技术领域technical field
本发明涉及医疗设备技术领域，尤其涉及一种基于光电容积脉搏波特征的无创血压测量装置。The invention relates to the technical field of medical equipment, in particular to a noninvasive blood pressure measuring device based on the characteristics of photoplethysmography waves.
背景技术Background technique
血压是反映心脑血管功能的重要生理参数指标，在疾病诊断和治疗效果观察等方面具有重要的意义。在实际应用中需要能方便快捷准确连续的检测出血压指标，而目前的测量方法主要包括听诊法和示波法，恒定容积法和脉搏波波速法。Blood pressure is an important physiological parameter that reflects cardiovascular and cerebrovascular functions, and is of great significance in disease diagnosis and treatment effect observation. In practical applications, blood pressure indicators need to be detected conveniently, quickly, accurately and continuously, and the current measurement methods mainly include auscultation and oscillometric methods, constant volume methods and pulse wave velocity methods.
听诊法也叫柯式音法，就是将压力计(一般称血压计)的臂带绑扎于上臂肱动脉搏动位置，充气加压将肱动脉压瘪，然后再放气减压。随着外压力的下降，血流重新冲开血管，发出与心动节拍相同的节律音，这就是柯氏音。用听诊器探听到“第一音”时压力计显示的外压力记为收缩压，“最末音”时记为舒张压。这是国际无创血压测量的金标准，也是检验所有无创血压计精度的临床标准。但听诊法需要接受过专业培训的人员操作，并会有听觉和视觉及人为主观判断的误差，且需要对肱动脉进行加压，容易造成人体的不适，不适合长时间的血压监测。The auscultation method is also called the Keshi sound method. It is to bind the armband of the manometer (commonly called a sphygmomanometer) to the pulse position of the brachial artery of the upper arm, inflate and pressurize the brachial artery, and then deflate and decompress. As the external pressure drops, the blood flow opens the blood vessel again, and the same rhythmic sound as the heartbeat is issued, which is the Korotkoff sound. When the "first sound" is heard with a stethoscope, the external pressure displayed by the manometer is recorded as the systolic pressure, and when the "last sound" is recorded as the diastolic pressure. This is the gold standard for international non-invasive blood pressure measurement and the clinical standard for testing the accuracy of all non-invasive blood pressure monitors. However, the auscultation method needs to be operated by professionally trained personnel, and there will be errors in auditory, visual and subjective judgments, and it needs to pressurize the brachial artery, which is likely to cause discomfort to the human body and is not suitable for long-term blood pressure monitoring.
示波法是通过袖带加压来阻断动脉血流，利用袖带内的压力传感器来检测血流流过血管时产生的振动波，袖带放气过程中，第一个被检测到的脉动信号所对应的袖带压就叫做收缩压。继续放气脉动信号幅度由小增大，达到极值后开始减小，振幅骤然减小处的袖带压被认为舒张压，示波法的收缩压和舒张压的计算没有统一标准，因此测量结果不如听诊法准确。The oscillometric method is to block the arterial blood flow by pressurizing the cuff. The pressure sensor in the cuff is used to detect the vibration wave generated when the blood flows through the blood vessel. During the deflation process of the cuff, the first detected The cuff pressure corresponding to the pulse signal is called the systolic pressure. The amplitude of the pulsation signal increases from small to small after deflation, and then decreases after reaching the extreme value. The cuff pressure at the place where the amplitude suddenly decreases is regarded as the diastolic pressure. The results are not as accurate as auscultation.
恒定容积法测量原理是当动脉血管在处于去负荷状态下的动脉压力就等于外加压力，因此可以预先设定外加压力值，并将其作用于动脉血管处使其处于去负荷状态,同时利用伺服补偿系统快速补偿因为动脉内压变化而产生的容积变化,使得动脉血管始终处于恒定容积的状态,从而可化通过测量外加压力间接获得动脉血压。容积补偿法是目前较为成熟的连续血压测量方法,这种测量方法的优点是可以连续跟踪动脉血压的变化,但长时间测量时静脉充血影响较大,舒适性差,且测得的用该原理测量装置测得的收缩压和平均压的离散型较大,没有达到AAMI标准。The measurement principle of the constant volume method is that when the arterial blood vessel is in an unloaded state, the arterial pressure is equal to the external pressure, so the external pressure value can be preset and act on the arterial blood vessel to make it in an unloaded state. The compensation system quickly compensates the volume change caused by the change of arterial internal pressure, so that the arterial blood vessel is always in a state of constant volume, so that the arterial blood pressure can be obtained indirectly by measuring the external pressure. The volume compensation method is a relatively mature continuous blood pressure measurement method at present. The advantage of this measurement method is that it can continuously track the change of arterial blood pressure. However, the venous congestion has a great influence on long-term measurement, and the comfort is poor, and the measured value is measured by this principle. The discrete type of systolic blood pressure and mean pressure measured by the device was relatively large, which did not reach the AAMI standard.
脉搏波速测定法是根据脉搏波沿动脉传播速率与动脉血压之间具有正相关性的特点提出,通过测量PWV间接推算出动脉血压值。脉搏波速可通过脉搏波在动脉中两点间传递时间计算出来,因此可采用相同原理利用脉搏波传导时间(PAT)间接推算出动脉血压值，该方法已经得到很大发展，但仍存在一些缺陷，血压算法精度上还有待提高。The pulse wave velocity measurement method is based on the positive correlation between the pulse wave propagation velocity along the artery and the arterial blood pressure, and the arterial blood pressure value can be calculated indirectly by measuring PWV. The pulse wave velocity can be calculated by the pulse wave transit time between two points in the artery, so the same principle can be used to indirectly calculate the arterial blood pressure value using the pulse wave transit time (PAT). This method has been greatly developed, but there are still some defects , the accuracy of the blood pressure algorithm needs to be improved.
目前最相近的已有的技术方案是基于脉搏波传导时间(PAT)的血压连续测量方法及装置，包括心电信号检测单元、脉搏波信号检测单元、信息处理单元、血压测量校准单元和显示单元组成。The most similar existing technical solution is a blood pressure continuous measurement method and device based on pulse transit time (PAT), including an electrocardiogram signal detection unit, a pulse wave signal detection unit, an information processing unit, a blood pressure measurement calibration unit and a display unit composition.
具体的方案步骤是：首先利用传统的标准血压计对受测者进行血压测量用来校准，把测量值手动输入到血压测量校准单元，血压测量校准单元会根据测量值计算出校准参数并保存在微处理器单元。利用心电信号检测单元和脉搏波信号检测单元分别采集受测者的心电信号(ECG)和脉搏波信号(PPG)，通过信号处理单元对采集到的信号进行滤波去噪和放大，然后进入微处理器单元。利用微处理器单元在心电信号(ECG)上选择参考点，并在脉搏波信号(PPG)上选择参考点，并根据两个信号之间的参考点算出脉搏波传导时间PAT(详见图1)，结合微处理器单元中保存的血压测量公式计算出血压测量结果，最后通过显示单元进行同步显示。The specific program steps are: firstly, use the traditional standard sphygmomanometer to measure the blood pressure of the subject for calibration, then manually input the measured value into the blood pressure measurement and calibration unit, and the blood pressure measurement and calibration unit will calculate the calibration parameters according to the measured value and save them in the microprocessor unit. The electrocardiogram signal (ECG) and pulse wave signal (PPG) of the subject are respectively collected by the electrocardiographic signal detection unit and the pulse wave signal detection unit, and the collected signal is filtered, denoised and amplified by the signal processing unit, and then entered into microprocessor unit. Use the microprocessor unit to select the reference point on the electrocardiogram signal (ECG), and select the reference point on the pulse wave signal (PPG), and calculate the pulse wave transit time PAT according to the reference point between the two signals (see Figure 1 for details) ), combine the blood pressure measurement formula stored in the microprocessor unit to calculate the blood pressure measurement result, and finally display it synchronously through the display unit.
背景技术的缺点及产生原因：Shortcomings and causes of background technology:
受干扰严重：现有的技术来检测血压是基于脉搏波传导时间(PAT)的，而脉搏波传导时间严格意义来讲不是我们所需要的脉搏传输时间(PTT)，脉搏波传导时间(PAT)它还包含有心脏射血前期的时间(PEP)，由于心脏射血前期时间的不确定性，会影响血压算法的精度。Serious interference: the existing technology to detect blood pressure is based on pulse wave transit time (PAT), and pulse wave transit time is not strictly speaking the pulse transit time (PTT) we need, pulse wave transit time (PAT) It also includes the pre-ejection time (PEP), which will affect the accuracy of the blood pressure algorithm due to the uncertainty of the pre-ejection time.
装置模块单元多：需要同时采集心电信号(ECG)和脉搏波信号(PPG)。There are many device module units: ECG and pulse wave signals (PPG) need to be collected at the same time.
检测信号种类多：需要同时处理心电和脉搏信号，并且要同步校准。There are many types of detection signals: ECG and pulse signals need to be processed at the same time, and they need to be calibrated synchronously.
便携性差：现有的血压连续测量装置体积过于庞大，不适合随身携带。Poor portability: The existing continuous blood pressure measurement devices are too bulky to be carried around.
主动式测量：现有测量方式多为主动式测量，受测者要主动去迎合检测装置才能获取检测结果，不适合日常生活的使用。Active measurement: Most of the existing measurement methods are active measurement. The testee must actively cater to the detection device to obtain the test result, which is not suitable for daily use.
发明内容Contents of the invention
本发明提供了一种基于光电容积脉搏波特征的无创血压测量装置，包括处理器、脉搏波模块、信号处理模块、血压测量校准模块，所述脉搏波模块，用于采集人体的脉搏波信号，得到PPG信号；所述信号处理模块，用于接收脉搏博模块传输的PPG信号，对PPG信号进行预处理；所述血压测量校准模块，用于提供血压的校准参数，并将校准参数传输至所述处理器；所述处理器，用于接收血压测量校准模块传输的校准参数、以及所述信号处理模块传输的经预处理的PPG信号，从预处理后的PPG信号中提取平均斜率传输时间MSTT、特征S和特征PA，然后根据平均斜率传输时间MSTT、特征S和特征PA与血压之间的关系，结合血压测量校准模块提供的校准参数进行线性拟合建立算法模型，获取模型系数，再进行血压的估算，从而得到实时血压数据。The invention provides a non-invasive blood pressure measurement device based on photoplethysmography features, including a processor, a pulse wave module, a signal processing module, and a blood pressure measurement and calibration module. The pulse wave module is used to collect pulse wave signals of the human body, Obtain the PPG signal; the signal processing module is used to receive the PPG signal transmitted by the pulse pulse module, and preprocess the PPG signal; the blood pressure measurement calibration module is used to provide blood pressure calibration parameters, and transmit the calibration parameters to the The processor; the processor is used to receive the calibration parameters transmitted by the blood pressure measurement calibration module and the preprocessed PPG signal transmitted by the signal processing module, and extract the average slope transit time MSTT from the preprocessed PPG signal , feature S, and feature PA, and then according to the relationship between the average slope transit time MSTT, feature S, and feature PA and blood pressure, combined with the calibration parameters provided by the blood pressure measurement calibration module, perform linear fitting to establish an algorithm model, obtain model coefficients, and then perform Estimation of blood pressure, so as to obtain real-time blood pressure data.
作为本发明的进一步改进，在所述信号处理模块中，对PPG信号进行预处理包括滤波、去基线漂移和放大处理。As a further improvement of the present invention, in the signal processing module, preprocessing the PPG signal includes filtering, removing baseline drift and amplifying.
作为本发明的进一步改进，所述平均斜率传输时间MSTT＝f(A/m1)，m1是平均上坡斜度，m1包含最大上坡斜度m，f是关于m1的函数，A是在最大斜度点处给定的一个固定高度值。As a further improvement of the present invention, the average slope transit time MSTT=f(A/m1 ), m1 is the average uphill slope, m1 includes the maximum uphill slope m, and f is a function about m1 , A is a fixed height value given at the point of maximum slope.
作为本发明的进一步改进，根据平均斜率传输时间MSTT，建立算法模型：As a further improvement of the present invention, according to the average slope transit time MSTT, an algorithm model is established:
SBP＝a1*ln(MSTT)+b1SBP=a1 *ln(MSTT)+b1
DEP＝a2*ln(MSTT)+b2DEP＝a2*ln(MSTT )+ b2
其中SBP和DBP分别为收缩压和舒张压，a1、a2、b1、b2为回归系数。Among them, SBP and DBP are systolic blood pressure and diastolic blood pressure respectively, and a1 , a2 , b1 , b2 are regression coefficients.
作为本发明的进一步改进，所述特征S汲取了脉搏波波形的主波波峰和波谷以及主波波峰上升支的平均值，特征S反映整体的脉搏波波形的形态特征，特征S通过反映人体的血管特性从而间接的代表血压的变化，通过只分析脉搏波的形态特点，把特征S作为血压连续估算的特征，实现血压的连续估算。As a further improvement of the present invention, the feature S draws the main wave peak and trough of the pulse wave waveform and the average value of the rising branch of the main wave peak, the feature S reflects the morphological characteristics of the overall pulse wave waveform, and the feature S reflects the human body. The blood vessel characteristics thus indirectly represent the change of blood pressure. By only analyzing the morphological characteristics of the pulse wave, the feature S is used as the feature of the continuous estimation of blood pressure to realize the continuous estimation of blood pressure.
作为本发明的进一步改进，光电容积脉搏波的特征S的血压模型：As a further improvement of the present invention, the blood pressure model of the characteristic S of photoplethysmography:
SBP＝a1*ln(特征S)+b1SBP=a1 *ln(feature S)+b1
DBP＝a2*ln(特征S)+b2DBP=a2 *ln(feature S)+b2
其中SBP和DBP分别为收缩压和舒张压，a1、a2、b1、b2为回归系数。Among them, SBP and DBP are systolic blood pressure and diastolic blood pressure respectively, and a1 , a2 , b1 , b2 are regression coefficients.
作为本发明的进一步改进，所述特征PA通过分析脉搏波波形上升支和下降支之间的面积比来分析血压的波动变化，脉搏波的上升支信息代表了收缩压，下降支代表舒张压。As a further improvement of the present invention, the characteristic PA analyzes the fluctuation of blood pressure by analyzing the area ratio between the ascending branch and the descending branch of the pulse wave waveform. The ascending branch of the pulse wave represents the systolic pressure, and the descending branch represents the diastolic pressure.
作为本发明的进一步改进，通过把脉搏波波形上升支和下降支的面积分别进行量化分析，建立血压与脉搏波波形面积比之间的关系模型：As a further improvement of the present invention, the relationship model between the blood pressure and the area ratio of the pulse wave waveform is established by quantitatively analyzing the areas of the ascending branch and the descending branch of the pulse wave waveform respectively:
SBP＝a1*ln(特征PA)+b1SBP=a1 *ln(characteristic PA)+b1
DBP＝a2*ln(特征PA)+b2DBP=a2 *ln(characteristic PA)+b2
其中SBP和DBP分别为收缩压和舒张压，a1、a2、b1、b2为回归系数。Among them, SBP and DBP are systolic blood pressure and diastolic blood pressure respectively, and a1 , a2 , b1 , b2 are regression coefficients.
作为本发明的进一步改进，该无创血压测量装置还包括与所述处理器相连的电源管理模块、显示模块、存储器模块和无线通信模块As a further improvement of the present invention, the non-invasive blood pressure measurement device also includes a power management module connected to the processor, a display module, a memory module and a wireless communication module
作为本发明的进一步改进，所述处理器将提取出的平均斜率传输时间MSTT、特征S和特征PA进行融合，获得新的特征方程用于血压的估算：As a further improvement of the present invention, the processor fuses the extracted mean slope transit time MSTT, feature S, and feature PA to obtain a new feature equation for blood pressure estimation:
SBP＝a1*ln(MSTT)+b1*ln(特征S)+C1*ln(特征PA)+d1SBP=a1 *ln(MSTT)+b1 *ln(feature S)+C1 *ln(feature PA)+d1
DBP＝a2*ln(MSTT)+b2*ln(特征S)+C2*ln(特征PA)+d2DBP=a2*ln(MSTT )+ b2*ln(feature S)+C2 *ln(feature PA)+d2
其中SBP和DBP分别为收缩压和舒张压，a1、a2、b1、b2、c1、c2、d1、d2为回归系数。Among them, SBP and DBP are systolic blood pressure and diastolic blood pressure respectively, and a1 , a2 , b1 , b2 , c1 , c2 , d1 , and d2 are regression coefficients.
本发明的有益效果是：本发明通过对光电容积脉搏波信号的处理，提取脉搏波的特征，提出了新的可以替代脉搏波传输时间的参数：平均斜率传输时间MSTT，由于平均斜率传输时间不受心脏射血前期(PEP)的影响，从而消除了PEP对于无创血压连续测量装置的影响，实现了通过单一的生理信号光电容积脉搏波来估算血压，并且采用被动式的测量方式，减少了外部因素对于测量装置的影响，本发明可以实现实时的无创血压连续测量，易于操作，可用于穿戴式，方便用户日常使用。The beneficial effect of the present invention is: the present invention extracts the characteristic of pulse wave through the processing of photoplethysmography signal, proposes the new parameter that can replace pulse wave transmission time: average slope transit time MSTT, because average slope transit time is not Affected by the pre-ejection period (PEP), the influence of PEP on the non-invasive blood pressure continuous measurement device is eliminated, and the blood pressure is estimated by a single physiological signal photoplethysmography, and the passive measurement method reduces external factors Regarding the influence of the measuring device, the present invention can realize real-time non-invasive blood pressure continuous measurement, is easy to operate, can be used in wearable type, and is convenient for daily use by users.
附图说明Description of drawings
图1是基于心电和脉搏的脉搏波传输时间示意图。Fig. 1 is a schematic diagram of pulse wave transit time based on ECG and pulse.
图2是脉搏波成分图。Fig. 2 is a diagram of pulse wave components.
图3是STT原理图。Fig. 3 is the schematic diagram of STT.
图4是STT计算的简易模型图。Fig. 4 is a simple model diagram of STT calculation.
图5是特征S示意图。Fig. 5 is a schematic diagram of feature S.
图6是基于MSTT的血压连续测量的流程图。Fig. 6 is a flowchart of continuous measurement of blood pressure based on MSTT.
图7是本发明的原理框图。Fig. 7 is a functional block diagram of the present invention.
具体实施方式detailed description
如图7所示，本发明公开了一种基于光电容积脉搏波特征的无创血压测量装置，本发明的无创血压测量装置不但可以克服传统血压计因为袖带而通常体积较大、不便于携带的缺点，而且相对于基于脉搏波传导时间PAT的血压连续测量装置，本发明的无创血压测量装置更加简单精准。As shown in Figure 7, the present invention discloses a non-invasive blood pressure measurement device based on the characteristics of photoplethysmography. Shortcomings, and compared with the blood pressure continuous measurement device based on the pulse wave transit time PAT, the non-invasive blood pressure measurement device of the present invention is simpler and more accurate.
本发明的基于光电容积脉搏波特征的无创血压测量装置包括处理器、以及与所述处理器相连的脉搏波模块、信号处理模块、血压测量校准模块。The non-invasive blood pressure measurement device based on photoplethysmography features of the present invention includes a processor, a pulse wave module connected to the processor, a signal processing module, and a blood pressure measurement calibration module.
所述脉搏波模块用于采集人体的脉搏波信号，脉搏波信号采用光电容积脉搏波法(PPG)，在处理器的控制下，由脉搏波模拟前端驱动发光二极管工作并采集接收二极管的光学模拟信号进行初步处理，形成脉搏波形。The pulse wave module is used to collect the pulse wave signal of the human body. The pulse wave signal adopts photoplethysmography (PPG). The signal is preliminarily processed to form a pulse waveform.
信号处理模块：与脉搏波模块相连，用于接收被检测者的PPG信号，对接收到的PPG信号进行预处理，对PPG信号进行基本的滤波、去基线漂移和放大等处理，主要使用工频陷波器，巴特沃斯低通滤波器，形态学滤波器等使信号达到医疗诊断的标准。Signal processing module: connected to the pulse wave module, used to receive the PPG signal of the detected person, preprocess the received PPG signal, perform basic filtering, baseline drift removal and amplification on the PPG signal, mainly using power frequency Notch filter, Butterworth low-pass filter, morphological filter, etc. make the signal reach the standard of medical diagnosis.
血压测量校准模块：用于提供血压的校准参数。Blood pressure measurement calibration module: used to provide blood pressure calibration parameters.
处理器：对采集到PPG信号进行模数转换，特征点检测，计算平均斜率传输时间(MSTT)、波形特征S、脉搏波直径PR，结合血压测量校准模块提供的校准参数来实时的计算血压，从而得到实时血压数据。Processor: Perform analog-to-digital conversion on the collected PPG signal, detect feature points, calculate mean slope transit time (MSTT), waveform characteristic S, and pulse wave diameter PR, and combine the calibration parameters provided by the blood pressure measurement calibration module to calculate blood pressure in real time. Thereby real-time blood pressure data can be obtained.
本发明还包括与处理器相连的显示模块，显示模块：用于接收脉搏波模块采集到的脉搏波信号和处理器计算的实时血压数据，实现对各种生理信号和血压测量值的实时直观显示。The present invention also includes a display module connected to the processor, and the display module is used to receive the pulse wave signal collected by the pulse wave module and the real-time blood pressure data calculated by the processor, so as to realize real-time visual display of various physiological signals and blood pressure measurement values .
具体的方案：首先利用传统的标准血压计对受测者进行血压测量用来校准，把测量值手动输入到血压测量校准单元，血压测量校准单元会根据测量值计算出校准参数并保存在处理器。利用脉搏波模块采集得到脉搏波信号(PPG)，通过信号处理单元对采集到的信号进行滤波去噪和放大，然后进入处理器。利用处理器在脉搏波信号(PPG)上选择参考点，结合处理器中保存的血压测量公式计算出血压测量结果，最后通过显示模块进行同步显示。Specific plan: First, use a traditional standard blood pressure monitor to measure the blood pressure of the subject for calibration, and manually input the measured value into the blood pressure measurement and calibration unit, which will calculate the calibration parameters based on the measured value and save them in the processor . The pulse wave signal (PPG) is collected by the pulse wave module, and the collected signal is filtered, denoised and amplified by the signal processing unit, and then enters the processor. A processor is used to select a reference point on the pulse wave signal (PPG), combined with a blood pressure measurement formula stored in the processor, the blood pressure measurement result is calculated, and finally displayed synchronously through a display module.
1.光电容积脉搏波的特征MSTT：1. Characteristics of photoplethysmography MSTT:
本发明提出一种新的可以替代脉搏波传输时间的参数平均斜率传输时间(MSTT)，下面是MSTT提出的整个思路：The present invention proposes a new parameter mean slope transit time (MSTT) that can replace the pulse wave transit time. The following is the whole idea proposed by MSTT:
脉搏波传输时间整个血压连续估算的核心，而脉搏波的传输时间与血压是呈反向变化关系，我们可以假设，在一个呼吸周期内，其将同由呼吸活动所引发的血压一起周期性变化。在吸气的时候，动脉树中的动脉血压会降低，因此传输时间就会升高。相应地，在呼气的时候，血压会升高，那么传输时间就会相应减少。然而，在整个呼吸周期中，脉搏的周期性变化以及内部脉搏分量(脉搏波由它们合成)的周期性变化相互产生反作用，共同组成了脉搏波，基于这项发现，我们就引导出了一种新型的单脉冲，单点传输时间STT。The pulse wave transit time is the core of the continuous estimation of the entire blood pressure, and the pulse wave transit time and blood pressure have an inverse relationship. We can assume that in a breathing cycle, it will change periodically with the blood pressure caused by respiratory activity . During inspiration, the arterial blood pressure in the arterial tree decreases, so the transit time increases. Correspondingly, during exhalation, blood pressure increases and the transit time decreases accordingly. However, based on the discovery that the periodic changes of the pulse and the internal pulse components from which the pulse wave is synthesized react against each other throughout the respiratory cycle to form the pulse wave, we lead to a Novel monopulse, single point transit time STT.
传感器端所接收到的信号其实是由一个初始脉冲波形叠加上一系列的反射波形所组成的，如图2所示。这些波形叠加在一起，形成了实际中最后我们所观察到PPG波形。然而，这个波形包含两个相互矛盾的时间元素(机理如图3所示)：在呼气的时候，因为动脉血压会升高，所以初始波也会传输的快一些，因此PPT会下降，故周期P1变短。然而，脉搏周期P2(例如：心脏脉搏中任何两个重复特征的周期)就会增加，这是由于在这个阶段的呼吸周期中心率降低(原因是呼吸性窦性心律RSA)。事实上P2＝60/HR(心率)。在吸气过程中恰好相反，血压降低因此P1增加，心率升高因此P2变短。这两个时间元素互为反比，并有可能带来不好的结果——当在单个PPG脉冲中由两个基点分开来测传输时间的话，有可能会得到两个相反的结果。The signal received by the sensor end is actually composed of an initial pulse waveform superimposed on a series of reflected waveforms, as shown in Figure 2. These waveforms are superimposed to form the last PPG waveform we observe in practice. However, this waveform contains two contradictory time elements (the mechanism is shown in Figure 3): During exhalation, because the arterial blood pressure will increase, the initial wave will also travel faster, so the PPT will decrease, so The period P1 becomes shorter. However, the pulse period P2 (eg, any two repeating characteristic periods in the cardiac pulse) increases due to the decrease in heart rate during this phase of the respiratory cycle (due to respiratory sinus rhythm RSA). In fact P2 = 60/HR (heart rate). The opposite is true during inspiration, blood pressure decreases so P1 increases and heart rate increases so P2 becomes shorter. These two time elements are inversely proportional to each other and may lead to bad results - when the transit time is measured by two base points separated in a single PPG pulse, two opposite results may be obtained.
再回到图3中来，从几何角度出发，可以看到当PTT(PAT)以及P1相应增加的时候，初始脉冲分量的上坡梯度(m)是减少的。另外实践证明，初始脉冲信号应该在接收到的合成PPG中占主导地位，也就是说从接收到的PPG信号中提取的结果应与初始信号中的斜率m近似。再进一步，我们考虑固定高度A变化下的斜坡梯度，该梯度可以认为是特征时间差的倒数，如图4所示。作为常数可变幅度A，它可以看作是特征时间差——STT，可以根据P1的“时间伸展”来变化。因此有m＝A/STT，传输时间STT＝A/m。如图3所示，由于STT不受心率和心脏射血前期影响，所以相对于获取PTT的其他方式，STT更适合取代PTT。Returning to Figure 3, from a geometric point of view, it can be seen that when the PTT (PAT) and P1 increase accordingly, the uphill gradient (m) of the initial pulse component decreases. In addition, practice has proved that the initial pulse signal should dominate the received synthetic PPG, that is to say, the result extracted from the received PPG signal should be similar to the slope m in the original signal. Going a step further, we consider the slope gradient under a fixed height A change, which can be considered as the reciprocal of the characteristic time difference, as shown in Figure 4. As a constant variable amplitude A, it can be seen as a characteristic time difference - STT, which can be varied according to the "time stretch" of P1. Therefore m=A/STT, transmission time STT=A/m. As shown in Figure 3, since STT is not affected by heart rate and pre-ejection, STT is more suitable to replace PTT than other methods of obtaining PTT.
另一方面，由于上坡斜度m是脉搏波信号上坡斜度最大值的位置，只是一个单点的斜度，脉搏波信号的质量的好坏对于m的影响很大，造成m的稳定性不高，不能代表真个信号，所以为了提高整体的抗噪声性能，本发明提出了平均斜率传输时间MSTT＝f(A/m1)，m1是平均上坡斜度，它包含最大上坡斜度m。f是关于m1的函数，用来计算MSTT。根据血压和平均斜率传输时间MSTT的特点，建立算法模型：On the other hand, since the uphill slope m is the position of the maximum value of the uphill slope of the pulse wave signal, it is only a single-point slope, and the quality of the pulse wave signal has a great influence on m, resulting in the stability of m Therefore, in order to improve the overall anti-noise performance, the present invention proposes the average slope transit time MSTT=f(A/m1 ), where m1 is the average uphill slope, which includes the maximum uphill slope Slope slope m. f is a function of m1 and is used to calculate MSTT. According to the characteristics of blood pressure and mean slope transit time MSTT, an algorithm model is established:
SBP＝a1*ln(MSTT)+b1SBP=a1 *ln(MSTT)+b1
DBP＝a2*ln(MSTT)+b2DBP=a2*ln(MSTT )+ b2
注：模型不仅仅局限于特征MSTT参数。Note: The model is not limited to the characteristic MSTT parameters.
其中SBP和DBP分别为收缩压和舒张压，a1、a2、b1、b2为回归系数。Among them, SBP and DBP are systolic blood pressure and diastolic blood pressure respectively, and a1 , a2 , b1 , b2 are regression coefficients.
该模型首先需要对受试者进行标定，获取受试者的平均斜率传输时间、收缩压、舒张压，通过回归分析求出模型系数，然后根据采集到的受试者的脉搏波提取MSTT，进行每搏血压的计算。The model first needs to calibrate the subject, obtain the subject's average slope transit time, systolic blood pressure, and diastolic blood pressure, and obtain the model coefficients through regression analysis, and then extract the MSTT according to the collected subject's pulse wave, and carry out Calculation of stroke blood pressure.
2.光电容积脉搏波的特征S2. Characteristics of photoplethysmography S
MSTT作为脉搏波的特征之一可以提供血压的连续测量，除了MSTT外，我们还提出了一种新的光电容积脉搏波的特征S(如图5所示)，特征S汲取了脉搏波波形的主波波峰和波谷以及主波波峰上升支的平均值，它可以反映整体的脉搏波波形的形态特征，脉搏波波形的形态与血管的生理信息和外周阻力有很大的关联，脉搏波波形的主波波峰和波谷的变化信息可以反映出血管弹性进和血管壁的僵硬化程度，人体的血压与血管的生理特征有很大的关系，当血管壁的僵硬化程度较高或者血管弹性较低时，直接的反映是脉搏波的主波波峰和波谷的绝对高端的减小，而此时血压会升高。与血管弹性相似，外周阻力大小也可以通过特征S反映出来，所以特征S可以通过反映人体的血管特性从而间接的代表血压的变化，通过只分析脉搏波的形态特点，把特征S作为血压连续估算的特征，可以实现血压的连续估算。As one of the characteristics of pulse wave, MSTT can provide continuous measurement of blood pressure. In addition to MSTT, we also propose a new feature S of photoplethysmography (as shown in Figure 5). Feature S draws the pulse wave waveform The average value of the peak and trough of the main wave and the ascending branch of the main wave can reflect the morphological characteristics of the overall pulse wave waveform. The shape of the pulse wave waveform is closely related to the physiological information of blood vessels and peripheral resistance. The change information of the peak and trough of the main wave can reflect the elasticity of the blood vessel and the degree of stiffness of the blood vessel wall. The blood pressure of the human body has a great relationship with the physiological characteristics of the blood vessel. When , the direct reflection is the reduction of the absolute high end of the main wave peak and trough of the pulse wave, and at this time the blood pressure will increase. Similar to blood vessel elasticity, the peripheral resistance can also be reflected by the feature S, so the feature S can indirectly represent the change of blood pressure by reflecting the vascular characteristics of the human body. By only analyzing the morphological characteristics of the pulse wave, the feature S can be used as a continuous estimation of blood pressure The characteristics of the system can realize the continuous estimation of blood pressure.
光电容积脉搏波的特征S的血压模型：Blood pressure model of characteristic S of photoplethysmography:
SBP＝a1*ln(特征S)+b1SBP=a1 *ln(feature S)+b1
DBP＝a2*ln(特征S)+b2DBP=a2 *ln(feature S)+b2
注：模型不仅仅局限于特征S参数。Note: The model is not limited to the characteristic S-parameters.
其中SBP和DBP分别为收缩压和舒张压，a1、a2、b1、b2为回归系数。Among them, SBP and DBP are systolic blood pressure and diastolic blood pressure respectively, and a1 , a2 , b1 , b2 are regression coefficients.
该模型首先需要对受试者进行标定，获取受试者的特征S、收缩压、舒张压，通过回归分析求出模型系数，然后根据采集到的受试者的脉搏波提取特征S，进行每搏血压的计算。The model first needs to calibrate the subject, obtain the subject's characteristic S, systolic blood pressure, and diastolic blood pressure, and obtain the model coefficients through regression analysis, and then extract the characteristic S according to the collected subject's pulse wave, and perform each Calculation of stroke blood pressure.
特征S的生理意义：特征S是从单一生理信号光电容积脉搏波PPG中提取，它代表了整个脉搏波波形形态，可以反映血管的生理形态信息，包括血管弹性和血管壁僵硬度，同时特征S还可以反映人体血管外周阻力的大小，而血管弹性和外周阻力的大小都是血压的重要影响因素，所以特征S可以很好的反映血压的变化。Physiological significance of feature S: Feature S is extracted from a single physiological signal photoplethysmography PPG, which represents the entire pulse waveform shape and can reflect the physiological shape information of blood vessels, including blood vessel elasticity and blood vessel wall stiffness, while feature S It can also reflect the peripheral resistance of human blood vessels, and both the elasticity of blood vessels and the peripheral resistance are important factors affecting blood pressure, so feature S can well reflect changes in blood pressure.
3.光电容积脉搏波的特征PA3. Characteristics of photoplethysmography PA
本发明是基于桡动脉脉搏波特征来进行血压的连续测量，除了上述的两个特征MSTT和特征S外，光电容积脉搏波的特征PA也是一个重要特征，特征PA通过分析脉搏波波形上升支和下降支之间的面积比来分析血压的波动变化。脉搏波的上升支信息代表了收缩压，下降支代表舒张压，通过把脉搏波波形上升支和下降支的面积分别进行量化分析，可以建立血压与脉搏波波形面积比之间的关系模型。The present invention is based on radial artery pulse wave characteristics to carry out continuous measurement of blood pressure, in addition to the above-mentioned two characteristics MSTT and characteristic S, the characteristic PA of the photoplethysmography wave is also an important characteristic, the characteristic PA is by analyzing the pulse wave waveform ascending branch and The area ratio between the descending branches was used to analyze the fluctuation of blood pressure. The ascending branch of the pulse wave represents the systolic blood pressure, and the descending branch represents the diastolic pressure. By quantitatively analyzing the areas of the ascending and descending branches of the pulse wave waveform, the relationship model between blood pressure and the area ratio of the pulse wave waveform can be established.
SBP＝a1*ln(特征PA)+b1SBP=a1 *ln(characteristic PA)+b1
DBP＝a2*ln(特征PA)+b2DBP=a2 *ln(characteristic PA)+b2
注：模型不仅仅局限于特征PA参数。NOTE: The model is not limited to the characteristic PA parameters.
其中SBP和DBP分别为收缩压和舒张压，a1、a2、b1、b2为回归系数。注：模型不仅仅局限于特征PA参数。Among them, SBP and DBP are systolic blood pressure and diastolic blood pressure respectively, and a1 , a2 , b1 , b2 are regression coefficients. NOTE: The model is not limited to the characteristic PA parameters.
该模型首先需要对受试者进行标定，获取受试者的特征PA、收缩压、舒张压，通过回归分析求出模型系数，然后根据采集到的受试者的脉搏波提取特征PA，进行每搏血压的计算。The model first needs to calibrate the subject, obtain the subject's characteristic PA, systolic blood pressure, and diastolic blood pressure, and obtain the model coefficients through regression analysis, and then extract the characteristic PA according to the collected subject's pulse wave, and perform each Calculation of stroke blood pressure.
生理意义：光电容积脉搏波波形的上升支和下降支的面积可以反映心脏收缩和舒张时候的强度，心脏收缩左心室射血进入动脉，血流量可以通过上升支的面积来进行量化，不同的面积可以代表血压大小，上升支和下降支的面积比也可以衡量心脏生理活动的信息。Physiological significance: The area of the ascending branch and descending branch of the photoplethysmogram can reflect the strength of the heart during systole and diastole. The left ventricle ejects blood into the artery during systole, and the blood flow can be quantified by the area of the ascending branch. Different areas It can represent the blood pressure, and the area ratio of the ascending and descending branches can also measure the information of the physiological activity of the heart.
4.MSTT、特征S和特征PA的融合4. Fusion of MSTT, feature S and feature PA
通过对桡动脉脉搏波波形的分析，我们提取了平均斜率传输时间、特征S和特征PA，三种特征分别可以反映不同的人体生理信息，为了提高本发明装置的准确性，我们把提取出的三个特征进行融合，获得新的特征方程用于血压的估算。By analyzing the pulse waveform of the radial artery, we have extracted the average slope transit time, the characteristic S and the characteristic PA, and the three characteristics can reflect different human physiological information respectively. In order to improve the accuracy of the device of the present invention, we extract the The three features are fused to obtain a new characteristic equation for blood pressure estimation.
SBP＝a1*ln(MSTT)+b1*ln(特征S)+C1*ln(特征PA)+d1SBP=a1 *ln(MSTT)+b1 *ln(feature S)+C1 *ln(feature PA)+d1
DBP＝a2*ln(MSTT)+b2*ln(特征S)+C2*ln(特征PA)+d2DBP=a2*ln(MSTT )+ b2*ln(feature S)+C2 *ln(feature PA)+d2
注：模型不仅仅局限于3个参数。NOTE: Models are not limited to just 3 parameters.
其中SBP和DBP分别为收缩压和舒张压，a1、a2、b1、b2、c1、c2、d1、d2为回归系数。Among them, SBP and DBP are systolic blood pressure and diastolic blood pressure respectively, and a1 , a2 , b1 , b2 , c1 , c2 , d1 , and d2 are regression coefficients.
该模型首先需要对受试者进行标定，获取受试者的收缩压、舒张压，通过回归分析求出模型系数，然后根据采集到的受试者的脉搏波提取MSTT、特征S和特征PA，进行每搏血压的计算。The model first needs to calibrate the subject, obtain the systolic blood pressure and diastolic blood pressure of the subject, and obtain the model coefficients through regression analysis, and then extract the MSTT, feature S and feature PA according to the collected pulse wave of the subject, Calculate the stroke blood pressure.
生理意义：通过对特征MSTT、特征S和特征PA的融合，可以综合的反映光电容积脉搏波中隐含的人体生理活动信息，心血管的活动变化，血管的生理状况以及外周阻力的大小，通过几个特征的结合，可以比较全面的反映与血压相关的生理参数信息，从而可以提高本发明装置的血测量血压的准确性。Physiological significance: Through the fusion of feature MSTT, feature S and feature PA, it can comprehensively reflect the hidden human physiological activity information in the photoplethysmography wave, the change of cardiovascular activity, the physiological condition of blood vessels and the size of peripheral resistance. The combination of several features can comprehensively reflect the physiological parameter information related to blood pressure, thereby improving the accuracy of blood pressure measurement by the device of the present invention.
本发明具有如下特点：The present invention has following characteristics:
1.光电容积脉搏波的特征点提取；只利用脉搏波信号，提取脉搏波上坡斜度参数，相比传统的利用心电信号(ECG)和脉搏波信号(PPG)来说更加简单。1. Feature point extraction of photoplethysmographic pulse wave; only using pulse wave signal to extract pulse wave upslope slope parameters is simpler than the traditional use of electrocardiogram (ECG) and pulse wave signal (PPG).
2.平均斜率传输时间(MSTT)的计算；平均斜率传输时间是我们提出的一种新的可以代替传统脉搏波传输时间(PTT)的参数，因为MSTT不含有心脏射血前期(PEP)，可靠性和稳定性更高。2. Calculation of mean slope transit time (MSTT); mean slope transit time is a new parameter proposed by us that can replace traditional pulse wave transit time (PTT), because MSTT does not contain pre-ejection pre-ejection (PEP), reliable Higher performance and stability.
3.基于MSTT的血压连续估算模型；此模型是基于MSTT(外加其他特征)而设计的算法模型，相比于传统的算法模型，该算法模型更可靠，算法精度更高，开辟了一个新的算法模型。3. The blood pressure continuous estimation model based on MSTT; this model is an algorithm model designed based on MSTT (plus other features). Compared with the traditional algorithm model, this algorithm model is more reliable and has higher algorithm accuracy, opening up a new Algorithmic model.
在图1中，ECG为心电图，PPG为脉搏曲线图。In Fig. 1, ECG is an electrocardiogram, and PPG is a pulse graph.
脉搏波传输时间(PTT)：脉搏波传输时间是指脉搏波从心脏近端到心脏远端的传输时间，传统的脉搏波传输时间是通过设备同时采集人体的心电信号(ECG)和脉搏波信号(PPG)，由于人体内心电信号的传导速度要比脉搏波的传导速度快，心电信号的传导时间可以忽略不计，脉搏波的传输时间可以视为心电信号和脉搏波信号固定点之间的时间差，一般取心电信号R波开始和脉搏波信号的波峰结束之间的时间差值为脉搏波传输时间PTT。注：此处的PTT其实应为PAT(PAT＝PTT+PEP)，由于传统的基于脉搏波传输时间PTT的血压算法忽略了心脏射血期PEP，所以把PAT默认为PTT。Pulse wave transit time (PTT): The pulse wave transit time refers to the transit time of the pulse wave from the proximal end of the heart to the far end of the heart. The traditional pulse wave transit time is to simultaneously collect the human body's electrocardiogram (ECG) and pulse wave Signal (PPG), because the conduction speed of the electrical signal in the human body is faster than the conduction speed of the pulse wave, the conduction time of the ECG signal can be ignored, and the transmission time of the pulse wave can be regarded as the distance between the fixed point of the ECG signal and the pulse wave signal. Generally, the time difference between the start of the R wave of the ECG signal and the end of the peak of the pulse wave signal is taken as the pulse wave transmission time PTT. Note: The PTT here should actually be PAT (PAT=PTT+PEP). Since the traditional blood pressure algorithm based on pulse wave transit time PTT ignores the cardiac ejection period PEP, PAT is defaulted to PTT.
如图4所示，A为定义固定高度，m为最大斜度，STT为斜率传输时间。As shown in Figure 4, A is the defined fixed height, m is the maximum slope, and STT is the slope transmission time.
平均斜率传输时间(MSTT)：斜率传输时间是从光电容积脉搏波中提取出的新的因子，在心脏收缩时，心脏射血进入动脉，此时血液容量会上升，在脉搏波中体现为波形上升阶段，找到脉搏波上升段的最大斜度m，并且在最大斜度点处给定一个固定高度值A，则最大斜度m＝A/STT，从而可以计算出最大斜率传输时间STT＝A/m。为了减少误差和提高抗噪性能，提出平均斜率传输时间MSTT＝f(A/m1)，其中m1代表平均坡度，f是关于m1的函数。Mean Slope Transit Time (MSTT): Slope Transit Time is a new factor extracted from photoplethysmography. When the heart contracts, the heart ejects blood into the artery. At this time, the blood volume will increase, which is reflected in the pulse wave as a waveform In the rising stage, find the maximum slope m of the pulse wave rising section, and give a fixed height value A at the maximum slope point, then the maximum slope m=A/STT, so that the maximum slope transmission time STT=A can be calculated /m. In order to reduce the error and improve the anti-noise performance, the average slope transit time MSTT=f(A/m1 ), where m1 represents the average slope, and f is a function about m1 .
如图6所示，其工作原理如下：采集脉搏数据后，将数据通过平滑滤波，去基线偏移等预处理。从预处理过的脉搏信号中提取特征MSTT、特征S和特征PA，然后根据平均斜率脉搏传输时间MSTT、特征S和特征PA于血压之间的关系，结合对受测者预先进行的标定参数进行线性拟合建立算法模型，获取模型系数，再进行血压的估算。As shown in Figure 6, its working principle is as follows: After the pulse data is collected, the data is preprocessed by smoothing and filtering, removing baseline offset, etc. Extract feature MSTT, feature S and feature PA from the preprocessed pulse signal, and then according to the relationship between the average slope pulse transit time MSTT, feature S and feature PA and blood pressure, combined with the pre-calibrated parameters of the subject. Linear fitting establishes an algorithm model, obtains model coefficients, and then estimates blood pressure.
如图7所示，其工作原理如下：下位机通过无线方式接收到来自上位机的控制信息及用户信息，下位机在本地数据库中检查是否存在该用户的信息，如没有则为该用户创建本地数据目录。处理器驱动脉搏波模块采集人体生理参数，待数据采集结束后将相关生理参数存入本地的存储器模块，同时将其以无线方式发送至上位机，并且采集的生理参数经处理器处理后通过显示模块展示。其中无线通信模块采用蓝牙4.0通信方式，下位机到上位机采取通知的传输形式。As shown in Figure 7, its working principle is as follows: the lower computer receives the control information and user information from the upper computer through wireless, and the lower computer checks whether the user’s information exists in the local database, and if not, creates a local database for the user. data directory. The processor drives the pulse wave module to collect the physiological parameters of the human body. After the data collection is completed, the relevant physiological parameters are stored in the local memory module, and at the same time, they are sent to the host computer wirelessly, and the collected physiological parameters are processed by the processor and displayed on the display. Module display. Among them, the wireless communication module adopts Bluetooth 4.0 communication mode, and the transmission form of notification is adopted from the lower computer to the upper computer.
ECG：心电信号，PPG：光电容积脉搏波，PTT：脉搏波传输时间，PAT：脉搏波传导时间，PEP：心脏射血前期，STT：斜率传输时间，MSTT：平均斜率传输时间。ECG: ECG signal, PPG: Photoplethysmography, PTT: Pulse wave transit time, PAT: Pulse wave transit time, PEP: Pre-ejection period, STT: Slope transit time, MSTT: Mean slope transit time.
本发明具有如下有益效果：本发明通过对光电容积脉搏波信号的处理，提取脉搏波的特征，提出了新的可以替代脉搏波传输时间的参数：平均斜率传输时间MSTT，由于平均斜率传输时间不受心脏射血前期(PEP)的影响，从而消除了PEP对于无创血压连续测量装置的影响，实现了通过单一的生理信号光电容积脉搏波来估算血压，并且采用被动式的测量方式，减少了外部因素对于测量装置的影响，本发明可以实现实时的无创血压连续测量，易于操作，可用于穿戴式，方便用户日常使用。The present invention has the following beneficial effects: the present invention extracts the characteristics of the pulse wave through the processing of the photoplethysmography signal, and proposes a new parameter that can replace the pulse wave transit time: the average slope transit time MSTT. Affected by the pre-ejection period (PEP), the influence of PEP on the non-invasive blood pressure continuous measurement device is eliminated, and the blood pressure is estimated by a single physiological signal photoplethysmography, and the passive measurement method reduces external factors Regarding the influence of the measuring device, the present invention can realize real-time non-invasive blood pressure continuous measurement, is easy to operate, can be used in wearable type, and is convenient for daily use by users.
以上内容是结合具体的优选实施方式对本发明所作的进一步详细说明，不能认定本发明的具体实施只局限于这些说明。对于本发明所属技术领域的普通技术人员来说，在不脱离本发明构思的前提下，还可以做出若干简单推演或替换，都应当视为属于本发明的保护范围。The above content is a further detailed description of the present invention in conjunction with specific preferred embodiments, and it cannot be assumed that the specific implementation of the present invention is limited to these descriptions. For those of ordinary skill in the technical field of the present invention, without departing from the concept of the present invention, some simple deduction or replacement can be made, which should be regarded as belonging to the protection scope of the present invention.
| Application Number | Priority Date | Filing Date | Title |
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| CN201710300226.7ACN107233087A (en) | 2017-04-28 | 2017-04-28 | A kind of Woundless blood pressure measuring device based on photoplethysmographic feature |
| Application Number | Priority Date | Filing Date | Title |
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| CN201710300226.7ACN107233087A (en) | 2017-04-28 | 2017-04-28 | A kind of Woundless blood pressure measuring device based on photoplethysmographic feature |
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| CN107233087Atrue CN107233087A (en) | 2017-10-10 |
| Application Number | Title | Priority Date | Filing Date |
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| CN201710300226.7APendingCN107233087A (en) | 2017-04-28 | 2017-04-28 | A kind of Woundless blood pressure measuring device based on photoplethysmographic feature |
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