技术领域Technical Field
本发明涉及光学测量技术领域，具体而言，涉及基于自混合干涉和微纳光纤的人体多参量监测装置。The present invention relates to the field of optical measurement technology, and in particular to a human body multi-parameter monitoring device based on self-mixing interference and micro-nano optical fiber.
背景技术Background technique
随着人们生活水平的不断提高和饮食结构的改变，心脑血管疾病对人类健康的威胁日益严重，在日常生活中通过持续监测脉搏信息和血压来自我管理健康状况和预防疾病变得更加重要。因此脉搏波和血压的持续监测对日常生活中心脑血管疾病的预防和诊断具有重要的临床价值。传统的测量装置多采用水银血压计和电子血压计，水银血压计监测血压和脉搏由于人为的听觉和视觉误差，需要凭借个人经验测量数值，对操作者的要求较高，一般为医生或有经验的护士，不适合普通人自行测量；电子血压计使用更便捷，但也需要佩戴袖套进行间歇性充气，测量的操作不便。With the continuous improvement of people's living standards and changes in dietary structure, cardiovascular and cerebrovascular diseases pose an increasingly serious threat to human health. It has become more important to self-manage health status and prevent diseases by continuously monitoring pulse information and blood pressure in daily life. Therefore, continuous monitoring of pulse waves and blood pressure has important clinical value for the prevention and diagnosis of cardiovascular and cerebrovascular diseases in daily life. Traditional measuring devices mostly use mercury sphygmomanometers and electronic sphygmomanometers. Mercury sphygmomanometers monitor blood pressure and pulse due to human auditory and visual errors. The values need to be measured based on personal experience, and the requirements for operators are high. Generally, they are doctors or experienced nurses, and are not suitable for ordinary people to measure by themselves; electronic sphygmomanometers are more convenient to use, but they also need to wear cuffs for intermittent inflation, which makes the measurement inconvenient.
目前，将光子传感技术应用于监测人体血压和脉搏备受研究者们的关注，然而现阶段研究得到的装置存在开发成本高、准确性差，缺乏舒适性、难实现等问题，甚至由于所用材料的弯曲和延展性差，缺乏弹性易断裂等问题而存在安全隐患，因此，亟需开发一种成本低、准确性高、舒适可行的光学人体血压和脉搏检测装置。At present, the application of photon sensing technology in monitoring human blood pressure and pulse has attracted much attention from researchers. However, the devices currently developed have problems such as high development cost, poor accuracy, lack of comfort, and difficulty in implementation. There are even safety hazards due to the poor bending and ductility of the materials used, lack of elasticity and easy breakage. Therefore, there is an urgent need to develop a low-cost, high-accuracy, comfortable and feasible optical human blood pressure and pulse detection device.
发明内容Summary of the invention
本发明要解决的技术问题是：The technical problems to be solved by the present invention are:
现有的光学脉搏、血压监测装置存在成本高、准确性差以及难实现的问题。Existing optical pulse and blood pressure monitoring devices have the problems of high cost, poor accuracy and difficulty in implementation.
本发明为解决上述技术问题所采用的技术方案：The technical solution adopted by the present invention to solve the above technical problems is as follows:
本发明提供的基于自混合干涉和微纳光纤的人体多参量监测装置，包括传感膜片、激光器、光电探测器，数据采集卡、信号处理单元和血压计算单元；The human multi-parameter monitoring device based on self-mixing interference and micro-nano optical fiber provided by the present invention includes a sensing diaphragm, a laser, a photoelectric detector, a data acquisition card, a signal processing unit and a blood pressure calculation unit;
所述传感膜片包括微纳光纤和柔性膜片，所述微纳光纤嵌于所述柔性膜片中，所述传感膜片用于采集脉搏信息，脉搏振动引起柔性膜片发生形变导致微纳光纤的折射坡面发生改变；The sensing membrane comprises a micro-nano optical fiber and a flexible membrane, wherein the micro-nano optical fiber is embedded in the flexible membrane, and the sensing membrane is used to collect pulse information. Pulse vibration causes the flexible membrane to deform, resulting in a change in the refractive slope of the micro-nano optical fiber.
所述激光器通过光纤与微纳光纤的一端连接，所述微纳光纤的另一端设有反射端，在驱动电流作用下激光器可发射一定波长的输出光信号，所述输出光信号经脉搏振动处，经反射端反射后，携带脉搏信息的光信号返回至激光器谐振腔内与原光场生成自混合干涉信号；The laser is connected to one end of the micro-nano optical fiber through an optical fiber, and the other end of the micro-nano optical fiber is provided with a reflection end. Under the action of the driving current, the laser can emit an output optical signal of a certain wavelength. After the output optical signal passes through the pulse vibration point and is reflected by the reflection end, the optical signal carrying the pulse information returns to the laser resonant cavity to generate a self-mixing interference signal with the original optical field;
所述光电探测器设于所述激光器内部，用于将自混合干涉信号转化为连续的模拟信号并发送至数据采集卡；The photoelectric detector is arranged inside the laser and is used to convert the self-mixing interference signal into a continuous analog signal and send it to a data acquisition card;
所述数据采集卡与光电探测器连接，所述数据采集卡为USB动态信号采集卡，用于将接收的模拟信号转换为数字信号，并将数字信号传送至信号处理单元；The data acquisition card is connected to the photoelectric detector, and the data acquisition card is a USB dynamic signal acquisition card, which is used to convert the received analog signal into a digital signal and transmit the digital signal to the signal processing unit;
所述信号处理单元用于对接收的数字信号进行处理得到脉搏波信息，并将脉搏波信息传送至血压计算单元；The signal processing unit is used to process the received digital signal to obtain pulse wave information, and transmit the pulse wave information to the blood pressure calculation unit;
所述血压计算单元用于根据脉搏波信息计算人体血压数值。The blood pressure calculation unit is used to calculate the blood pressure value of the human body according to the pulse wave information.
进一步地，所述微纳光纤为双锥微纳光纤，所述双锥微纳光纤两端的锥形区长度均为15mm，腰区长度为12mm，腰区直径为1.8μm。Furthermore, the micro-nano optical fiber is a double-tapered micro-nano optical fiber, the length of the tapered regions at both ends of the double-tapered micro-nano optical fiber is 15 mm, the length of the waist region is 12 mm, and the diameter of the waist region is 1.8 μm.
进一步地，所述柔性膜片为聚二甲基硅氧烷膜片。Furthermore, the flexible membrane is a polydimethylsiloxane membrane.
进一步地，所述传感膜片的长度为7.5cm、宽度为2.2cm。Furthermore, the sensing membrane has a length of 7.5 cm and a width of 2.2 cm.
进一步地，所述微纳光纤嵌于所述柔性膜片中的具体实现过程为：将适量进行脱气处理的聚二甲基硅氧烷平铺在一定尺寸的玻片上，将微纳光纤嵌入到聚二甲基硅氧烷中，对其进行固化处理形成膜片，将膜片从玻片上取下，即将微纳光纤嵌于柔性膜片中。Furthermore, the specific implementation process of embedding the micro-nano optical fiber in the flexible membrane is: spreading an appropriate amount of degassed polydimethylsiloxane on a glass slide of a certain size, embedding the micro-nano optical fiber into the polydimethylsiloxane, curing it to form a membrane, and removing the membrane from the glass slide, thereby embedding the micro-nano optical fiber in the flexible membrane.
进一步地，所述固化处理的条件为在80℃温度下加热20分钟。Furthermore, the curing treatment is carried out under the condition of heating at 80° C. for 20 minutes.
进一步地，所述双锥微纳光纤的制备方法为采用熔融拉伸法通过拉锥机进行制备。Furthermore, the preparation method of the double-tapered micro-nano optical fiber is to prepare it by a melt-drawing method using a taper machine.
进一步地，所述信号处理单元用于对接收的数字信号进行处理得到脉搏波信息，具体实现过程为：通过LabVIEW软件，将数字信号进行处理得到脉搏波形图，同时通过傅里叶变换将脉搏波形图转换为脉搏频谱图，得到脉搏波形信息和频率信息。Furthermore, the signal processing unit is used to process the received digital signal to obtain pulse wave information. The specific implementation process is: through LabVIEW software, the digital signal is processed to obtain a pulse waveform diagram, and at the same time, the pulse waveform diagram is converted into a pulse spectrum diagram through Fourier transform to obtain pulse waveform information and frequency information.
进一步地，所述血压计算单元用于根据脉搏波信息计算人体血压数值，具体实现过程为：Furthermore, the blood pressure calculation unit is used to calculate the blood pressure value of the human body according to the pulse wave information, and the specific implementation process is:
根据脉搏频谱图确定主波峰值到重振波峰值之间的时间跨度，表示为脉搏传输时间PTT，脉搏传输时间PTT与脉搏波速度PWV的关系为：The time span between the peak value of the main wave and the peak value of the re-vibration wave is determined according to the pulse spectrum diagram, which is expressed as the pulse transmission time PTT. The relationship between the pulse transmission time PTT and the pulse wave velocity PWV is:
其中，L表示脉搏波经过的血管长度；Among them, L represents the length of the blood vessel through which the pulse wave passes;
根据Brawell-hill方程，脉搏波速PWV可由血液密度ρ和动脉血容量v表示，具体为：According to the Brawell-hill equation, pulse wave velocity PWV can be expressed by blood density ρ and arterial blood volume v, specifically:
其中，V为动脉内血液体积，dV为动脉内血容量的变化量，dP为收缩压SBP和舒张压DBP之间的血压差，单位是mmHg，dP可以表示为：Where V is the blood volume in the artery, dV is the change in blood volume in the artery, and dP is the blood pressure difference between systolic pressure SBP and diastolic pressure DBP, in mmHg. dP can be expressed as:
dP＝SBP-DBP (3)dP＝SBP-DBP (3)
因此脉搏波速PWV可以表示为：Therefore, the pulse wave velocity PWV can be expressed as:
根据公式(1)和公式(4)可得到：According to formula (1) and formula (4), we can get:
另一方面，脉搏波速PWV可以用Moens-korteweg方程表示：On the other hand, pulse wave velocity PWV can be expressed by the Moens-Korteweg equation:
其中Ein为动脉弹性模量，h为动脉厚度，r为动脉半径，ρ为血液密度；Where Ein is the elastic modulus of the artery, h is the thickness of the artery, r is the radius of the artery, and ρ is the blood density;
随着平均血压MBP的增加，动脉的弹性模量呈指数增长，则动脉弹性模量可表示为：As the mean blood pressure MBP increases, the elastic modulus of the artery increases exponentially, and the elastic modulus of the artery can be expressed as:
Ein＝E0eα*MBP (7)Ein =E0 eα*MBP (7)
其中，E0为血压值为0时血管壁的杨氏模量，ɑ是人体血管相关的特定参数；Among them, E0 is the Young's modulus of the blood vessel wall when the blood pressure value is 0, and ɑ is a specific parameter related to human blood vessels;
通过公式(1)、(6)和(7)可得：According to formulas (1), (6) and (7), we can get:
且平均血压MBP可表示为：And the mean blood pressure MBP can be expressed as:
则可得：Then we can get:
根据公式(5)、(10)可得收缩压、舒张压与时间延迟之间的关系式为：According to formulas (5) and (10), the relationship between systolic pressure, diastolic pressure and time delay is:
其中，Ha、Hb、Hc、Ja、Jb、Jc分别是与个体相关的系数；可通过对大量个体进行脉搏传递时间的检测，并将得到的值与标准血压计测得的血压结果比对，然后通过数据拟合获得相关系数。Among them,Ha ,Hb ,Hc ,Ja ,Jb , andJc are coefficients related to individuals respectively; the pulse transit time of a large number of individuals is tested, the obtained value is compared with the blood pressure result measured by a standard sphygmomanometer, and then the correlation coefficient is obtained by data fitting.
进一步地，确定所述系数Ha、Hb、Hc、Ja、Jb、Jc的具体过程为：收集多个无高血压心病史的成人血压数据，以商用腕带血压计作为参考标准；将权利要求1所述的监测装置与商用腕带血压计同步采集受试者血压和脉搏信息，监测装置采集的脉搏波形至少包括10个脉冲周期，求得脉搏传输时间的平均值作为最终的PTT值，采用非线性最小二乘法拟合PTT-BP曲线，拟合得到参考数值，得到的各系数的值分别为：Furthermore, the specific process of determining the coefficientsHa , Hb,Hc ,Ja,Jb , andJc is as follows: blood pressure data of multiple adults with no history of hypertension and heart disease are collected, and a commercial wristband sphygmomanometer is used as a reference standard; the monitoring device described in claim 1 and the commercial wristband sphygmomanometer are used to synchronously collect blood pressure and pulse information of the subject, the pulse waveform collected by the monitoring device includes at least 10 pulse cycles, and the average value of the pulse transmission time is obtained as the final PTT value, and the PTT-BP curve is fitted by nonlinear least squares method to obtain reference values, and the values of the obtained coefficients are:
Ha＝370.12、Hb＝17.73、Hc＝358.46、Ja＝192.30、Jb＝9.13、Jc＝196.99。Ha =370.12,Hb =17.73,Hc =358.46,Ja =192.30,Jb =9.13,Jc =196.99.
相较于现有技术，本发明的有益效果是：Compared with the prior art, the present invention has the following beneficial effects:
本发明基于自混合干涉和微纳光纤的人体多参量监测装置，使用嵌有微纳光纤的传感膜片捕捉脉搏振动信号，利用微纳光纤的弯曲变形导致波导结构变形对脉搏振动信号进行捕捉，具有较高的灵敏度；利用激光的自混合干涉技术，通过自混合干涉信号监测脉搏信息，进一步通过脉搏信息计算血压，可得到准确的脉搏信息和血压测量结果，为准确监测人体的脉搏和血压提供便利。The invention discloses a human multi-parameter monitoring device based on self-mixing interference and micro-nano optical fiber. The device uses a sensing diaphragm embedded with micro-nano optical fiber to capture pulse vibration signals, and utilizes the bending deformation of the micro-nano optical fiber to cause the deformation of the waveguide structure to capture the pulse vibration signals, thereby having high sensitivity. The device utilizes the self-mixing interference technology of laser to monitor pulse information through self-mixing interference signals, and further calculates blood pressure through the pulse information, thereby obtaining accurate pulse information and blood pressure measurement results, thereby providing convenience for accurately monitoring the human body's pulse and blood pressure.
本发明装置对血压的计算中综合考虑到了血液密度、动脉半径、动脉厚度、动脉血容量、动脉弹性各血管生理因素的影响，分别得到收缩压、舒张压与脉搏传输时间之间的非线性关系模型，可通过脉搏传输时间准确测量收缩压、舒张压。The device of the present invention comprehensively considers the influence of various vascular physiological factors such as blood density, arterial radius, arterial thickness, arterial blood volume, and arterial elasticity in the calculation of blood pressure, and obtains nonlinear relationship models between systolic pressure, diastolic pressure and pulse transmission time, respectively, and can accurately measure systolic pressure and diastolic pressure through pulse transmission time.
本发明装置准确性高、结构简单、舒适度好、成本低且测量方便，是一种应用前景较好的脉搏和血压监测装置。The device of the present invention has high accuracy, simple structure, good comfort, low cost and convenient measurement, and is a pulse and blood pressure monitoring device with good application prospects.
附图说明BRIEF DESCRIPTION OF THE DRAWINGS
图1为本发明实施例中基于自混合干涉和微纳光纤的人体血压监测装置的结构示意图；FIG1 is a schematic structural diagram of a human blood pressure monitoring device based on self-mixing interference and micro-nano optical fiber in an embodiment of the present invention;
图2为本发明实施例中传感膜片的结构示意图和通入650nm波长的光后传感膜片的照片；FIG2 is a schematic diagram of the structure of the sensing membrane in an embodiment of the present invention and a photograph of the sensing membrane after light of 650 nm wavelength is introduced;
图3为本发明实施例中不同弯曲状态的微纳光纤对应的电场强度分布图；FIG3 is a diagram showing the electric field intensity distribution of micro-nano optical fibers in different bending states according to an embodiment of the present invention;
图4为本发明实施例中对脉搏波进行傅里叶变换的得到频谱图，其中(a)为脉搏波形图，(b)为部分脉搏波形图，(c)为经傅里叶变换得到的脉搏频谱图；FIG4 is a spectrum diagram obtained by Fourier transforming a pulse wave in an embodiment of the present invention, wherein (a) is a pulse waveform diagram, (b) is a partial pulse waveform diagram, and (c) is a pulse spectrum diagram obtained by Fourier transforming;
图5为本发明实施例中SBP和DBP与PTT的关系曲线图，及SBP和DBP的Bland-Altman图，其中(a)为SBP与PTT的关系曲线图，(b)为DBP与PTT的关系曲线图，(c)为SBP的Bland-Altman图，(d)为DBP的Bland-Altman图；5 is a graph showing the relationship between SBP and DBP and PTT, and a Bland-Altman graph of SBP and DBP in an embodiment of the present invention, wherein (a) is a graph showing the relationship between SBP and PTT, (b) is a graph showing the relationship between DBP and PTT, (c) is a Bland-Altman graph of SBP, and (d) is a Bland-Altman graph of DBP;
图6为本发明实施例中受试者一天内的SBP和DBP的测量结果图；FIG6 is a graph showing the measurement results of SBP and DBP of a subject in one day according to an embodiment of the present invention;
图7为本发明实施例中手指脉搏的波形图和傅里叶转换后的频谱图。FIG. 7 is a waveform diagram of a finger pulse and a spectrum diagram after Fourier transformation in an embodiment of the present invention.
具体实施方式Detailed ways
在本发明的描述中，应当说明的是，在本发明的实施例中所提到的术语“第一”、“第二”、“第三”仅用于描述目的，并不能理解为指示或暗示相对重要性或者隐含指明所指示的技术特征的数量。由此，限定有“第一”、“第二”、“第三”的特征可以明示或者隐含地包括一个或者多个该特征。In the description of the present invention, it should be noted that the terms "first", "second", and "third" mentioned in the embodiments of the present invention are only used for descriptive purposes and cannot be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Therefore, the features defined as "first", "second", and "third" may explicitly or implicitly include one or more of the features.
为使本发明的上述目的、特征和优点能够更为明显易懂，下面结合附图对本发明的具体实施例做详细的说明。In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, specific embodiments of the present invention are described in detail below with reference to the accompanying drawings.
如图1所示，本发明提供基于自混合干涉和微纳光纤的人体多参量监测装置，包括传感膜片、激光器、光电探测器，数据采集卡、信号处理单元和血压计算单元；所述激光器的型号为S1FC1550PM，THORLABS，输出波长为1550nm的光，输出功率为2mW，所述数据采集卡型号为USB-4431，NI；As shown in FIG1 , the present invention provides a human multi-parameter monitoring device based on self-mixing interference and micro-nano optical fiber, including a sensing diaphragm, a laser, a photodetector, a data acquisition card, a signal processing unit and a blood pressure calculation unit; the model of the laser is S1FC1550PM, THORLABS, the output wavelength is 1550nm, the output power is 2mW, and the model of the data acquisition card is USB-4431, NI;
所述传感膜片包括微纳光纤和柔性膜片，所述微纳光纤嵌于所述柔性膜片中，所述传感膜片用于采集脉搏信息，脉搏振动引起柔性膜片发生形变导致微纳光纤的折射坡面发生改变；The sensing membrane comprises a micro-nano optical fiber and a flexible membrane, wherein the micro-nano optical fiber is embedded in the flexible membrane, and the sensing membrane is used to collect pulse information. Pulse vibration causes the flexible membrane to deform, resulting in a change in the refractive slope of the micro-nano optical fiber.
所述激光器通过光纤与微纳光纤的一端连接，所述微纳光纤的另一端设有反射端，在驱动电流作用下激光器可发射一定波长的输出光信号，所述输出光信号经脉搏振动处，经反射端反射后，携带脉搏信息的光信号返回至激光器谐振腔内与原光场生成自混合干涉信号；The laser is connected to one end of the micro-nano optical fiber through an optical fiber, and the other end of the micro-nano optical fiber is provided with a reflection end. Under the action of the driving current, the laser can emit an output optical signal of a certain wavelength. After the output optical signal passes through the pulse vibration point and is reflected by the reflection end, the optical signal carrying the pulse information returns to the laser resonant cavity to generate a self-mixing interference signal with the original optical field;
所述光电探测器设于所述激光器内部，用于将自混合干涉信号转化为连续的模拟信号并发送至数据采集卡；The photoelectric detector is arranged inside the laser and is used to convert the self-mixing interference signal into a continuous analog signal and send it to a data acquisition card;
所述数据采集卡与光电探测器连接，所述数据采集卡为USB动态信号采集卡，用于将接收的模拟信号转换为数字信号，并将数字信号传送至信号处理单元；The data acquisition card is connected to the photoelectric detector, and the data acquisition card is a USB dynamic signal acquisition card, which is used to convert the received analog signal into a digital signal and transmit the digital signal to the signal processing unit;
所述信号处理单元用于对接收的数字信号进行处理得到脉搏波信息，并将脉搏波信息传送至血压计算单元；The signal processing unit is used to process the received digital signal to obtain pulse wave information, and transmit the pulse wave information to the blood pressure calculation unit;
所述血压计算单元用于根据脉搏波信息计算人体血压数值。The blood pressure calculation unit is used to calculate the blood pressure value of the human body according to the pulse wave information.
如图2所示，所述传感膜片的制作过程为：采用熔融拉伸法通过拉锥机将标准单模光纤(包层直径为125um，纤芯直径为9um)拉伸成双锥形微纳光纤，得到两端锥形区长度均为15mm、腰区长度为12mm、腰区直径为1.8um的微纳光纤；柔性膜片的制备选用道康宁硅橡胶，将聚二甲基硅氧烷(PDMS)和固化剂按照质量比为10:1的比例混合，用真空泵抽真空的方式对其脱气，取适量脱气的聚二甲基硅氧烷混合液平铺在长7.5cm、宽2.2cm玻片上，将拉制好的微纳光纤嵌入到聚二甲基硅氧烷混合液中，于80℃下固化20分钟，形成薄膜，然后将其从玻片上取下，得到长度为7.5cm、宽度为2.2cm、厚度为0.3mm的传感膜片。As shown in FIG2 , the manufacturing process of the sensing membrane is as follows: a standard single-mode optical fiber (cladding diameter of 125 um, core diameter of 9 um) is stretched into a double-tapered micro-nano optical fiber by a taper machine using a melt stretching method to obtain a micro-nano optical fiber with a tapered region length of 15 mm at both ends, a waist region length of 12 mm, and a waist region diameter of 1.8 um; Dow Corning silicone rubber is used to prepare the flexible membrane, polydimethylsiloxane (PDMS) and a curing agent are mixed in a mass ratio of 10:1, and the mixture is degassed by vacuum pumping, and an appropriate amount of the degassed polydimethylsiloxane mixture is spread on a glass slide with a length of 7.5 cm and a width of 2.2 cm, and the drawn micro-nano optical fiber is embedded in the polydimethylsiloxane mixture, and cured at 80° C. for 20 minutes to form a thin film, which is then removed from the glass slide to obtain a sensing membrane with a length of 7.5 cm, a width of 2.2 cm, and a thickness of 0.3 mm.
如图3所示，腰区直径为1.8um的微纳光纤在1550nm波长下弯曲处的电场强度分布，弯曲半径分别为60μm、30μm和10μm。可以明显地看出，当光纤的弯曲半径越来越小时，约束良好的导模泄漏越明显，逐渐转变为非对称辐射模，激光的能量损失越大。As shown in Figure 3, the electric field intensity distribution at the bend of a micro-nano optical fiber with a waist diameter of 1.8um at a wavelength of 1550nm, with bending radii of 60μm, 30μm and 10μm respectively. It can be clearly seen that as the bending radius of the optical fiber becomes smaller and smaller, the leakage of the well-constrained guided mode becomes more obvious, gradually transforming into an asymmetric radiation mode, and the energy loss of the laser becomes greater.
传感膜片的PDMS柔性膜片的折射率(RI＝1.40)低于微纳光纤的折射率(RI＝1.46)，柔性膜片对微纳光纤进行封装保护，可以有效地包裹微纳光纤并隔离倏逝场，保证微纳光纤的高机械柔韧性和低光学损耗。The refractive index of the PDMS flexible membrane of the sensing membrane (RI=1.40) is lower than the refractive index of the micro-nano optical fiber (RI=1.46). The flexible membrane encapsulates and protects the micro-nano optical fiber, which can effectively wrap the micro-nano optical fiber and isolate the evanescent field, ensuring the high mechanical flexibility and low optical loss of the micro-nano optical fiber.
通过本方法制备的传感膜片相较于夹层结构膜片，可避免因膜片中产生气泡影响探测结果。且传感膜片具有生物相容性好、耐腐蚀、可紧密地贴合在皮肤表面消除空气间隙、灵敏性高的优点。Compared with the sandwich structure membrane, the sensor membrane prepared by this method can avoid the influence of bubbles in the membrane on the detection result. In addition, the sensor membrane has the advantages of good biocompatibility, corrosion resistance, close fit on the skin surface to eliminate air gaps, and high sensitivity.
如图4所示，信号处理单元对接收的数字信号进行处理得到脉搏波信息，具体实现过程为：通过LabVIEW软件，将数字信号进行处理得到脉搏波形图，同时通过傅里叶变换将脉搏波形图转换为脉搏频谱图，得到脉搏波形信息和频率信息。As shown in FIG4 , the signal processing unit processes the received digital signal to obtain pulse wave information. The specific implementation process is as follows: the digital signal is processed by LabVIEW software to obtain a pulse waveform diagram, and the pulse waveform diagram is converted into a pulse spectrum diagram by Fourier transform to obtain pulse waveform information and frequency information.
所述血压计算单元根据脉搏波信息计算人体血压数值，具体实现过程为：The blood pressure calculation unit calculates the blood pressure value of the human body according to the pulse wave information, and the specific implementation process is:
根据脉搏频谱图确定主波峰值到重振波峰值之间的时间跨度，表示为脉搏传输时间PTT；脉搏传输时间PTT与脉搏波速度PWV的关系为：The time span between the peak value of the main wave and the peak value of the re-energization wave is determined according to the pulse spectrum diagram, which is expressed as the pulse transmission time PTT. The relationship between the pulse transmission time PTT and the pulse wave velocity PWV is:
其中，L表示脉搏波经过的血管长度；Among them, L represents the length of the blood vessel through which the pulse wave passes;
根据Brawell-hill方程，脉搏波速PWV可由血液密度ρ和动脉血容量v表示，具体为：According to the Brawell-hill equation, pulse wave velocity PWV can be expressed by blood density ρ and arterial blood volume v, specifically:
其中，V为动脉内血液体积，dV为动脉内血容量的变化量，dP为收缩压SBP和舒张压DBP之间的血压差，单位是mmHg，dP可以表示为：Where V is the blood volume in the artery, dV is the change in blood volume in the artery, and dP is the blood pressure difference between systolic pressure SBP and diastolic pressure DBP, in mmHg. dP can be expressed as:
dP＝SBP-DBP (3)dP＝SBP-DBP (3)
因此脉搏波速PWV可以表示为：Therefore, the pulse wave velocity PWV can be expressed as:
根据公式(1)和公式(4)可得到：According to formula (1) and formula (4), we can get:
另一方面，脉搏波速PWV可以用Moens-korteweg方程表示：On the other hand, pulse wave velocity PWV can be expressed by the Moens-Korteweg equation:
其中Ein为动脉弹性模量，h为动脉厚度，r为动脉半径，ρ为血液密度；Where Ein is the elastic modulus of the artery, h is the thickness of the artery, r is the radius of the artery, and ρ is the blood density;
随着平均血压MBP的增加，动脉的弹性模量呈指数增长，则动脉弹性模量可表示为：As the mean blood pressure MBP increases, the elastic modulus of the artery increases exponentially, and the elastic modulus of the artery can be expressed as:
Ein＝E0eα*MBP (7)Ein =E0 eα*MBP (7)
其中，E0为血压值为0时血管壁的杨氏模量，ɑ是人体血管相关的特定参数；Among them, E0 is the Young's modulus of the blood vessel wall when the blood pressure value is 0, and ɑ is a specific parameter related to human blood vessels;
通过公式(1)、(6)和(7)可得：According to formulas (1), (6) and (7), we can get:
且平均血压MBP可表示为：And the mean blood pressure MBP can be expressed as:
则可得：Then we can get:
根据公式(5)、(10)可得收缩压、舒张压与时间延迟之间的关系式为：According to formulas (5) and (10), the relationship between systolic pressure, diastolic pressure and time delay is:
其中，Ha、Hb、Hc、Ja、Jb、Jc分别是与个体相关的系数；可通过对大量个体进行脉搏传递时间的检测，并将得到的值与标准血压计测得的血压结果比对，然后通过数据拟合获得相关系数。Among them,Ha ,Hb ,Hc ,Ja ,Jb , andJc are coefficients related to individuals respectively; the pulse transit time of a large number of individuals is tested, the obtained value is compared with the blood pressure result measured by a standard sphygmomanometer, and then the correlation coefficient is obtained by data fitting.
确定所述系数Ha、Hb、Hc、Ja、Jb、Jc的具体过程为：收集多个无高血压心病史的成人血压数据，以商用腕带血压计作为参考标准；将权利要求1所述的监测装置与商用腕带血压计同步采集受试者血压和脉搏信息，监测装置采集的脉搏波形至少包括10个脉冲周期，求得脉搏传输时间的平均值作为最终的PTT值，采用非线性最小二乘法拟合PTT-BP曲线，拟合得到参考数值，得到的各系数的值分别为：The specific process of determining the coefficientsHa ,Hb ,Hc ,Ja ,Jb , andJc is as follows: blood pressure data of multiple adults with no history of hypertension and heart disease are collected, and a commercial wristband sphygmomanometer is used as a reference standard; the monitoring device described in claim 1 and the commercial wristband sphygmomanometer are used to synchronously collect blood pressure and pulse information of the subject, the pulse waveform collected by the monitoring device includes at least 10 pulse cycles, and the average value of the pulse transmission time is obtained as the final PTT value, and the PTT-BP curve is fitted by nonlinear least squares method to obtain reference values, and the values of the obtained coefficients are:
Ha＝370.12、Hb＝17.73、Hc＝358.46、Ja＝192.30、Jb＝9.13、Jc＝196.99。Ha =370.12,Hb =17.73,Hc =358.46,Ja =192.30,Jb =9.13,Jc =196.99.
构建收缩压和舒张压的计算模型分别为：The calculation models for systolic and diastolic blood pressure are:
本发明血压测量装置的性能评价：Performance evaluation of the blood pressure measuring device of the present invention:
如表1所示，选取18位受试者进行了血压测量，对于每位受试者，使用本实施方式装置检测血压，同时使用欧姆龙血压计验证准确性，表1中包括脉搏波时间延迟PTT(s)、收缩压SBP(mmHg)、舒张压DBP(mmHg)、脉搏波频率HR(bpm)以及欧姆龙血压计的参考值和偏差值。As shown in Table 1, 18 subjects were selected for blood pressure measurement. For each subject, the blood pressure was detected using the device of this embodiment, and the accuracy was verified using an Omron sphygmomanometer. Table 1 includes pulse wave time delay PTT (s), systolic blood pressure SBP (mmHg), diastolic blood pressure DBP (mmHg), pulse wave frequency HR (bpm) and the reference value and deviation value of the Omron sphygmomanometer.
根据平均绝对误差(Mean Absolute Deviation，MEAN)、标准差(StandardDeviation,SD)作为装置的性能预测指标。The mean absolute error (MEAN) and standard deviation (SD) are used as performance prediction indicators of the device.
表1Table 1
经过计算得平均绝对误差和平均标准差分别为：MeanSBP＝-0.222、MeanDBP＝-1.056、SDSBP＝2.636、SDDBP＝2.198，结果均在可接受的范围内，可满足人们对血压测量装置的精度要求，同时证明本发明装置的可靠性。The calculated mean absolute error and mean standard deviation are: MeanSBP = -0.222, MeanDBP = -1.056, SDSBP = 2.636, SDDBP = 2.198, respectively. The results are all within an acceptable range, which can meet the accuracy requirements of people on blood pressure measurement devices and prove the reliability of the device of the present invention.
为了更好的验证系统检测结果，如图5(a)和图5(b)所示，分别展示了SBP和DBP与PTT的关系曲线图，可以看到18位受试者的测量值与关系曲线具有高度的相关性；如图5(c)和图5(d)所示，采用Bland-Altman一致性分析法对所有测试者的血压进行分析，其中，SBP的95％置信区间为-5.457～4.822mmHg，DBP的95％置信区间为-5.651～3.105mmHg；可以看出，SBP和DBP的测量结果均在95％置信检验范围内，这也说明两者具有较强的一致性，进一步验证了本发明装置的可靠性。In order to better verify the detection results of the system, as shown in Figures 5(a) and 5(b), the relationship curves of SBP and DBP with PTT are respectively shown. It can be seen that the measurement values of the 18 subjects are highly correlated with the relationship curves; as shown in Figures 5(c) and 5(d), the blood pressure of all test subjects was analyzed using the Bland-Altman consistency analysis method, where the 95% confidence interval of SBP is -5.457 to 4.822 mmHg, and the 95% confidence interval of DBP is -5.651 to 3.105 mmHg; it can be seen that the measurement results of SBP and DBP are both within the 95% confidence test range, which also shows that the two have strong consistency, further verifying the reliability of the device of the present invention.
如图6所示，为验证本发明装置在一天内多次监测血压波动的准确性，在一天时间内每两小时对受试者分别用本发明装置测量2分钟，并用欧姆龙血压计测量受试者血压作为参考值，共测量8次；可以清楚地看到受试者的血压变化趋势与参考值趋势相近，证明本发明装置能够在一段时间多次准确监测血压，为本发明进一步研究成为可穿戴的便携式实时血压监测装置的研发奠定基础。As shown in FIG6 , in order to verify the accuracy of the device of the present invention in monitoring blood pressure fluctuations multiple times within a day, the subject's blood pressure is measured for 2 minutes every two hours within a day using the device of the present invention, and the subject's blood pressure is measured using an Omron sphygmomanometer as a reference value, for a total of 8 measurements. It can be clearly seen that the trend of the subject's blood pressure changes is similar to the trend of the reference value, proving that the device of the present invention can accurately monitor blood pressure multiple times over a period of time, laying a foundation for further research of the present invention into a wearable, portable, real-time blood pressure monitoring device.
为进一步验证本发明装置测量血压的性能，对受试者连续十天测量血压。测量时间均选择晚上8点到9点，并用欧姆龙血压计测量受试者血压作为参考值。如表2所示，为一受试者十天的测量结果及与参考血压的测量误差。从表2中可以看出测量误差不大，均在可接受的范围内。To further verify the performance of the device of the present invention in measuring blood pressure, the blood pressure of the subjects was measured for ten consecutive days. The measurement time was selected from 8 to 9 pm, and the blood pressure of the subjects was measured with an Omron sphygmomanometer as a reference value. As shown in Table 2, the measurement results of a subject for ten days and the measurement error with the reference blood pressure are shown. It can be seen from Table 2 that the measurement error is not large and is within an acceptable range.
表2Table 2
如图7所示，将该传感器置于食指指尖时，也可以检测到指尖脉冲，可以看出得到的波形结果中的重振波不够明显，因此需要使用直径更小的微纳光纤、更薄的PDMS膜片提高传感器的灵敏度，以实现手指脉冲的高质量信号采集。As shown in Figure 7, when the sensor is placed on the tip of the index finger, the fingertip pulse can also be detected. It can be seen that the re-oscillation wave in the obtained waveform result is not obvious enough. Therefore, it is necessary to use a micro-nano optical fiber with a smaller diameter and a thinner PDMS membrane to improve the sensitivity of the sensor in order to achieve high-quality signal acquisition of finger pulses.
虽然本发明公开披露如上，但本发明公开的保护范围并非仅限于此。本发明领域技术人员在不脱离本发明公开的精神和范围的前提下，可进行各种变更与修改，这些变更与修改均将落入本发明的保护范围。Although the present invention is disclosed as above, the protection scope of the present invention is not limited thereto. Those skilled in the art may make various changes and modifications without departing from the spirit and scope of the present invention, and these changes and modifications will fall within the protection scope of the present invention.
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| CN202210873107.1ACN115153469B (en) | 2022-07-22 | 2022-07-22 | Human multi-parameter monitoring device based on self-mixing interference and micro-nano optical fiber |
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| CN202210873107.1ACN115153469B (en) | 2022-07-22 | 2022-07-22 | Human multi-parameter monitoring device based on self-mixing interference and micro-nano optical fiber |
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