CN1236597A - 遥测动态心功能自动分析系统及其测动态心动能方法 - Google Patents
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Abstract
一种遥测动态心功能自动分析系统,包括由信号采集器、放大器、A/D转换器、移频键控调制器、发射机连接组成的发射装置和一个由调频接收机、数字解调器、数据处理器、记录输出装置连接组成的接收装置、发射装置可由若干路组成,测动态心功能的方法仅测ECG和PCG就能直接查出PEP/LUET,测试方法简单,测试点清晰重复性强,并能早期或辅助诊断某些疾病并可作予后估计和分析,还可作为评价各种治疗方法及药物疗效指标。
Description
本发明涉及一种以诊断为目的测量装置,尤其涉及一种遥控测量动态心功能并能自动分析,例如:是否为心绞痛的测量分析装置,它是根据心脏收缩时间间期的变化与微电了计算机技术综合为一体的无创遥控检测仪器。
心脏病是常见的一种疾病,其死亡率比率较大,而心功能的好坏是反映心脏病轻重的重要标志,心脏病发作突然而剧烈。而现有的心脏监护诊断多为单信号的遥测或多导联的床边检查监测仪,如日本的DS880 Houlter等。由于存在信号单一,遥测距离近,检测范围小,只能用于对心律失常的监护与观察难以同时实施对多个病人、多个信号、多种功能的诊断、分析与观察。在最近虽然已有多功能(血压、脉搏、血氧、心率、呼吸)有线床边监护,但心功能的检测仍然依靠以阻抗的原理和以心电图、心音图、静动脉搏动图和心尖搏动图检测的多导生理记录仪,如西门子Mingo grat生理记录仪,其仪器笨重、价格昴贵、测量方法复杂,检测数据受外界干扰因素太多,且无法检测心绞痛,心脏收缩时间间期(PEP LVET)及心电图中的QTC JTC等各参数的随时记录,观察与诊断。
本发明目的在于:研制一种体积小、功耗小、双路信号传输与采集装置并使其随机性强,能随机地检测心功能和心绞痛有变化时的收缩时间间期,并能使用发射装置将心电图、心音图同时发射,使接收装置及时显示出,对人体无损害,对冠心病、心绞痛和心功能不全的患者的心功能能进行连续动态地观察,记录,打印与分析。还可对早期或辅助诊断某些疾病,以作出估计分析,以及评价各种治疗方法和药特疗效指标,和了解人体对各种不同状态和外界因素对心室收缩功能的影响。
本发明的又一个目的,研究一种同时供多个患者使用,并能减少外界干扰,一种遥测动态心功能自动分析系统。在测试方法上,使测量点清晰、重复性强、分辨力强、方便简单。
本发明是这样实现的:本系统是由发射装置和接收装置组成的。发射装置依次是由信号采集器、放大器、A/D转换器、移频键控调制器、发射机连接组成,发射机依次由放大器、振荡电路、倍频电路、功放连接组成。接收装置依次由调频接收器、数字解调器、数据处理器、记录输出装置连接组成。发射装置可由若干路组成,各路发射的频率不同,而接收装置分别依不同的频率将各路解调出来分别在记录输出装置中的显示屏上显示。
测动态心功方法为仅测心电图ECG和心音图PCG就能直接检查出心功能收缩时间比值PEP/LVET。
本发明和现有技术相比,具有的有益效果为:
1、本发明能适时、简便、敏感、准确的反应出心功能变化,可对危重病人的心功能进行连续动态的观测、记录、打印及分析。
2、可早期或辅助诊断某些疾病及作予后的估计分析,如冠心病人收缩时间比值PEP/LVET变化及其变化规律,可判定冠心病被阻塞的程度和心绞痛病人的严重程度,防止冠心病的漏治、漏诊与误治现象的出现,对心绞痛患者如果收缩时间比值PEP/LVET>0.5±0.09一般为死亡组,而PEP/LVET=0.4±0.05即为存活组,此分析能达到冠脉造影的目的。
3、可作为评价各种治疗方法和药物疗效的指标,如评价使用某种手术(如PTCA)或服用某种药物后心功能改善情况。
4、能了解机体对各种不同状态和外界因素对心室收缩功能的影响,如估价血透后心功能变化情况及高原环境对心脏功能的影响。
5、本发明采用数调式低频调制方法,可直接实现移频键控(FSK)而与传统的FSK直接调制或间接调制有区别,原来直接调制线路简单但由于数字信号直接加到变容二极管,虽实现简单,但会影响频率的稳定。而FSK间接调频,由于数字信号控制两个f1f2两个振荡器的切换,虽保障了载频的稳定,但增加了两个振荡器使用电路越显繁杂,而现用的数调式FSK调制方法减少了两个振荡器又保证了载频稳定性不受影响。
6、减少了外界干扰,因在采集器中增加了新设计的传感器抗干扰静音耗,它能减少传感器外界干扰,尤其是信号采集过程中的干扰。
7、采用了新的测定心功能方法,只测心电图ECG和心音图PCG。因此测量点清晰,重复性强,方法简单。为心功能,心绞痛诊断创造了条件,优于用心脏收缩间期Stl老方法,并省去只能在床边有线多路检测,利用ECG PCG CPW ACG同步测量方法,而且仪器贵重,且不能随机检测等问题。
8、本发明可以同时供多个病员使用,任一患者感到不适时均可通过本发明将患者ECG PCG信息及时传到计算机进行处理以判断患者心功能变化,同时为医务人员探寻心脑和种参数变化与病痛的联系提供了有利工具。
9、本发明采用CMOS器件设计的双路信号采集器,功耗低,输入电阻>10兆欧姆,因此漏电流小,对人体无伤害。类似无线测试装置相比信号丰富。
下面结合附图对实施例加以详述:
图1为本发明的方框图
图2为信号采集、A/D转换器电原理图
图3-1为发射机装置电原理图的左半部;
图3-2为发射机装置电原理图的右半部
图4-1为接收解调装置电原理图的左半部
图4-2为接收解调装置电原理图的右半部
如图1所示,当采集电路放到任一患者身上时,其患者的心音心电信号通过信号采集器变成电信号再经过A/D转换器变成数字信号进行移频键控(FSK)调制后送发射机发射出去,接收机将此接收到的调频信号变成数字信号(即数字解调)送到数据处理器(DPU)或计算机(CPU)进行处理并判断该患者心脑功能是否正常最后输出结果。
如图2所示P1,P2分别为输入的心电(ECG)和心音(PCG)信号,该信号经放大器放大后经A/D转换器(可用ADC0804)转换成数字信号再经单片机(可用8051)控制双路信号的切换控制A/D转换器工作并输出编码后的移频键控FSK信号,由P0输出到发射机部分的B1输入口。
如图3所示,依次由放大电路、振荡电路、倍频电路、功放和稳压电路组成,倍频电路是将晶体振荡器提供的较低频率的振荡信号变为满足通信要求超短波信号再经过功放发射到空中由发射天线T1发出去。
如图4所示为接收解调装置电路图,依次由放大器、振荡器、变频器、接收电路组件、放大解调部分组成。放大器将收到的信号放大,振荡器为变频器提供振荡源,用于下一步变频;接收电路组件再次变频并解调出移频键控FSK信号;放大解调器是将FSK信号变换成数字信号并送往计算机接口,具体通路为:图4中的A1接收到空中信号后将其放大,滤波由MC3357接收芯片解调出FSK信号送LM386放大,再由D8检波成高低电平的数字信号(串行)送S-OUT输出,该输出信号可送到计算机的并行口上,并行口读入计算机进行处理、显示、打印。
具体实施例主要技术指标:为通信是距离200M、监护病员8人信源组成ECG、PCG、传感器漏电流<0.5MA,输出数据PEP LVET数据分辨率1/28。
Claims (3)
1、一种遥测动态心功能自动分析系统,包括一外发射装置和一个接收装置其特征在于:发射装置依次由信号采集器、放大器、A/D转换器、移频键控,调制器、发射机连接组成,发射机又依次由放大器、振荡电路、倍频电路、功放组成;接收装置依次由调频接收器、数字解调器、数据处理器、记录输出装置组成;发射装置可由若干路组成,各路发射的频率不同,而接收装置依不同的频率将各路解调出来分别显示在记录输出装置中心显示屏上。
2、根据权利要求1所述的分析系统其特征在于:所述发射装置的采集器是双路信号采集器,是用CMOS器件制成的,输入电阻>10MΩ,采集器中的传感器有抗干扰静音耗。
3、如权利要求1所述分析系统的测试动态心功能的方法,其特征在于:测动态心功能仅测心电图的ECG,心音图的PCG就能直接查出心功能收缩时间比值PEP/LUET。
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Cited By (12)
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US8068906B2 (en) | 2004-06-21 | 2011-11-29 | Aorora Technologies Pty Ltd | Cardiac monitoring system |
US8233974B2 (en) | 1999-06-22 | 2012-07-31 | Impedimed Limited | Method and device for measuring tissue oedema |
US8700121B2 (en) | 2011-12-14 | 2014-04-15 | Intersection Medical, Inc. | Devices for determining the relative spatial change in subsurface resistivities across frequencies in tissue |
US8761870B2 (en) | 2006-05-30 | 2014-06-24 | Impedimed Limited | Impedance measurements |
US8781551B2 (en) | 2005-07-01 | 2014-07-15 | Impedimed Limited | Apparatus for connecting impedance measurement apparatus to an electrode |
US9504406B2 (en) | 2006-11-30 | 2016-11-29 | Impedimed Limited | Measurement apparatus |
US9615767B2 (en) | 2009-10-26 | 2017-04-11 | Impedimed Limited | Fluid level indicator determination |
US9615766B2 (en) | 2008-11-28 | 2017-04-11 | Impedimed Limited | Impedance measurement process |
US9724012B2 (en) | 2005-10-11 | 2017-08-08 | Impedimed Limited | Hydration status monitoring |
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US8233974B2 (en) | 1999-06-22 | 2012-07-31 | Impedimed Limited | Method and device for measuring tissue oedema |
US8068906B2 (en) | 2004-06-21 | 2011-11-29 | Aorora Technologies Pty Ltd | Cardiac monitoring system |
US8509886B2 (en) | 2004-06-21 | 2013-08-13 | Aorora Technologies Pty Ltd | Cardiac monitoring system |
US11737678B2 (en) | 2005-07-01 | 2023-08-29 | Impedimed Limited | Monitoring system |
US8781551B2 (en) | 2005-07-01 | 2014-07-15 | Impedimed Limited | Apparatus for connecting impedance measurement apparatus to an electrode |
US11660013B2 (en) | 2005-07-01 | 2023-05-30 | Impedimed Limited | Monitoring system |
US9724012B2 (en) | 2005-10-11 | 2017-08-08 | Impedimed Limited | Hydration status monitoring |
US11612332B2 (en) | 2005-10-11 | 2023-03-28 | Impedimed Limited | Hydration status monitoring |
US8761870B2 (en) | 2006-05-30 | 2014-06-24 | Impedimed Limited | Impedance measurements |
US9504406B2 (en) | 2006-11-30 | 2016-11-29 | Impedimed Limited | Measurement apparatus |
US10307074B2 (en) | 2007-04-20 | 2019-06-04 | Impedimed Limited | Monitoring system and probe |
US9615766B2 (en) | 2008-11-28 | 2017-04-11 | Impedimed Limited | Impedance measurement process |
US9615767B2 (en) | 2009-10-26 | 2017-04-11 | Impedimed Limited | Fluid level indicator determination |
US8700121B2 (en) | 2011-12-14 | 2014-04-15 | Intersection Medical, Inc. | Devices for determining the relative spatial change in subsurface resistivities across frequencies in tissue |
US9149225B2 (en) | 2011-12-14 | 2015-10-06 | Intesection Medical, Inc. | Methods for determining the relative spatial change in subsurface resistivities across frequencies in tissue |
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