CN109394187B - Wearable cardiovascular health monitoring system based on single side signal detection - Google Patents

Abstract

Translated fromChinese

本发明公开一种基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于包括：单侧数据检测设备，用于采集待监测者的基础心血管信息；数据处理器，用于计算检测数据，得到监测比较参数；数据存储器，用于存储数据内容；数据显示装置，用于显示监测内容。有益效果：单体侧的数据可以准确反映心血管到各部分器官的血管情况，同类数据的比值可以大大降低个体差异对数据分析的影响，使数据分析的有效性加强，本发明可以准确达到监测的效果，精确反应心血管到人体各部分的血流情况是否正常。对心血管健康进行监测及评估、指导心血管疾病的用药和治疗效果的评估等产生良好的社会效益，提高人民的生活质量，降低就医成本。

The invention discloses a wearable cardiovascular health monitoring system based on single side signal detection, which is characterized by comprising: a single side data detection device for collecting basic cardiovascular information of a person to be monitored; a data processor for The detection data is calculated to obtain monitoring and comparison parameters; the data memory is used to store the data content; the data display device is used to display the monitoring content. Beneficial effects: the data on the single side can accurately reflect the blood vessels from the cardiovascular to each part of the organ, the ratio of the same data can greatly reduce the impact of individual differences on data analysis, and enhance the effectiveness of data analysis, the present invention can accurately achieve monitoring. It accurately reflects whether the blood flow from the cardiovascular to various parts of the human body is normal. Monitoring and evaluating cardiovascular health, guiding the use of drugs for cardiovascular diseases and evaluating the effects of treatment have produced good social benefits, improved people's quality of life, and reduced medical costs.

Description

Wearable cardiovascular health monitoring system based on monomer side signal detection

Technical Field

The invention relates to the technical field of cardiovascular health monitoring, in particular to a wearable cardiovascular health monitoring system based on monomer side signal detection.

Background

Cardiovascular diseases are the first important diseases with the mortality rate in developed countries at present, are the diseases with the highest mortality rate in China, and are listed as the first killers harmful to human health in the 21 st century by the world health organization. Therefore, how to actively carry out early risk screening, early warning and health management of cardiovascular diseases is a very prominent problem.

The prior art has the following disadvantages: the blood vessel conditions of all parts of a human body are independently detected, the analysis result is directly obtained from the detected basic blood vessel data, and the analysis result is inaccurate due to the individual difference of the basic blood vessel data.

Disclosure of Invention

Aiming at the defect that an analysis result is directly obtained from basic blood vessel data, the invention provides a wearable cardiovascular health monitoring system based on monomer side signal detection, which is used for detecting data of fingers, earlobes, wrists and ankles on a monomer side, calculating analysis parameters by combining the data of each part, and finally obtaining accurate cardiovascular health parameters; on the other hand, the kit is beneficial to monitoring cardiovascular diseases, guiding medication and evaluating the curative effect.

In order to achieve the purpose, the invention adopts the following specific technical scheme:

a wearable cardiovascular health monitoring system based on monomer-side signal detection, comprising:

the unilateral data detection equipment is used for collecting basic cardiovascular information of a person to be monitored, and the basic cardiovascular information comprises: the device comprises a single channel electrocardiosignal, a finger blood oxygen dual-wavelength signal and an earlobe blood oxygen dual-wavelength signal in the non-inflation process of an air band, and a single channel electrocardiosignal, a finger blood oxygen dual-wavelength signal, an earlobe blood oxygen dual-wavelength signal, wrist air band pressure, wrist pressure pulse signal, ankle joint air band pressure and ankle joint pressure pulse signal in the deflation process and the constant pressure process of the air band, wherein the finger blood oxygen dual-wavelength signal comprises two signals obtained by detecting light with two wavelengths, the earlobe blood oxygen dual-wavelength signal also comprises two signals obtained by detecting light with two wavelengths, and one signal can be selected to extract a corresponding photoelectric pulse signal;

the basic cardiovascular information is data corresponding to fingers, earlobes, wrists and ankles on the same side of the person to be monitored;

the data processor is used for calculating the detection data to obtain a monitoring comparison parameter;

a data storage for storing data content;

the data display device is used for displaying monitoring content, and the displayed monitoring content comprises basic cardiovascular information or/and monitoring comparison parameters;

the output end group of the single-side data detection equipment is connected with the data receiving end group of the data processor, the parameter output end group of the data processor is connected with the display receiving end group of the data display device, and the data memory is connected with the data processor.

Because the blood vessel conditions of the same side of the human body are closer, the data of the single side can be adopted to obtain approximate parameter values, and once the difference of the originally approximate parameter values is overlarge, the blood vessel condition of a part of organs is not good, so the blood vessel condition of the heart blood vessel to each part of organs can be accurately reflected; meanwhile, parameter values of the homologus data (such as blood oxygen dual-wavelength signals) in the health state on different organs (fingers and earlobes) reflect the cardiovascular blood transfusion capacity, the capacity is that for the whole human body, even if differences exist among different individuals, the cardiovascular capacity of the normal operation of the human body is close to each other, the ratio of the homologus data is within a small health interval, and the ratio exceeding the health interval does not belong to the reason of individual difference but is the reason of the blood transfusion capacity of the individual, so that the influence of the individual difference on data analysis can be greatly reduced by the ratio of the homologus data, and the effectiveness of the data analysis is enhanced. Through the design, the monitoring effect can be accurately achieved: can well reflect whether the blood flow condition from the cardiovascular system to each part of the human body is normal or not to a certain extent.

Further designed, the system also comprises user input equipment which is used for acquiring personal information of a person to be monitored;

the wireless data transmission module is used for sending the detection comparison parameters to the network terminal;

the user input equipment and the wireless data transmission module are respectively connected with the data processor.

Through the design, the person to be monitored can input own basic personal information through the user input equipment, so that independent databases of each person are generated, the content of the database can be uploaded to the network through the wireless data transmission module, and finally a large database is formed, so that the data reference interval of a healthy person is obtained more accurately, and the result of cardiovascular unhealthy can be obtained accurately by the numerical value in the non-interval.

In a further design, the single-side data detection device comprises an earlobe photoelectric blood oxygen dual-wavelength sensor, a finger blood oxygen dual-wavelength sensor, a wrist air belt pressure sensor, an ankle air belt pressure sensor and an electrocardio electrode, and basic cardiovascular information required by the invention can be acquired through the existing detection device.

In a further design, the data processor comprises a cardiovascular characteristic parameter extraction module and a monitoring evaluation data calculation module, the cardiovascular characteristic parameter extraction module is connected with the unilateral data detection device, the monitoring evaluation data calculation module is connected with the data display device, and the cardiovascular characteristic parameter extraction module is connected with the monitoring evaluation data calculation module;

the cardiovascular characteristic parameter extraction module extracts cardiovascular characteristic parameters of the basic cardiovascular information, wherein the cardiovascular characteristic parameters at least comprise: the specific value ROS of the electrocardio R wave and the blood oxygen saturation dual-wavelength signal, the waveform of the pressure pulse signal and the change rate of the pressure pulse signal;

the ratio ROS of the two wavelength signals of the blood oxygen saturation is the average ratio of two direct current signals with different wavelengths for measuring the blood oxygen saturation in the same cardiac cycle;

the monitoring evaluation data calculation module calculates to obtain monitoring evaluation data according to the cardiovascular characteristic parameters, wherein the monitoring evaluation data reflects the cardiovascular health state of a person to be monitored;

the monitoring evaluation data at least comprises the following data in the whole air belt deflation process: average rate R at which the ratio ROS decreases with cardiac cycleOS_decThe average speed ROS of the ratio ROS increasing along with the cardiac cycle_incDifferential pressure ratio RP of 80% on both sides of pulse wave peak value_m0.8Pressure ratio RAP of 50% on both sides of pulse wave peak_m0.5Pressure ratio RAP of 50% on both sides of maximum rate of change_MR0.5Differential pressure ratio RP of 50% on both sides of maximum rate of change_MR0.5。

In the process of wrist deflation, blood hardly flows into and out of the fingers because the pressure of the air belt of the wrist is greater than the contraction pressure, and the oxygen in the blood is gradually consumed by finger tissues, so that the ROS value is gradually reduced; along with the further reduction of the pressure of the gas band, when the pressure of the gas band is smaller than the systolic pressure, the blood of the fingers flows, the flow quantity is increased along with the reduction of the pressure of the gas band, and further the oxygen in the blood of the fingers is obviously increased, so the ROS value is increased; finally, the cuff pressure is lower than the diastolic pressure, the blood vessel is substantially not deformed, so that the ROS value reaches a substantially stable value, and therefore, during the deflation of the cuff, there is a maximum ROS value of said ratio ROS_maxMinimum ROS_min。

Through the design, the electrocardio R wave is extracted from the single channel electrocardio signal; extracting a ratio ROS of a blood oxygen saturation dual-wavelength signal at a finger position from the finger blood oxygen dual-wavelength signal, extracting a ratio ROS of a blood oxygen saturation dual-wavelength signal at an earlobe position from the earlobe blood oxygen dual-wavelength signal, and respectively displaying a hemoglobin ratio of the finger/the earlobe by the two ratios ROS to reflect an oxygen supply condition; the ear lobe photoelectric pulse signal can extract the waveform and the change rate of the photoelectric pulse signal at the ear lobe, the wrist pressure pulse signal extracts the waveform and the change rate of the pressure pulse signal at the wrist, the ankle pressure pulse signal extracts the waveform and the change rate of the pressure pulse signal at the ankle, and therefore the RP of the fingers is calculated respectively_m0.8、RAP_m0.5、RAP_MR0.5、RP_MR0.5RP at the ankle_m0.8、RAP_m0.5、RAP_MR0.5、RP_MR0.5The series of parameters respectively reflect the elasticity of blood vessels from the heart to the wrist and the elasticity of blood vessels from the heart to the ankle.

In the further design, the device is provided with a plurality of grooves,average rate ROS of said ratio ROS decreasing with cardiac cycle_decThe average speed ROS of the ratio ROS increasing along with the cardiac cycle_incThe calculation method of (2) is as follows:

a1, extracting the maximum value ROS of the ratio ROS in all cardiac cycles_maxMinimum ROS_minRatio of the first cardiac cycle ROS_staThe ratio of the last cardiac cycle ROS_endOf minimum value of ROS_minThe sequence of the cardiac cycles is n;

a2, calculating the average rate ROS of the decrease of the ratio ROS along the cardiac cycle_dec：

A3, calculating the average speed ROS of the ratio ROS increasing along the cardiac cycle_inc：

Wherein, ROS_cmaxTo satisfy:

maximum value of (3), ROS_mAnd ROS_m-1Are respectively the ratio ROS of two adjacent cardiac cycles, and the sequence of the cardiac cycles is m and m-1 respectively.

Because the numerical value of direct detection has individual difference to influence for the health judges the interval very big, and the parameter ratio reaction blood behavior of same individual, if one of them parameter is unusual, the ratio of 2 parameters can appear several times even bigger very obvious change, and healthy different individual than the ratio just can not the difference very big, consequently the judged result can judge more accurately than direct numerical value, can also reduce the interference of individual difference, and the ratio change: average rate ROS at which ratio ROS decreases with cardiac cycle_decThe average speed ROS of the ratio ROS increasing along with the cardiac cycle_incThe method can reflect the slight difference of data to judge the blood working condition more comprehensively.

Further, the pressure difference ratio RP of 80% of two sides of the pulse wave peak value_m0.8Pressure ratio RAP of 50% on both sides of pulse wave peak_m0.5The calculation method of (2) is as follows:

b1, extracting the maximum amplitude A of the pressure pulse signal waveform_maxAnd the maximum amplitude A_maxCorresponding to the pressure of air belt PA_max；

B2, calculating the maximum amplitude A in the waveform of thepressure pulse signal_max80% amplitude A of front and rear sides_d0.8、A_s0.8And obtaining A_d0.8Corresponding to the pressure P of the air belt_d0.8、A_s0.8Corresponding to the pressure P of the air belt_s0.8Calculating the maximum amplitude A in the waveform of thepressure pulse signal_max50% amplitude A of front and rear sides_d0.5、A_s0.5And obtaining A_d0.5Corresponding to the pressure P of the air belt_d0.5、A_s0.5Corresponding to the pressure P of the air belt_s0.5；

B3, calculating the pressure difference ratio RP of 80% on both sides of the pulse wave peak value_m0.8Pressure ratio RAP of 50% on both sides of pulse wave peak_m0.5：

Similarly, the ratio has obvious effect of eliminating the influence of individual difference and is more accurate in reflecting the systolic strength and the diastolic strength.

Further contemplated, the pressure ratio RAP of 50% on either side of the maximum rate of change_MR0.5Differential pressure ratio RP of 50% on both sides of maximum rate of change_MR0.5The calculation method of (2) is as follows:

c1, extracting the most varied rate of the pressure pulse signalLarge rate of change MR_maxAnd the maximum rate of change MR_maxCorresponding to the pressure PMR of the air belt_max；

C2, calculating the maximum change rate MR in the change rate of thepressure pulse signal_max50% value MR of front and rear sides_d0.5、MR_s0.5And obtaining MR_d0.5Corresponding to the pressure P of the air belt_MRd0.5、MR_s0.5Corresponding to the pressure P of the air belt_MRs0.5；

C3, calculating the pressure ratio RAP of 50% on both sides of the maximum change rate_MR0.5Differential pressure ratio RP of 50% on both sides of maximum rate of change_MR0.5：

Pressure ratio RAP_MR0.5Pressure difference ratio RP_MR0.5Can accurately reflect the elasticity of the blood vessel.

In a further design, the monitoring and evaluation data further includes a pulse change time ratio Δ T/T_aThe ratio of the pulse change time DeltaT/T_aOr through the data calculation of the process without air pressure or through the data calculation of the process of air belt deflation or through the data calculation of the process of air belt constant pressure, the calculation method is as follows:

d1, extracting the maximum change rate PMR of each cardiac cycle in the pulse signal_maxAnd the maximum rate of change PMR_maxAt a time t_PMRThe pulse signal is pressure pulse or photoelectric pulse;

extracting the time point t of the electrocardio R wave of each cardiac cycle simultaneously_iI is the order of the cardiac cycles;

d2, calculating each time point t_iAnd time t_PMRDifference Δ t of_iAnd extracting said difference Δ t_iMaximum value t of_maxAnd a minimum value t_min，

D3, calculating the maximum value t_maxAnd a minimum value t_minThe difference of (a):

ΔT＝t_max-t_min

all differences Δ t_iAverage value of (d):

wherein k is the total number of cardiac cycles;

d4, calculating the pulse change time ratio delta T/T_aThe ratio of the pulse change time DeltaT/T_aReflecting the elasticity of the blood vessels and the blood flow of the person to be monitored.

The pressure pulse signal in the above steps can be replaced by a photoelectric pulse signal.

In a further design, the monitoring and evaluation data further includes a pulse propagation velocity, the pulse propagation velocity is calculated by data of a process without air pressure or by data of a process with constant pressure in the air belt, and the calculation method of the pulse propagation velocity is as follows:

e1, obtaining the distance d from the heart to the ankle artery₁Heart to radial artery distance d₂Heart to earlobe distance d₃Then obtain the distance difference | d₁-d₂|、|d₂-d₃|；

E2, extracting the maximum change rate PMR of each cardiac cycle in the pulse signal_maxAnd the maximum rate of change PMR_maxAt a time t_PMRThe pulse signal is pressure pulse or photoelectric pulse;

extracting the time point t of the electrocardio R wave of each cardiac cycle_iI is the order of the cardiac cycles;

e3, calculating each time point t_iAnd time t_PMRDifference Δ t of_iCalculating all differences Δ t_iAverage value of (d):

wherein k is the total number of cardiac cycles;

e4, calculating the pulse propagation velocity:

wherein DL and Td are either: DL is distance difference | d₁-d₂And Td is ankle wrist time difference: mean value of ankle joint T_aMean value of the wrist T_a；

DL and Td are either: DL is distance difference | d₂-d₃And Td is ear-wrist time difference: mean value of earlobe T_aMean value of the wrist T_a。

The pulse propagation velocity is responsive to the degree of vascular sclerosis, and if DL and Td adopt the first parameter values, the vascular sclerosis condition from hand to foot can be obtained, and if the second parameter values, the vascular sclerosis condition from head to hand can be obtained.

In a further aspect, the monitoring assessment data further includes:

the ratio of parameters in different acquisition processes: the ratio of the ROS mean value of the fingers in the non-inflation process to the maximum ROS value of the fingers in the deflation process, and the ratio of the ROS mean value of the fingers in the non-inflation process to the ROS mean value of the fingers in the constant pressure process, wherein the ROS mean value of the fingers is the mean value of all ROS values in the corresponding process, and the ROS maximum value of the fingers is the maximum value of the ROS values in the corresponding process; the relative ratio of similar earlobes can also be calculated;

the ratio of the mean value of the pulse propagation speeds in the non-inflation process to the maximum value of the pulse propagation speeds in the deflation process, and the ratio of the mean value of the pulse propagation speeds in the non-inflation process to the mean value of the pulse propagation speeds in the constant pressure process, wherein the mean value of the pulse propagation speeds is the mean value of all the pulse propagation speeds in the corresponding process, and the maximum value of the pulse propagation speed is the maximum value of the pulse propagation speeds in the corresponding process;

ratio of similar parameters of finger and ear lobe: the ratio of the ratio ROS of the fingers to the ratio ROS of the earlobe;

ratio of the same parameters of wrist and ankle: a of the wrist_maxA with ankle_maxRatio of (A) to (B), PA of the wrist_maxPA for ankle_maxRatio of (A) to (B), RP of the wrist_m0.8RP with ankle_m0.8Ratio of (A) to (B), RAP of wrist_m0.5RAP with ankle_m0.5Ratio of (1), MR of the wrist_maxMR of ankle_maxRatio of (A) to (B), RAP of wrist_MR0.5RAP with ankle_MR0.5Ratio of (A) to (B), RP of the wrist_MR0.5RP with ankle_MR0.5The ratio of (a) to (b).

It can also include the finger and ear lobe under no-pressure condition (i.e. non-inflation process): the ratio of the direct current average value of the photoelectric pulse with the same wavelength in each cardiac cycle at the ear lobe position and the index finger position, the ratio of the ascending maximum change rate, the ratio of the descending maximum change rate, the ratio of the maximum peak value, the ratio of the change amplitude and the average value of the ratios are obtained;

during deflation of the wrist and ankle joints: systolic pressure ratio, diastolic pressure ratio, mean blood pressure ratio.

Through the ratio, the blood flowing condition of the part under the non-pressurizing and pressurizing conditions can be known through the ratio of the parameters in different acquisition processes, whether the blood vessel is blocked or not is analyzed, the difference of the blood vessels and the blood flows of the upper limb and the lower limb can be analyzed through the similar parameter ratio, the health conditions of the blood vessels and the blood flows of the upper limb and the lower limb are judged, the individual difference influence is eliminated, and the judgment result is more accurate.

The invention has the beneficial effects that: the data of the single body side can accurately reflect the blood vessel condition from the heart vessels to each part of organs, the ratio of the same type of data can greatly reduce the influence of individual difference on data analysis, so that the effectiveness of the data analysis is enhanced. Besides generating considerable economic benefits, the cardiovascular disease early-finding instrument can generate good social benefits for capturing precious time for treatment, monitoring and evaluating cardiovascular health, guiding the medication of the cardiovascular disease, evaluating treatment effect and the like, improves the life quality of people, and reduces the hospitalization cost. The invention can be used in clinic, family and other occasions, and has good application prospect and market value.

Drawings

FIG. 1 is a block diagram of the present invention;

FIG. 2 is a schematic illustration of a preferred embodiment;

FIG. 3 is a schematic view of a human monitoring location;

FIG. 4 is a circuit layout of a microprocessor in a preferred embodiment;

FIG. 5 is a flow chart of a method of operation of the present invention;

FIG. 6 is a ROS_dec、ROS_incA flow chart of the calculation method of (1);

FIG. 7 is a graph showing the variation of ROS in the example;

FIG. 8 is an RP_m0.8、RAP_m0.5A flow chart of the calculation method of (1);

FIG. 9 is a graph showing the variation of the pressure pulse signal during inflation and deflation according to an embodiment;

FIG. 10 is a graph illustrating the variation of the pressure pulse signal and the pressure of the air belt according to an embodiment;

FIG. 11 is a RAP_MR0.5、RP_MR0.5A flow chart of the calculation method of (1);

FIG. 12 is a graph of the rate of change of the pressure pulse signal versus the pressure in the air belt;

FIG. 13 is a diagram showing the pulse variation time ratio Δ T/T_aA flow chart of a calculation method;

FIG. 14 is a flow chart of a method of calculating pulse propagation velocity;

FIG. 15 is a schematic view of an ear lobe photoplethysmography sensor;

FIG. 16 is a schematic diagram of a finger photo-pulse sensor;

FIG. 17 is a schematic view of a wrist pneumatic cuff sphygmomanometer.

Detailed Description

The invention is described in further detail below with reference to the figures and the embodiments.

As shown in fig. 1, a wearable cardiovascular health monitoring system based on monomer-side signal detection includes:

the unilateral data detection equipment is used for collecting basic cardiovascular information of a person to be monitored, and the basic cardiovascular information comprises: single channel electrocardiosignal, finger blood oxygen dual wavelength signal and ear lobe blood oxygen dual wavelength signal in the non-inflation process of the air belt, single channel electrocardiosignal, finger blood oxygen dual wavelength signal, ear lobe blood oxygen dual wavelength signal, wrist air belt pressure, wrist pressure pulse signal, ankle joint air belt pressure and ankle joint pressure pulse signal in the deflation process and constant pressure process of the air belt;

the basic cardiovascular information is data corresponding to fingers, earlobes, wrists and ankles on the same side of the person to be monitored;

the data processor is used for calculating the detection data to obtain a monitoring comparison parameter;

a data storage for storing data content;

the data display device is used for displaying monitoring content, and the displayed monitoring content comprises basic cardiovascular information or/and monitoring comparison parameters;

the output end group of the single-side data detection equipment is connected with the data receiving end group of the data processor, the parameter output end group of the data processor is connected with the display receiving end group of the data display device, and the data memory is connected with the data processor.

The data processor comprises a cardiovascular characteristic parameter extraction module and a monitoring evaluation data calculation module;

the cardiovascular characteristic parameter extraction module extracts cardiovascular characteristic parameters of the basic cardiovascular information, wherein the cardiovascular characteristic parameters at least comprise: the specific value ROS of the electrocardio R wave and the blood oxygen saturation dual-wavelength signal, the waveform of the pressure pulse signal and the change rate of the pressure pulse signal;

the ratio ROS of the two wavelength signals of the blood oxygen saturation is the average ratio of two direct current signals with different wavelengths for measuring the blood oxygen saturation in the same cardiac cycle;

the monitoring evaluation data calculation module calculates to obtain monitoring evaluation data according to the cardiovascular characteristic parameters, wherein the monitoring evaluation data reflects the cardiovascular health state of a person to be monitored;

the monitoring evaluation data at least comprises the following data in the whole air belt deflation process: average rate ROS at which ratio ROS decreases with cardiac cycle_decThe average speed ROS of the ratio ROS increasing along with the cardiac cycle_incDifferential pressure ratio RP of 80% on both sides of pulse wave peak value_m0.8Pressure ratio RAP of 50% on both sides of pulse wave peak_m0.5Pressure ratio RAP of 50% on both sides of maximum rate of change_MR0.5Differential pressure ratio RP of 50% on both sides of maximum rate of change_MR0.5。

The system also comprises user input equipment which is used for acquiring personal information of a person to be monitored;

the wireless data transmission module is used for sending the detection comparison parameters to the network terminal;

the user input equipment and the wireless data transmission module are respectively connected with the data processor.

Preferably, the single-side data detection device comprises an earlobe photoelectric blood oxygen dual-wavelength sensor (as shown in fig. 15), a finger blood oxygen dual-wavelength sensor (as shown in fig. 16), a wrist air band pressure sensor (as shown in fig. 17), an ankle air band pressure sensor and an electrocardio-electrode.

During the monitoring use, place earlobe photoelectricity blood oxygen dual wavelength sensor and detect earlobe blood oxygen dual wavelength signal on the earlobe, earlobe photoelectricity pulse signal, place finger blood oxygen dual wavelength sensor and detect finger blood oxygen dual wavelength signal on the finger, detect the wrist air belt pressure of gassing and constant voltage in-process behind wrist air belt pressure sensor parcel wrist, wrist pressure pulse signal, detect the ankle joint air belt pressure of gassing and constant voltage in-process behind ankle joint of ankle air belt pressure sensor parcel, ankle joint pressure pulse signal, and wrist air belt and ankle air belt fill gassing simultaneously or keep the same constant voltage, the position that detects or all be the left earlobe of the human body, the finger, wrist and ankle, or all be the earlobe on the right side of the human body, the finger, wrist and ankle, as shown in figure 3.

The embodiment is described by using the structure shown in fig. 2, and includes a sensor and execution unit, a pre-amplification unit, a band-pass filter and 50Hz trap unit, a programmable amplification unit, a microprocessor unit, an inflation and deflation driving unit, an SD card memory unit, a calendar unit, a positioning unit, a WiFi communication unit, an LED light intensity control unit, a touch screen input and display unit, and a DC-DC power supply unit. The sensor and the execution unit mainly comprise a unilateral earlobe and index finger photoelectric pulse sensor, a unilateral wrist and ankle joint air belt internal pressure sensor, a miniature inflator pump, an air release valve, an electrocardio electrode, a patch type body temperature sensor and the like; the pre-amplification unit is mainly composed of high-precision integrated operational amplifiers such as AD620, LMC6082 and the like; the band-pass filter and 50Hz trap unit mainly comprises an active filter and a 50Hz trap which are formed by high-precision integrated operational amplifiers LMC6084 and LMC6082 to realize filtering; the programmable amplifying unit is mainly composed of a digital control amplifier PGA 112; the microprocessor unit is mainly composed of an STM32F407 VG; the inflation and deflation driving unit mainly comprises a triode and a field effect transistor; the SD card memory unit mainly comprises an SD card; the calendar unit mainly comprises a calendar chip; the positioning unit mainly comprises a Beidou positioning module; the WiFi communication unit mainly comprises a wireless WiFi communication module; the LED light intensity control unit mainly comprises a voltage-current conversion circuit and a digital-to-analog conversion chip, and realizes the control of the LED light intensity used in the measurement of the blood oxygen dual-wavelength signals at the earlobe and the finger; the touch screen input and display unit mainly comprises a color touch screen and realizes the input and display of various information; the DC-DC power supply unit is composed of various voltage stabilizing chips and supplies power to other units.

Wherein the microprocessor is preferably an STM32F407VG, as shown in FIG. 4, and the core is an ARM 32-bit Cortex with FPU^TMAn M4CPU, a flash memory with 1024Kbytes, a static memory with 192Kbytes, 14 timers, 3 SPI interfaces, 6 serial interfaces, 1 SD card interface, 3 12-bit A/D converters and 2 12-bit D/A converters, wherein the maximum frequency of the CPU can reach 168 MHz. Wherein, the analog input nodes AD _ ECG, AD _ Ear, AD _ Wrist, AD _ Finger, AD _ Ankle, Temp are respectively connected with the digital control output of electrocardio, the digital control output of earlobe dual-wavelength photoelectric signal, the digital control output of Wrist pressure and pressure pulse signal, the digital control output of Finger dual-wavelength photoelectric signal, the digital control output of Ankle joint pressure and pressure pulse signal, the temperature signalThe numerical control outputs are connected, and corresponding measurement is realized by utilizing the A/D conversion of the inner belt of the microprocessor; the digital-to-analog conversion output nodes DA1 and DA2 are connected with the programmable amplifying unit and control the direct current bias voltage of the blood oxygen saturation dual-wavelength; the nodes BloodEnable1, BloodEnable2, DAC122SCLK, DAC122SYNC and DAC122DIN are connected with the LED light intensity control unit to realize the control of the blood oxygen saturation dual-wavelength LED light intensity; the nodes SD _ DAT0-SD _ DAT3, SD _ CLK and SD _ CMD are respectively connected with the nodes corresponding to the SD card memory unit to realize the storage of various data; the nodes GPS _ RX, GPS _ TX and PPS are respectively connected with corresponding nodes of the positioning unit to realize the acquisition of position information; the nodes WiFi _ RXD and WiFi _ TXD are respectively connected with the WiFi communication unit, and communication with external equipment is realized through a wireless party; the nodes DS1302CLK, DS1302IO and DS1302RST are respectively connected with the calendar unit to realize the setting and reading of the date; the nodes LCD _ CLK, LCD _ MISO, LCD _ MOSI, TDout, TDin, TCLK, TBusy and TPenIRQ are respectively connected with the corresponding nodes of the touch screen input and display unit to realize the input and display of various information; the nodes ChangeAir1, ChangeAir2, PWM1 and PWM2 are respectively connected with corresponding nodes of the air charging and discharging unit to realize the control of air charging and discharging; the node PGA112_ SCK _ A, PGA112_ DIO _ A, PGA112_ CS _ A, PGA112_ SCK _ W, PGA112_ DIO _ W, PGA112_ CS _ W, PGA112_ SCK _ E, PGA112_ DIO _ E, PGA112_ CS _ E, PGA112_ SCK _ F, PGA112_ DIO _ F, PGA112_ CS _ F is respectively connected with corresponding nodes in the programmable amplification unit, so that the control of the amplification factor of each channel signal is realized; the interface Serial is connected with an external Serial port and used for the online downloading of the microprocessor software; the buzzer Buzz realizes the purpose that a prompt tone is sent out when a key is pressed and the like under the control of the microprocessor; the interface Boot is connected with the outside and used for controlling the microprocessor to enter an operating state or a programming state after being electrified; ADR363B provides high-precision 3.0V reference voltage for the A/D conversion and D/A conversion of the microprocessor; 74HC04 converts the 3.3V pulse modulation signal output by the microprocessor into 5.0V pulse width modulation signal; light emitting diodes D1 and D2 are used for indication of program running status; the power supply nodes AV3.3V, DV3.3V, AV +5.0V, DV +5.0V, DGND and AGND are respectively connected with the analog power supply 3.3V, digital power supply 3.3V, analog power supply 5.0V, digital ground and analog ground in the power supply unitConnected to provide operating power to the unit.

The working method of the invention is shown in fig. 5, and the embodiment only uses the data of the finger and the wrist to calculate:

s1, synchronously acquiring a single channel electrocardiosignal, a finger blood oxygen dual-wavelength signal and an earlobe blood oxygen dual-wavelength signal of a person to be monitored in the process of not aerating the gas band, extracting an earlobe photoelectric pulse signal from the earlobe blood oxygen dual-wavelength signal, and setting the acquisition time as 30S by default; synchronously acquiring wrist air band pressure, wrist pressure pulse signals, ankle joint air band pressure and ankle joint pressure pulse signals, single channel electrocardiosignals, finger blood oxygen dual-wavelength signals and earlobe blood oxygen dual-wavelength signals in the process of simultaneously inflating and deflating air bands at the wrist and the ankle joint of a person to be monitored and constant pressures (default four pressures of 60mmHg, 80mmHg, 100mmHg and 120mmHg), wherein the whole acquisition process is about 240 s;

the finger blood oxygen dual-wavelength signal, the earlobe photoelectric pulse signal, the wrist air belt pressure, the wrist pressure pulse signal, the ankle joint air belt pressure and the ankle joint pressure pulse signal are preferably data corresponding to a finger, an earlobe, a wrist and an ankle joint on the left side of a person to be monitored;

s2, extracting the heart rate, the heart rate variation rate and the electrocardio R wave in the electrocardiosignals by a difference threshold method;

extracting systolic pressure, diastolic pressure, average blood pressure and blood pressure index of radial artery through wrist air band pressure and wrist pressure pulse signals, and extracting systolic pressure, diastolic pressure, average blood pressure and blood pressure index of ankle artery through ankle joint air band pressure and ankle joint pressure pulse signals;

calculating the ratio ROS of the finger blood oxygen saturation dual-wavelength signals of each cardiac cycle, wherein the ratio ROS is the average value of 940nm wavelength direct current signals to the average value of 660nm wavelength direct current signals;

extracting the waveform of the wrist pressure pulse signal to obtain the maximum amplitude A_maxAnd the maximum amplitude A_maxCorresponding wrist air belt pressure PA_maxExtracting the change rate of the wrist pressure pulse signal,obtaining maximum rate of change MR_maxAnd the maximum rate of change MR_maxCorresponding wrist air belt pressure PMR_max；

S3, calculating to obtain monitoring and evaluating data according to the cardiovascular characteristic parameters, wherein the monitoring and evaluating data reflect the cardiovascular health state of the person to be monitored;

the monitoring evaluation data at least comprises the following data in the whole air belt deflation process: average rate ROS at which ratio ROS decreases with cardiac cycle_decThe average speed ROS of the ratio ROS increasing along with the cardiac cycle_incDifferential pressure ratio RP of 80% on both sides of pulse wave peak value_m0.8Pressure ratio RAP of 50% on both sides of pulse wave peak_m0.5Pressure ratio RAP of 50% on both sides of maximum rate of change_MR0.5Differential pressure ratio RP of 50% on both sides of maximum rate of change_MR0.5。

Wherein the average rate ROS of the ratio ROS decreasing with the cardiac cycle_decThe average speed ROS of the ratio ROS increasing along with the cardiac cycle_incThe calculation method (2) is shown in fig. 6:

a1, extracting the maximum value ROS of the ratio ROS in all cardiac cycles_maxMinimum ROS_minRatio of the first cardiac cycle ROS_staThe ratio of the last cardiac cycle ROS_endOf minimum value of ROS_minThe sequence of the cardiac cycles is n;

a2, calculating the average rate ROS of the decrease of the ratio ROS along the cardiac cycle_dec：

A3, calculating the average speed ROS of the ratio ROS increasing along the cardiac cycle_inc：

Wherein, ROS_cmaxTo satisfy:

maximum value of (3), ROS_mAnd ROS_m-1Are respectively the ratio ROS of two adjacent cardiac cycles, and the sequence of the cardiac cycles is m and m-1 respectively.

FIG. 7 is a graph of ROS change at the finger obtained from the deflation process during one acquisition.

And calculating the ratio of the average value of the ROS of the fingers in the non-inflation process to the maximum value of the ROS of the fingers in the deflation process, and the ratio of the average value of the ROS of the fingers in the non-inflation process to the average value of the ROS of the fingers in the constant pressure process, wherein the average value of the ROS of the fingers is the average value of all ROS values in the corresponding process, and the maximum value of the ROS of the fingers is the maximum value of the ROS value in the corresponding process.

Differential pressure ratio RP of 80% at both sides of pulse wave peak value at wrist_m0.8Pressure ratio RAP of 50% on both sides of pulse wave peak_m0.5The calculation method of (2) is shown in fig. 8, wherein the pressure pulse signal change during inflation and deflation is shown in fig. 9 and 10:

calculating the maximum amplitude A in the waveform of the wrist pressure pulse signal by using alinear interpolation method_max80% amplitude A of front and rear sides_d0.8、A_s0.8And obtaining A_d0.8Corresponding wrist air belt pressure P_d0.8、A_s0.8Corresponding wrist air belt pressure P_s0.8，

Calculating the maximum amplitude A in the waveform of the wrist pressure pulse signal by using alinear interpolation method_max50% amplitude A of front and rear sides_d0.5、A_s0.5And obtaining A_d0.5Corresponding wrist air belt pressure P_d0.5、A_s0.5Corresponding wrist air belt pressure P_s0.5；

Calculating the differential pressure ratio RP of 80 percent of amplitude values on two sides_m0.8Pressure ratio RAP of 50% amplitude on both sides_m0.5：

The pressure ratio RAP of 50% on both sides of the maximum rate of change as shown in FIG. 11_MR0.5Differential pressure ratio RP of 50% on both sides of maximum rate of change_MR0.5The calculation method of (2) is as follows:

calculating the maximum change rate MR in the change rate of the wristpressure pulse signal_max50% value MR of front and rear sides_d0.5、MR_s0.5And obtaining MR_d0.5Corresponding wrist air belt pressure P_MRd0.5、MR_s0.5Corresponding wrist air belt pressure P_MRs0.5；

Calculate the pressure ratio RAP of the two-sided 50% rate of change_MR0.5Differential pressure ratio RP of 50% change rate on both sides_MR0.5：

Fig. 12 shows the rate of change of the pressure pulse signal versus the pressure in the air belt.

The above calculation is data at the wrist, and similarly, the corresponding parameters at the ankle joint may be calculated according to the above method for calculating the parameters at the wrist: maximum amplitude A of ankle joint pressure pulse signal_maxAnd the corresponding ankle joint air belt pressure PA_maxDifferential pressure ratio RP of 80% amplitude on both sides_m0.8Pressure ratio RAP of 50% amplitude on both sides_m0.5Maximum rate of change MR of ankle joint pressure pulse signal_maxPressure ratio RAP of 50% rate of change on both sides_MR0.5Differential pressure ratio RP of 50% change rate on both sides_MR0.5；

And finally, calculating the ratio of the similar parameters of the wrist and the ankle joint: ratio of systolic pressure of wrist to systolic pressure of ankle, ratio of diastolic pressure of wrist to diastolic pressure of ankle, mean blood pressure of wrist to mean blood pressure of ankleRatio of pressure, A of the wrist_maxA with ankle_maxRatio of (A) to (B), PA of the wrist_maxPA for ankle_maxRatio of (A) to (B), RP of the wrist_m0.8RP with ankle_m0.8Ratio of (A) to (B), RAP of wrist_m0.5RAP with ankle_m0.5Ratio of (1), MR of the wrist_maxMR of ankle_maxRatio of (A) to (B), RAP of wrist_MR0.5RAP with ankle_MR0.5Ratio of (A) to (B), RP of the wrist_MR0.5RP with ankle_MR0.5The ratio of (a) can reflect the blood flow condition of the upper limb and the lower limb of the person to be monitored;

the pulse variation time ratio Δ T/T shown in FIG. 13_aThe calculation method is as follows:

the present embodiment is calculated by using the data of the air belt deflation process, and the calculation method is as follows:

extracting a maximum rate of change PMR for each cardiac cycle in a pressure pulse signal_maxAnd the maximum rate of change PMR_maxAt a time t_PMRSimultaneously extracting the time point t of the electrocardio R wave of each cardiac cycle_iI is the order of the cardiac cycles;

calculating each time point t_iAnd time t_PMRDifference Δ t of_iAnd extracting said difference Δ t_iMaximum value t of_maxAnd a minimum value t_minCalculating the maximum value t_maxAnd a minimum value t_minThe difference of (a):

ΔT＝t_max-t_min

all differences Δ t_iAverage value of (d):

k is the total number of cardiac cycles;

then the time ratio DeltaT/T is obtained_aThe time ratio DeltaT/T_aCan reflect the elasticity and blood flow condition of the blood vessel of the person to be monitored;

the pulse propagation velocity is likewise calculated as a pressure pulse of the deflation process, whichMiddle T_aThe above calculation results can be used, and the calculation method is shown in fig. 14:

obtaining the distance d from the heart to the ankle artery₁Heart to radial artery distance d₂Heart to earlobe distance d₃Then obtain the distance difference | d₁-d₂|、|d₁-d₃|；

Calculating the pulse propagation speed:

wherein, DL and Td are preferably: DL is distance difference | d₁-d₂And Td is ankle wrist time difference: mean value of ankle joint T_aMean value of the wrist T_a；

Calculating the ratio of the mean value of the pulse propagation speeds in the non-inflation process to the maximum value of the pulse propagation speeds in the deflation process, and the ratio of the mean value of the pulse propagation speeds in the non-inflation process to the mean value of the pulse propagation speeds in the constant pressure process, wherein the mean value of the pulse propagation speeds is the mean value of all the pulse propagation speeds in the corresponding process, and the maximum value of the pulse propagation speed is the maximum value of the pulse propagation speeds in the corresponding process;

and evaluating the cardiovascular health condition of the person to be monitored according to the cardiovascular characteristic parameters.

Claims (10)

Translated fromChinese

1.一种基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于包括：1. a wearable cardiovascular health monitoring system based on single side signal detection, is characterized in that comprising:单侧数据检测设备，用于采集待监测者的基础心血管信息，所述基础心血管信息包括：气带未充气过程中的单道心电信号、手指血氧双波长信号、耳垂血氧双波长信号，气带放气过程及恒压过程中的单道心电信号、手指血氧双波长信号、耳垂血氧双波长信号、手腕气带压力、手腕压力脉搏信号、踝关节气带压力、踝关节压力脉搏信号；The unilateral data detection device is used to collect the basic cardiovascular information of the person to be monitored. The basic cardiovascular information includes: the single-channel ECG signal during the uninflated process of the air belt, the finger blood oxygen dual-wavelength signal, the earlobe blood oxygen dual-wavelength signal. Wavelength signal, single-channel ECG signal during air belt deflation and constant pressure process, finger blood oxygen dual-wavelength signal, earlobe blood oxygen dual-wavelength signal, wrist air belt pressure, wrist pressure pulse signal, ankle air belt pressure, Ankle joint pressure pulse signal;所述基础心血管信息为待监测者同一体侧的手指、耳垂、手腕、踝关节所对应的数据；The basic cardiovascular information is the data corresponding to the fingers, earlobes, wrists, and ankles on the same side of the person to be monitored;数据处理器，用于计算检测数据，得到监测比较参数，具体包括：The data processor is used to calculate the detection data and obtain the monitoring and comparison parameters, including:用于提取所述基础心血管信息的心血管特征参数，根据所述心血管特征参数计算得到监测评估数据；Cardiovascular characteristic parameters for extracting the basic cardiovascular information, and monitoring and evaluation data are obtained by calculating according to the cardiovascular characteristic parameters;所述心血管特征参数至少包括：心电R波、血氧饱和度双波长信号的比值ROS、压力脉搏信号的波形、压力脉搏信号的变化率；The cardiovascular characteristic parameters include at least: ECG R wave, ratio of blood oxygen saturation dual-wavelength signal ROS, waveform of pressure pulse signal, and rate of change of pressure pulse signal;所述监测评估数据至少包括整个气带放气过程中的：比值ROS随心动周期减小的平均速率ROS_dec、比值ROS随心动周期增加的平均速度ROS_inc、脉搏波峰值两侧80％的压差比RP_m0.8、脉搏波峰值两侧50％的压力比RAP_m0.5、最大变化率两侧50％的压力比RAP_MR0.5、最大变化率两侧50％的压差比RP_MR0.5；The monitoring and evaluation data at least include: the average rate of the ratio ROS decreasing with the cardiac cycle ROS_dec , the average rate_ROS in Difference ratio RP_m0.8 , 50% pressure ratio on both sides of pulse wave peak value RAP_m0.5 , 50% pressure ratio on both sides of maximum change rate RAP_MR0.5 , 50% pressure difference ratio on both sides of maximum change rate RP_{MR0 .5} ;数据存储器，用于存储数据内容；Data storage for storing data content;数据显示装置，用于显示监测内容，该显示监测内容包括基础心血管信息或/和监测比较参数；a data display device for displaying monitoring content, where the displayed monitoring content includes basic cardiovascular information or/and monitoring comparison parameters;所述单侧数据检测设备的输出端组连接数据处理器的数据接收端组，所述数据处理器的参数输出端组连接数据显示装置的显示接收端组，所述数据存储器连接数据处理器。The output terminal group of the single-side data detection device is connected to the data receiving terminal group of the data processor, the parameter output terminal group of the data processor is connected to the display receiving terminal group of the data display device, and the data memory is connected to the data processor.2.根据权利要求1所述基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于还包括用户输入设备，用于获取待监测者的个人信息；2. The wearable cardiovascular health monitoring system based on single-side signal detection according to claim 1, further comprising a user input device for obtaining personal information of the person to be monitored;无线数据传输模块，用于发送检测比较参数至网络端；Wireless data transmission module, used to send detection and comparison parameters to the network;所述用户输入设备和无线数据传输模块分别连接所述数据处理器。The user input device and the wireless data transmission module are respectively connected to the data processor.3.根据权利要求1所述基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于：所述单侧数据检测设备包括耳垂光电血氧双波长传感器、手指血氧双波长传感器、手腕气带压力传感器、脚踝气带压力传感器、心电电极。3. The wearable cardiovascular health monitoring system based on single-side signal detection according to claim 1, wherein the single-side data detection device comprises an earlobe photoelectric blood oxygen dual-wavelength sensor, a finger blood oxygen dual-wavelength sensor , wrist air belt pressure sensor, ankle air belt pressure sensor, ECG electrode.4.根据权利要求1所述基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于：所述数据处理器包括心血管特征参数提取模块、监测评估数据计算模块；4. The wearable cardiovascular health monitoring system based on single-side signal detection according to claim 1, wherein the data processor comprises a cardiovascular feature parameter extraction module and a monitoring evaluation data calculation module;其中，所述心血管特征参数提取模块提取所述基础心血管信息的心血管特征参数；Wherein, the cardiovascular feature parameter extraction module extracts the cardiovascular feature parameters of the basic cardiovascular information;所述血氧饱和度双波长信号的比值ROS为测量血氧饱和度的两种不同波长的直流信号在同一心动周期内平均值之比；The ratio ROS of the blood oxygen saturation dual-wavelength signal is the ratio of the average value of the two different wavelengths of direct current signals for measuring blood oxygen saturation in the same cardiac cycle;所述监测评估数据计算模块根据所述心血管特征参数计算得到监测评估数据，所述监测评估数据即反应待监测者的心血管健康状态。The monitoring and evaluation data calculation module calculates and obtains monitoring and evaluation data according to the cardiovascular characteristic parameters, and the monitoring and evaluation data reflects the cardiovascular health state of the person to be monitored.5.根据权利要求4所述基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于：所述比值ROS随心动周期减小的平均速率ROS_dec、比值ROS随心动周期增加的平均速度ROS_inc的计算方法如下：5 . The wearable cardiovascular health monitoring system based on single-side signal detection according to claim 4 , wherein the average rate ROS_dec of the ratio ROS decreases with the cardiac cycle, and the ratio ROS increases with the cardiac cycle. 6 . The average speed ROS_inc is calculated as follows:A1，提取所有心动周期中所述比值ROS的最大值ROS_max、最小值ROS_min、第一个心动周期的比值ROS_sta、最后一个心动周期的比值ROS_end，其中最小值ROS_min所在的心动周期次序为n；A1, extract the maximum value ROS_max of the ratio ROS in all cardiac cycles, the minimum value ROS_min , the ratio ROS_sta of the first cardiac cycle, and the ratio ROS_end of the last cardiac cycle, wherein the cardiac cycle where the minimum value ROS_min is located The order is n;A2，计算所述比值ROS随心动周期减小的平均速率ROS_dec：A2, calculate the average rate ROS_dec at which the ratio ROS decreases with the cardiac cycle:

A3，计算所述比值ROS随心动周期增加的平均速度ROS_inc：A3, calculate the mean velocity ROS_inc of the ratio ROS increasing with cardiac cycle:

其中，ROS_cmax为满足：Among them, ROS_cmax satisfies:

的最大值，ROS_m和ROS_m-1分别是相邻两个心动周期的比值ROS，其心动周期次序分别为m和m-1。The maximum value of ROS_m and ROS_m-1 are the ratios of ROS in two adjacent cardiac cycles, respectively, and their cardiac cycle order is m and m-1, respectively.6.根据权利要求4所述基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于：所述脉搏波峰值两侧80％的压差比RP_m0.8、脉搏波峰值两侧50％的压力比RAP_m0.5的计算方法如下：6 . The wearable cardiovascular health monitoring system based on single-side signal detection according to claim 4 , wherein 80% of the pressure difference ratios on both sides of the pulse wave peak value are RP_m0.8 , and the pulse wave peak value two The pressure ratio of the side 50% RAP_m0.5 is calculated as follows:B1，提取所述压力脉搏信号波形的最大幅值A_max及该最大幅值A_max处对应的气带压力PA_max；B1, extract the maximum amplitude_Amax of the pressure pulse signal waveform and the air band pressure_{PAmax corresponding to the maximum amplitude Amax;}B2，计算所述压力脉搏信号的波形中最大幅值A_max前后两侧的80％幅值A_d0.8、A_s0.8，并获得A_d0.8处对应的气带压力P_d0.8、A_s0.8处对应的气带压力P_s0.8，B2: Calculate the 80% amplitudes A_d0.8 and A_s0.8 on the front and back sides of the maximum amplitude A_max in the waveform of the pressure pulse signal, and obtain the air band pressure P_d0.8 corresponding to A_d0.8 , the corresponding gas belt pressure P_s0.8 at A_s0.8 ,计算所述压力脉搏信号的波形中最大幅值A_max前后两侧的50％幅值A_d0.5、A_s0.5，并获得A_d0.5处对应的气带压力P_d0.5、A_s0.5处对应的气带压力P_s0.5；Calculate the 50% amplitudes A_d0.5 and A_s0.5 on both sides before and after the maximum amplitude A_max in the waveform of the pressure pulse signal, and obtain the corresponding air band pressures P_d0.5 and A at A_d0.5 Corresponding air belt pressure P_s0.5 at_s0.5 ;B3，计算所述脉搏波峰值两侧80％的压差比RP_m0.8、脉搏波峰值两侧50％的压力比RAP_m0.5：B3, calculate the pressure difference ratio RP_m0.8 of 80% on both sides of the pulse wave peak value, and the pressure ratio RAP_m0.5 of 50% on both sides of the pulse wave peak value:

7.根据权利要求4所述基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于：所述最大变化率两侧50％的压力比RAP_MR0.5、最大变化率两侧50％的压差比RP_MR0.5的计算方法如下：7 . The wearable cardiovascular health monitoring system based on single side signal detection according to claim 4 , wherein 50% of the pressure ratios on both sides of the maximum rate of change are RAP_MR0.5 , and the two sides of the maximum rate of change are 50% . 8 . The 50% differential pressure ratio RP_MR0.5 is calculated as follows:C1，提取所述压力脉搏信号的变化率中最大变化率MR_max及该最大变化率MR_max处对应的气带压力PMR_max；C1, extracting the maximum rate of change MR_max in the rate of change of the pressure pulse signal and the air band pressure PMR_{max corresponding to the maximum rate of change MR max;}C2，计算所述压力脉搏信号的变化率中最大变化率MR_max前后两侧的50％值MR_d0.5、MR_s0.5，并获得MR_d0.5处对应的气带压力P_MRd0.5、MR_s0.5处对应的气带压力P_MRs0.5；C2: Calculate the 50% values MR_d0.5 and MR_s0.5 on both sides of the maximum change rate MR_max in the change rate of the pressure pulse signal, and obtain the air band pressure P_MRd0.5 corresponding to MR_d0.5 , the corresponding gas belt pressure P_{MRs0.5 at MR s0.5;}C3，计算所述最大变化率两侧50％的压力比RAP_MR0.5、最大变化率两侧50％的压差比RP_MR0.5：C3, calculate the pressure ratio RAP_MR0.5 of 50% on both sides of the maximum change rate and the differential pressure ratio RP_MR0.5 of 50% on both sides of the maximum change rate:

8.根据权利要求4所述基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于：所述监测评估数据还包括脉搏变化时间比值ΔT/T_a，该脉搏变化时间比值ΔT/T_a或通过无气带压过程的数据计算，或通过气带放气过程的数据计算，或气带恒压过程的数据计算，其计算方法如下：8 . The wearable cardiovascular health monitoring system based on single-side signal detection according to claim 4 , wherein the monitoring evaluation data further comprises a pulse change time ratio ΔT/T_a , the pulse change time ratio ΔT . /T_a is calculated by the data of the process without air with pressure, or calculated by the data of the process of deflation in the gas belt, or calculated by the data of the process of constant pressure in the gas belt, the calculation method is as follows:D1，提取脉搏信号中每个心动周期的最大变化率PMR_max及该最大变化率PMR_max处的时间t_PMR，所述脉搏信号为压力脉搏或光电脉搏；D1, extract the maximum change rate PMR_max of each cardiac cycle and the time t_PMR at the maximum change rate PMR_max in the pulse signal, where the pulse signal is a pressure pulse or a photoelectric pulse;同时提取每个心动周期的心电R波的时间点t_i，i为心动周期的次序；At the same time, the time point t_i of the ECG R wave of each cardiac cycle is extracted, where i is the order of the cardiac cycle;D2，计算每个时间点t_i与时间t_PMR的差值Δt_i，并提取所述差值Δt_i的最大值t_max和最小值t_min，D2, calculate the difference Δt_i between each time point t_i and time t_PMR , and extract the maximum value t_max and the minimum value t_min of the difference Δt_i ,D3，计算最大值t_max和最小值t_min的差值：D3, calculate the difference between the maximum value t_max and the minimum value t_min :

所有差值Δt_i的平均值：Average of all differences Δt_i :

其中，k为心动周期的总数；where k is the total number of cardiac cycles;D4，计算得到脉搏变化时间比值ΔT/T_a，该脉搏变化时间比值ΔT/T_a反应待监测者的血管弹性和血流情况。D4, the pulse change time ratio ΔT/T_a is calculated and obtained, and the pulse change time ratio ΔT/T_a reflects the vascular elasticity and blood flow of the subject to be monitored.9.根据权利要求4所述基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于：所述监测评估数据还包括脉搏传播速度，该脉搏传播速度或通过无气带压过程的数据计算，或通过气带放气过程的数据计算，或气带恒压过程的数据计算，所述脉搏传播速度的计算方法如下：9 . The wearable cardiovascular health monitoring system based on single-side signal detection according to claim 4 , wherein the monitoring and evaluation data further comprises a pulse propagation speed, the pulse propagation speed or the process of airless belt pressure. 10 . The calculation method of the pulse propagation speed is as follows:E1，获取心脏到踝动脉的距离d₁、心脏到桡动脉的距离d₂、心脏到耳垂的距离d₃，则得到距离差|d₁-d₂|、|d₂-d₃|；E1, obtain the distance d 1 from the heart to the ankle artery, the distance d₂ from the heart to the radial artery, and the distance d₃ from the heart to the earlobe, then obtain the distance differences |d₁ -d₂ |, |d₂ -d₃ |_;E2，提取脉搏信号中每个心动周期的最大变化率PMR_max及该最大变化率PMR_max处的时间t_PMR，所述脉搏信号为压力脉搏或光电脉搏；E2, extract the maximum change rate PMR_max of each cardiac cycle and the time t_PMR at the maximum change rate PMR_max in the pulse signal, where the pulse signal is a pressure pulse or a photoelectric pulse;提取每个心动周期的心电R波的时间点t_i，i为心动周期的次序；The time point t_i for extracting the ECG R wave of each cardiac cycle, i is the order of the cardiac cycle;E3，计算每个时间点t_i与时间t_PMR的差值Δt_i，计算所有差值Δt_i的平均值：E3, calculate the difference Δt_i between each time point t_i and time t_PMR , and calculate the average value of all the differences Δt_i :

其中，k为心动周期的总数；where k is the total number of cardiac cycles;E4，计算脉搏传播速度：E4, calculate the pulse propagation speed:

其中，DL与Td或为：DL为距离差|d₁-d₂|，Td为踝腕时间差：踝关节的平均值T_a-手腕的平均值T_a；Wherein, DL and Td may be: DL is the distance difference |d₁ -d₂ |, Td is the ankle-wrist time difference: the average value of the ankle joint T_a - the average value of the wrist T_a ;DL与Td或为：DL为距离差|d₂-d₃|，Td为耳腕时间差：耳垂的平均值T_a-手腕的平均值T_a。DL and Td are either: DL is the distance difference |d₂ -d₃ |, Td is the ear-wrist time difference: the average value of the earlobe T_a - the average value of the wrist T_a .10.根据权利要求4-7之一所述基于单体侧信号检测的可穿戴式心血管健康监测系统，其特征在于所述监测评估数据还包括：10. The wearable cardiovascular health monitoring system based on single side signal detection according to one of claims 4-7, characterized in that the monitoring evaluation data further comprises:不同采集过程中参数的比值：未充气过程的手指ROS均值与放气过程的手指ROS最大值之比，未充气过程的手指ROS均值与恒压过程的手指ROS均值之比，所述手指ROS均值为对应过程中所有ROS值的平均值，所述手指ROS最大值为对应过程中ROS值的最大值；The ratio of parameters in different collection processes: the ratio of the mean ROS value of the finger in the uninflated process to the maximum ROS value of the finger during the deflation process, the ratio of the mean ROS value of the finger in the uninflated process to the mean ROS value of the finger in the constant pressure process, the mean ROS value of the finger is the average value of all ROS values in the corresponding process, and the maximum ROS value of the finger is the maximum value of the ROS value in the corresponding process;未充气过程的脉搏传播速度均值与放气过程的脉搏传播速度最大值之比，未充气过程的脉搏传播速度均值与恒压过程的脉搏传播速度均值之比，所述脉搏传播速度均值为对应过程中所有脉搏传播速度的平均值，所述脉搏传播速度最大值为对应过程中脉搏传播速度的最大值；The ratio of the mean value of the pulse propagation velocity of the non-inflated process to the maximum value of the pulse propagation speed of the deflation process, the ratio of the mean value of the pulse propagation speed of the non-inflated process to the mean value of the pulse propagation speed of the constant pressure process, the mean value of the pulse propagation speed of the corresponding process The average value of all pulse propagation velocities in , the maximum value of the pulse propagation speed is the maximum value of the pulse propagation speed in the corresponding process;手指与耳垂同类参数的比值：手指的比值ROS与耳垂的比值ROS的比值；The ratio of similar parameters between fingers and earlobes: the ratio of fingers to the ratio of ROS to the ratio of earlobes to the ratio of ROS;手腕与脚踝同类参数的比值：手腕的A_max与脚踝的A_max的比值、手腕的PA_max与脚踝的PA_max的比值、手腕的RP_m0.8与脚踝的RP_m0.8的比值、手腕的RAP_m0.5与脚踝的RAP_m0.5的比值、手腕的MR_max与脚踝的MR_max的比值、手腕的RAP_MR0.5与脚踝的RAP_MR0.5的比值、手腕的RP_MR0.5与脚踝的RP_MR0.5的比值。The ratio of similar parameters of wrist and ankle: ratio of A_max of wrist to A_max of ankle, ratio of PA_max of wrist to PA_max of ankle, ratio of RP_m0.8 of wrist to RP_m0.8 of ankle, ratio of wrist RAP_m0.5 to ankle RAP_m0.5 ratio, wrist MR_max to ankle MR_max ratio, wrist RAP_MR0.5 to ankle RAP_MR0.5 ratio, wrist RP_MR0.5 to ankle The ratio of RP_MR0.5 .

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