 (fr) * | 2005-04-25 | 2006-11-02 | The First Affiliated Hospital, Sun Yat-Sen University | Systeme de traitement pour la sante et la readaptation des vaisseaux sanguins |
CN101690692B (zh) * | 2009-09-28 | 2011-06-29 | 山东碧通通信技术有限公司 | 一种自动计算并寻找最佳施加反搏压力时刻的方法 |
CN113018135A (zh) * | 2021-02-24 | 2021-06-25 | 山东交通学院 | 体外反搏协同控制系统及方法 |
CN113018135B (zh) * | 2021-02-24 | 2023-01-31 | 山东交通学院 | 体外反搏协同控制系统及方法 |
CN113925484A (zh) * | 2021-09-26 | 2022-01-14 | 深圳市千帆电子有限公司 | 血流动力测量方法及系统 |
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AU1006897A (en) | 1997-06-12 |
KR100274697B1 (en) | 2000-12-15 |
JPH06292721A (ja) | 1994-10-21 |
NO931649L (no) | 1993-11-08 |
CA2095690C (en) | 1999-01-12 |
US5554103A (en) | 1996-09-10 |
US5997540A (en) | 1999-12-07 |
FI932059A (fi) | 1993-11-08 |
AU682647B2 (en) | 1997-10-09 |
IL105633A (en) | 1997-04-15 |
KR940005293A (ko) | 1994-03-21 |
FI932059A0 (fi) | 1993-05-06 |
CA2095690A1 (en) | 1993-11-08 |
EP0569308A1 (en) | 1993-11-10 |
AU3839493A (en) | 1993-11-11 |
US6572621B1 (en) | 2003-06-03 |
EP0569308B1 (en) | 2005-12-28 |
DE69333949D1 (de) | 2006-02-02 |
KR100274696B1 (ko) | 2000-12-15 |
FI110754B (fi) | 2003-03-31 |
NO931649D0 (no) | 1993-05-06 |
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