A non-invasive continuous detection device and method for human blood pressure under high pressure

Abstract

The present invention discloses a non-invasive continuous detection device and method for human blood pressure under high pressure: a host computer subtracts the potential value of an RA electrocardiogram from the potential value of an LL electrocardiogram at a shallow depth to obtain a two-lead electrocardiogram at a shallow depth, and then analyzes the time difference between the peak value of a pulse wave at a shallow depth and the nearest peak value in the two-lead electrocardiogram as the pulse wave conduction time PWTT at a shallow depth and the corresponding blood pressure value BP, thereby analyzing multiple groups of pulse wave conduction times PWTT and blood pressure values ​​BP at a shallow depth, and substituting the values ​​of the multiple groups of PWTT and BP into a target formula to obtain the values ​​of variables a and b; and then subtracting the potential value of an RA electrocardiogram from the potential value of an LL electrocardiogram at a great depth to obtain a two-lead electrocardiogram at a great depth, and then analyzing the time difference between the peak value of a pulse wave at a great depth and the nearest peak value in the two-lead electrocardiogram as the PWTT at a great depth, and substituting the PWTT value into the target formula to calculate the blood pressure value as the true blood pressure value of the person to be detected at a great depth.

Description

Technical Field

[0001] The present invention relates to the technical field of blood pressure detection, and in particular to a device and method for non-invasive continuous detection of human blood pressure under high pressure. Background Art

[0002] In the field of continuous blood pressure monitoring, domestic and foreign scholars have proposed a number of mature blood pressure monitoring methods, among which the common non-invasive continuous blood pressure measurement methods mainly include arterial tension method, volume compensation method and photoplethysmography. Arterial tension method and volume compensation method can accurately measure arterial blood pressure, but the operation of these two methods is relatively complicated, and the long-term wearing of hardware devices will affect the measurement accuracy, and cause discomfort to the measured person, which is not suitable for long-term continuous measurement; photoplethysmography overcomes the disadvantage of complex devices, but the calculation relationship model between blood pressure value and blood flow information still has great problems and has not been well solved.

[0003] The commonly used blood pressure measurement method is the cuff-type electronic blood pressure measurement method, but the cuff-type electronic blood pressure measurement can only work under small depth / shallow depth conditions. The cuff-type electronic blood pressure measurement value is inaccurate under large depth conditions. Based on this, the present invention designs a non-invasive continuous detection device and method for human blood pressure under high pressure, which can accurately and non-invasively obtain the real blood pressure value of the human body under large depth conditions. Summary of the invention

[0004] In view of the problems and shortcomings of the prior art, the present invention provides a non-invasive continuous detection device and method for human blood pressure under high pressure.

[0005] The present invention solves the above technical problems through the following technical solutions:

[0006] The present invention provides a non-invasive continuous detection device for human blood pressure under high pressure, which is characterized in that it comprises a smart vest for a person to be detected to wear and a host computer, the smart vest comprises a vest body, an integrated box and a battery box are fixed on the outer layer of the vest body, a switch is installed on the integrated box, an electrocardiogram acquisition front end, an electrocardiogram simulation front end, a pulse wave simulation front end, an MCU circuit and a power supply circuit are integrated in the integrated box, a battery is installed in the battery box, a blood pressure cuff is installed on the outer layer of the sleeve part of the vest body, a photoelectric sensor is installed on the inner layer of the sleeve part of the vest body, and an electrocardiogram electrode RA corresponding to the first intercostal space of the right clavicle midline of the human body, an electrocardiogram electrode LL corresponding to the xiphoid process level of the left clavicle midline of the human body, and an electrocardiogram electrode RL corresponding to the xiphoid process level of the right clavicle midline of the human body are installed on the inner layer of the vest body for grounding;

[0007] The power supply circuit is used to convert the battery voltage into the power supply voltage required by the ECG acquisition front end, the ECG simulation front end, the pulse wave simulation front end, the MCU circuit and the power supply circuit when the switch is turned on;

[0008] The ECG acquisition front end is used to collect RA ECG signals and LL ECG signals of the person to be tested in the pressurized cabin at shallow depth and deep depth respectively through the ECG electrodes RA and LL, and transmit the ECG signals to the MCU circuit after amplifying them through the ECG simulation front end;

[0009] The pulse wave simulation front end is used to synchronously collect the pulse wave signals of the person to be detected in the pressurized cabin at shallow depth and deep depth through the photoelectric sensor and transmit them to the MCU circuit;

[0010] The blood pressure cuff is used to synchronously collect the blood pressure signal of the person to be tested at a shallow depth in the pressurized chamber and transmit it to the MCU circuit;

[0011] The MCU circuit is used to upload the RA ECG signal, LL ECG signal, pulse wave signal and blood pressure signal of the person to be tested at a shallow depth, and the RA ECG signal, LL ECG signal and pulse wave signal at a great depth to the host computer;

[0012] The host computer is used to subtract the potential value of the RA electrocardiogram from the potential value of the LL electrocardiogram at a shallow depth to obtain a two-lead electrocardiogram at a shallow depth, and then analyze the time difference between the peak value of the pulse wave at the shallow depth and the nearest R wave peak value in the two-lead electrocardiogram as the pulse wave conduction time PWTT at the shallow depth, and the PWTT at the shallow depth corresponds to a blood pressure value BP in the blood pressure signal at the shallow depth, thereby analyzing multiple groups of corresponding pulse wave conduction times PWTT and blood pressure values ​​BP at the shallow depth, and substituting the values ​​of the multiple groups of PWTT and BP into the target formula to obtain the values ​​of variables a and b;

[0013] The host computer is also used to subtract the potential value of the RA electrocardiogram from the potential value of the LL electrocardiogram at a great depth to obtain a two-lead electrocardiogram at a great depth, and then analyze the time difference between the peak value of the pulse wave at a great depth and the nearest R wave peak value in the two-lead electrocardiogram as the pulse wave transmission time PWTT at a great depth, and substitute the PWTT value into the target formula to calculate the blood pressure value at a great depth as the true blood pressure value of the subject to be tested at a great depth;

[0014] Among them, the target formula BP=a×PWTT+b(a<0), shallow depth refers to the underwater depth corresponding to the pressure in the pressurized cabin not exceeding 7ATA, and deep depth refers to the underwater depth corresponding to the pressure in the pressurized cabin exceeding 7ATA.

[0015] The present invention also provides a method for non-invasive continuous detection of human blood pressure under high pressure, which is characterized in that it is implemented by using the above-mentioned non-invasive continuous detection device for human blood pressure under high pressure, and the method comprises the following steps:

[0016] Step 1: Press the switch, and the power circuit converts the battery voltage into the power supply voltage required by the ECG acquisition front end, ECG simulation front end, pulse wave simulation front end, MCU circuit and power circuit;

[0017] Step 2: The ECG acquisition front end collects the RA ECG signal and the LL ECG signal of the person to be tested in the pressurized chamber at a shallow depth through the ECG electrode RA and the ECG electrode LL respectively, and transmits the ECG signals to the MCU circuit after amplifying the ECG signals through the ECG simulation front end, the pulse wave simulation front end synchronously collects the pulse wave signal of the person to be tested in the pressurized chamber at a shallow depth through the photoelectric sensor and transmits it to the MCU circuit, and the blood pressure cuff synchronously collects the blood pressure signal of the person to be tested in the pressurized chamber at a shallow depth and transmits it to the MCU circuit;

[0018] Step 3: The MCU circuit uploads the RA ECG signal, LL ECG signal, pulse wave signal and blood pressure signal of the subject to be tested at a shallow depth to the host computer;

[0019] Step 4: the host computer subtracts the potential value of the RA ECG signal from the potential value of the LL ECG signal at the shallow depth to obtain a two-lead ECG at the shallow depth, and then analyzes the time difference between the peak value of the pulse wave at the shallow depth and the nearest R wave peak value in the two-lead ECG as the pulse wave conduction time PWTT at the shallow depth. The PWTT at the shallow depth corresponds to a blood pressure value BP in the blood pressure signal at the shallow depth, thereby analyzing multiple groups of corresponding pulse wave conduction times PWTT and blood pressure values ​​BP at the shallow depth, and substituting the values ​​of the multiple groups of PWTT and BP into the target formula to obtain the values ​​of variables a and b;

[0020] Among them, the target formula BP = a × PWTT + b (a < 0);

[0021] Step 5: The ECG acquisition front end collects the RA ECG signal and the LL ECG signal of the person to be detected in the pressurized cabin at a great depth through the ECG electrode RA and the ECG electrode LL respectively, and transmits the ECG signals to the MCU circuit after amplifying the ECG signals through the ECG simulation front end, and the pulse wave simulation front end synchronously collects the pulse wave signal of the person to be detected in the pressurized cabin at a great depth through the photoelectric sensor and transmits it to the MCU circuit;

[0022] Step 6: The MCU circuit uploads the RA ECG signal, LL ECG signal and pulse wave signal of the person to be tested at a great depth to the host computer;

[0023] Step 7: The host computer subtracts the potential value of the RA electrocardiogram from the potential value of the LL electrocardiogram at a great depth to obtain a two-lead electrocardiogram at a great depth, and then analyzes the time difference between the peak value of the pulse wave at a great depth and the nearest R wave peak value in the two-lead electrocardiogram as the pulse wave conduction time PWTT at a great depth, and substitutes the PWTT value into the target formula to calculate the blood pressure value at a great depth as the true blood pressure value of the subject to be tested at a great depth;

[0024] Shallow depth refers to the underwater depth corresponding to the pressure in the pressurized cabin not exceeding 7ATA, and deep depth refers to the underwater depth corresponding to the pressure in the pressurized cabin exceeding 7ATA.

[0025] The positive and progressive effects of the present invention are:

[0026] The present invention utilizes a wearable smart vest to synchronously collect the ECG, pulse wave and blood pressure signals of a subject to be detected under shallow depth conditions, utilizes these signals to obtain multiple groups of corresponding pulse wave conduction times PWTT and blood pressure values ​​BP, substitutes the multiple groups of PWTT and BP values ​​into a target formula to calibrate variables a and b in the target formula to obtain the values ​​of variables a and b, then utilizes the wearable smart vest to synchronously collect the ECG and pulse wave signals of the subject to be detected under great depth conditions, analyzes and obtains the pulse wave conduction time PWTT at great depth, substitutes the PWTT value into the target formula to calculate the blood pressure value at great depth as the real blood pressure value of the subject to be detected at great depth, thereby being able to accurately and non-invasively detect the real blood pressure value of the subject to be detected at great depth. BRIEF DESCRIPTION OF THE DRAWINGS

[0027] Figure 1 Schematic diagram of the structure of the outer layer of the smart vest according to an embodiment of the present invention.

[0028] Figure 2 Schematic diagram of the structure of the inner layer of the smart vest according to an embodiment of the present invention.

[0029] Figure 3 It is a structural schematic diagram of the installation position of the integrated box according to an embodiment of the present invention.

[0030] Figure 4 This is a control relationship diagram of a device for non-invasive and continuous detection of human blood pressure under high pressure according to an embodiment of the present invention.

[0031] Figure 5 4 is a circuit diagram of an MCU circuit according to an embodiment of the present invention.

[0032] Figure 5 (a) is an enlarged view of the left side of the MCU circuit of an embodiment of the present invention.

[0033] Figure 5 (b) is an enlarged view of the right side of the MCU circuit of the embodiment of the present invention.

[0034] Figure 6 The circuit diagram of the ECG acquisition front end of the embodiment of the present invention.

[0035] Figure 7 4 is a circuit diagram of an electrocardiogram simulation front end according to an embodiment of the present invention.

[0036] Figure 8 4 is a circuit diagram of a pulse wave simulation front end according to an embodiment of the present invention. DETAILED DESCRIPTION

[0037] In order to make the purpose, technical solution and advantages of the embodiments of the present invention clearer, the technical solution in the embodiments of the present invention will be clearly and completely described below in conjunction with the drawings in the embodiments of the present invention. Obviously, the described embodiments are part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative work are within the scope of protection of the present invention.

[0038] like Figure 1-8 As shown, this embodiment provides a non-invasive continuous detection device for human blood pressure under high pressure, which includes a smart vest 100 for a person to be detected to wear and a host computer 200. The smart vest 100 includes a vest body 1, an integrated box 2 is fixed on the front outer layer of the vest body 1, a switch 3 is installed on the integrated box 2, an ECG acquisition front end 21, an ECG simulation front end 22, a pulse wave simulation front end 23, an MCU circuit 24 and a power supply circuit 25 are integrated in the integrated box 2, a battery box 4 is fixed on the front outer layer of the vest body 1, a battery 41 is installed in the battery box 4, a blood pressure cuff 5 is installed on the outer layer of the sleeve part of the vest body 1, a photoelectric sensor 6 is installed on the inner layer of the sleeve part of the vest body 1, and an ECG electrode RA corresponding to the first intercostal space of the right clavicle midline of the human body, an ECG electrode LL corresponding to the xiphoid process level of the left clavicle midline of the human body, and an ECG electrode RL corresponding to the xiphoid process level of the right clavicle midline of the human body are installed on the inner layer of the vest body 1 for grounding.

[0039] Among them, a first mounting seat 11 with a first buckle 111 is fixed on the front of the vest body 1, and a first push-type clip 26 is embedded on the top of the integrated box 2. When the first push-type clip 26 is pressed, the first push-type clip 26 moves downward along the outer wall of the first buckle 111 and clamps the first buckle 111 in the first push-type clip 26, thereby installing the integrated box 2 on the first mounting seat 11.

[0040] A second mounting seat 12 with a second buckle is fixed to the surface of the sleeve portion of the vest body 1, and a second push-type clip is embedded in the top of the blood pressure cuff 5. When the second push-type clip is pressed, the second push-type clip moves downward along the outer wall of the second buckle and clamps the second buckle in the second push-type clip, thereby installing the blood pressure cuff 5 on the second mounting seat 12.

[0041] The power circuit 25 is used to convert the voltage of the battery 41 into 3.3V and 3V when the switch 3 is turned on. The 3.3V voltage is used to power the ECG acquisition front end 21, the ECG simulation front end 22, the MCU circuit 24 and the power circuit 25, and the 3V voltage is used to power the pulse wave simulation front end 23. The specific circuit structure of the power circuit 25 is the specific circuit structure of the power circuit in the invention patent with application number 2024112033175 and the name of a wearable multi-physiological parameter wireless monitoring system and monitoring method.

[0042] When in use, the person to be tested wears the smart vest 100 and is located in the pressurized cabin, and the host computer 200 is located outside the pressurized cabin.

[0043] The ECG acquisition front end 21 is used to collect RA ECG signals and LL ECG signals of the person to be tested in the pressurized cabin at shallow depth and great depth respectively through the ECG electrodes RA and LL, and transmit the ECG signals to the MCU circuit 24 after amplifying them through the ECG simulation front end 22.

[0044] The pulse wave analog front end 23 is used to synchronously collect the pulse wave signals of the person to be detected in the pressurized cabin at shallow depth and deep depth through the photoelectric sensor 6 and transmit them to the MCU circuit 24.

[0045] The blood pressure cuff 5 is used to synchronously collect the blood pressure signal of the person to be tested at a shallow depth in the pressurized chamber and transmit it to the MCU circuit 24.

[0046] The MCU circuit 24 is used to upload the RA ECG signal, LL ECG signal, pulse wave signal and blood pressure signal of the person to be tested at a shallow depth, as well as the RA ECG signal, LL ECG signal and pulse wave signal at a great depth to the host computer 200. The connection between the MCU circuit 24 and the host computer 200 can be a wired connection or a wireless connection such as using a wireless communication module.

[0047] The host computer 200 is used to subtract the potential value of the RA ECG signal from the potential value of the LL ECG signal at the shallow depth to obtain a two-lead ECG at the shallow depth, and then analyze the time difference between the peak value of the pulse wave at the shallow depth and the nearest R wave peak value in the two-lead ECG as the pulse wave conduction time PWTT at the shallow depth. The PWTT at the shallow depth corresponds to a blood pressure value BP in the blood pressure signal at the shallow depth, thereby analyzing multiple groups of corresponding pulse wave conduction times PWTT and blood pressure values ​​BP at the shallow depth, and substituting the values ​​of the multiple groups of PWTT and BP into the target formula to obtain the values ​​of variables a and b.

[0048] The host computer 200 is also used to subtract the potential value of the RA ECG signal from the potential value of the LL ECG signal at a great depth to obtain a two-lead ECG at a great depth, and then analyze the time difference between the peak value of the pulse wave at a great depth and the nearest R wave peak value in the two-lead ECG as the pulse wave conduction time PWTT at a great depth, and substitute the PWTT value into the target formula to calculate the blood pressure value at a great depth as the actual blood pressure value of the person to be tested at a great depth.

[0049] Among them, the target formula BP=a×PWTT+b(a<0), shallow depth refers to the underwater depth corresponding to the pressure in the pressurized cabin not exceeding 7ATA, and deep depth refers to the underwater depth corresponding to the pressure in the pressurized cabin exceeding 7ATA.

[0050] In this scheme, there is an inverse relationship between human arterial blood pressure and pulse wave transmission time. By measuring multiple groups of pulse wave transmission time PWTT and blood pressure value BP, the target formula is calibrated to obtain the values ​​of variables a and b, and then the true blood pressure value of the tester at great depth is calculated based on the calibrated target formula. The size of a and b varies from individual to individual, but the values ​​of a and b for the same individual are fixed. Therefore, the target formula calibrated based on the same individual can accurately calculate the true blood pressure value of the same individual at great depth. Since the high-pressure environment has an impact on the ECG, but according to previous animal experiments, the high-pressure environment does not change the R wave in the animal's ECG signal, so PWTT can be calculated.

[0051] like Figure 5 , Figure 5 (a) and Figure 5As shown in (b), the MCU circuit 24 includes a main control chip of model STM32F413VGT6, the PC14 pin and the PC15 pin of the main control chip U1 are connected to the high-speed crystal oscillator circuit, the VCAP_1 pin of the main control chip U1 is grounded through the capacitor C12, and the VCAP_2 pin is grounded through the capacitor C14, the OSC_IN pin and the OSC_OUT pin of the main control chip U1 are connected to the low-speed crystal oscillator circuit, the PA13 pin and the PA14 pin of the main control chip U1 are connected to the burning port for program burning, the PD3 pin of the main control chip U1 is electrically connected to the pin 3 of the status indicator chip (model GMIWA55321A) through the resistor R2, the PD4 pin is electrically connected to the pin 2 of the status indicator chip through the resistor R3, the PD5 pin is electrically connected to the pin 1 of the status indicator chip through the resistor R4, the pin 4 of the status indicator chip is grounded, and the PB2 pin of the main control chip U1 is connected to the pin 3 of the status indicator chip (model GMIWA55321A) through the resistor R2, the PD Ground, the NRST pin of the main control chip U1 is connected to the reset circuit, the reset circuit is grounded through the decoupling capacitor C3, the BOOT0 pin of the main control chip U1 is grounded through the resistor R6, the VBAT pin of the main control chip U1 is grounded through the decoupling capacitor C4, the VDD_1 pin is grounded through the decoupling capacitor C5, the VDD_2 pin is grounded through the decoupling capacitor C6, the VDD_3 pin is grounded through the decoupling capacitor C7, the VDD_4 pin is grounded through the decoupling capacitor C8, and the VDD_5 pin is grounded through the decoupling capacitor C9. The VSS_1 pin, VSS_2 pin, VSS_3 pin, VSS_4 pin and VSS_5 pin of the main control chip U1 are all grounded, the VDD pin of the main control chip U1 is grounded through the decoupling capacitor C10, the VDDA pin is grounded through the resistor R7 and the decoupling capacitor C10, the VREF+ pin is grounded through the resistor R7 and the decoupling capacitor C10, and the VSSA pin is grounded through the resistor R9.

[0052] like Figure 6 As shown, the ECG acquisition front end includes: one end of the resistor R25 is connected to the ECG electrode RA and is also grounded through the electrostatic diode D6, the other end of the resistor R25 is connected to the ECG simulation front end and is also grounded through the capacitor C32, one end of the resistor R26 is connected to the ECG electrode LL and is also grounded through the electrostatic diode D7, the other end of the resistor R26 is connected to the ECG simulation front end and is also grounded through the capacitor C33, one end of the resistor R31 is connected to the ECG electrode RL and is also grounded through the electrostatic diode D10, and the other end of the resistor R31 is connected to the ECG simulation front end.

[0053] like Figure 7As shown, the ECG simulation front end adopts the ECG chip U2 of model WL1298, the IN3N pin of the ECG chip U2 is electrically connected to the other end of the resistor R25, the IN3P pin is electrically connected to the other end of the resistor R26, the five AVDD pins (pin 19, pin 21, pin 22, pin 59 and pin 56) of the ECG chip U2 are connected to the analog ground through capacitors C54, C55, C56, C57 and C58 respectively, the five AVSS pins (pin 20, pin 23, pin 32, pin 58 and pin 57) of the ECG chip U2 are connected to the analog ground, the VREFP pin of the ECG chip U2 is electrically connected to the VREF+ pin of the main control chip U1, and is used to access the VREFP reference voltage, the VREFN pin of the ECG chip U2 is connected to the analog ground, the VREFP pin and the VREFN pin of the ECG chip U2 are connected with capacitors C60 and C61 in parallel, and the VCAP4 pin of the ECG chip U2 is connected through capacitor C62 The VCAP1 pin is connected to the analog ground through the capacitor C63, the VCAP2 pin is connected to the analog ground through the capacitor C64, the RESV1 pin of the ECG chip U2 is grounded through the resistor R59, the WCT pin of the ECG chip U2 is connected to the analog ground through the capacitor C44, the RLDOUT pin of the ECG chip U2 is electrically connected to the other end of the resistor R31, and the capacitor C47 and the resistor R42 are connected in parallel between the RLDOUT pin and the RLDINV pin. The VCAP3 pin of the ECG chip U2 is connected to the analog ground through the capacitor C53, the AVDD1 pin of the ECG chip U2 is connected to the analog ground through the resistor R45 and the capacitor C59, the AVSS1 pin is connected to the analog ground through the resistor R46, and the CLKSEL pin is grounded through the resistor R47. The three DGND pins (pin 51, pin 49 and pin 33) of the ECG chip U2 are grounded, and the two DVDD pins (pin 50 and pin 48) are grounded through the capacitor C50 and the capacitor C51 respectively. The DOUT pin of the ECG chip U2 is electrically connected to the PD14 pin of the main control chip U1 through the resistor R52, and the SCLK pin of the ECG chip U2 is electrically connected to the PD13 pin of the main control chip U1 through the resistor R54. The START pin of the ECG chip U2 is electrically connected to the PD8 pin of the main control chip U1 through a resistor R56. The pin is electrically connected to the PD9 pin of the main control chip U1 through a resistor R57, and the DIN pin is electrically connected to the PB14 pin of the main control chip U1 through a resistor R60.

[0054] like Figure 8As shown, the pulse wave analog front end 23 includes an integrated analog front end U3 of model TS9517, the OUT pin of the integrated analog front end U3 is electrically connected to the PC15 pin of the main control chip U1, the CS pin is electrically connected to the PC4 pin of the main control chip U1, the SDI pin is electrically connected to the PA6 pin of the main control chip U1, the CLK pin is electrically connected to the PE9 pin of the main control chip U1, the GND pin of the integrated analog front end U3 is grounded, the COE pin is grounded through a resistor R63, the CAP pin is grounded through a capacitor C67, and the PROG pin is grounded through a resistor R62 is grounded, the IR pin of the integrated analog front end U3 is connected to the infrared light emitting end of the photoelectric sensor, the RED pin is connected to the red light emitting end of the photoelectric sensor, the IN pin is connected to the infrared light receiving end of the photoelectric sensor, and the ANOD pin is connected to the red light receiving end of the photoelectric sensor. The VDD pin of the integrated analog front end U3 is connected to the voltage of 3V and is also grounded through the capacitor C66 and the resistor R61. The PVDD pin of the integrated analog front end U3 is connected to the voltage of 3V and is also grounded through the capacitor C65 and the resistor R61. The GND pin of the integrated analog front end U3 is grounded through the resistor R61.

[0055] This embodiment also provides a method for non-invasive continuous detection of human blood pressure under high pressure, which is implemented by using the above-mentioned non-invasive continuous detection device for human blood pressure under high pressure, and the method includes the following steps:

[0056] Step 1: Press the switch 3, the power circuit 25 converts the voltage of the battery 41 into the voltage of the ECG acquisition front end 21, the ECG simulation front end 22, the pulse wave simulation front end 23, the MCU circuit 24 and the power circuit 25. Required supply voltage.

[0057] Step 2: The ECG acquisition front end 21 collects the RA ECG signal and LL ECG signal of the person to be tested in the pressurized chamber at a shallow depth through the ECG electrode RA and the ECG electrode LL respectively, and transmits the ECG signals to the MCU circuit 24 after amplifying the ECG signals through the ECG simulation front end 22. The pulse wave simulation front end 23 synchronously collects the pulse wave signal of the person to be tested in the pressurized chamber at a shallow depth through the photoelectric sensor 6 and transmits it to the MCU circuit 24. The blood pressure cuff 5 synchronously collects the blood pressure signal of the person to be tested in the pressurized chamber at a shallow depth and transmits it to the MCU circuit 24.

[0058] Step 3: The MCU circuit 24 uploads the RA ECG signal, LL ECG signal, pulse wave signal and blood pressure signal of the subject at a shallow depth to the host computer 200 .

[0059] Step 4: The host computer 200 subtracts the potential value of the RA ECG signal from the potential value of the LL ECG signal at the shallow depth to obtain a two-lead ECG at the shallow depth, and then analyzes the time difference between the peak value of the pulse wave at the shallow depth and the nearest R wave peak value in the two-lead ECG as the pulse wave conduction time PWTT at the shallow depth. The PWTT at the shallow depth corresponds to a blood pressure value BP in the blood pressure signal at the shallow depth, thereby analyzing multiple groups of corresponding pulse wave conduction times PWTT and blood pressure values ​​BP at the shallow depth, and substituting the values ​​of the multiple groups of PWTT and BP into the target formula to obtain the values ​​of variables a and b.

[0060] Among them, the target formula BP=a×PWTT+b (a<0).

[0061] Step 5: The ECG acquisition front end 21 collects the RA ECG signal and LL ECG signal of the person to be detected in the pressurized cabin at a great depth through the ECG electrode RA and the ECG electrode LL respectively, and transmits the ECG signals to the MCU circuit 24 after amplifying the ECG signals through the ECG simulation front end 22. The pulse wave simulation front end 23 synchronously collects the pulse wave signal of the person to be detected in the pressurized cabin at a great depth through the photoelectric sensor 6 and transmits it to the MCU circuit 24.

[0062] Step 6: The MCU circuit 24 uploads the RA ECG signal, LL ECG signal and pulse wave signal of the subject under test at a great depth to the host computer 200 .

[0063] Step 7: The host computer 200 subtracts the potential value of the RA ECG signal from the potential value of the LL ECG signal at a great depth to obtain a two-lead ECG at a great depth, and then analyzes the time difference between the peak value of the pulse wave at a great depth and the nearest R wave peak value in the two-lead ECG as the pulse wave conduction time PWTT at a great depth, and substitutes the PWTT value into the target formula to calculate the blood pressure value at a great depth as the true blood pressure value of the person to be tested at a great depth.

[0064] Although the specific embodiments of the present invention are described above, those skilled in the art should understand that these are only examples, and the protection scope of the present invention is defined by the appended claims. Those skilled in the art may make various changes or modifications to these embodiments without departing from the principles and essence of the present invention, but these changes and modifications all fall within the protection scope of the present invention.

Claims

1. A non-invasive and continuous detection device for human blood pressure under high pressure, characterized in that: It includes a smart vest for a person to be tested to wear and a host computer, the smart vest includes a vest body, an integrated box and a battery box are fixed on the outer layer of the vest body, a switch is installed on the integrated box, an ECG acquisition front end, an ECG simulation front end, a pulse wave simulation front end, an MCU circuit and a power supply circuit are integrated in the integrated box, a battery is installed in the battery box, a blood pressure cuff is installed on the outer layer of the sleeve part of the vest body, a photoelectric sensor is installed on the inner layer of the sleeve part of the vest body, and an ECG electrode RA corresponding to the first intercostal space of the right clavicle midline of the human body, an ECG electrode LL corresponding to the xiphoid process level of the left clavicle midline of the human body, and an ECG electrode RL corresponding to the xiphoid process level of the right clavicle midline of the human body are installed on the inner layer of the vest body for grounding; The power supply circuit is used to convert the battery voltage into the power supply voltage required by the ECG acquisition front end, the ECG simulation front end, the pulse wave simulation front end, the MCU circuit and the power supply circuit when the switch is turned on; The ECG acquisition front end is used to collect RA ECG signals and LL ECG signals of the person to be tested in the pressurized cabin at shallow depth and deep depth respectively through the ECG electrodes RA and LL, and transmit the ECG signals to the MCU circuit after amplifying them through the ECG simulation front end; The pulse wave simulation front end is used to synchronously collect the pulse wave signals of the person to be detected in the pressurized cabin at shallow depth and deep depth through the photoelectric sensor and transmit them to the MCU circuit; The blood pressure cuff is used to synchronously collect the blood pressure signal of the person to be tested at a shallow depth in the pressurized chamber and transmit it to the MCU circuit; The MCU circuit is used to upload the RA ECG signal, LL ECG signal, pulse wave signal and blood pressure signal of the person to be tested at a shallow depth, and the RA ECG signal, LL ECG signal and pulse wave signal at a great depth to the host computer; The host computer is used to subtract the potential value of the RA electrocardiogram from the potential value of the LL electrocardiogram at a shallow depth to obtain a two-lead electrocardiogram at a shallow depth, and then analyze the time difference between the peak value of the pulse wave at the shallow depth and the nearest R wave peak value in the two-lead electrocardiogram as the pulse wave conduction time PWTT at the shallow depth, and the PWTT at the shallow depth corresponds to a blood pressure value BP in the blood pressure signal at the shallow depth, thereby analyzing multiple groups of corresponding pulse wave conduction times PWTT and blood pressure values ​​BP at the shallow depth, and substituting the values ​​of the multiple groups of PWTT and BP into the target formula to obtain the values ​​of variables a and b; The host computer is also used to subtract the potential value of the RA electrocardiogram from the potential value of the LL electrocardiogram at a great depth to obtain a two-lead electrocardiogram at a great depth, and then analyze the time difference between the peak value of the pulse wave at a great depth and the nearest R wave peak value in the two-lead electrocardiogram as the pulse wave transmission time PWTT at a great depth, and substitute the PWTT value into the target formula to calculate the blood pressure value at a great depth as the true blood pressure value of the subject to be tested at a great depth; Among them, the target formula BP=a×PWTT+b, a<0, shallow depth refers to the underwater depth corresponding to the pressure in the pressurized cabin not exceeding 7ATA, and deep depth refers to the underwater depth corresponding to the pressure in the pressurized cabin exceeding 7ATA.

2. The non-invasive continuous detection device for human blood pressure under high pressure as claimed in claim 1, characterized in that: The MCU circuit includes a main control chip of model STM32F413VGT6, PC14 pin and PC15 pin of the main control chip U1 are connected to the high-speed crystal oscillator circuit, VCAP_1 pin of the main control chip U1 is grounded through capacitor C12, VCAP_2 pin is grounded through capacitor C14, OSC_IN pin and OSC_OUT pin of the main control chip U1 are connected to the low-speed crystal oscillator circuit, PA13 pin and PA14 pin of the main control chip U1 are connected to the burning port for program burning, PD3 pin of the main control chip U1 is electrically connected to pin 3 of the status indicator chip through resistor R2, PD4 pin is electrically connected to pin 2 of the status indicator chip through resistor R3, PD5 pin is electrically connected to pin 1 of the status indicator chip through resistor R4, pin 4 of the status indicator chip is grounded, PB2 pin of the main control chip U1 is grounded through resistor R1, N The RST pin is connected to the reset circuit, and the reset circuit is grounded through the decoupling capacitor C3. The BOOT0 pin of the main control chip U1 is grounded through the resistor R6. The VBAT pin of the main control chip U1 is grounded through the decoupling capacitor C4, the VDD_1 pin is grounded through the decoupling capacitor C5, the VDD_2 pin is grounded through the decoupling capacitor C6, the VDD_3 pin is grounded through the decoupling capacitor C7, the VDD_4 pin is grounded through the decoupling capacitor C8, and the VDD_5 pin is grounded through the decoupling capacitor C9. The VSS_1 pin, VSS_2 pin, VSS_3 pin, VSS_4 pin and VSS_5 pin of the main control chip U1 are all grounded, the VDD pin of the main control chip U1 is grounded through the decoupling capacitor C10, the VDDA pin is grounded through the resistor R7 and the decoupling capacitor C10, the VREF+ pin is grounded through the resistor R7 and the decoupling capacitor C10, and the VSSA pin is grounded through the resistor R9.

3. The non-invasive continuous detection device for human blood pressure under high pressure as claimed in claim 2, characterized in that: The ECG acquisition front end includes: one end of a resistor R25 is connected to an ECG electrode RA and is also grounded through an electrostatic diode D6; the other end of the resistor R25 is connected to an ECG simulation front end and is also grounded through a capacitor C32; one end of a resistor R26 is connected to an ECG electrode LL and is also grounded through an electrostatic diode D7; the other end of the resistor R26 is connected to an ECG simulation front end and is also grounded through a capacitor C33; one end of a resistor R31 is connected to an ECG electrode RL and is also grounded through an electrostatic diode D10; the other end of the resistor R31 is connected to an ECG simulation front end; The ECG simulation front end adopts an ECG chip U2 of model WL1298, the IN3N pin of the ECG chip U2 is electrically connected to the other end of the resistor R25, the IN3P pin is electrically connected to the other end of the resistor R26, the five AVDD pins of the ECG chip U2, namely pin 19, pin 21, pin 22, pin 59 and pin 56 are respectively connected to the analog ground through capacitors C54, capacitor C55, capacitor C56, capacitor C57 and capacitor C58, the five AVSS pins of the ECG chip U2, namely pin 20, pin 23, pin 32, pin 58 and pin 57 are connected to the analog ground, the VREFP pin of the ECG chip U2 is electrically connected to the VREF+ pin of the main control chip U1, and is used to access the VREFP reference voltage, the VREFN pin of the ECG chip U2 is connected to the analog ground, the VREFP pin and the VREFN pin of the ECG chip U2 are connected with capacitors C60 and C61 in parallel, and the VCAP4 pin of the ECG chip U2 is connected to the analog ground through capacitor C62. The analog ground, the VCAP1 pin is connected to the analog ground through the capacitor C63, the VCAP2 pin is connected to the analog ground through the capacitor C64, the RESV1 pin of the ECG chip U2 is grounded through the resistor R59, the WCT pin of the ECG chip U2 is connected to the analog ground through the capacitor C44, the RLDOUT pin of the ECG chip U2 is electrically connected to the other end of the resistor R31, and the capacitor C47 and the resistor R42 are connected in parallel between the RLDOUT pin and the RLDINV pin. The VCAP3 pin of the ECG chip U2 is connected to the analog ground through the capacitor C53, the AVDD1 pin of the ECG chip U2 is connected to the analog ground through the resistor R45 and the capacitor C59, the AVSS1 pin is connected to the analog ground through the resistor R46, and the CLKSEL pin is grounded through the resistor R47. The three DGND pins of the ECG chip U2, namely the pin 51, the pin 49 and the pin 33 are grounded, and the two DVDD pins, namely the pin 50 and the pin 48 are grounded through the capacitor C50 and the capacitor C51 respectively. The DOUT pin of the ECG chip U2 is electrically connected to the PD14 pin of the main control chip U1 through the resistor R52, and the SCLK pin of the ECG chip U2 is electrically connected to the PD13 pin of the main control chip U1 through the resistor R54. The START pin of the ECG chip U2 is electrically connected to the PD8 pin of the main control chip U1 through a resistor R56. The pin is electrically connected to the PD9 pin of the main control chip U1 through a resistor R57, and the DIN pin is electrically connected to the PB14 pin of the main control chip U1 through a resistor R60.

4. The non-invasive continuous detection device for human blood pressure under high pressure as claimed in claim 2, characterized in that: The pulse wave analog front end includes an integrated analog front end U3 of model TS9517, the OUT pin of the integrated analog front end U3 is electrically connected to the PC15 pin of the main control chip U1, the CS pin is electrically connected to the PC4 pin of the main control chip U1, the SDI pin is electrically connected to the PA6 pin of the main control chip U1, the CLK pin is electrically connected to the PE9 pin of the main control chip U1, the GND pin of the integrated analog front end U3 is grounded, the COE pin is grounded through a resistor R63, the CAP pin is grounded through a capacitor C67, and the PROG pin is grounded through a resistor R 62 is grounded, the IR pin of the integrated analog front end U3 is connected to the infrared light emitting end of the photoelectric sensor, the RED pin is connected to the red light emitting end of the photoelectric sensor, the IN pin is connected to the infrared light receiving end of the photoelectric sensor, and the ANOD pin is connected to the red light receiving end of the photoelectric sensor. The VDD pin of the integrated analog front end U3 is connected to the voltage of 3V and is also grounded through the capacitor C66 and the resistor R61. The PVDD pin of the integrated analog front end U3 is connected to the voltage of 3V and is also grounded through the capacitor C65 and the resistor R61. The GND pin of the integrated analog front end U3 is grounded through the resistor R61.

5. The non-invasive continuous detection device for human blood pressure under high pressure as claimed in claim 1, characterized in that: The power supply circuit is used to convert the battery voltage into 3.3V voltage and 3V voltage when the switch is turned on. The 3.3V voltage is used to power the ECG acquisition front end, ECG simulation front end, MCU circuit and power supply circuit, and the 3V voltage is used to power the pulse wave simulation front end.

6. The non-invasive continuous detection device for human blood pressure under high pressure as claimed in claim 1, characterized in that: A first mounting seat is fixed on the front of the vest body, an integrated box is installed on the first mounting seat, and a battery box is fixed on the front of the vest body.

7. The non-invasive continuous detection device for human blood pressure under high pressure as claimed in claim 6, characterized in that: A first mounting seat with a first buckle is fixed on the front side of the vest body, and a first push-type clip is embedded in the top of the integrated box. When the first push-type clip is pressed, the first push-type clip moves downward along the outer wall of the first buckle and clamps the first buckle in the first push-type clip, thereby installing the integrated box on the first mounting seat.

8. The non-invasive continuous detection device for human blood pressure under high pressure as claimed in claim 1, characterized in that: A second mounting seat is fixed on the surface of the sleeve portion of the vest body, and a blood pressure cuff is mounted on the second mounting seat.

9. The non-invasive continuous detection device for human blood pressure under high pressure as claimed in claim 8, characterized in that: A second mounting seat with a second buckle is fixed to the surface of the sleeve portion of the vest body, and a second push-type clip is embedded in the top of the blood pressure cuff. When the second push-type clip is pressed, the second push-type clip moves downward along the outer wall of the second buckle and clamps the second buckle in the second push-type clip, thereby installing the blood pressure cuff on the second mounting seat.

10. A method for non-invasive continuous detection of human blood pressure under high pressure, characterized in that: The method is implemented by using the non-invasive continuous detection device for human blood pressure under high pressure according to any one of claims 1 to 9, and the method comprises the following steps: Step 1: Press the switch, and the power circuit converts the battery voltage into the power supply voltage required by the ECG acquisition front end, ECG simulation front end, pulse wave simulation front end, MCU circuit and power circuit; Step 2: The ECG acquisition front end collects the RA ECG signal and the LL ECG signal of the person to be tested in the pressurized chamber at a shallow depth through the ECG electrode RA and the ECG electrode LL respectively, and transmits the ECG signals to the MCU circuit after amplifying the ECG signals through the ECG simulation front end, the pulse wave simulation front end synchronously collects the pulse wave signal of the person to be tested in the pressurized chamber at a shallow depth through the photoelectric sensor and transmits it to the MCU circuit, and the blood pressure cuff synchronously collects the blood pressure signal of the person to be tested in the pressurized chamber at a shallow depth and transmits it to the MCU circuit; Step 3: The MCU circuit uploads the RA ECG signal, LL ECG signal, pulse wave signal and blood pressure signal of the subject to be tested at a shallow depth to the host computer; Step 4: the host computer subtracts the potential value of the RA ECG signal from the potential value of the LL ECG signal at the shallow depth to obtain a two-lead ECG at the shallow depth, and then analyzes the time difference between the peak value of the pulse wave at the shallow depth and the nearest R wave peak value in the two-lead ECG as the pulse wave conduction time PWTT at the shallow depth. The PWTT at the shallow depth corresponds to a blood pressure value BP in the blood pressure signal at the shallow depth, thereby analyzing multiple groups of corresponding pulse wave conduction times PWTT and blood pressure values ​​BP at the shallow depth, and substituting the values ​​of the multiple groups of PWTT and BP into the target formula to obtain the values ​​of variables a and b; Among them, the target formula BP = a × PWTT + b, a < 0; Step 5: The ECG acquisition front end collects the RA ECG signal and the LL ECG signal of the person to be detected in the pressurized cabin at a great depth through the ECG electrode RA and the ECG electrode LL respectively, and transmits the ECG signals to the MCU circuit after amplifying the ECG signals through the ECG simulation front end, and the pulse wave simulation front end synchronously collects the pulse wave signal of the person to be detected in the pressurized cabin at a great depth through the photoelectric sensor and transmits it to the MCU circuit; Step 6: The MCU circuit uploads the RA ECG signal, LL ECG signal and pulse wave signal of the person to be tested at a great depth to the host computer; Step 7: The host computer subtracts the potential value of the RA electrocardiogram from the potential value of the LL electrocardiogram at a great depth to obtain a two-lead electrocardiogram at a great depth, and then analyzes the time difference between the peak value of the pulse wave at a great depth and the nearest R wave peak value in the two-lead electrocardiogram as the pulse wave conduction time PWTT at a great depth, and substitutes the PWTT value into the target formula to calculate the blood pressure value at a great depth as the true blood pressure value of the subject to be tested at a great depth; Shallow depth refers to the underwater depth corresponding to the pressure in the pressurized cabin not exceeding 7ATA, and deep depth refers to the underwater depth corresponding to the pressure in the pressurized cabin exceeding 7ATA.

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