CN105326491B - A kind of photo-electric reflection type pulse heart rate sensor self-adapting changeable threshold filter method - Google Patents
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Abstract
一种光电反射式脉搏心率传感器自适应可变阈值滤波方法，涉及一种医疗电子测量方法，由于重搏波的幅度和引起它的脉搏波的幅度成正比关系，在某一时刻测得正常脉搏波引起的电压峰值后，设定一个阈值，该阈值电压是正常脉搏波引起的电压峰值的三分之一；采样值在阈值以下的都认为是脉搏波引起的干扰值，直到出现采样值大于阈值后，采样值才认为是正常正常脉搏波电压上升过程，当再次出现脉搏波电压峰值出现后，记住该时刻；通过这两次电压峰值时间只差即可测得两次脉搏的时间差，进而求得心率值；本发明能够实时监测人体组织在血管搏动时引起的电压波动信号，能够有效的去除重搏波引起的干扰。能够大幅提高心率非接触式测量的稳定性。
A photoelectric reflective pulse heart rate sensor self-adaptive variable threshold filtering method, involving a medical electronic measurement method, since the amplitude of the dicrotic wave is proportional to the amplitude of the pulse wave that caused it, a normal pulse is measured at a certain moment After the voltage peak caused by the pulse wave, set a threshold, the threshold voltage is one-third of the voltage peak caused by the normal pulse wave; the sampling value below the threshold is considered to be the interference value caused by the pulse wave, until the sampling value is greater than After the threshold, the sampling value is considered to be a normal pulse wave voltage rising process. When the pulse wave voltage peak appears again, remember this moment; the time difference between the two pulses can be measured by only the difference between the two voltage peak times. Further, the heart rate value is obtained; the present invention can monitor the voltage fluctuation signal caused by the human tissue in real time when the blood vessel pulsates, and can effectively remove the interference caused by the dicrotic wave. It can greatly improve the stability of non-contact heart rate measurement.
Description
技术领域technical field
本发明涉及一种医疗电子测量方法，具体为一种光电反射式脉搏心率传感器自适应可变阈值滤波方法。The invention relates to a medical electronic measurement method, in particular to a photoelectric reflective pulse heart rate sensor adaptive variable threshold filtering method.
背景技术Background technique
无创伤监护技术是未来医学工程发展的重要方向，而人体脉搏信号中含有丰富的生理信息，也逐渐引起了临床医生的很大兴趣。传统的脉搏测量方法主要有三种：一是从心电信号中提取；二是从测量血压时压力传感器检测到的波动来计算脉搏心率；三是光电容积法。前两种方法提取信号都会限制被测者的活动，如果长时间使用会增加被测者生理和心理上的不舒适感。而光电容积法脉搏测量作为监护测量中最普遍的方法之一，其具有方法简单、佩戴方便、可靠性高等特点。光电容积法的基本原理是利用人体组织在血管搏动时造成透光率不同来进行脉搏测量的。当光束透过人体外周血管，由于动脉搏动充血容积变化导致光束的透光率发生改变，此时由光电变换器接收经人体组织反射的光线，转变为电信号并将其放大和输出。由于脉搏是随心脏的周期搏动而周期性变化的信号，脉动血管容积也周期性变化，因此，光电变换器的电信号变化周期就是脉搏。通过采集相邻两个脉搏信号峰值的时间差即可换算得到心率。Non-invasive monitoring technology is an important direction for the development of medical engineering in the future, and the human pulse signal contains rich physiological information, which has gradually aroused great interest of clinicians. There are three main traditional pulse measurement methods: one is to extract from the ECG signal; the other is to calculate the pulse heart rate from the fluctuation detected by the pressure sensor when measuring blood pressure; the third is the photoelectric volume method. The first two methods of extracting signals will limit the activity of the subject, and if used for a long time, it will increase the physical and psychological discomfort of the subject. As one of the most common methods in monitoring and measurement, photoplethysmography pulse measurement has the characteristics of simple method, convenient wearing and high reliability. The basic principle of photoplethysmography is to use the difference in light transmittance caused by human tissue when the blood vessels are pulsating to measure the pulse. When the light beam passes through the peripheral blood vessels of the human body, the light transmittance of the light beam changes due to the change of the arterial pulsation and congestion volume. At this time, the photoelectric converter receives the light reflected by the human body tissue, converts it into an electrical signal, and amplifies and outputs it. Since the pulse is a signal that changes periodically with the periodic beating of the heart, and the volume of the pulsating blood vessel also changes periodically, therefore, the change period of the electrical signal of the photoelectric transducer is the pulse. The heart rate can be converted by collecting the time difference between two adjacent pulse signal peaks.
但由于在光电容积法测量过程中存在重搏波，对测量结果造成干扰导致心率测量结果不准确。目前为了去除重搏波的影响，现有的算法都是在测量一个脉搏峰值之后，延时一段时间测量下一个脉搏峰值，通过延时过程去掉重搏波的影响。但由于人体每两次脉搏之间的时间间隔都不是一样的，导致重搏波在脉搏峰值之后的时间也不一样，这时通过延迟方法去掉脉搏波就不准确。However, due to the presence of dicrotic waves in the process of photoplethysmography measurement, the measurement results are disturbed and the heart rate measurement results are inaccurate. At present, in order to remove the influence of the dicrotic wave, the existing algorithms all measure the next pulse peak with a delay for a period of time after measuring a pulse peak, and remove the influence of the dicrotic wave through the delay process. However, since the time interval between every two pulses of the human body is not the same, the time after the pulse peak of the dicrotic wave is also different. At this time, it is not accurate to remove the pulse wave by the delay method.
由于重搏波的幅度和引起它的脉搏波的幅度成正比关系，因此，本发明提出一种光电反射式脉搏心率传感器自适应可变阈值滤波方法，通过自适应算法自动调整阈值，滤掉重搏波的干扰，获得准确地脉搏心率。Since the amplitude of the dicrotic wave is directly proportional to the amplitude of the pulse wave causing it, the present invention proposes a photoelectric reflective pulse heart rate sensor adaptive variable threshold filtering method, which automatically adjusts the threshold through an adaptive algorithm to filter out heavy Pulse wave interference, to obtain accurate pulse heart rate.
现有的算法：在某一刻测得正常脉搏波引起的电压峰值后，通过延时一段时间后，再次测量搏波电压上升过程，直到下一次脉搏波电压峰值出现后，记住该时刻。通过这两次电压峰值时间只差即可测得两次脉搏的时间差，进而求得心率值。由于延迟时间内重搏波已经通过，所以可以去除重搏波的干扰。The existing algorithm: After measuring the voltage peak caused by the normal pulse wave at a certain moment, after a period of delay, measure the rising process of the pulse wave voltage again until the next pulse wave voltage peak appears, and remember this moment. The time difference between the two pulses can be measured by only the difference between the two voltage peak times, and then the heart rate value can be obtained. Since the dicrotic wave has passed through within the delay time, the interference of the dicrotic wave can be removed.
但由于人体每两次脉搏之间的时间间隔都不是一样的，也就在正常脉搏波引起的电压峰值的时间后重搏波出现的时间是不同的，这是由于延时时间是固定的，所以就有可能出现重搏波没有去除的现象。如果增加延时时间也会出现将正常脉搏波去除掉。所以现有算法测量精度不高。However, since the time interval between every two pulses of the human body is not the same, the time of the dicrosis wave is different after the time of the voltage peak caused by the normal pulse wave. This is because the delay time is fixed. Therefore, there may be a phenomenon that the dicrotic wave is not removed. If the delay time is increased, the normal pulse wave will be removed. Therefore, the measurement accuracy of existing algorithms is not high.
在T1时刻测得正常脉搏波引起的电压峰值Vi后，通过延时时间dT后，再次测量搏波电压上升过程，直到下一次脉搏波电压峰值出现后，记住该时刻T2。通过这两次电压峰值时间只差即可测得两次脉搏的时间差|T2-T1|，进而求得心率值。由于延迟时间dT内重搏波已经通过，所以可以去除重搏波的干扰。After measuring the peak voltage Vi caused by the normal pulse wave at T1, after the delay time dT, measure the rising process of the pulse wave voltage again until the next peak pulse wave voltage appears, and remember this time T2. The time difference |T2-T1| of the two pulses can be measured by only the difference between the two voltage peak times, and then the heart rate value can be obtained. Since the dicrotic wave has passed within the delay time dT, the interference of the dicrotic wave can be removed.
但由于人体每两次脉搏之间的时间间隔都不是一样的，也就在正常脉搏波引起的电压峰值的时间后重搏波出现的时间是不同的，这是由于延时时间dT是固定的，所以就有可能出现重搏波没有去除的现象。如果增加延时时间dT也会出现将正常脉搏波去除掉。所以现有算法测量精度不高。However, since the time interval between every two pulses of the human body is not the same, the time after the peak voltage caused by the normal pulse wave is different when the dicrosis wave appears, because the delay time dT is fixed , so there may be a phenomenon that the dicrotic wave is not removed. If the delay time dT is increased, the normal pulse wave will also be removed. Therefore, the measurement accuracy of existing algorithms is not high.
发明内容Contents of the invention
本发明的目的在于提供一种光电反射式脉搏心率传感器自适应可变阈值滤波方法，该方法通过正常脉搏波电压峰值阈值来滤除重搏波干扰的，避免了重搏波出现时间不固定的问题，由于每一次正常脉搏波电压峰值都是不一样的，而每一次阈值都是基于本次采样脉搏波电压峰值三分之一设定的，所以也实现了自适应可变阈值设定，提高了测量精度。The object of the present invention is to provide a photoelectric reflective pulse heart rate sensor self-adaptive variable threshold filtering method, which filters out the dicrotic wave interference through the normal pulse wave voltage peak threshold, avoiding the non-fixed occurrence time of the dicrotic wave Problem, since the peak value of the normal pulse wave voltage is different every time, and each threshold is set based on one-third of the peak value of the pulse wave voltage of this sampling, so the adaptive variable threshold setting is also realized. Improved measurement accuracy.
本发明的目的是通过以下技术方案实现的：The purpose of the present invention is achieved through the following technical solutions:
一种光电反射式脉搏心率传感器自适应可变阈值滤波方法，所述方法由于重搏波的幅度和引起它的脉搏波的幅度成正比关系，在某一时刻测得正常脉搏波引起的电压峰值后，设定一个阈值，该阈值电压是正常脉搏波引起的电压峰值的三分之一；在接下来的采样中，采样值在阈值以下的都认为是脉搏波引起的干扰值，直到出现采样值大于阈值后，采样值才认为是正常正常脉搏波电压上升过程，当再次出现脉搏波电压峰值出现后，记住该时刻；通过这两次电压峰值时间只差即可测得两次脉搏的时间差，进而求得心率值；A photoelectric reflective pulse heart rate sensor self-adaptive variable threshold filtering method, because the amplitude of the dicrotic wave is proportional to the amplitude of the pulse wave that causes it, the method measures the voltage peak value caused by the normal pulse wave at a certain moment Finally, set a threshold, the threshold voltage is one-third of the peak voltage caused by the normal pulse wave; in the next sampling, the sampling value below the threshold is considered to be the interference value caused by the pulse wave, until the sampling After the value is greater than the threshold, the sampling value is considered as a normal pulse wave voltage rising process. When the pulse wave voltage peak appears again, remember this moment; the two pulses can be measured only by the difference between the two voltage peak times. Time difference, and then obtain the heart rate value;
其流程如下：The process is as follows:
(1)、在设定重搏波阈值初始值后，程序开始无限循环计算心率值；(1) After setting the initial value of the dicrotic wave threshold, the program starts to calculate the heart rate value in an infinite loop;
(2)、通过采样时间间隔为2ms进行采样；(2) Sampling is performed at a sampling interval of 2 ms;
(3)、根据每一次采样值与前一次采样值作比较，寻找脉搏上升阶段；(3), according to each sampling value is compared with the previous sampling value, looking for the pulse rising stage;
(4)、在上升阶段出现拐点处寻找峰值电压；(4) Look for the peak voltage at the inflection point in the rising stage;
(5)、通过峰值电压与重搏波阈值进行比较，如果峰值电压小于重搏波阈值，是重搏波的干扰，滤掉该值，返回到第(2)步进行重新采样；如果峰值电压大于重搏波阈值，是正常脉搏波峰值，进入到第(6)步；(5), compare the peak voltage with the dicrotic wave threshold, if the peak voltage is less than the dicrotic wave threshold, it is the interference of the dicrotic wave, filter out this value, return to step (2) for re-sampling; if the peak voltage If it is greater than the dicrotic wave threshold, it is the peak value of the normal pulse wave, and enters step (6);
(6)、更新重搏波阈值；(6), update the dicrotic wave threshold;
(7)、计算心率值；(7), calculate the heart rate value;
(8)、输出心率值，返回到第(2)步，进行下一轮采样；(8), output the heart rate value, return to step (2), and perform the next round of sampling;
所述的一种光电反射式脉搏心率传感器自适应可变阈值滤波方法，所述算法具体数值如下：According to the photoelectric reflective pulse heart rate sensor adaptive variable threshold filtering method, the specific values of the algorithm are as follows:
(1)、设定滤除重搏波阈值E，初始值为1V；(1), set the dicrotic wave threshold E for filtering, the initial value is 1V;
(2)、对传感器进行周期性采样，采样周期为为2毫秒，设每次读取的采样电压为Vi(i=1,2,3…m)；(2), the sensor is periodically sampled, the sampling period is 2 milliseconds, and the sampling voltage read each time is V i (i=1,2,3...m);
(3)、当连续出现Vi>Vi-1时，表示脉搏波处于上升阶段，记录每一次采样值；(3) When V i >V i-1 appears continuously, it means that the pulse wave is in the rising stage, and each sampling value is recorded;
(4)、在上升阶段中出现Vi<Vi-1时，表示在上升阶段出现了峰值，记录该峰值电压；(4) When V i <V i-1 occurs in the rising phase, it means that a peak value has appeared in the rising phase, and record the peak voltage;
(5)、如果该峰值电压小于阈值E时，则认为该峰值电压是由重搏波引起的，返回第(2)步；如果该峰值电压大于阈值E时，则认为该峰值电压是由正常脉搏波引起的，程序继续运行；(5) If the peak voltage is less than the threshold E, it is considered that the peak voltage is caused by the dicrotic wave, and return to step (2); if the peak voltage is greater than the threshold E, it is considered that the peak voltage is caused by the normal Caused by the pulse wave, the program continues to run;
(6)、记录峰值电压，记录时间点，更新重搏波阈值E为新峰值电压的三分之一；(6), record the peak voltage, record the time point, and update the dicrotic wave threshold E to be one-third of the new peak voltage;
(7)、根据连续两次正常脉搏波峰值电压时间差，计算心率值；(7) Calculate the heart rate value according to the time difference between two consecutive normal pulse wave peak voltages;
(8)、输出心率值，返回第(2)步，进行下一轮采样。(8) Output the heart rate value, return to step (2) for the next round of sampling.
本发明的有益效果：本发明能够实时监测人体组织在血管搏动时引起的电压波动信号，能够有效的去除重搏波引起的干扰。由于不同人的人体组织对传感器反应不同，或同一个人由于佩戴传感器的位置不同造成的脉搏波波动引起的电压波动信号强弱不同，本发明采用了一种自适应可变阈值滤波方法滤掉重搏波，得到准确地心率值。基于本方法，得到创新改进后的脉搏心率检测设备的准确度和稳定性指标，大大优于国际标准化组织ISO 和国内行业标准指标，其具体有益效果可以体现在以下医学测量指标参数的改进：(1) 同一个人，佩戴传感器位置变化后，计算得出的心率值与真实心率值误差在正负5次/分钟；(2)不同的人，由于人体组织对传感器反应不同，计算得出的心率值与真实心率值误差在正负5次/分钟。因此本发明能够大幅提高心率非接触式测量的稳定性。Beneficial effects of the present invention: the present invention can monitor in real time the voltage fluctuation signal caused by the pulsation of blood vessels in human tissue, and can effectively remove the interference caused by dicrotic waves. Since the human tissues of different people respond differently to the sensor, or the strength of the voltage fluctuation signal caused by the pulse wave fluctuation caused by the different positions of the same person wearing the sensor is different, the present invention adopts an adaptive variable threshold filtering method to filter out heavy Pulse wave to get accurate heart rate value. Based on this method, the accuracy and stability indicators of the innovative and improved pulse heart rate detection equipment are much better than the ISO and domestic industry standard indicators. The specific beneficial effects can be reflected in the improvement of the following medical measurement index parameters: ( 1) For the same person, after the position of the sensor is changed, the error between the calculated heart rate value and the real heart rate value is plus or minus 5 beats per minute; (2) For different people, due to the different reactions of human body tissues to the sensor, the calculated heart rate value The error between the value and the real heart rate value is plus or minus 5 beats/minute. Therefore, the present invention can greatly improve the stability of the heart rate non-contact measurement.
附图说明Description of drawings
图1为光电容积法测量脉搏波的波形示意图；Fig. 1 is the waveform schematic diagram of measuring pulse wave by photoplethysmography;
图2为本发明方法的流程图。Fig. 2 is a flow chart of the method of the present invention.
图中参数：1为正常脉搏波电压波形，2为重搏波电压波形。T1为当前正常脉搏波电压峰值采样时刻，T2为下一次正常脉搏波电压峰值采样时刻，dT为两次正常脉搏波电压峰值时间差，Vi为正常脉搏波电压峰值，E为前正阈值。Parameters in the figure: 1 is the normal pulse wave voltage waveform, and 2 is the heavy pulse wave voltage waveform. T1 is the current normal pulse wave voltage peak sampling time, T2 is the next normal pulse wave voltage peak sampling time, dT is the time difference between two normal pulse wave voltage peak values, Vi is the normal pulse wave voltage peak value, and E is the front positive threshold.
具体实施方式Detailed ways
实施例Example
下面参照附图并结合实例对本发明作进一步详细描述。The present invention will be described in further detail below with reference to the accompanying drawings and examples.
如图1所示，光电容积法测量的正常脉搏波电压波形如图1中1所示，但在正常脉搏波电压波形1后面存在一个重搏波电压波形2。As shown in Figure 1, the normal pulse wave voltage waveform measured by photoplethysmography is shown as 1 in Figure 1, but there is a dicrotic wave voltage waveform 2 behind the normal pulse wave voltage waveform 1.
为了去掉重搏波电压波形2的干扰，In order to remove the interference of dicrotic wave voltage waveform 2,
本发明算法：由于重搏波的幅度和引起它的脉搏波的幅度成正比关系，在T1时刻测得正常脉搏波引起的电压峰值Vi后，设定一个阈值E，该阈值电压E是正常脉搏波引起的电压峰值Vi的三分之一。在接下来的采样中，采样值在阈值以下的都认为是脉搏波引起的干扰值，直到出现采样值大于阈值后，采样值才认为是正常正常脉搏波电压上升过程，当再次出现脉搏波电压峰值出现后，记住该时刻T2。通过这两次电压峰值时间只差即可测得两次脉搏的时间差，进而求得心率值。由于本发明是通过正常脉搏波电压峰值阈值来滤除重搏波干扰的，避免了重搏波出现时间不固定的问题。由于每一次正常脉搏波电压峰值都是不一样的，而每一次阈值都是基于本次采样脉搏波电压峰值三分之一设定的，所以也实现了自适应可变阈值设定。提高了测量精度。Algorithm of the present invention: because the amplitude of the dicrotic wave is proportional to the amplitude of the pulse wave that causes it, after measuring the voltage peak value Vi caused by the normal pulse wave at T1 moment, a threshold E is set, and the threshold voltage E is the normal pulse wave caused by one-third of the peak voltage Vi. In the next sampling, the sampling value below the threshold is considered to be the interference value caused by the pulse wave, until the sampling value is greater than the threshold, the sampling value is considered to be a normal normal pulse wave voltage rising process, when the pulse wave voltage appears again After the peak appears, remember the moment T2. The time difference between the two pulses can be measured by only the difference between the two voltage peak times, and then the heart rate value can be obtained. Since the present invention filters out the dicrotic wave interference through the normal pulse wave voltage peak value threshold, the problem that the occurrence time of the dicrotic wave is not fixed is avoided. Since the peak value of the normal pulse wave voltage is different every time, and each threshold is set based on one-third of the peak value of the pulse wave voltage sampled this time, an adaptive variable threshold setting is also realized. Improved measurement accuracy.
根据本算法设计的流程图如图2所示：The flow chart designed according to this algorithm is shown in Figure 2:
(1)、在设定重搏波阈值初始值E后，程序开始无限循环计算心率值；(1) After setting the initial value E of the dicrotic wave threshold, the program starts to calculate the heart rate value in an infinite loop;
(2)、通过采样时间间隔为2ms进行采样；(2) Sampling is performed at a sampling interval of 2 ms;
(3)、根据每一次采样值与前一次采样值作比较，寻找脉搏上升阶段；(3), according to each sampling value is compared with the previous sampling value, looking for the pulse rising stage;
(4)、在上升阶段出现拐点处寻找峰值电压；(4) Look for the peak voltage at the inflection point in the rising stage;
(5)、通过峰值电压与重搏波阈值进行比较，如果峰值电压小于重搏波阈值，我们认为是重搏波的干扰，滤掉该值，返回到第(2)步进行重新采样；如果峰值电压大于重搏波阈值，我们认为是正常脉搏波峰值，进入到第(6)步；(5), compare the peak voltage with the dicrotic wave threshold, if the peak voltage is less than the dicrotic wave threshold, we consider it to be the interference of the dicrotic wave, filter out this value, and return to step (2) for re-sampling; if If the peak voltage is greater than the dicrotic wave threshold, we consider it to be the peak value of the normal pulse wave, and enter step (6);
(6)、更新重搏波阈值；(6), update the dicrotic wave threshold;
(7)、计算心率值；(7), calculate the heart rate value;
(8)、输出心率值，返回到第(2)步，进行下一轮采样；(8), output the heart rate value, return to step (2), and perform the next round of sampling;
根据图2所示流程结合具体数值再做如下进一步说明：According to the process shown in Figure 2 and the specific values, further explanations are made as follows:
(1)、设定滤除重搏波阈值E，初始值为1V；(1), set the dicrotic wave threshold E for filtering, the initial value is 1V;
(2)、对传感器进行周期性采样，采样周期为为2毫秒，设每次读取的采样电压为Vi(i=1,2,3…m)；(2), the sensor is periodically sampled, the sampling period is 2 milliseconds, and the sampling voltage read each time is Vi (i=1,2,3...m);
(3)、当连续出现Vi>Vi-1时，表示脉搏波处于上升阶段，记录每一次采样值；(3) When Vi>Vi-1 appears continuously, it means that the pulse wave is in the rising stage, and each sampling value is recorded;
(4)、在上升阶段中出现Vi<Vi-1时，表示在上升阶段出现了峰值，记录该峰值电压；(4) When Vi<Vi-1 appears in the rising stage, it means that a peak value has appeared in the rising stage, and record the peak voltage;
(5)、如果该峰值电压小于阈值E时，则认为该峰值电压是由重搏波引起的，返回第(2)步；如果该峰值电压大于阈值E时，则认为该峰值电压是由正常脉搏波引起的，程序继续运行；(5) If the peak voltage is less than the threshold E, it is considered that the peak voltage is caused by the dicrotic wave, and return to step (2); if the peak voltage is greater than the threshold E, it is considered that the peak voltage is caused by the normal Caused by the pulse wave, the program continues to run;
(6)、记录峰值电压，记录时间点，更新重搏波阈值E为新峰值电压的三分之一；(6), record the peak voltage, record the time point, and update the dicrotic wave threshold E to be one-third of the new peak voltage;
(7)、根据连续两次正常脉搏波峰值电压时间差，计算心率值；(7) Calculate the heart rate value according to the time difference between two consecutive normal pulse wave peak voltages;
(8)、输出心率值，返回第(2)步，进行下一轮采样。(8) Output the heart rate value, return to step (2) for the next round of sampling.
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