技术领域technical field
本发明属于医疗器械技术领域，特别涉及一种基于蓝牙的便携式心脏除颤器。The invention belongs to the technical field of medical devices, in particular to a portable heart defibrillator based on bluetooth.
背景技术Background technique
“室颤”这个名词其实由来已久，人们对它的认识和了解也越来越全面。有许多科学家做出了突出贡献。早期的除颤可以追溯到1882年，美国科学家Battelli和Prevost通过实验证实，高强度的交流电对除颤有很大帮助。1887年Mcwilliam用诱导的对心脏的直接电击消除了处于氯仿麻醉下的室颤，尽管当时还未能用心电图(Electrocardiogram，ECG)记录到室颤。1938年，Beck和Wiggers对狗进行了电除颤的实验，并取得成功；真正临床应用始于1947年，Beck用交流电击消除麻醉下的室颤，而在1956年Zoll采用经胸电击救治病人。而沿用至今的直流电击则是1962年Lown引入的，第一台直流电除颤器问世。1982年，半自动除颤器投入使用。90年代，埋藏式心律转复除颤器(Implantable CardioverterDefibrillator，ICD)问世并应用于临床。The term "ventricular fibrillation" has actually been around for a long time, and people's knowledge and understanding of it is becoming more and more comprehensive. There are many scientists who have made outstanding contributions. Early defibrillation can be traced back to 1882. American scientists Battelli and Prevost confirmed through experiments that high-intensity alternating current is of great help to defibrillation. In 1887, Mcwilliam eliminated ventricular fibrillation under chloroform anesthesia by inducing direct electric shock to the heart, although it could not be recorded by electrocardiogram (ECG) at that time. In 1938, Beck and Wiggers experimented with electrical defibrillation on dogs and achieved success; the real clinical application began in 1947, when Beck used AC electric shock to eliminate ventricular fibrillation under anesthesia, and in 1956 Zoll used transthoracic electric shock to treat patients . The DC shock that is still used today was introduced by Lown in 1962, and the first DC defibrillator came out. In 1982, the semi-automatic defibrillator became available. In the 1990s, the implantable cardioverter defibrillator (Implantable Cardioverter Defibrillator, ICD) came out and was used clinically.
心脏除颤器是生物，医学，信号处理、工程等的结合体，涉及面很广，如心脏颤动的机制及除颤机制；除颤波形；心电信号的预处理以及特征波形的识别；除颤波形的实现等几个方面。自动体外除颤器(Automated External Defibrillator，AED)是在上个世纪80年代才研发成功并开始投入使用。到现在AED的生产厂家有很多，样式和功能的多少都不尽相同，但是有一点是一样的，那就是能量释放的方式。几乎所有AED产品都是以“波”的形式释放能量，但是按照波的分类，可以将目前的AED分为两种类型：单相波和双相波，后者是当前除颤领域的研究热点，其原因是其在除颤时，可以控制电流强度，有效的避免电流过大，对人体造成不必要的伤害。其实这种除颤波形就是一个双向脉冲，这个脉冲由电流调节，它的特点是方向在一段时间内是正向的，而在剩余的数毫秒内电流方向变成相反方向，这种对电流方向的有效控制大大提高了AED的安全性。除了安全因素外，在相同除颤效果的情况下，双相除颤波形所需要的能量几乎是单相波形的1/2。在医院内，对室颤患者分别用两种波形除颤的临床试验说明，单相波除颤器用200焦耳能量得到的除颤效果，双相波只需要110～130焦耳，而且双相波对心电图ST波段的改变较小。Cardiac defibrillator is a combination of biology, medicine, signal processing, engineering, etc. It involves a wide range of areas, such as the mechanism of heart fibrillation and defibrillation mechanism; defibrillation waveform; preprocessing of ECG signals and identification of characteristic waveforms; There are several aspects such as the realization of trembling waveform. The Automated External Defibrillator (AED) was successfully developed and put into use in the 1980s. Up to now, there are many manufacturers of AEDs, with different styles and functions, but one thing is the same, that is, the way of energy release. Almost all AED products release energy in the form of "waves", but according to the classification of waves, current AEDs can be divided into two types: monophasic waves and biphasic waves, the latter being the current research focus in the field of defibrillation , the reason is that it can control the current intensity during defibrillation, effectively avoiding excessive current and causing unnecessary damage to the human body. In fact, this defibrillation waveform is a bidirectional pulse, which is regulated by the current. Its characteristic is that the direction is positive for a period of time, and the direction of the current changes to the opposite direction in the remaining milliseconds. Effective control greatly improves the safety of the AED. In addition to the safety factor, under the condition of the same defibrillation effect, the energy required by the biphasic defibrillation waveform is almost 1/2 of that of the monophasic waveform. In the hospital, the clinical trials of using two waveforms to defibrillate patients with ventricular fibrillation showed that the defibrillation effect obtained by the monophasic wave defibrillator with 200 joules of energy, the biphasic wave only needs 110-130 joules, and the biphasic wave has no effect on the electrocardiogram. The changes in the ST band are minor.
国内的该产品的相关研究才刚刚起步，限制了该类产品在国内临床上面的推广和应用，单纯的依靠进口也不是办法。所以我们希望搭建一套简易的除颤系统，实现其基本功能，为其他嵌入式除颤产品提供一些有价值的参考。Domestic research on this product has just started, which limits the promotion and application of this type of product in domestic clinical practice, and simply relying on imports is not an option. So we hope to build a simple defibrillation system to realize its basic functions and provide some valuable references for other embedded defibrillation products.
发明内容Contents of the invention
本发明的目的是克服现有心脏除颤器心电信号采集不稳定，滤波效果差的缺陷，提供了一种基于蓝牙的便携式心脏除颤器。The purpose of the present invention is to overcome the defects of unstable electrocardiographic signal acquisition and poor filtering effect of the existing cardiac defibrillator, and provide a portable cardiac defibrillator based on bluetooth.
本发明提供的技术方案为：The technical scheme provided by the invention is:
一种基于蓝牙的便携式心脏除颤器，包括：A Bluetooth-based portable cardiac defibrillator comprising:
控制器；controller;
心电采集模块，用于采集心电信号，所述心电采集模块通过A/D转换器与控制器连接，以将心电模拟信号转换为心电数字信号并传递给控制器；An electrocardiographic acquisition module is used to acquire electrocardiographic signals, and the electrocardiographic acquisition module is connected with the controller through an A/D converter to convert the electrocardiographic analog signals into electrocardiographic digital signals and transmit them to the controller;
蓝牙模块，其与控制器连接，用于与手机进行无线数据传输；Bluetooth module, which is connected with the controller for wireless data transmission with the mobile phone;
充放电模块，其与所述控制器连接，在所述控制其控制下进行充电后对人体电击除颤；The charging and discharging module is connected to the controller, and after being charged under the control of the controller, it defibrillates the human body by electric shock;
其中，所述控制器将获取的心电数字信号x(i)进行滤波，得到滤波后心电信号y(i)Wherein, the controller filters the acquired ECG digital signal x(i) to obtain the filtered ECG signal y(i)
其中，x(i)为第i个采样点原始心电信号，y(i)为滤波后第i个采样点心电信号，TL为第一阈值，TH为第二阈值，λ为常数；Wherein, x (i) is the original ECG signal of the i sampling point, y (i) is the i sampling point ECG signal after filtering, TL is the first threshold,TH is the second threshold, and λ is a constant;
所述充放电模块根据患者身高a，体重b，年龄c以及身体健康指数d，释放相应的电击电压vThe charging and discharging module releases the corresponding shock voltage v according to the patient's height a, weight b, age c and body health index d
其中，V0为标准电击电压。Among them, V0 is the standard electric shock voltage.
优选的是，所述控制器采用STM32F103ZET6芯片，并且包括复位电路和外部时钟电路。Preferably, the controller adopts STM32F103ZET6 chip, and includes a reset circuit and an external clock circuit.
优选的是，所述蓝牙模块采用AD8232芯片。Preferably, the Bluetooth module adopts AD8232 chip.
优选的是，所述充放电模块包括依次连接的电源模块、逆变电路、升压整流电路、以及电容充电电路。Preferably, the charging and discharging module includes a power module, an inverter circuit, a boost rectification circuit, and a capacitor charging circuit connected in sequence.
优选的是，所述电源模块能够输出24V、9V和5V直流电。Preferably, the power supply module can output 24V, 9V and 5V direct current.
优选的是，所述电容充电电路上设置有三个并联的充电电容。Preferably, the capacitor charging circuit is provided with three parallel charging capacitors.
优选的是，所述充放电模块还包括电压检测电路。Preferably, the charging and discharging module further includes a voltage detection circuit.
一种基于蓝牙的便携式心脏除颤器的心电信号采集方法，包括如下步骤：A kind of electrocardiographic signal acquisition method based on bluetooth portable heart defibrillator, comprises the steps:
步骤一、通过心电采集模块采集心电模拟信号X(t)；Step 1, collecting the analog ECG signal X(t) through the ECG acquisition module;
步骤二、通过A/D转换器将心电模拟信号X(t)转换为心电数字信号x(i)，并将心电数字信号x(i)传递给控制器；Step 2, converting the analog ECG signal X(t) into a digital ECG signal x(i) through an A/D converter, and transmitting the digital ECG signal x(i) to the controller;
步骤三、所述控制器对心电数字信号x(i)进行滤波，得到滤波后的心电信号y(i)Step 3, the controller filters the ECG digital signal x(i) to obtain the filtered ECG signal y(i)
其中，x(i)为第i个采样点原始心电信号，y(i)为滤波后第i个采样点心电信号，TL为第一阈值，TH为第二阈值，λ为常数。Among them, x(i) is the original ECG signal of the i-th sampling point, y(i) is the filtered ECG signal of the i-th sampling point, TL is the first threshold,TH is the second threshold, and λ is a constant.
本发明的有益效果体现在以下方面：The beneficial effects of the present invention are reflected in the following aspects:
(1)低压电池供电再升到高压对电容进行充电，可实现高压快速充电且便于携带或在公共场所存放。设计电路可在小面积电路板上实现出来，所以整体设计小巧便捷，心电采集部分配带有电极夹，可与人体稳固接触。因此具有使用方便、便于携带、简单实用的优点。(1) The low-voltage battery is powered and then raised to a high voltage to charge the capacitor, which can realize high-voltage fast charging and is easy to carry or store in public places. The design circuit can be implemented on a small-area circuit board, so the overall design is compact and convenient. The ECG collection part is equipped with electrode clips, which can be in stable contact with the human body. Therefore, it has the advantages of convenient use, portability, simplicity and practicality.
(2)与传统心脏除颤器相比，本发明的优点是装有蓝牙发送模块可将检测到的实时数据发送到手机，便于现场人员将手机上信号发送到云端以方便下载或者发送到医院工作室由医学专家进行数据分析，这样无论病人是室颤还是其他的疾病都可以及时作出判断并进行救治。(2) Compared with the traditional cardiac defibrillator, the advantage of the present invention is that the bluetooth sending module is installed to send the detected real-time data to the mobile phone, which is convenient for field personnel to send the signal on the mobile phone to the cloud for easy downloading or sending to the hospital In the studio, medical experts conduct data analysis, so that no matter whether the patient has ventricular fibrillation or other diseases, they can make timely judgments and treat them.
(3)本发明采用了AD8232较高的截止频率以及极大地改善共模抑制性能，这会使ECG信号得以更快地恢复稳定，从而心电信号的采集需要克服外界的诸多干扰，得到正确稳定的心电信号。(3) The present invention adopts the higher cut-off frequency of AD8232 and greatly improves the common-mode rejection performance, which will allow the ECG signal to recover and stabilize more quickly, so that the acquisition of the ECG signal needs to overcome many external interferences to obtain correct and stable ECG signal.
综上，与现有的便携式心脏除颤器相比，本发明将蓝牙通信技术与先进的采集电路相集成，可以得到正确的心电信号，并能够将数据发送到手机上。To sum up, compared with the existing portable cardiac defibrillator, the present invention integrates the bluetooth communication technology and the advanced acquisition circuit, can obtain the correct electrocardiogram signal, and can send the data to the mobile phone.
附图说明Description of drawings
图1为本发明所述的基于蓝牙的便携式心脏除颤器总体结构示意图。FIG. 1 is a schematic diagram of the general structure of the Bluetooth-based portable cardiac defibrillator of the present invention.
图2为本发明所述的复位电路示意图。FIG. 2 is a schematic diagram of a reset circuit according to the present invention.
图3为本发明所述的外部时钟电路示意图。FIG. 3 is a schematic diagram of an external clock circuit according to the present invention.
图4为本发明所述的STM32F103ZET6最小系统电路示意图。FIG. 4 is a schematic diagram of the minimum system circuit of STM32F103ZET6 according to the present invention.
图5为本发明所述的心电采集电路示意图。Fig. 5 is a schematic diagram of the ECG acquisition circuit according to the present invention.
图6为本发明所述的蓝牙电路示意图。FIG. 6 is a schematic diagram of the bluetooth circuit of the present invention.
图7为本发明所述的电源电路示意图。Fig. 7 is a schematic diagram of the power circuit of the present invention.
图8为本发明所述的逆变电路示意图。Fig. 8 is a schematic diagram of an inverter circuit according to the present invention.
图9为本发明所述的升压、整流电路示意图。Fig. 9 is a schematic diagram of a boosting and rectifying circuit according to the present invention.
图10为本发明所述的电容充电电路示意图。FIG. 10 is a schematic diagram of a capacitor charging circuit according to the present invention.
图11为本发明所述的电压检测电路Fig. 11 is the voltage detection circuit of the present invention
图12为本发明所述的主程序流程图。Fig. 12 is a flow chart of the main program of the present invention.
图13为本发明所述的客户端应用程序流程图。Fig. 13 is a flowchart of the client application program of the present invention.
图14为本发明所述的正常心电波形示意图。Fig. 14 is a schematic diagram of a normal ECG waveform according to the present invention.
图15为本发明所述的较大干扰时心电波形示意图。Fig. 15 is a schematic diagram of an electrocardiogram waveform during a large disturbance according to the present invention.
具体实施方式detailed description
下面结合附图对本发明做进一步的详细说明，以令本领域技术人员参照说明书文字能够据以实施。The present invention will be further described in detail below in conjunction with the accompanying drawings, so that those skilled in the art can implement it with reference to the description.
如图1所示，本发明提供一种基于蓝牙的便携式心脏除颤器，包括控制器110、心电采集模块120、蓝牙模块130、充放电模块140、A/D转换器150、显示电路160、按键电路170。As shown in Figure 1, the present invention provides a portable cardiac defibrillator based on Bluetooth, including a controller 110, an ECG acquisition module 120, a Bluetooth module 130, a charging and discharging module 140, an A/D converter 150, and a display circuit 160 1. Button circuit 170.
其中，所述控制器110选用STM32F103ZET6芯片，该控制器为32位微处理器，处理速度快，功能齐全。Wherein, the controller 110 selects STM32F103ZET6 chip, which is a 32-bit microprocessor with fast processing speed and complete functions.
便携式心脏除颤器的整体结构是由控制器110控制心电采集模块120采集人体心电信号并实现放大滤波，采集到心电信号之后通过蓝牙模块130在智能手机180上显示心电波形，根据波形判断如果发生室颤则给充放电模块140充电后对人体190电击除颤。The overall structure of the portable cardiac defibrillator is that the controller 110 controls the ECG acquisition module 120 to collect human ECG signals and realize amplification and filtering. After the ECG signals are collected, the ECG waveform is displayed on the smart phone 180 through the Bluetooth module 130. According to Waveform judgment If ventricular fibrillation occurs, the charging and discharging module 140 will be charged and then the human body 190 will be defibrillated by electric shock.
所述控制器110包括复位电路、外部时钟电路、最小系统电路。The controller 110 includes a reset circuit, an external clock circuit, and a minimum system circuit.
复位电路则主要用来进行STM32F103ZET6最小系统、射频模块、液晶显示等多个电路的复位。The reset circuit is mainly used to reset the STM32F103ZET6 minimum system, radio frequency module, liquid crystal display and other circuits.
如图2所示，本发明采用按键复位的方式，当开关按钮S1按下时，RESET引脚与地相连通，其电平被拉低实现单片机的复位。当S1断开，RESET电平重新变高，控制器从复位模式转为正常工作模式。电容C26的存在可以消除杂波、干扰使得复位电路更加可靠，不会因为外界干扰使单片机频繁复位。As shown in FIG. 2 , the present invention adopts a button reset method. When the switch button S1 is pressed, the RESET pin is connected to the ground, and its level is pulled down to reset the single-chip microcomputer. When S1 is disconnected, the RESET level becomes high again, and the controller changes from the reset mode to the normal working mode. The presence of capacitor C26 can eliminate clutter and interference, making the reset circuit more reliable, and will not cause the microcontroller to reset frequently due to external interference.
如图3所示，在STM32F103ZET6的系统中，有5个时钟源，分别为HSI高速内部时钟、HSE高速外部时钟、LSI低速内部时钟、LSE低速外部时钟、PLL锁相环倍频输出，在本设计中，仅需要对其两个外部时钟电路进行设计，实际的高速外部时钟既可接石英/陶瓷谐振器，又可接外部时钟源，频率范围一般为4MHz-16MHz，本设计中采用的是8MHz晶振，经过系统内部倍频后可升至72MHz，而低速外部时钟则主要是用来做RTC的时钟源，设计中连接的是32.768KHz晶振。As shown in Figure 3, in the STM32F103ZET6 system, there are five clock sources, which are HSI high-speed internal clock, HSE high-speed external clock, LSI low-speed internal clock, LSE low-speed external clock, and PLL phase-locked loop frequency multiplication output. In the design, only two external clock circuits need to be designed. The actual high-speed external clock can be connected to both a quartz/ceramic resonator and an external clock source. The frequency range is generally 4MHz-16MHz. In this design, the The 8MHz crystal oscillator can be increased to 72MHz after the internal frequency multiplication of the system, while the low-speed external clock is mainly used as the clock source of the RTC, and the 32.768KHz crystal oscillator is connected in the design.
如图4所示，STM32F103ZET6最小系统设计主要由STM32F103ZET6芯片电路、复位电路、外部高速时钟电路、外部低速时钟电路四部分电路设计组成。根据整个系统设计所需的电路的功能及连接方式，来进行STM32F103ZET6芯片相应I/O口的分配，以实现整体系统设计的合理性与可靠性。As shown in Figure 4, the minimum system design of STM32F103ZET6 is mainly composed of four parts: STM32F103ZET6 chip circuit, reset circuit, external high-speed clock circuit, and external low-speed clock circuit. According to the function and connection mode of the circuit required by the whole system design, the allocation of the corresponding I/O port of the STM32F103ZET6 chip is carried out, so as to realize the rationality and reliability of the overall system design.
所述心电采集模块120选用AD8232芯片，AD8232是一款用于ECG及其他生物电测量应用的集成信号调理模块。该器件设计用于在具有运动或远程电极放置产生的噪声的情况下提取、放大及过滤微弱的生物电信号。该设计使得超低功耗模数转换器(ADC)或嵌入式控制器能够轻松地采集输出信号。The ECG acquisition module 120 uses the AD8232 chip, which is an integrated signal conditioning module for ECG and other bioelectric measurement applications. The device is designed to extract, amplify, and filter weak bioelectrical signals in the presence of noise from motion or remote electrode placement. This design enables an ultra-low power analog-to-digital converter (ADC) or embedded controller to easily acquire the output signal.
AD8232是一款集成前端，适用于对心脏生物电信号进行信号调理来进行心率监护。它内置一个专用仪表放大器、一个运算放大器、一个右腿驱动放大器和一个中间电源电压基准电压缓冲器。The AD8232 is an integrated front end for signal conditioning of cardiac bioelectrical signals for heart rate monitoring. It contains a dedicated instrumentation amplifier, an operational amplifier, a right leg drive amplifier, and a mid-supply voltage reference buffer.
此外，AD8232内置导联脱落检测电路和一个自动快速恢复电路，该电路可在导联重新连接后迅速恢复信号。传统的ECG前端因半电池电位而存在增益限制，这款仪表放大器则不同，它采用间接电流反馈架构和集成隔直放大器，不仅可以提供输出直流电平反馈(信号增益可达100)，而且可以抑制来自电极的失调，却不会造成内部节点饱和。In addition, the AD8232 includes lead-off detection circuitry and an automatic fast recovery circuit that quickly restores the signal after a lead is reconnected. Unlike traditional ECG front-ends which are gain limited due to the half-cell potential, this in-amp uses an indirect current feedback architecture and an integrated DC blocking amplifier to provide output DC level feedback (signal gain up to 100) and suppress Offset from electrodes without saturating internal nodes.
AD8232通过给仪表放大器输入端提供一个100kHz的小电流源来检测电极何时断开。此电流通过外部电阻从IN+流入IN-并在输入端产生一个差分电压，然后该电压经同步检测并与内部阈值进行比较。这两个外部电阻的建议值为10MΩ。较低的电阻值会使差分压降过低而无法检测，同时会降低放大器的输入阻抗。The AD8232 detects when the electrode is disconnected by supplying a small 100kHz current source to the input of the instrumentation amplifier. This current flows from IN+ to IN- through an external resistor and produces a differential voltage at the input, which is then synchronously sensed and compared to an internal threshold. The recommended value for these two external resistors is 10MΩ. Lower resistor values will make the differential voltage drop too low to detect and will lower the amplifier's input impedance.
与直流导联脱落检测模式相反，AD8232只能确定有电极失去连接，但无法确定具体电极。这种情况下，LOD+引脚变为高电平。该模式中，LOD-引脚未使用并一直保持逻辑低电平状态。若要使用交流导联脱落模式，应将AC/DC引脚接正供电轨。Contrary to the dc leads-off detection mode, the AD8232 can only determine that an electrode has lost its connection, but not the specific electrode. In this case, the LOD+ pin goes high. In this mode, the LOD- pin is not used and remains in a logic low state. To use AC lead-off mode, tie the AC/DC pin to the positive rail.
AD8232中的仪表放大器设计用于施加增益并同时滤除近直流信号。这使得它能够将小ECG信号放大100倍，同时抑制高达±300mV的电极失调。为实现失调抑制，应在仪表放大器的输出端、HPSENSE和HPDRIVE之间连接一个RC网络，该RC网络构成一个积分器，用于将任何近直流信号反馈给仪表放大器，从而消除失调，而又不会造成任何节点出现饱和，并同时保持高信号增益。除阻止仪表放大器输入端上的失调以外，该积分器还用作高通滤波器，用于将基线漂移等慢速变化信号的影响降至最低。该滤波器的截止频率计算公式如下：The instrumentation amplifier in the AD8232 is designed to apply gain while filtering near dc signals. This enables it to amplify small ECG signals by a factor of 100 while rejecting electrode offsets up to ±300mV. For offset suppression, an RC network should be connected between the output of the in-amp, HPSENSE, and HPDRIVE. This RC network forms an integrator that feeds any near-dc signal back to the in-amp, thereby canceling the offset without Will cause any node to become saturated while maintaining high signal gain. In addition to blocking offsets at the input of the in-amp, the integrator acts as a high-pass filter to minimize the effects of slowly changing signals such as baseline drift. The formula for calculating the cutoff frequency of this filter is as follows:
其中，R的单位为欧姆，C的单位为法拉。注意，滤波器截止频率比通常预计的单极点滤波器要高100倍。由于仪表放大器的反馈架构，因此需使用仪表放大器的100增益对典型的滤波器截止频率公式进行修改。Among them, the unit of R is ohm, and the unit of C is farad. Note that the filter cutoff frequency is 100 times higher than would normally be expected for a single-pole filter. Because of the feedback architecture of the in-amp, the typical filter cutoff frequency equation needs to be modified using a gain of 100 for the in-amp.
就与任何具有低截止频率的高通滤波器一样，直流失调上的任何快速变化都需要很长时间来建立。如果此类变化造成仪表放大器输出端出现饱和，S1开关会短暂使能10kΩ电阻路劲，从而使截止频率变为：As with any high-pass filter with a low cutoff frequency, any rapid change in dc offset takes a long time to settle. If such a change causes saturation at the in-amp output, the S1 switch briefly enables the 10kΩ resistor path so that the cutoff frequency becomes:
当R值大于100kΩ时，表达式可以近似表示为：When the R value is greater than 100kΩ, the expression can be approximated as:
较高的截止频率会缩短建立时间，从而使ECG信号得以更快地恢复。A higher cutoff frequency reduces settling time, allowing for faster recovery of the ECG signal.
驱动导联(或参考电极)通常用于将电源线及其它干扰源引入的共模电压影响降至最低。AD8232从仪表放大器的输入端提取共模电压，然后通过RLD放大器提供，以驱动相反信号进入患者体内。该功能使患者和AD8232之间的电压几乎保持恒定，从而极大地改善共模抑制性能。AD8232利用一个积分器来驱动该电极，该积分器由一个内部150kΩ电阻和一个外部电容组成。A driven lead (or reference electrode) is often used to minimize the effects of common-mode voltages introduced by power lines and other sources of interference. The AD8232 extracts the common-mode voltage from the input of the instrumentation amplifier and provides it through the RLD amplifier to drive the opposite signal into the patient. This feature keeps the voltage between the patient and the AD8232 nearly constant, greatly improving common-mode rejection. The AD8232 drives this electrode with an integrator consisting of an internal 150kΩ resistor and an external capacitor.
如图5所示，心电放大滤波电路0.5～30Hz，用户手臂和上身运动会产生较大的运动伪像，并且长引线使得系统非常容易受到共模干扰影响。需要具有极窄的带通特性，以便将心脏信号与干扰信号区分开来。此电路通过滤波可以消除其它噪音。As shown in Figure 5, the ECG amplification filter circuit is 0.5-30Hz, and the movement of the user's arms and upper body will produce large motion artifacts, and the long leads make the system very susceptible to common-mode interference. An extremely narrow bandpass characteristic is required to separate the cardiac signal from interfering signals. This circuit eliminates other noise by filtering.
蓝牙4.0技术在2010更新的新型短距离通信技术，与其他相似的短距离通讯技术相比有诸多优点，比如：功耗低、体积小、速度快、抗干扰能力强等。利用蓝牙4.0能够快速有效的与智能手机终端设备进行通讯。Bluetooth 4.0 technology is a new short-distance communication technology updated in 2010. Compared with other similar short-distance communication technologies, it has many advantages, such as: low power consumption, small size, fast speed, and strong anti-interference ability. Using Bluetooth 4.0 can quickly and effectively communicate with smart phone terminal equipment.
如图6所示，蓝牙模块130采用HM-13系列蓝牙模块，此种模块采用CSR双模蓝牙芯片，配合ARM构架单片机，支持AT指令，用户可根据需要串口波特率、设备名称、配对密码等参数，使用灵活。As shown in Figure 6, the Bluetooth module 130 uses the HM-13 series Bluetooth module. This module uses a CSR dual-mode Bluetooth chip, cooperates with an ARM-based microcontroller, and supports AT commands. and other parameters, flexible to use.
心电信号通过心电采集模块120采集到以后，将心电信号连接到HM-13蓝牙模块120自带的A/D转换传到HM-13蓝牙模块130处理将心电数据转换、处理、发送。在本设计中系统开启之后，智能手机不断的监听本地的蓝牙端口，检测到心电采集模块就可以实现配对，按下开始按钮，通过蓝牙接收献点采集模块发来的数据在智能手机上进行显示出实时的心电波形。检测出来的波形存储在手机中，可将数据内容实时上传到云空间，医务人员可通过云空间查看病人的心电波形图。After the ECG signal is collected by the ECG acquisition module 120, the ECG signal is connected to the A/D conversion of the HM-13 Bluetooth module 120 and transmitted to the HM-13 Bluetooth module 130 for processing. The ECG data is converted, processed, and sent . After the system is turned on in this design, the smartphone monitors the local bluetooth port constantly, detects that the ECG acquisition module can be paired, and presses the start button to receive the data sent by the point collection module through bluetooth to be processed on the smartphone. Display real-time ECG waveform. The detected waveform is stored in the mobile phone, and the data content can be uploaded to the cloud space in real time, and the medical staff can view the patient's ECG waveform through the cloud space.
如图7所示，本发明提供的便携式心脏除颤器还包括电源电路，其采用一块24V电池来给系统供电，其中，7809可以得到9V的稳定电压，而7805可以提供5V稳定的电压。As shown in Figure 7, the portable cardiac defibrillator provided by the present invention also includes a power supply circuit, which uses a 24V battery to supply power to the system, wherein the 7809 can obtain a stable voltage of 9V, and the 7805 can provide a stable voltage of 5V.
如图8所示，逆变部分采用H桥电路，实现把直流24V电源逆变成交流电。如图8所示为H桥逆变电路部分。其中，24V为直流电源部分电源，PWM1和PWM2为逆变控制器的输出，本设计中，逆变控制器采用STC52单片机来实现，通过定时改变输出口电平，通过单片机的P1.0口、P1.1口来实现输出PWM波。out1和out2端接入下一级升压部分。As shown in Figure 8, the inverter part uses an H-bridge circuit to realize the inversion of the DC 24V power supply into AC power. As shown in Figure 8, it is part of the H-bridge inverter circuit. Among them, 24V is the power supply of the DC power supply, PWM1 and PWM2 are the output of the inverter controller. In this design, the inverter controller is realized by STC52 single-chip microcomputer, and the level of the output port is changed regularly, through the P1.0 port of the single-chip microcomputer, P1.1 port to realize the output PWM wave. The out1 and out2 terminals are connected to the next step-up part.
Q1、Q2为IRF4905PMOS管，IR的第五代HEXFETs功率场效应管IRF4905采用先进的工艺技术制造，具有极低的导通阻抗。Q1 and Q2 are IRF4905 PMOS transistors. IR's fifth-generation HEXFETs power field effect transistor IRF4905 is manufactured with advanced technology and has extremely low on-resistance.
Q3、Q4为IRF3205NMOS管，IR的HEXFET功率场效应管IRF3205采用先进的工艺技术制造，具有极低的导通阻抗。IRF4905和IRF3205这种特性，加上快速的转换速率，和以坚固耐用著称的HEXFET设计，使得IRF4905和IRF3205成为极其高效可靠、应用范围超广的器件。Q3 and Q4 are IRF3205NMOS tubes. IR's HEXFET power field effect tube IRF3205 is manufactured with advanced technology and has extremely low conduction resistance. This feature of the IRF4905 and IRF3205, together with the fast slew rate and the well-known rugged HEXFET design, make the IRF4905 and IRF3205 extremely efficient and reliable devices for a wide range of applications.
Q5、Q6为IRF540NMOS管，使用沟渠工艺封装的N通道增强型场效应功率晶体管应用：DC到DC转换器开关电源；电视及电脑显示器电源。Q5 and Q6 are IRF540NMOS transistors, N-channel enhanced field effect power transistors packaged by trench technology Applications: DC to DC converter switching power supply; TV and computer monitor power supply.
Q1、Q2、Q3、Q4构成H桥逆变电路，Q5、Q6和分压电阻构成PMOS管的驱动电路，根据电路图的设计，IRF4905的导通电压为19V，截止电压为24V，IRF3205的导通电压为5V，IRF540的导通电压为5V，所以本发明采用上图的驱动。Q1, Q2, Q3, and Q4 constitute the H-bridge inverter circuit, and Q5, Q6 and voltage dividing resistors constitute the driving circuit of the PMOS transistor. According to the design of the circuit diagram, the conduction voltage of IRF4905 is 19V, the cut-off voltage is 24V, and the conduction of IRF3205 The voltage is 5V, and the turn-on voltage of IRF540 is 5V, so this invention adopts the drive in the above figure.
如图9所示，out1和out2的输出电流经过电感L滤波后由升压变压器进行升压，之后经整流滤波电路作用后，out3和out4输出直流。As shown in Figure 9, the output currents of out1 and out2 are filtered by the inductor L and then boosted by the step-up transformer, and then the output currents of out3 and out4 output DC after being acted on by the rectification and filtering circuit.
如图10所示，电容充电电路中采用电容并联，保证电容的耐压值，增大电容的容量，同样也可以使用电容并联，牺牲电容容量以提升耐压值，因为本设计中变压器升压能力有限故，无需提高耐压值，仅采用电容并联实现电能的储存。电压为376V。As shown in Figure 10, capacitors are connected in parallel in the capacitor charging circuit to ensure the withstand voltage value of the capacitor and increase the capacity of the capacitor. Similarly, parallel capacitors can be used to sacrifice the capacitor capacity to increase the withstand voltage value, because the transformer in this design boosts the voltage Due to the limited capacity, there is no need to increase the withstand voltage value, and only the parallel connection of capacitors is used to realize the storage of electric energy. The voltage is 376V.
为达到能量需求，即放电能量达到200J左右，需要1.1mf的电容，故采用3个470uf电容串联实现。out3、out4为前一极升压部分的输出，out5、out6作为点击部分输出，out7、out8作为电容电压检测信号相控制器部分实时采集数据。In order to meet the energy demand, that is, the discharge energy reaches about 200J, a capacitor of 1.1mf is needed, so three 470uf capacitors are used in series to realize. out3 and out4 are the output of the boost part of the previous pole, out5 and out6 are the output of the click part, and out7 and out8 are used as the capacitor voltage detection signal phase controller to collect data in real time.
如图11所示，电压检测部分主要是检测电容充电时的实时电压，out7和out8是上一级电容两侧电压通过U1光电耦合器将电压信号转到运放端将信号放大后，确保输出在0-3.3V之间。选择光电耦合器是因为电容侧的电压与控制侧的电压不共地，所以不能直接检测。Port为检测电压输出，接入控制器。As shown in Figure 11, the voltage detection part is mainly to detect the real-time voltage when the capacitor is charged. out7 and out8 are the voltages on both sides of the upper capacitor. Between 0-3.3V. The optocoupler is chosen because the voltage on the capacitor side and the voltage on the control side are not in the same ground, so they cannot be directly detected. Port is the detection voltage output, connected to the controller.
本发明还提供了一种基于蓝牙的便携式心脏除颤器的心电信号采集方法，包括如下步骤：The present invention also provides a method for collecting electrocardiographic signals based on a bluetooth-based portable cardiac defibrillator, comprising the steps of:
步骤一、通过心电采集模块采集心电模拟信号X(t)；Step 1, collecting the analog ECG signal X(t) through the ECG acquisition module;
步骤二、通过A/D转换器将心电模拟信号X(t)转换为心电数字信号x(i)，并将心电数字信号x(i)传递给控制器；Step 2, converting the analog ECG signal X(t) into a digital ECG signal x(i) through an A/D converter, and transmitting the digital ECG signal x(i) to the controller;
步骤三、所述控制器对心电数字信号x(i)进行滤波，得到滤波后的心电信号y(i)Step 3, the controller filters the ECG digital signal x(i) to obtain the filtered ECG signal y(i)
其中，x(i)为第i个采样点原始心电信号，y(i)为滤波后第i个采样点心电信号，TL为第一阈值，TH为第二阈值，λ为常数。Among them, x(i) is the original ECG signal of the i-th sampling point, y(i) is the filtered ECG signal of the i-th sampling point, TL is the first threshold,TH is the second threshold, and λ is a constant.
第一阈值TL和第二阈值TH根据经验进行设定，也可以根据波形情况进行调整。The first threshold TL and the second threshold TH are set according to experience, and can also be adjusted according to the waveform conditions.
所述充放电模块根据患者身高a，体重b，年龄c以及身体健康指数d，释放相应的电击电压vThe charging and discharging module releases the corresponding shock voltage v according to the patient's height a, weight b, age c and body health index d
其中，V0为标准电击电压，一般为24V。Among them, V0 is the standard shock voltage, generally 24V.
健康指数d可以按照患者的健康状况，分为5级，即d＝1～5，其中，1代表健康状态最差，5代表健康状况最好。The health index d can be divided into 5 grades according to the patient's health status, that is, d=1 to 5, where 1 represents the worst health status and 5 represents the best health status.
本发明提供的基于蓝牙的便携式心脏除颤器，软件设计如下：The bluetooth-based portable heart defibrillator provided by the present invention has software design as follows:
(1)主程序的设计：(1) Design of the main program:
整个系统在上电后，进行系统的初始化，初始化结束后，首先进行心电采集，通过显示器进行心电波形的显示，判断波形是否正常，若ECG波形发生室颤等，则进行除颤的能量存储，然后在短时间内对患者进行除颤。如果判断波形为非室颤发生波形则结束。主程序流程图如图12所示。After the whole system is powered on, the system is initialized. After the initialization is completed, the ECG is collected first, and the ECG waveform is displayed on the monitor to judge whether the waveform is normal. If the ECG waveform has ventricular fibrillation, etc., the defibrillation energy Store, then defibrillate the patient for a short time. If it is judged that the waveform is a non-ventricular fibrillation waveform, the process ends. The flow chart of the main program is shown in Figure 12.
(2)客户端应用程序的设计：(2) Design of client application:
智能手机与蓝牙模块连接成功后，首先由蓝牙模块主控器开始发送控制命令到心电采集部分，判断心电采集模块是否已经采集到心电波形，如果没有采集到返回开始，如果采集到了心电波形客户端开始收集心电数据，再进行判断，如果没有接收到清晰高质量的心电波形则返回重新开始，如果接收到了就在客户端上显示。流程框图如图13所示After the smart phone is successfully connected to the Bluetooth module, the main controller of the Bluetooth module first sends control commands to the ECG collection part to judge whether the ECG collection module has collected the ECG waveform. The electric waveform client starts to collect ECG data, and then judges. If it does not receive a clear and high-quality ECG waveform, it will return to start again. If it is received, it will be displayed on the client. The flow chart is shown in Figure 13
(3)心电波形分析：(3) ECG waveform analysis:
心电信号采集时干扰会很多，就算是被采集者手臂抖动也会带来较大干扰。图14为正常健康人的心电波形。图15为刚刚开始采集身体尚未平静时的心电波形。对比知，心电采集时必须让病人夹上电极夹后稍微平静3-4s，不能贸然判断波形对病人进行电击，病人有可能不是室颤而是其他疾病。本设备的优点就是消除干扰较快，可以在几秒钟内波形恢复正常，实现图形采集。There will be a lot of interference when the ECG signal is collected, even if the collected person's arm shakes, it will cause greater interference. Figure 14 is the ECG waveform of a normal healthy person. Fig. 15 is the ECG waveform when the body has just started to be collected and not yet calm. In contrast, when collecting ECG, the patient must be clamped on the electrode clip and then calm down for 3-4 seconds, and the patient should not be shocked by judging the waveform rashly. The patient may not have ventricular fibrillation but other diseases. The advantage of this device is that it eliminates interference quickly, and the waveform can return to normal within a few seconds to realize graphic acquisition.
(4)电池及电容充电分析：(4) Battery and capacitor charging analysis:
设备采用的是蓄电池给电容充电，考虑到平时发生室颤的病人并不会很多，甚至有时会很长一段时间不会使用，所以需要定期对设备的电池进行维护充电。为了保障有室颤病人出现时能够充到足够的电量，当设备存放时间过长或设备使用后都要对蓄电池进行充电。且电池所存放的电量并不是很多，每次充电过程需要的电流都较大，容易使电路发热，所以维护时要及时进行线路检测，并及时更换已损坏或快要损坏的电路线。增大救活每一位病人的可能性。The device uses a battery to charge the capacitor. Considering that there are not many patients with ventricular fibrillation, and sometimes they will not be used for a long time, the battery of the device needs to be maintained and charged regularly. In order to ensure that a patient with ventricular fibrillation can be charged with enough power, the battery must be charged when the device is stored for a long time or after the device is used. Moreover, the amount of power stored in the battery is not very large, and the current required for each charging process is relatively large, which can easily cause the circuit to heat up. Therefore, it is necessary to perform line inspection in time during maintenance, and replace damaged or about to be damaged circuit lines in time. Increase the likelihood of saving every patient.
电容为储能元件并且为暂时的储能元器件，我们充电和放电的都是快速进行的，也都有高压情况的存在，所以电容的使用寿命也是有限的，多次充放电后电容就容易出现充不进去电或者是漏电的情况发生，这时电容就会不能正常使用，要及时更换。当对设备进行维修时也要对电容进行耐压值检测，发现异常时就及时更换。Capacitors are energy storage components and are temporary energy storage components. Our charging and discharging are carried out quickly, and there are also high-voltage conditions, so the service life of the capacitor is also limited. After multiple charges and discharges, the capacitor is easy. In the event of failure to charge or leakage, the capacitor will not work normally and must be replaced in time. When repairing the equipment, the withstand voltage value of the capacitor should also be tested, and it should be replaced in time if any abnormality is found.
尽管本发明的实施方案已公开如上，但其并不仅仅限于说明书和实施方式中所列运用，它完全可以被适用于各种适合本发明的领域，对于熟悉本领域的人员而言，可容易地实现另外的修改，因此在不背离权利要求及等同范围所限定的一般概念下，本发明并不限于特定的细节和这里示出与描述的图例。Although the embodiment of the present invention has been disclosed as above, it is not limited to the use listed in the specification and implementation, it can be applied to various fields suitable for the present invention, and it can be easily understood by those skilled in the art Therefore, the invention is not limited to the specific details and examples shown and described herein without departing from the general concept defined by the claims and their equivalents.
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
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| CN108309282A (en)* | 2018-03-26 | 2018-07-24 | 华南理工大学 | A kind of ECG detecting foot ring and its detection method |
| CN108543221A (en)* | 2018-05-14 | 2018-09-18 | 上海掌门科技有限公司 | It is a kind of for the stethoscope system of electric defibrillation, electric defibrillation method, equipment and medium |
| CN108815707A (en)* | 2018-04-25 | 2018-11-16 | 广州磁力元科技服务有限公司 | Remote alarm cardiac defibrillation monitor |
| CN110292375A (en)* | 2019-07-05 | 2019-10-01 | 陈大为 | Therapeutic apparatus for heart disease |
| CN111450418A (en)* | 2020-03-31 | 2020-07-28 | 韩雪峰 | Sample entropy algorithm for external defibrillator |
| CN111449648A (en)* | 2020-03-31 | 2020-07-28 | 韩雪峰 | Electrocardio acquisition technology based on external defibrillator |
| CN113391539A (en)* | 2021-06-16 | 2021-09-14 | 北京康斯特仪表科技股份有限公司 | RTC (real time clock) calibration method and industrial field calibration device |
| CN114400880A (en)* | 2022-01-30 | 2022-04-26 | 电子科技大学 | A Large Common Mode Interference Suppression Circuit Applicable to Two Electrodes |
| CN114515386A (en)* | 2020-11-20 | 2022-05-20 | 深圳迈瑞生物医疗电子股份有限公司 | Power strips, defibrillators and medical equipment |
| CN115633414A (en)* | 2022-12-21 | 2023-01-20 | 苏州维伟思医疗科技有限公司 | Automatic Bluetooth connection method, device, equipment and storage medium for AED and communicator |
| CN116492598A (en)* | 2023-03-13 | 2023-07-28 | 苏州维伟思医疗科技有限公司 | Cardioversion defibrillation method, device and system with low false alarm rate and storage medium |
| CN119607412A (en)* | 2024-12-04 | 2025-03-14 | 浙江省立同德医院(浙江省精神卫生研究院) | A control circuit of a multi-mode electrical therapy instrument |
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| US20130012151A1 (en)* | 2011-07-05 | 2013-01-10 | Hankins Mark S | Defibrillator with integrated telecommunications |
| CN102974039A (en)* | 2012-12-20 | 2013-03-20 | 久心医疗科技（苏州）有限公司 | Defibrillator output stage with H bridge circuit and diphase sawtooth square wave defibrillation high-voltage discharge method |
| CN104367316A (en)* | 2014-11-13 | 2015-02-25 | 重庆邮电大学 | Electrocardiosignal denoising method based on morphological filtering and lifting wavelet transformation |
| CN204522007U (en)* | 2015-04-03 | 2015-08-05 | 蔡恒娟 | Cardiac resuccitation electric shock shirt |
| CN205758549U (en)* | 2016-05-30 | 2016-12-07 | 高鹏 | A kind of Low Power Consumption Portable electrocardiogram monitor system |
| CN106208325A (en)* | 2016-08-25 | 2016-12-07 | 苏州苏宝新能源科技有限公司 | There is the solar air-conditioner system of H bridge inversion |
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| CN107582166A (en)* | 2017-10-12 | 2018-01-16 | 天津市鹰泰利安康医疗科技有限责任公司 | A kind of ECG Synchronization system for the ablation of high pressure steep-sided pulse |
| CN108309282A (en)* | 2018-03-26 | 2018-07-24 | 华南理工大学 | A kind of ECG detecting foot ring and its detection method |
| CN108815707A (en)* | 2018-04-25 | 2018-11-16 | 广州磁力元科技服务有限公司 | Remote alarm cardiac defibrillation monitor |
| CN108543221A (en)* | 2018-05-14 | 2018-09-18 | 上海掌门科技有限公司 | It is a kind of for the stethoscope system of electric defibrillation, electric defibrillation method, equipment and medium |
| CN110292375A (en)* | 2019-07-05 | 2019-10-01 | 陈大为 | Therapeutic apparatus for heart disease |
| CN111449648A (en)* | 2020-03-31 | 2020-07-28 | 韩雪峰 | Electrocardio acquisition technology based on external defibrillator |
| CN111450418A (en)* | 2020-03-31 | 2020-07-28 | 韩雪峰 | Sample entropy algorithm for external defibrillator |
| CN114515386A (en)* | 2020-11-20 | 2022-05-20 | 深圳迈瑞生物医疗电子股份有限公司 | Power strips, defibrillators and medical equipment |
| CN113391539A (en)* | 2021-06-16 | 2021-09-14 | 北京康斯特仪表科技股份有限公司 | RTC (real time clock) calibration method and industrial field calibration device |
| CN114400880A (en)* | 2022-01-30 | 2022-04-26 | 电子科技大学 | A Large Common Mode Interference Suppression Circuit Applicable to Two Electrodes |
| CN114400880B (en)* | 2022-01-30 | 2023-04-18 | 电子科技大学 | Large common mode interference suppression circuit suitable for double electrodes |
| CN115633414A (en)* | 2022-12-21 | 2023-01-20 | 苏州维伟思医疗科技有限公司 | Automatic Bluetooth connection method, device, equipment and storage medium for AED and communicator |
| CN116492598A (en)* | 2023-03-13 | 2023-07-28 | 苏州维伟思医疗科技有限公司 | Cardioversion defibrillation method, device and system with low false alarm rate and storage medium |
| CN116492598B (en)* | 2023-03-13 | 2023-09-29 | 苏州维伟思医疗科技有限公司 | Cardioversion defibrillation method, device and system with low false alarm rate and storage medium |
| CN119607412A (en)* | 2024-12-04 | 2025-03-14 | 浙江省立同德医院(浙江省精神卫生研究院) | A control circuit of a multi-mode electrical therapy instrument |
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