CN105852832B - Blood pressure real-time measuring device and method for measuring average blood pressure - Google Patents

Abstract

The invention relates to a blood pressure real-time measuring device, which is characterized in that it comprises: a pulse wave sensing module at the first position, including a first pulse wave sensing module at the first position and a second pulse wave sensing module at the first position Module; a pulse wave sensing module at a second position, including a first pulse wave sensing module at a second position and a second pulse wave sensing module at a second position; and a signal processing module for calculating the first position The first transmission signal difference Δt _A between the first pulse wave signal A ₁ and the second pulse wave signal A ₂ at the position, and the difference Δt A between the first pulse wave signal B ₁ and the second pulse wave signal B ₂ at the second position The second transmission signal difference Δt _B , and the mean arterial blood pressure MBP of each cardiac cycle is obtained according to the difference Δt between the first transmission signal difference Δt _A and the second transmission signal difference Δt _B . The present invention further relates to a method for measuring average blood pressure.

Description

Blood pressure real-time measuring device and method for measuring average blood pressure

technical field

The invention relates to a blood pressure measuring device and an average blood pressure measuring method, in particular to a blood pressure noninvasive, continuous and real-time measuring device and a measuring method.

Background technique

Cardiovascular disease is currently the leading cause of death in both developed and developing countries. Hypertension is one of the most important risk factors for cardiovascular and cerebrovascular diseases. 50% to 70% of strokes and 40% to 50% of myocardial infarctions are related to elevated blood pressure. Blood pressure monitoring plays an important role in the prevention, early detection and treatment of cardiovascular and cerebrovascular diseases. Therefore, realizing non-invasive and continuous measurement of blood pressure is of great significance for health monitoring and clinical research.

The traditional measurement of blood pressure based on Pulse Transit Time (PTT) is a relatively common non-invasive continuous blood pressure measurement method, which is widely used in wearable devices for blood pressure measurement. The core idea is to obtain PTT based on the electrocardiogram (ECG) and the pulse wave at the distal end of the artery, and there is a strong correlation between PTT and blood pressure, so the blood pressure value can be calculated based on the measured PTT. However, the blood pressure measurement method based on PTT needs to measure the ECG signal and the pulse wave signal simultaneously. However, ECG signals need to fix electrodes in multiple parts of the human body, and multiple electrode leads are required, which makes measurement inconvenient. Moreover, the electrocardiographic electrode cannot ensure good contact with the skin after being used for a period of time, and is not suitable for continuous monitoring of blood pressure for a long time (such as 24 hours/7 days).

The phase difference of pulse wave (Phase Difference of Pulse Waves, PDPW) is a concept newly proposed in recent years, which refers to two different types of pulse waves (such as pressure pulse wave and volume pulse wave), due to the difference in propagation velocity, The phase difference formed from the same location where the ventricles start to propagate to the arteries. It is specifically reflected in the time difference between the two pulse wave feature points. The time difference of the pulse wave contains rich information, which itself can be used for non-invasive blood pressure measurement.

In the prior art, the phase difference is measured at a single position. However, since the measurement process is very sensitive to the position of the sensor, a small change in the position of the sensor during the two measurements requires re-calibration, which is cumbersome and leads to errors. The accuracy of blood pressure calculation needs to be improved.

Contents of the invention

In view of this, it is necessary to provide a non-invasive, continuous, real-time and accurate blood pressure measurement device and measurement method.

A blood pressure real-time measurement device, characterized in that it includes: a pulse wave sensing module at a first position, including a first pulse wave sensing module at the first position and a second pulse wave sensing module at the first position, and Sensing different types of pulse wave signals at the first position; a pulse wave sensing module at the second position, including a first pulse wave sensing module at the second position and a second pulse wave sensing module at the second position to sense Different types of pulse wave signals at the second position; and a signal processing module for the first pulse wave signal A ₁ induced by the first pulse wave sensing module at the first position, the second pulse wave sensing module at the first position The induced second pulse wave signal A ₂ , the first pulse wave signal B ₁ induced by the second pulse wave sensing module at the second position, and the second pulse wave signal B ₂ induced by the second pulse wave sensing module at the second position processing, and calculate the first transmission signal difference Δt A between the first pulse wave signal A ₁ and the second pulse wave signal A ₂ , and the first transmission signal difference Δt _A between the first pulse wave signal B ₁ and the second pulse wave signal B ₂ Two transmission signal differences Δt _B , and the mean arterial blood pressure MBP of each cardiac cycle is obtained according to the difference Δt between the first transmission signal difference Δt _A and the second transmission signal difference Δt _B .

The pulse wave sensing module at the first position and the pulse wave sensing module at the second position are two identical modules, which are respectively arranged at different sensing positions to obtain the pulse wave signal of each cardiac cycle at different positions .

The different types of pulse wave signals are selected from pressure pulse waves, photoplethysmography pulse waves or blood velocity pulse waves.

The first pulse wave signal A1 at the _first position is the same type of pulse wave signal as the _first pulse wave signal B1 at the second position, and the second pulse wave signal A2 at the first position is the same as that at the _second position The _second pulse wave signal B2 is the same type of pulse wave signal.

The pulse wave sensing module at the first position further includes a first digital-to-analog conversion module for filtering the first pulse wave signal A1 at the _first position and the _second pulse wave signal A2 at the first position, Signal amplification and analog-to-digital conversion, and the converted signal is transmitted to the signal processing module; the pulse wave induction module at the second position further includes a second digital-to-analog conversion module, which is used for the second position at the second The _first pulse wave signal B1 and the second pulse wave signal B2 at the _second location are filtered, signal amplified, and analog-to-digital converted, and the converted signal is transmitted to the signal processing module.

The relationship between the difference Δt between the first transmission signal difference Δt _A and the second transmission signal difference Δt _B and the average blood pressure MBP is:

Among them, k and c are two calibration parameters.

A method for measuring blood pressure using the real-time blood pressure measuring device as described above, comprising the following steps:

S1, acquiring the _first pulse wave signal A1 and the _second pulse wave signal A2 at the first position of the human body;

S2, acquiring the _first pulse wave signal B1 and the second pulse wave signal B2 at the _second position of the human body;

S3, calculating the transit time difference Δt _A between the _first pulse wave signal A1 and the _second pulse wave signal A2;

S4, calculating the transit time difference Δt _B between the _first pulse wave signal B1 and the _second pulse wave signal B2;

S5, acquiring the difference Δt between the transmission time difference Δt _A and the transmission time difference Δt _B ; and

S6. Calculate the average blood pressure value according to the difference Δt between the transit time difference Δt _A and the transit time difference Δt _B.

Compared with the prior art, the blood pressure real-time measurement device and measurement method provided by the present invention calculate the average blood pressure by collecting pulse wave phase difference information at two positions of the human body, which has the following beneficial effects: two different positions are extracted from two different positions. pulse wave phase difference information, and calculate the average blood pressure based on the difference, which eliminates the interference caused by a small change in the sensor at a certain position, and simplifies the operation a lot; Select a reasonable collection point according to the specific situation.

Description of drawings

Fig. 1 is a functional block diagram of a real-time blood pressure measurement device provided by an embodiment of the present invention.

Fig. 2 is a functional block diagram of a device for acquiring two pulse waves at a first position provided by an embodiment of the present invention.

Fig. 3 is a functional block diagram of a device for acquiring two pulse waves at a second position provided by an embodiment of the present invention.

Fig. 4 is a flowchart of a method for real-time blood pressure measurement provided by an embodiment of the present invention.

Fig. 5 is the waveform and phase difference of different pulse waves obtained from the measurement of the first position of the human body provided by the embodiment of the present invention.

Fig. 6 is the waveform and phase difference of different pulse waves obtained from the measurement of the second position of the human body provided by the embodiment of the present invention.

Description of main component symbols

Blood pressure real-time measurement device 10

Pulse wave sensing module at the first position 12

Pulse wave sensing module at the second position 14

Signal Processing Modules 16

The first pulse wave sensing module 122 at the first position

The second pulse wave sensing module 124 at the first position

The first analog-to-digital conversion module 126

The first pulse wave sensing module 142 at the second position

second pulse wave sensing module 144 at the second position

The second analog-to-digital conversion module 146

The following specific embodiments will further illustrate the present invention in conjunction with the above-mentioned drawings.

Detailed ways

The blood pressure real-time measurement device provided by the embodiment of the present invention will be described in detail below with reference to the accompanying drawings.

Please refer to Fig. 1 to Fig. 3 together, the embodiment of the present invention provides a blood pressure real-time measurement device 10, the blood pressure real-time measurement device 10 includes a pulse wave sensing module 12 at the first position, and a pulse wave sensing module 12 at the second position 14 and a signal processing module 16.

The pulse wave sensing module 12 at the first position and the pulse wave sensing module 14 at the second position are two identical modules, which can be respectively arranged in different positions of the human body, and are used to obtain each pulse wave at different positions of the human body. pulse wave signals of one cardiac cycle, for example, two pulse wave signals of each cardiac cycle at the first position and the second position. The pulse wave sensing module 12 at the first position includes a first pulse wave sensing module 122 at the first position, a second pulse wave sensing module 124 at the first position, and a first analog-to-digital conversion module 126 . The pulse wave sensing module 14 at the second position includes a first pulse wave sensing module 142 at the second position, a second pulse wave sensing module 144 at the second position, and a second analog-to-digital conversion module 146 .

The position of the pulse wave sensing module needs to be close to the epidermis or rich in capillaries, which are easy to detect, including but not limited to radial fingertips, arteries, carotid arteries, earlobes, or dorsalis pedis arteries. The sensing positions of the pulse wave sensing module 12 at the first position and the pulse wave sensing module 14 at the second position are different. The first location selected in the first embodiment of the present invention is the radial artery of the left arm, and the second location is the fingertip of the left arm.

The first pulse wave sensing module 122 at the first position is used to acquire the first pulse wave signal A ₁ at the first position of the human body in each cardiac cycle, and the first pulse wave sensing module 142 at the second position is used to acquire The first pulse wave signal B ₁ at the second position of each cardiac cycle; the second pulse wave sensing module 124 at the first position is used to obtain the second pulse wave signal A ₂ at the first position of each cardiac cycle, The second pulse wave sensing module 144 at the second position is used to acquire the second pulse wave signal B ₂ at the second position of each cardiac cycle. The pulse wave types induced by the first pulse wave sensing module 122 at the first position and the second pulse wave sensing module 124 at the first position are different, so as to measure different types of pulse waves; similarly, the first pulse wave at the second position The types of pulse waves sensed by the wave sensing module 142 and the second pulse wave sensing module 144 at the second position are also different, so as to measure different types of pulse waves. The first pulse wave signal A1 at the _first position and the _first pulse wave signal B1 at the second position may be the same type of pulse wave signal, and the second pulse wave signal A2 at the first position is the same as the _second pulse wave signal B1 at the second position. The _second pulse wave signal B2 at the location may be the same type of pulse wave signal.

The type of pulse wave may include pressure pulse wave, photoplethysmography pulse wave or blood flow velocity pulse wave. Correspondingly, the first pulse wave sensing module 122 at the first position, the first pulse wave sensing module 142 at the second position, the second pulse wave sensing module 124 at the first position, and the second pulse wave sensing module 142 at the second position The modules 144 can be one of the pressure pulse wave sensing module, the photoplethysmography pulse wave sensing module and the blood flow velocity pulse wave sensing module, as long as the first pulse wave sensing module 122 at the first position and the second pulse wave sensing module at the first position are ensured. The pulse wave sensing module 124 selects sensors with different pulse wave sensing types, and the pulse wave sensing types selected by the first pulse wave sensing module 142 at the second position and the second pulse wave sensing module 144 at the second position are different from each other sensor.

The pressure pulse wave sensing module is used for sensing the pressure pulse wave of each cardiac cycle. The pressure pulse wave sensing module can be realized by a pressure sensor. The pressure sensor includes at least one of a piezoelectric film sensor and a silicon-based piezoresistive sensor. The signal sensed by the pressure sensor can be converted into an electrical signal and transmitted to the first analog-to-digital conversion module 126 and the second analog-to-digital conversion module 146 , and converted into a digital signal to be transmitted to the signal processing module 16 .

The photoplethysmography sensing module is used for sensing the photoplethysmography of each cardiac cycle. The photoplethysmography sensing module can convert the light intensity received by the photodetector into an electrical signal through the pulsating change of the volume of blood in the artery at the sensing position of the cardiac cycle to obtain the optical signal obtained by the photodetector. Photoplethysmography. The photoplethysmography sensing module may include a photoelectric tube and a photodetector. The photoelectric cell may be a light emitting diode. The photodetector can be a transmissive photodetector or a reflective photodetector, which can be determined according to the selected measurement position. Preferably, a reflective photodetector is used to detect the light signal reflected by the artery. The operating wavelength range of the photoelectric tube and the photodetector may be the infrared light range of 600nm to 1000nm. Preferably, the working wavelength range of the photoelectric tube and photodetector is 800nm to 960nm.

The blood flow velocity pulse wave sensing module is used for sensing the blood flow velocity pulse wave of each cardiac cycle. The blood flow velocity pulse wave sensing module may be a magnetic sensing blood flow velocity pulse wave sensing module or other sensors capable of measuring the blood flow velocity pulse wave in each cardiac cycle. Preferably, the blood flow velocity pulse wave sensing module adopts a magnetic sensing blood flow velocity pulse wave sensing module. The magnetic sensing blood flow velocity pulse wave sensing module may include a bias magnetic sheet and a magnetic sensor. The bias magnetic sheet is arranged at the position of the artery to generate a bias magnetic field, and the magnetic sensor senses the signal of the change of the magnetic field at the sensing position caused by the change of the blood flow velocity in each cardiac cycle. The sensing signal is converted into an electrical signal and transmitted to the first analog-to-digital conversion module 126 and the second analog-to-digital conversion module 146 , and converted into a digital signal to be transmitted to the signal processing module 16 . The magnetic sensor may be a giant magnetoresistance sensor, a tunnel magnetoresistance sensor or a Hall magnetic sensor.

In the first embodiment of the present invention, the first pulse wave sensing module 122 at the first position and the first pulse wave sensing module 142 at the second position are pressure pulse wave sensing modules; the second pulse wave sensing module at the first position Module 124, the second pulse wave sensing module 144 at the second position is a photoplethysmography sensing module.

In the second embodiment of the present invention, the first pulse wave sensing module 122 at the first position and the first pulse wave sensing module 142 at the second position are blood flow velocity pulse wave sensing modules, and the second pulse wave sensing module at the first position The wave sensing module 124 and the second pulse wave sensing module 144 at the second position are photoplethysmography sensing modules.

In the third embodiment of the present invention, the first pulse wave sensing module 122 at the first position and the first pulse wave sensing module 142 at the second position are pressure pulse wave sensing modules, and the second pulse wave sensing module at the first position Module 124, the second pulse wave sensing module 144 at the second position is a blood flow velocity pulse wave sensing module.

The first analog-to-digital conversion module 126 and the second analog-to-digital conversion module 146 may further include a filtering and signal amplification module, which is used to filter and amplify the received first pulse wave signal and second pulse wave signal , and then perform analog-to-digital conversion. The filtering and signal amplifying module can be realized by using a filtering circuit and a signal amplifier. Further, the first analog-to-digital conversion module 126 and the second analog-to-digital conversion module 146 can be integrated into the signal processing module 16 .

The signal processing module 16 receives the four pulse wave signals A ₁ , A ₂ , B ₁ , B ₂ transmitted by the pulse wave sensing module 12 at the first position and the pulse wave sensing module 14 at the second position, And the first transmission time difference Δt _A between the first pulse wave signal A ₁ received at the first position and the second pulse wave signal A ₂ can be obtained, and the first pulse wave signal B received at the second position ₁ and the second transit time difference Δt _B between the second pulse wave signal B ₂ , and then obtain the average arterial blood pressure of each cardiac cycle according to the transit time difference Δt between the first position and the second position at two different sensing positions , where Δt=|Δt _A -Δt _B |. Further, the transit time difference Δt _A between the _first pulse wave signal A1 and the _second pulse wave signal A2 can be determined by the phase difference ΔP _A between the _first pulse wave signal A1 and the second pulse wave signal _A2 Obtain; similarly, the transit time difference Δt _B between the first pulse wave signal B ₁ and the second pulse wave signal B ₂ can be obtained by the phase between the first pulse wave signal B ₁ and the second pulse wave signal B ₂ The difference ΔP _B is obtained. Then the difference Δt of the transmission time difference between two different sensing positions at the first position and the second position can be obtained by the difference PDD between the phase difference ΔP _A at the first position and the phase difference ΔP _B at the second position, wherein PDD = |ΔP _A -ΔP _B |.

When the signal processing module 16 calculates the phase difference ΔP _A and ΔP _B of the two pulse wave signals from the same position, that is, the first position or the second position, the first peak points of the two pulse waves can be used, such as Shown in Figure 5 and Figure 6.

When the signal processing module 16 calculates the difference Δt of the transit time difference between two different sensing locations, ie, the first location and the second location, it only needs to directly subtract the transit time differences between the two different sensing locations.

The mean arterial blood pressure of each cardiac cycle is inversely proportional to the difference Δt of the pulse wave transit time difference at different sensing positions, that is, is inversely proportional to the difference PDD of the pulse wave phase difference at different sensing positions.

The relationship between the difference Δt of the pulse wave transit time difference at different sensing positions and the average blood pressure in the embodiment of the present invention is:

Among them, MBP is the mean blood pressure. k and c are two calibration parameters, which can be obtained through the calibration module.

At the same time, due to the corresponding relationship between Δt and PDD, the relationship between the phase difference PDD of the pulse wave at different sensing positions and the average blood pressure satisfies:

The signal processing module 16 may further include a calibration module, which is used to determine the calibration parameters k and c. The calibration module can execute a calibration program, the calibration program includes:

Use standard blood pressure measurement methods to measure standard systolic blood pressure ( _PS ) and standard diastolic blood pressure ( _PD ) to obtain multiple sets of standard data;

And record the difference PDD between the phase difference ΔP _A at the first position and the phase difference ΔP _B at the second position measured at the same time;

The systolic blood pressure (P _S ) and diastolic blood pressure (P _D ) obtained by the calibration are used to calculate the average blood pressure using an empirical formula, and the empirical formula is:

The average blood pressure MBP calculated by calibration was fitted with the corresponding measured PDD to calculate the parameters k and c.

The standard blood pressure measurement method can be obtained by using a standard mercury sphygmomanometer. The calibration process is simple and convenient to operate and can improve the accuracy of blood pressure measurement. In this embodiment, 5 sets of standard data are used. It can be understood that the calibration procedure is only a specific example, and k and c can also be obtained through other existing calibration methods.

The real-time blood pressure measurement device 10 may further include a display module to display the measured blood pressure or blood pressure curve in real time.

The blood pressure real-time measurement device 10 may further include a transmission module for transmitting the measured real-time blood pressure value to an intelligent terminal for further analysis and monitoring.

Preferably, the transmission module can be a wireless transmission module. The transmission mode adopted by the wireless transmission module may be at least one of Bluetooth transmission, infrared transmission and radio frequency transmission. The smart terminal can be a monitoring device used for real-time monitoring of measured blood pressure values. In addition, the intelligent terminal may also receive the pulse wave transit time difference through the transmission module, and calculate the average arterial blood pressure of each cardiac cycle through the intelligent terminal.

Taking the pulse wave sensing module 12 at the first position as an example, the first pulse wave sensing module 122 at the first position, the second pulse wave sensing module 124 at the first position and the first analog-to-digital conversion module can be 126 is integrated on a printed circuit board. The printed circuit board is preferably a flexible printed circuit board, so that the blood pressure real-time measurement device 10 can be a flexible device. Similarly, the pulse wave sensing module 14 at the second position can also be integrated.

The pulse wave sensing module 12 at the first position and the pulse wave sensing module 14 at the second position may respectively include a body, the first pulse wave sensing module 122 at the first position and the first pulse wave sensing module 122 at the second position The pulse wave sensing module 142, the second pulse wave sensing module 124 at the first position, the second pulse wave sensing module 144 at the second position, the first analog-to-digital conversion module 126, and the second analog-to-digital conversion module 146 are packaged therein. Preferably, the body can easily fix the blood pressure real-time measurement device 10 at the position of the artery. Preferably, the body may be a wearable structure. In addition, the body can also be a patch structure, which is used to stick the body device on the surface of the skin near the artery.

The signal processing module 16, the transmission module and even the display module can also be integrated. Preferably, the signal processing module 16, the transmission module and even the display module can be integrated into the pulse wave sensing module 12 at the first position or the pulse wave sensing module 14 at the second position.

Please refer to FIG. 4 , an embodiment of the present invention further provides a method for real-time blood pressure measurement using the above-mentioned real-time blood pressure measurement device 10, including the following steps:

S1, acquiring the _first pulse wave signal A1 and the _second pulse wave signal A2 at the first position of the human body;

S2, acquiring the _first pulse wave signal B1 and the second pulse wave signal B2 at the _second position of the human body;

S3, calculating the transit time difference Δt _A between the _first pulse wave signal A1 and the _second pulse wave signal A2;

S4, calculating the transit time difference Δt _B between the _first pulse wave signal B1 and the _second pulse wave signal B2;

S5, acquiring the difference Δt between the transmission time difference Δt _A and the transmission time difference Δt _B ;

S6. Calculate the average blood pressure value according to the difference Δt between the transit time difference Δt _A and the transit time difference Δt _B.

In this method, the transmission time difference and the phase difference are in a corresponding relationship, and the phase difference is the peak time interval of the two signals measured at the same position as the transmission time difference. The acquisition method of the transit time difference and the corresponding relationship between the blood pressure and the transit time difference have been introduced, and will not be repeated here.

Example 1

The blood pressure real-time measurement device 10 includes a pulse wave sensing module 12 at a first position, a pulse wave sensing module 14 at a second position, a signal processing module 16 and a wireless transmission module (not shown). The pulse wave sensing module 12, the signal processing module 16 and the wireless transmission module at the first position are integrated on a flexible circuit board to form a wristband, which is installed on the wrist for real-time measurement of the blood pressure of the wrist radial artery. The pulse wave sensing module 14 at the second position is fixed on the fingertip of the middle finger with medical 3M scotch tape. Wherein, the first pulse wave sensing module 122 at the first position, the first pulse wave sensing module 142 at the second position are pressure pulse wave sensing modules, the second pulse wave sensing module 124 at the first position, and the second pulse wave sensing module 142 at the second position The second pulse wave sensing module 144 is a photoplethysmography sensing module.

Please refer to FIG. 5 . FIG. 5 is a pressure pulse wave signal and a photoplethysmography pulse wave signal measured at the first position. Wherein, in a certain cardiac cycle, the phase difference ΔPA between different pulse waves at the first position is the time interval between the first peaks of the above two pulse waves, and the pulse wave transit time difference Δt _A is obtained _. After testing, Δt _A is 33.75ms.

Please refer to FIG. 6 . FIG. 6 shows the pressure pulse wave signal and the photoplethysmogram signal measured at the second position. Wherein, in a certain cardiac cycle, the phase difference ΔP _B between different types of pulse waves at the second position is the time interval between the first peaks of the above two pulse waves, and the pulse wave transit time difference Δt _B is obtained. After testing, Δt _B is -35.25ms.

The calibration parameters k=0.048, c=79.2277, and the average blood pressure of this cardiac cycle was calculated to be 89.31mmHg.

Example 2

The blood pressure real-time measurement device of this embodiment is basically the same as the blood pressure real-time measurement device of Embodiment 1, the difference is that in this embodiment, the first pulse wave sensing module 122 at the first position and the first pulse wave sensing module 122 at the second position The sensing module 142 is a blood flow velocity pulse wave sensing module, the second pulse wave sensing module 124 at the first position, and the second pulse wave sensing module 144 at the second position are photoplethysmographic sensing modules.

After testing, Δt _A is 42.33ms, Δt _B is 22.15ms, calibration parameters k=0.0116, c=65.3333, and the calculated average blood pressure of this cardiac cycle is 93.8183mmHg.

Example 3

The blood pressure real-time measurement device of this embodiment is basically the same as the blood pressure real-time measurement device of Embodiment 1, the difference is that in this embodiment, the first pulse wave sensing module 122 at the first position and the first pulse wave sensing module 122 at the second position The sensing module 142 is a blood flow velocity pulse wave sensing module, the second pulse wave sensing module 124 at the first position, and the second pulse wave sensing module 144 at the second position are pressure pulse wave sensing modules.

After testing, Δt _A is 12.45ms, Δt _B is 55.27ms, calibration parameters k=0.0514, c=60.25, and the average blood pressure of this cardiac cycle is calculated to be 88.2830mmHg.

The present invention calculates the average blood pressure by collecting pulse wave phase difference information at two positions of the human body, and has the following advantages: firstly, it does not need to collect ECG signals to calculate PTT, and does not require electrodes to contact the body for a long time, and will not generate multiple electrode leads; secondly, Using the difference of pulse wave phase difference, that is, the relationship between the difference of transmission time difference and blood pressure, the sensor is convenient to obtain, and there is no discomfort during the process of human body measurement; moreover, two pulse wave phase difference information is extracted from two different positions, Obtain the pulse wave transit time difference, and calculate the average blood pressure based on the difference, which eliminates the interference caused by the small change of the single position sensor, and greatly simplifies the operation. Select a reasonable collection point for the situation.

In addition, those skilled in the art can also make other changes within the spirit of the present invention. Of course, these changes made according to the spirit of the present invention should be included within the scope of protection claimed by the present invention.

Claims (10)

1. a kind of blood pressure real-time measurement apparatus characterized by comprising

First pulse wave induction module and a first position at pulse wave inductive module, including a first position at one first position Locate the second pulse wave induction module, to incude different types of pulse wave signal at first position；

One second place pulse wave inductive module, including the second place the first pulse wave induction module and a second position Locate the second pulse wave induction module, to incude the different types of pulse wave signal in the second place；And

One signal processing mould group, the first pulse wave signal A for incuding to the first pulse wave induction module at first position₁, The second pulse wave signal A that the second pulse wave induction module incudes at one position₂, the second place the first pulse wave induction module First pulse wave signal B of induction₁And the second pulse wave signal B of the second place the second pulse wave induction module induction₂It carries out Processing, and calculate the first pulse wave signal A₁With the second pulse wave signal A₂Between first transmission signal difference Δ t_AAnd first Pulse wave signal B₁With the second pulse wave signal B₂Between second transmission signal difference Δ t_B, while according to the first transmission signal difference Δt_AWith the second transmission signal difference Δ t_BBetween poor Δ t, obtain the artery mean blood pressure MBP of each cardiac cycle；Wherein, institute Stating the first transmission signal difference is the first pulse wave signal A₁With the second pulse wave signal A₂Between time difference, it is described second transmission Signal difference is the first pulse wave signal B₁With the second pulse wave signal B₂Between time difference.

2. blood pressure real-time measurement apparatus as described in claim 1, which is characterized in that at first position pulse wave inductive module and The second place pulse wave inductive module is two identical mould groups, is respectively arranged at different sensed positions, to obtain The pulse wave signal of each cardiac cycle at different location.

3. blood pressure real-time measurement apparatus as described in claim 1, which is characterized in that the different types of pulse wave signal choosing From pressure pulse wave, photoplethysmographic or blood flow velocity pulse wave.

4. blood pressure real-time measurement apparatus as claimed in claim 3, which is characterized in that the first pulse wave is believed at the first position Number A₁With the second place the first pulse wave signal B₁For the pulse wave signal of same type, the second pulse at the first position Wave signal A₂With the second place the second pulse wave signal B₂For the pulse wave signal of same type.

5. blood pressure real-time measurement apparatus as claimed in claim 3, which is characterized in that pulse wave incudes mould at the first position Group further comprises one first analog-to-digital conversion module, for the first pulse wave signal A at first position₁With at first position Two pulse wave signal A₂It is filtered, signal amplification and analog-to-digital conversion, and the signal after conversion is transferred to signal processing mould group； The second place pulse wave inductive module further comprises one second analog-to-digital conversion module, for the second place first Pulse wave signal B₁With the second place the second pulse wave signal B₂Be filtered, signal amplification and analog-to-digital conversion, and will conversion after Signal be transferred to signal processing mould group.

6. blood pressure real-time measurement apparatus as described in claim 1, which is characterized in that the first transmission signal difference Δ t_AWith Two transmission signal difference Δ t_BBetween poor Δ t and mean blood pressure MBP between relationship are as follows:

Wherein, k and c is two calibration parameters.

7. blood pressure real-time measurement apparatus as claimed in claim 6, which is characterized in that the signal processing mould group further comprises One demarcating module, for the demarcating module for determining that the calibration parameter k and c, the demarcating module include calibrating procedure, this is calibrated Journey are as follows:

Utilize the blood pressure measuring method measurement standard systolic pressure P of standard_SWith standard diastolic pressure P_DObtain multiple groups normal data；

And the phase difference P at record while the first position measured_AWith the phase difference P of the second place_BPoor PDD；

By the resulting systolic pressure P of calibration_SWith diastolic pressure P_DApplication experience formula calculates mean blood pressure, empirical equation are as follows:

The mean blood pressure MBP that calibrated and calculated goes out is fitted with the corresponding PDD measured, calculates parameter k and c.

8. a kind of obtain different sensed position pulse waves using blood pressure real-time measurement apparatus described in claim 1-7 any one The method of the poor Δ t of transmission time difference, comprising the following steps:

S1 obtains the first pulse wave signal A at human body first position₁And the second pulse wave signal A₂；

S2 obtains the first pulse wave signal B of the human body second place₁And the second pulse wave signal B₂；

S3 calculates the first pulse wave signal A₁With the second pulse wave signal A₂Between transmission time difference Δ t_A；

S4 calculates the first pulse wave signal B₁With the second pulse wave signal B₂Between transmission time difference Δ t_B；

S5 obtains transmission time difference Δ t_AWith transmission time difference Δ t_BBetween poor Δ t.

9. the method for obtaining the poor Δ t of different sensed position pulse wave transmission time differences as claimed in claim 8, feature exist In pulse wave inductive module is set at wrist at the first position；The second place pulse wave inductive module setting At finger tip.

10. the method for obtaining the poor Δ t of different sensed position pulse wave transmission time differences as claimed in claim 8, feature It is, the first pulse wave signal A₁With the second pulse wave signal A₂Between transmission time difference Δ t_APass through the first pulse wave Signal A₁With the second pulse wave signal A₂Between phase difference P_AIt obtains；The first pulse wave signal B₁With the second pulse wave Signal B₂Between transmission time difference Δ t_BPass through the first pulse wave signal B₁With the second pulse wave signal B₂Between phase difference P_BIt obtains；The poor Δ t of the transmission time difference of the different sensed positions at the first position and second place two passes through first position The phase difference P at place_AWith the phase difference P of the second place_BPoor PDD obtain, wherein PDD=| Δ P_A-ΔP_B|。