Blood pressure measuring system

Abstract

A blood pressure measuring system comprises a pressure applying device, a first sensing device, a second sensing device and a controller. The pressure applying device is used for applying pressure to limbs of a user; the first sensing device is used for obtaining a pressure signal; the second sensing device is used for obtaining a second target signal; the controller is programmed to execute the steps that the pressure applying device is controlled to progressively apply pressure to the limbs of the user so that the target artery can be blocked; the first sensing device is controlled to at least obtain a plurality of pressure shock wave signals in the pressure applying process; a first target signal is obtained through calculation based on the multiple pressure shock wave signals, and diastolic pressure is obtained based on the first target signal; the second sensing device detects a second target signal in the process of progressively applying pressure to the limbs of the user, and when the second target signal is detected, the pressure applied to the limbs of the user is obtained from the first sensing device; systolic pressure is obtained at least based on pressure applied to the limbs of the user when the second target signal is detected.

Description

Technical Field

[0001] The present invention belongs to the technical field of electronic sphygmomanometers, and in particular, relates to a blood pressure measurement system. Background Art

[0002] Blood pressure is one of the important physiological indicators of the human body and one of the important physiological parameters of the human body that reflects cardiovascular health. Commonly used non-invasive blood pressure measurement devices include: mercury sphygmomanometers using Korotkoff sound auscultation method and electronic sphygmomanometers using oscillometric method. The principles of the above two blood pressure measurement technologies are as follows:

[0003] 1) Korotkoff sound auscultation method uses an inflated cuff to compress the limb arteries. As the cuff pressure decreases, the arteries will gradually open from complete blockage to full opening. The stethoscope is used to identify the sound changes in the process of arterial blood flow from blockage to circulation, and the systolic and diastolic pressures are determined by referring to the corresponding gas pressure in the cuff.

[0004] 2) Oscillometric method principle: Use an inflatable cuff to compress the limb arteries to block arterial blood flow, detect and collect the pressure oscillation waves in the airbag cuff during the pressurization process, or detect the pressure oscillation waves in the cuff during the depressurization process, and calculate the systolic and diastolic blood pressures through the pressure oscillation waves.

[0005] like Figure 1 As shown, Figure 1 It is a schematic diagram of the change of the amplitude of the pulse (pressure oscillation wave signal) with the pressure of the air bag cuff during the pressurization process and the corresponding schematic diagram of the change of the cuff pressure (air bag cuff pressure) with time. During the process of slowly increasing the cuff pressure from 0mmHg, the amplitude of the pulse gradually increases. When the cuff pressure is equal to the mean pressure Pm, the arterial wall is in a deloaded state and the amplitude reaches the maximum; after the cuff pressure is greater than the mean pressure Pm, the amplitude gradually decreases; when the cuff pressure continues to increase to greater than the systolic pressure Ps, the pressure oscillation wave signal obtained is sufficient to calculate the systolic pressure by oscillometric method, and the cuff can be quickly deflated and the pressure can be reduced to end the measurement process. During the process of cuff pressure increase, the recorded pulse oscillation wave amplitude presents an envelope curve that is approximately parabolic. Based on a large number of population statistics, different manufacturers can find out the envelope curves of the systolic pressure Ps and diastolic pressure Pd of different types of blood pressure people and the shape characteristics of the pulse and establish a statistical model. The algorithm related to the statistical model is built into the memory of the electronic sphygmomanometer and applied to the blood pressure measurement process of individual users to calculate the systolic and diastolic pressures.

[0006] like Figure 2 As shown, Figure 2 It is a schematic diagram showing the change of the amplitude of the pulse (pressure oscillation wave signal) with the airbag cuff pressure during the blood pressure reduction process and a schematic diagram showing the change of the corresponding cuff pressure (airbag cuff pressure) with time.

[0007] First, the cuff is inflated quickly. When the cuff pressure is greater than the systolic pressure Ps, the arterial blood flow is blocked, and a small oscillation wave appears in the cuff due to the impact of the proximal pulse. The pressure oscillation wave signal is collected after the cuff starts to slowly reduce the pressure. When the cuff pressure is less than the systolic pressure Ps, the pulse amplitude gradually increases; when the cuff pressure is equal to the mean arterial pressure Pm, the arterial wall is in a deloaded state, and the pulse amplitude reaches the maximum; after the cuff pressure is less than the mean arterial pressure, the pulse amplitude gradually decreases; after the cuff slowly reduces the pressure until the cuff pressure is less than the diastolic pressure Pd, the oscillation wave signal is no longer collected, and the cuff can be quickly deflated to end the measurement. During the slow decrease of the cuff pressure, the pressure oscillation wave amplitude of the collected pulse presents an envelope curve that is approximately parabolic. Based on a large number of population statistics, different manufacturers can find out the envelope curves of the systolic blood pressure Ps and diastolic blood pressure Pd and the shape characteristics of the pulse of people with different types of blood pressure and establish a statistical model. The algorithm related to the statistical model is built into the memory of the electronic blood pressure monitor and used in the blood pressure measurement process of individual users to calculate the systolic and diastolic blood pressure.

[0008] The above blood pressure measurement principle has the following disadvantages:

[0009] 1. The Korotkoff sound auscultation method mercury sphygmomanometer is the gold standard for blood pressure measurement, but with the Minamata Convention on Mercury officially taking effect worldwide on August 16, 2017, mercury-containing sphygmomanometers will gradually be phased out.

[0010] In order to ensure the measurement accuracy of systolic and diastolic blood pressure, the cuff's blood pressure reduction speed needs to be controlled at least 5 mmHg per second or per pulse. In order to obtain higher measurement accuracy, the blood pressure reduction speed even needs to be controlled to 2-3 mmHg per second or per pulse. The overall measurement time is long and the comfort level is poor.

[0011] 2. The oscillometric electronic sphygmomanometer uses a large number of population statistics to obtain a unified model. In some special populations, individual adaptability is poor, and the accuracy of blood pressure measurement is lower than that of the Korotkoff sound auscultation method.

[0012] In addition, in the calculation of systolic and diastolic pressures in the pressurized oscillometric method or the depressurized oscillometric method, it is necessary to collect enough pulse signals to draw envelopes to calculate systolic and diastolic pressures, so the pressurization or depressurization speed during the measurement process cannot be too fast. In general, the pressure change rate during the measurement process is limited to 4-6 mmHg per second or per pulse, and the maximum pressurization height will be about 20-30 mmHg higher than the systolic pressure. In addition, the rapid depressurization process during the pressurized measurement process or the rapid pressurization process during the depressurized measurement process will also last for a certain period of time, so the overall measurement time of the oscillometric electronic sphygmomanometer is relatively long. Taking the measurement process of a user with a systolic blood pressure of 130 mmHg as an example, the entire measurement process needs to last for more than about 30 seconds. The higher the user's blood pressure, the higher the required pressurization height and the longer the measurement time. When the user's systolic blood pressure reaches 200 mmHg, the entire measurement time is nearly 1 minute, the user's arm is under pressure for a long time, and the comfort is poor.

[0013] 3. Some products simply combine the oscillometric pressure measurement process and the pressure relief measurement process to improve measurement accuracy. However, since the oscillometric principle requires that the measurement process covers sufficient pulse signals in the full pressure range from systolic pressure to diastolic pressure, the pressure increase and pressure relief measurement processes are combined, and the user's arm is compressed for too long, resulting in poor comfort. Summary of the invention

[0014] The present disclosure aims to provide a blood pressure measurement system that can improve measurement accuracy.

[0015] In a first aspect, a blood pressure measurement system is provided, comprising a pressure-applying device, a first sensor device, a second sensor device and a controller; the pressure-applying device is used to apply pressure to a user's limb; the first sensor device is used to obtain a pressure signal; the second sensor device is used to obtain a second target signal; the controller is programmed to perform: controlling the pressure-applying device to apply pressure to the user's limb incrementally so that a target artery is blocked; controlling the first sensor device to at least obtain a plurality of pressure oscillation wave signals generated by the pulsation of the target artery during the process of applying pressure to the user's limb; calculating and obtaining a first target signal based on the plurality of pressure oscillation wave signals, and obtaining a diastolic pressure based on the first target signal; controlling the pressure-applying device to apply pressure to the user's limb incrementally; controlling the second sensor device to detect a second target signal during the process of incrementally applying pressure to the user's limb, and obtaining the pressure applied to the user's limb from the first sensor device when the second target signal is detected, wherein the second target signal is used to characterize the transition of the state of the target artery in the user's limb from being blocked to being flowing; and obtaining a systolic pressure based at least on the pressure applied to the user's limb when the second target signal is detected.

[0016] In one possible implementation, the controller is programmed to control:

[0017] The pressure applying device, in the process of gradually applying pressure to the user's limb: reduces the pressure at a first average pressure reduction rate and then reduces the pressure at a second average pressure reduction rate;

[0018] The second sensing device detects the second target signal during the process of reducing the pressure: detecting the second target signal during the process of reducing the pressure at the first average pressure reduction rate;

[0019] The second average pressure reduction speed is greater than the first average pressure reduction speed.

[0020] In combination with the above possible implementations, in another possible implementation, the controller is programmed to control the pressure applying device: in response to confirming that the second target signal is detected, switching to reducing the pressure at a second average pressure reduction speed.

[0021] In combination with the above possible implementations, in another possible implementation, the controller is programmed to control the pressure-applying device in the process of incrementally applying pressure to the user's limbs: first applying pressure at a first average pressure speed and then applying pressure at a second average pressure speed; wherein the first average pressure speed is less than the second average pressure speed.

[0022] In combination with the above possible implementation manner, in another possible implementation manner, the controller is programmed to control the second sensor device to detect the third target signal during the process of the pressure applying device applying pressure, and control the pressure applying device:

[0023] The application of pressure is stopped in response to the failure to detect the third target signal, or the application of pressure is stopped in response to the first sensing device detecting that the applied pressure reaches a preset threshold, wherein the preset threshold is set based on the first target signal.

[0024] In combination with the above possible implementation methods, in another possible implementation method, the third target signal is a fluctuation signal obtained from downstream of the artery to which pressure is applied during the process of incrementally applying pressure to the user's limbs, and the fluctuation signal is an air pressure signal, a photoelectric signal, an electromagnetic wave signal, an ultrasonic signal or a piezoelectric signal, and the fluctuation signal reflects changes in blood flow.

[0025] In combination with the above possible implementation methods, in another possible implementation method, the first target signal is a predetermined pressure oscillation wave signal obtained based on multiple pressure oscillation wave signals, and / or the second target signal is: the first fluctuation signal detected in the process of reducing the pressure applied to the user's limbs, the fluctuation signal is an air pressure signal, a photoelectric signal, an electromagnetic wave signal, an ultrasonic signal or a piezoelectric signal, and the fluctuation signal is used to reflect changes in blood flow.

[0026] In combination with the foregoing possible implementation manner, in another possible implementation manner, the first fluctuation signal is the first fluctuation signal of at least two consecutive fluctuation signals detected for the first time.

[0027] In combination with the above possible implementations, in another possible implementation, the controller further calculates the predicted systolic pressure based on the first target signal, and calculates the systolic pressure based on the pressure applied to the user's limb when the second target signal is detected and the predicted systolic pressure.

[0028] In combination with the above possible implementations, in another possible implementation, the process in which the controller calculates the systolic blood pressure based on at least the second target signal includes extracting the pressure applied to the user's limb corresponding to the moment when the second target signal is detected.

[0029] In combination with the above possible implementation manner, in another possible implementation manner, the second sensing device is used to detect a second target signal downstream of the location where the target artery is blocked.

[0030] The blood pressure measurement method provided by the present invention utilizes the oscillometric method to obtain signals and calculate the diastolic pressure during the process of applying pressure to the limbs, and to obtain the systolic pressure by picking up the transition signal of the blood vessels from closed to open during the process of lowering the blood pressure, thereby improving the measurement accuracy of the systolic and diastolic pressures without significantly increasing the measurement time. BRIEF DESCRIPTION OF THE DRAWINGS

[0031] In order to more clearly illustrate the technical solutions of the embodiments of the present disclosure, the drawings required for use in the embodiments of the present disclosure will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present disclosure. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work.

[0032] Figure 1 It is a schematic diagram showing the change of pulse amplitude with air bag cuff pressure when measuring blood pressure using the pressurized oscillometric method and the change of the corresponding cuff pressure with time.

[0033] Figure 2 It is a schematic diagram showing the change of pulse amplitude with air bag cuff pressure when measuring blood pressure by the step-down oscillometric method and the change of the corresponding cuff pressure with time.

[0034] Figure 3 4 is a flow chart of a blood pressure measurement method according to an embodiment of the present disclosure.

[0035] Figure 4 Schematic diagram of the structure of a blood pressure measurement system according to an embodiment of the present disclosure.

[0036] Figure 5 for Figure 4 Another structural schematic diagram of the blood pressure measurement system.

[0037] Figure 6 for Figure 5Detailed structural diagram of the blood pressure measurement system.

[0038] Figure 7 This is a schematic diagram of the change of the pressure in the first airbag cuff over time using a blood pressure measurement method according to an embodiment of the present disclosure.

[0039] Figure 8 This is a schematic diagram of the change of the pressure in the first airbag cuff over time in a blood pressure measurement method using another embodiment of the present disclosure. DETAILED DESCRIPTION

[0040] In order to make the purpose, technical solution and advantages of the embodiments of the present disclosure clearer, the technical solution in the embodiments of the present disclosure will be clearly and completely described below in conjunction with the drawings in the embodiments of the present disclosure. Obviously, the described embodiments are part of the embodiments of the present disclosure, not all of the embodiments. Based on the embodiments in the present disclosure, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present disclosure.

[0041] The features and exemplary embodiments of various aspects of the present disclosure will be described in detail below. In the detailed description below, many specific details are proposed in order to provide a comprehensive understanding of the present disclosure. However, it is obvious to those skilled in the art that the present disclosure can be implemented without the need for some of these specific details. The following description of the embodiments is only to provide a better understanding of the present disclosure by illustrating the examples of the present disclosure. The present disclosure is by no means limited to any specific structure and configuration proposed below, but covers any modification, replacement and improvement of parts, components and connection modes without departing from the spirit of the present disclosure. In the accompanying drawings and the following description, known structures and technologies are not shown in order to avoid unnecessary ambiguity in the present disclosure.

[0042] Furthermore, the described features, structures, or characteristics may be combined in any suitable manner in one or more embodiments.In the following description, numerous specific details are provided to give a full understanding of the embodiments of the present disclosure.

[0043] The present disclosure provides a blood pressure measurement method and system. The blood pressure measurement method includes obtaining diastolic pressure in the process of applying pressure to the user's limbs, and obtaining systolic pressure based on at least a signal obtained in the process of reducing pressure on the user's limbs, which can improve the accuracy of measuring blood pressure. The main process of the method includes: using a pressure-applying device such as an air bag and an air pump to incrementally apply pressure to the user's limbs so that the target artery is blocked; obtaining multiple pressure oscillation wave signals when the target artery pulsates during the process of applying pressure to the user's limbs through a pressure sensor; obtaining a first target signal (such as a pressure oscillation wave signal with the largest pulse amplitude detected during the oscillometric blood pressure measurement process) based on multiple pressure oscillation wave signals, and obtaining diastolic pressure based on the first target signal. Afterwards, gradually reduce the pressure applied to the user's limbs, detect a second target signal in the process of reducing pressure and the pressure applied to the user's limbs when the signal is detected, wherein the second target signal is used to characterize the state transition of the target artery from blocking to flowing, and obtain systolic pressure based on at least the pressure applied to the user's limbs when the signal is detected.

[0044] The above-mentioned measurement method can make full use of the pressure growth characteristics during the process of incremental pressurization of the limbs. For example, the pressure of the air bag cuff increases slowly in the initial stage of pressurization, and more pressure oscillation wave data can be obtained when the pressure is low, thereby obtaining a more ideal envelope of the pressure oscillation wave signal, and obtaining a more accurate diastolic pressure on this basis; in addition, the systolic pressure is obtained based on at least a second target signal that represents the transition of the target artery from blocked to flowing state. Compared with the method of obtaining the average pressure in the traditional oscillometric method and then calculating the systolic pressure using the amplitude coefficient method, it is more suitable for different individuals and the systolic pressure obtained is more accurate.

[0045] refer to Figure 3 , Figure 3 4 is a flow chart of a blood pressure measurement method according to an embodiment of the present disclosure.

[0046] In this embodiment, the blood pressure measurement method includes the following steps:

[0047] S10. Incrementally apply pressure to the user's limbs to occlude the target artery.

[0048] Specifically, an airbag cuff can be used to wrap the user's upper arm, and the airbag cuff can be inflated using an air pump. During the inflation process, the pressure in the airbag cuff is gradually increased at an average pressurization speed V1. The airbag cuff will compress the brachial artery during the gradual expansion process, and the brachial artery can be blocked when the airbag cuff is sufficiently inflated.

[0049] S20. In the process of applying pressure to the user's limbs, at least a plurality of pressure oscillation wave signals generated by the pulsation of the target artery are obtained.

[0050] The pressure in the airbag cuff can be regarded as the pressure applied to the brachial artery. In addition, due to the force exerted by the arterial pulsation on the airbag cuff, a pressure oscillation wave corresponding to the pulse will also be generated in the airbag cuff. The airbag cuff can be connected to a pressure sensor through a pipeline, and in the process of applying pressure to the user's limb, the pressure sensor can read the real-time pressure signal in the airbag cuff during the above process. The static pressure signal and the pressure oscillation wave signal corresponding to the pulse can be separated from the above real-time pressure signal. The static pressure signal refers to a pressure signal that rises or falls smoothly over time when the airbag cuff is inflated or deflated.

[0051] S30. Obtain a first target signal based on the multiple pressure oscillation wave signals, and obtain diastolic pressure based on the first target signal.

[0052] The static pressure signal is a pressure signal that changes slowly over time in the airbag, which can be regarded as the pressure applied to the brachial artery. The pressure oscillation wave signal is a pressure oscillation wave signal that characterizes the pulsation of the brachial artery, and its oscillation wave amplitude has the following variation rule: during the pressurization process, before the airbag cuff pressure reaches the mean arterial pressure Pm, the oscillation wave amplitude gradually increases with the increase of pressure; when the airbag cuff pressure is equal to the mean arterial pressure Pm, the arterial wall is in a deloaded state, and the oscillation wave amplitude reaches the maximum; after the airbag cuff pressure reaches the mean arterial pressure Pm, the oscillation wave amplitude gradually decreases with the increase of pressure. In the process of the gradual increase of the airbag cuff pressure, the amplitudes of multiple pressure oscillation wave signals present an envelope curve that approximates a parabola. The pressure oscillation wave signal with the largest amplitude is the first target signal.

[0053] After obtaining the first target signal, the amplitude of the pressure oscillation wave signal corresponding to the diastolic pressure can be further calculated according to the preset amplitude coefficient. However, the amplitude may not completely match a pressure oscillation wave signal, and the first pressure oscillation wave signal slightly smaller than the amplitude can be selected to infer the diastolic pressure, and the airbag cuff static pressure signal corresponding to the starting point of the pressure oscillation wave signal can be used as the diastolic pressure. In addition, the diastolic pressure can be jointly inferred by two oscillation wave signals with adjacent amplitudes of the pressure oscillation wave signal corresponding to the diastolic pressure, and the proportional relationship between the amplitude corresponding to the diastolic pressure and the amplitude of the two adjacent oscillation wave signals is calculated, and the diastolic pressure value is calculated by interpolating the airbag cuff static pressure values ​​corresponding to the starting points of the two oscillation wave signals using this proportional relationship.

[0054] S40: Apply pressure to the user's limbs in a decreasing manner.

[0055] The air bag cuff can be deflated through a valve that can control the deflation speed to gradually reduce the air pressure in the cuff, so that the pressure on the brachial artery is gradually reduced until the blood in the brachial artery circulates again. Figure 7 As shown, the pressure in the airbag cuff is reduced at a first average pressure reduction speed V11.

[0056] S50, detecting a second target signal during the pressure reduction process and obtaining the pressure applied to the user's limb when the signal is detected, wherein the second target signal is used to represent the state transition of the target artery from occlusion to flow.

[0057] When the pressure on the brachial artery decreases from greater than the systolic pressure to equal to the systolic pressure, the blood in the brachial artery changes from being blocked to being recirculated, and the pulse is regenerated downstream of the blocked part of the artery, and the pressure oscillation wave signal can also be detected downstream. Specifically, the pressure oscillation wave signal can be detected at the artery downstream of the airbag cuff using a small airbag and a pressure sensor or other detection device, and the first pressure oscillation wave signal detected is the second target signal; or Korotkoff sound is detected at the artery of the airbag cuff, and the Korotkoff sound signal is the second target signal.

[0058] S60. Obtain the systolic pressure based at least on the pressure (stereoscopic systolic pressure SYS2) applied to the user's limb when the signal is detected.

[0059] When the blood in the brachial artery circulates again, the intravascular pressure is equal to the pressure of the airbag cuff. By detecting the change in the blood circulation in the brachial artery and the time corresponding to the change, the static pressure of the airbag cuff at that moment can be obtained, which is the systolic pressure.

[0060] The method used by the electronic sphygmomanometer of the auscultatory pulse wave method is similar to the Korotkoff sound auscultatory method. When in use, a sensor for detecting pulse waves needs to be placed at a distance downstream of the blood flow direction of the Korotkoff sound airbag cuff. After the airbag cuff is quickly inflated and pressurized to a height 20-30 mmHg higher than the systolic pressure of the subject, it begins to slowly deflate and reduce the pressure. During the blood pressure measurement process, an obvious pulse oscillation signal will be generated at the moment when the artery is completely compressed and the blood flow is opened. The downstream pulse wave sensor will detect this blood flow change information, and the pressure in the airbag cuff corresponding to this moment is the systolic pressure. After that, the inflated cuff continues to slowly deflate and reduce the pressure, and the pulse wave sensor gradually and stably detects the pulse signal. When the artery is fully opened and the blood flow flows normally, the pressure in the airbag cuff is the diastolic pressure. After the diastolic pressure is detected, the air can be quickly deflated and the pressure can be reduced to end the measurement. However, in the process from the blood flow in the artery to the complete opening of the artery, the change of the pulse signal is not significant, resulting in a large error in the calculation of the diastolic pressure. In addition, when using the quasi-auscultation method to calculate systolic and diastolic blood pressure, in order to ensure measurement accuracy, the pressure relief rate needs to be limited to 5 mmHg per second or per pulse, and even needs to be controlled to 2-3 mmHg per second or per pulse. In addition, the pressure application process means that the arm is compressed for a long time during the entire measurement process, which is uncomfortable.

[0061] In the process of inflating the airbag cuff, the air pump generally outputs pressurized gas at a uniform speed. In the initial stage of inflation, the volume of the airbag cuff increases as the air inside increases, so the pressure inside the airbag cuff increases slowly. At the end of the expansion of the airbag cuff, its volume no longer increases significantly as the air inside increases, so the pressure increases rapidly. Compared with the stage of rapid increase in the pressure of the airbag cuff, the stage of relatively slow pressure growth in the early stage takes longer, so more pressure shock wave signals can be collected at this stage, so that a more ideal pressure shock wave signal and its amplitude envelope curve can be obtained, thereby obtaining a more accurate diastolic pressure. In addition, in the process of venting the airbag cuff to reduce the pressure on the user's limbs, only the second target signal generated when the target artery changes from the blocked state to the flowing state is obtained to obtain the systolic pressure, and the systolic pressure and diastolic pressure can be output after the systolic pressure is obtained. Compared with the systolic pressure obtained by using the mean pressure Pm and the amplitude coefficient obtained by statistical data, the method of obtaining systolic pressure using the quasi-auscultation method disclosed in the present invention is better adaptable to different types of users and has higher accuracy for individuals. The measurement method disclosed in the present invention takes less time than the traditional oscillometric pressure measurement process and the simple superposition of the pressure reduction measurement process, while the latter will cause the user's limbs to be under pressure for too long and the measurement time is poor, resulting in poor comfort.

[0062] If the oscillometric pressure measurement process and the auscultatory pulse wave method's pressure relief measurement process are simply combined to improve measurement accuracy, the entire blood pressure measurement process will take a longer time, and the user's arm will be under pressure for a long time, which can easily cause numbness, swelling, or even pain.

[0063] Compared with the prior art, the embodiments of the present invention have at least one of the following beneficial effects:

[0064] 1. Improved the accuracy of diastolic and systolic blood pressure measurements:

[0065] The present invention adopts a method combining a quasi-auscultation method and an oscillometric method; in the process of applying pressure on the limbs, full use is made of the sufficient pulse signal in the low-pressure segment of the oscillometric method, and only the diastolic pressure is calculated to ensure the measurement accuracy of the diastolic pressure; at the same time, in the process of decompressing the limbs, the principle of the quasi-auscultation pulse wave method is adopted. Compared with the oscillometric principle based on statistics, the quasi-auscultation method fully reflects the state of individual blood flow when it is flushed, has better individual adaptability, and higher accuracy of systolic pressure.

[0066] 2. Reduced non-invasive blood pressure measurement time:

[0067] The method of the present invention can speed up the pressurization speed in the high pressure section; since the systolic pressure does not need to be calculated during the pressurization measurement process, the pressurization speed in the high pressure section can be accelerated to more than 10 mmHg / s, and the pressurization time is shorter;

[0068] The present invention predicts the cuff pressurization height under the condition of unknown systolic blood pressure, so that the maximum pressurization height will only be slightly higher than the systolic blood pressure of the subject, and pressurizes to the required pressurization height according to different blood pressure levels, thereby reducing unnecessary arm compression time;

[0069] During the pressure relief process, the present invention can quickly relieve pressure and complete the measurement after calculating the high pressure. Since the diastolic pressure has been obtained during the pressurization process, there is no need to repeat the calculation during the pressure relief process, so the measurement time can be significantly shortened. Taking the systolic pressure of 130 mmHg and the diastolic pressure of 80 mmHg as an example, compared with the oscillometric method and the stethograph pulse wave method of pressure relief measurement, the pressure needs to be relieved to below 80 mmHg, which reduces the slow pressure relief process of about 50 mmHg, and the pressure relief time is saved by about 10 seconds. For hypertensive patients with a large difference between systolic and diastolic blood pressure, the saved measurement time will be more obvious. For subjects with systolic / diastolic blood pressure of 180 / 80 mmHg, the present invention can save about 20 seconds in the pressure relief process alone.

[0070] 3. Improve the comfort of the entire blood pressure measurement process for the subject:

[0071] Compared with the existing blood pressure measurement principle, the present invention significantly shortens the overall blood pressure measurement time, shortens the limb compression time, and improves comfort. At the same time, it estimates the systolic blood pressure of the subject and predicts the pressurization height to avoid excessive pressure on the limbs, thereby effectively reducing the numbness and swelling of the arm during the measurement process, and even pain, and improving the comfort of blood pressure measurement.

[0072] In some embodiments, in step S10, incrementally applying pressure to the user's limbs to block the target artery specifically includes: first applying pressure at a first average pressure speed V11 and then applying pressure at a second average pressure speed V12. The first average pressure speed V11 is less than the second average pressure speed V12. Figure 8 As shown, Figure 8 The figure is a schematic diagram of the change of the pressure in the airbag cuff over time when the first average pressurization speed V11 and the second average pressurization speed V12 are used to apply pressure to the user's limbs. The second average pressurization speed V12 is greater than the first average pressurization speed V11. During the pressurization process at the first average pressurization speed, the pressure growth in the airbag cuff can be nonlinear (such as the pressure growth curve is in the shape of a parabola); during the pressurization process at the second average pressurization speed, the pressure growth can also be nonlinear (such as the pressure growth curve is in the shape of a parabola); the overall pressure growth curve of the pressurization at the first average pressurization speed and the second average pressurization speed can be two adjacent curves in a parabola, such as the pressure growth curve corresponding to the first average pressurization speed can be a relatively gentle section of the parabola (a section with a slower slope growth), and the pressure growth curve corresponding to the first average pressurization speed can be a relatively steep section of the parabola (a section with a faster slope growth).

[0073] In some optional embodiments, in response to the pressure increasing to a predetermined pressure at the first average pressure speed, the pressure is switched to the second average pressure speed. For example, after the average pressure Pm is calculated based on the first target signal, a pressure threshold for switching the pressure speed is set, and the pressure threshold can be greater than Pm by a predetermined value. When the pressure in the airbag cuff reaches the pressure threshold, the pressure speed is increased.

[0074] Further, in some embodiments, in step S10, a third target signal is also detected during the process of applying pressure to the user's limbs, and the application of pressure is stopped in response to the failure to detect the third target signal. The third target signal is a fluctuation signal during the process of incrementally applying pressure to the user's limbs, and the fluctuation signal represents the change in blood flow in the detected part caused by the pulse, such as a pressure oscillation wave signal of air pressure. When the fluctuation signal is not detected, it means that the target artery has been compressed and blocked, and then the pressure can be stopped and the process of reducing pressure can be started. For example, another second airbag cuff can be used at the downstream of the airbag cuff to cooperate with a pressure sensor to detect the pressure oscillation wave signal of the air pressure. In some optional embodiments, the third target signal can also be a fluctuation signal of other signals, such as a photoelectric signal, an electromagnetic wave signal, an ultrasonic signal or a piezoelectric signal. Specifically, the above-mentioned fluctuation signal can be obtained downstream of the target artery through a photoelectric sensor, an airbag pulse sensor, a radar sensor, a Doppler sensor or a piezoelectric pulse sensor during the process of incrementally applying pressure to the user's limbs.

[0075] In some other embodiments, in step S10, the application of pressure may be stopped in response to reaching a preset pressure threshold, where the preset threshold is set based on the first target signal. Figure 7 and Figure 8 As shown, Figure 7 It is a schematic diagram of the change of the pressure in the airbag cuff over time using the blood pressure measurement method of an embodiment of the present disclosure. The predicted systolic pressure SYS1 is calculated based on the first target signal, and the pressure threshold is set based on the predicted systolic pressure SYS1. When the pressure in the airbag cuff reaches the pressure threshold or thereafter, the pressure can be stopped and the process of reducing the pressure can be started. Specifically, the first target signal is the pressure oscillation wave signal with the largest amplitude value obtained in the process of applying pressure to the limb, and the corresponding oscillometric diastolic pressure DIA is obtained, and then the amplitude coefficient method is used to obtain the predicted systolic pressure SYS1, and then the pressure threshold is set to be slightly higher than the predicted systolic pressure SYS1.

[0076] In some embodiments, in step S40, reducing the pressure applied to the user's limbs specifically includes: reducing the pressure at a first average pressure reduction speed and then reducing the pressure at a second average pressure reduction speed. Among them, the second average pressure reduction speed is greater than the first average pressure reduction speed, which allows the airbag cuff to be deflated quickly and reduce the time the user's limbs are under pressure. Further, in some embodiments, in step S50, a second target signal is detected during the process of reducing the pressure at the first average pressure reduction speed. Further, in some embodiments, in step S50, in response to confirming that the second target signal is detected, switch to reducing the pressure at the second average pressure reduction speed. After the second target signal is detected, the user's systolic blood pressure can be calculated, so once the second target signal is detected, the airbag cuff can be quickly deflated at the second average pressure reduction speed to remove pressure from the user's limbs as soon as possible.

[0077] In some embodiments, in step S50, the second target signal is the first fluctuation signal detected in the process of reducing the pressure applied to the user's limbs, and the fluctuation signal represents the blood flow change of the detected part caused by the pulse, such as the pressure oscillation wave signal of the air pressure. The pressure oscillation wave signal of the target artery is detected downstream of the blocked artery by the second airbag cuff and the pressure sensor. In the process of reducing the pressure applied to the user's limbs, after the artery changes from closed to open, the pressure oscillation wave can be transmitted to the downstream, and the moment when the first pressure oscillation wave signal is detected can be regarded as the moment when the artery changes from closed to open. Specifically, the starting point of the first pressure oscillation wave signal is used as the moment when the artery changes from closed to open, and the static pressure of the airbag cuff at this moment can be obtained as the systolic pressure in step S60. The second target signal can also be a fluctuation signal of other signals, such as a photoelectric signal, an electromagnetic wave signal, an ultrasonic signal or a piezoelectric signal. Specifically, the above-mentioned fluctuation signal can be obtained downstream of the target artery by a photoelectric sensor device, an airbag pulse sensing device, a radar sensing device, a Doppler sensing device or a piezoelectric pulse sensing device in the process of decreasing the pressure applied to the user's limbs.

[0078] Further, in some embodiments, in step S50, the first fluctuation signal is the first fluctuation signal of two consecutive fluctuation signals detected for the first time. Specifically, when the fluctuation signal is collected using an airbag, the fluctuation signal is an air pressure signal, specifically a pressure oscillation wave signal. The first pressure oscillation wave signal is the first pressure oscillation wave signal of two consecutive pressure oscillation wave signals detected for the first time. In order to avoid interference, it can be determined whether the two detected pressure oscillation wave signals are continuous based on the user's heart rate. In some optional embodiments, the first fluctuation signal is the first fluctuation signal of three consecutive fluctuation signals detected for the first time.

[0079] In some embodiments, in step S50, the second target signal may also be detected downstream of the target artery by a photoelectric sensing device, a radar sensing device, a Doppler sensing device, or a piezoelectric pulse sensing device.

[0080] In some embodiments, in step S60, the predicted systolic pressure SYS1 is also calculated based on the first target signal, and the systolic pressure is calculated based on the pressure applied to the user's limbs when the second target signal is detected (the systolic pressure SYS2 of the quasi-auscultation method) and the predicted systolic pressure. The calculation of the predicted systolic pressure based on the first target signal may be to calculate the systolic pressure based on the mean pressure Pm using the amplitude coefficient method as the predicted systolic pressure. The calculation of the systolic pressure based on the pressure applied to the user's limbs when the second target signal is detected and the predicted systolic pressure may be to calculate the average or weighted average of the two.

[0081] refer to Figures 4 to 6 , the present disclosure provides a blood pressure measurement system.

[0082] The blood pressure measurement system includes a main unit, an air bag structure cuff and a blood flow sensing device. The main unit is provided with a blood pressure calculation module, a limb pressure module, a limb pressure sensing module, a blood flow sensing control module and a blood flow sensing module.

[0083] The limb pressure module is used to apply pressure to or release pressure on the limbs by the airbag structure cuff; the airbag structure cuff can wrap around the arm for a circle, and is used to apply pressure to the arm, press the blood vessels in the arm, and block the blood flow; the limb pressure module specifically includes a first air pump 31, a first airbag cuff 1, a first quick release valve 33, and a slow release valve 32, the first air pump 31 is used to inflate the first airbag cuff 1, and the first quick release valve 33 and the slow release valve 32 are used to deflate, so as to apply pressure to or release pressure on the limbs;

[0084] The limb pressure sensing module is used to sense the air pressure signal and collect the pulse wave signal from the air bag structure cuff; the limb pressure sensing module is a first air pressure sensor 11, which is used to sense the air pressure signal and collect the pulse wave signal from the first air bag cuff 1;

[0085] The blood flow sensing device is located downstream of the artery blocking point where the airbag structure cuff is located, and is used to pick up changes in blood flow in the blood vessel; the blood flow sensing device uses a second airbag cuff 2 filled with a certain amount of gas, and the second airbag cuff 2 is stably fixed downstream of the artery blocking point where the first airbag cuff 1 is located, and is used to pick up changes in the pulse when blood circulates in the blood vessel. The volume of the second airbag cuff 2 can be smaller than the first airbag cuff 1, and it is used to pick up signals of blood flow, not to completely block the artery.

[0086] The blood flow sensing module is used to collect blood flow change signals in limb blood vessels from the blood flow sensing device; the blood flow sensing module is a second air pressure sensor 21, which is used to sense the air pressure signal of blood circulation change from the second airbag cuff 2;

[0087] The blood flow sensing control module is used to control the start and stop of the blood flow sensing device. The blood flow sensing control module is composed of a second air pump 51 and a second quick release valve 53, which is used to inflate or quickly deflate the blood flow sensing device (i.e., the second air bag cuff 2) so as to pressurize or quickly release the limb;

[0088] The blood pressure calculation module is used to calculate the systolic pressure and the diastolic pressure according to the signals collected by the limb pressure sensing module and the blood flow through the induction sensing module; the blood pressure calculation module is a controller 40, which can be a single-chip microcomputer, and is used to calculate the systolic pressure and the diastolic pressure according to the signals collected by the limb pressure sensing module (the first air pressure sensor 11) and the blood flow through the induction sensing module.

[0089] During the process of the airbag structure cuff applying pressure to the limb through the limb pressure module, the limb pressure sensing module collects the pulse wave signal sensed by the airbag structure cuff, and when the pulse wave signal intensity decreases from strong to a certain degree or the current air pressure in the airbag structure cuff exceeds the estimated high pressure, or the blood flow sensing module cannot collect the blood flow signal in the limb blood vessels, the limb pressure module stops applying pressure and slowly releases the pressure, and the blood pressure calculation module calculates the diastolic pressure according to the oscillometric principle;

[0090] During the process of the airbag structure cuff relieving pressure on the limb through the limb pressure module, the blood flow detects the pulse oscillation signal when the blood flow is rushed through the sensing sensor module, and the blood pressure calculation module uses the current signal collected by the corresponding limb pressure sensing module at this time as the systolic pressure, and the limb pressure module controls the airbag structure cuff to quickly relieve pressure to complete the measurement.

[0091] Wherein, the blood flow sensing device is a photoelectric sensor probe, a second airbag cuff, a radar probe, a Doppler pulse probe or a piezoelectric sensor device.

[0092] The certain degree mentioned herein is 30-70% of the maximum pulse wave signal strength.

[0093] In some embodiments, the blood pressure measurement system includes a pressure-applying device 30, a first sensor device 10, a second sensor device 20, and a controller. The pressure-applying device 30 is used to apply pressure to the user's limbs in a controlled manner, such as applying pressure to the user's limbs incrementally or incrementally or applying pressure incrementally. The first sensor device 10 is used to obtain a pressure signal; the second sensor device 20 is used to obtain a second target signal. The controller 40 can be programmed to control the working process of the aforementioned devices and calculate the user's systolic and diastolic blood pressure after obtaining the corresponding signals.

[0094] The pressure-applying device 30 includes a first airbag cuff 1, a first air pump 31, a slow-release valve 32, and a first quick-release valve 33. The first air pump 31 can inflate the first airbag cuff 1 through an air circuit. The slow-release valve 32 and the first quick-release valve 33 are independently arranged in the air circuit between the first air pump 31 and the first airbag cuff 1. The first airbag cuff 1 can wrap around the arm and pressurize the blood vessels in the arm to block the blood flow when the internal air is inflated. In addition to compressing the limbs, the first airbag cuff 1 is also used to convert the pulse signal into an air pressure signal, so it is also a part of the first sensing device 10. The first sensing device 10 includes a first air pressure sensor 11, the first airbag cuff 1, and a first pipeline connecting the two. The first air pressure sensor 11 can pick up the air pressure signal in the first airbag cuff 1 through the first pipeline. The second sensing device 20 includes a second air pressure sensor 21, a second air bag cuff 2 and a second pipeline connecting the two. The second air pressure sensor 21 can pick up the air pressure signal in the second air bag cuff 2 through the second pipeline. The second air bag cuff 2 is stably fixed downstream of the artery occlusion point where the first air bag cuff 1 is located, and is used to pick up the pulse changes when the blood circulates in the blood vessel. The air pressure signal of the second air bag cuff 2 can reflect the arterial pulsation condition.

[0095] In addition, a second air pump 51 and a second quick release valve 53 are also provided in the host 3. The second air pump is used to inflate the second airbag cuff, and the second quick release valve is used to exhaust and reduce the pressure of the second airbag cuff. More specifically, the first airbag cuff 1 and the second airbag cuff 2 are arranged side by side. The first airbag cuff 1 is used to wrap the upper half of the upper arm of the upper limb, and the second airbag cuff 2 is used to wrap the lower half of the upper arm. The first airbag cuff 1 and the second airbag cuff 2 can be separate or connected side by side as a whole. The host 3 is also provided with an interface 8 and an interface 9, which are respectively connected to the pipeline of the first airbag cuff 1 and the pipeline of the second airbag cuff 2.

[0096] In addition to the airbag cuff and air pump, other mechanical structures can also be used to achieve pressurization and decompression of the limbs. For example, in some embodiments, the pressure-applying device can be a ring or C-shaped hoop with a variable diameter, which uses a mechanical structure instead of pressurized gas to change the diameter of the hoop. When the diameter of the hoop changes from large to small, it can gradually compress the user's limbs, which is equivalent to applying incremental pressure to the limbs; when the diameter of the hoop changes from small to large, it can gradually reduce the pressure on the user's limbs.

[0097] The first sensor device 10 and the second sensor device 20 are devices for collecting external signals, and they implement the operation of collecting signals according to the instructions of the controller 40. In some embodiments, the first sensor device 10 can also be a strain sensor that cooperates with a mechanical pressure device, and the second sensor device 20 can be a photoelectric sensor device, a radar sensor device, a Doppler sensor device, or a piezoelectric pulse sensor device.

[0098] The controller 40 may be a single chip microcomputer including a memory and a processor. The controller 40 may send a control signal to the pressure applying device 30 through a preset program to control the pressure applying device 30 to apply pressure to or unload pressure on the limb according to the instruction. The controller 40 may also calculate the signals collected by the first sensor device 10 and the second sensor device 20 according to the preset program to obtain the diastolic pressure and the systolic pressure.

[0099] After receiving the user's instruction and starting the measurement process, the blood pressure measurement system can automatically execute the blood pressure measurement method in the above embodiment. For example, the method of measuring blood pressure using the above blood pressure measurement system includes the following steps:

[0100] S1, pressurization process: the limb pressure module inflates and pressurizes the airbag structure cuff at an average pressurization speed V1, and the limb pressure sensing module collects the pulse wave signal in the airbag structure cuff. At the same time, the blood flow sensing control module controls the opening and closing of the blood flow sensing device. When the blood flow sensing device is in the open state, it can sense the blood flow state in the blood vessel, and the blood flow sensing module collects the blood flow signal sensed by the blood flow sensing device.

[0101] During the pressurization process, the pulse wave signal in the airbag structure cuff and the blood flow signal at the location where the blood flows through the sensing device are collected at the same time. In the blood pressure calculation module, when it is analyzed that the pulse wave signal strength in the airbag structure cuff is weakened from strong to half of the maximum pulse wave signal strength, or the blood flow signal at the location where the blood flows through the sensing device disappears completely, the air pressure signal in the airbag structure cuff at this time is used as the predicted systolic pressure SYS1, after which the limb pressure module stops pressurizing, and the blood pressure calculation module calculates the diastolic pressure DIA according to the oscillometric method.

[0102] S2, slow pressure relief process: the airbag structure cuff slowly relieves pressure at the first average pressure reduction speed V21 through the limb pressure module. At the same time, the blood flow passes through the sensing sensor module to collect the blood flow signal in the sensing device in real time. When the blood flow passes through the sensing sensor module to collect the oscillation signal when the blood flow rushes out, the air pressure value in the airbag structure cuff at this time is defined as the systolic pressure SYS2 of the auscultation method, and the slow pressure relief is stopped at this time.

[0103] S3, rapid decompression process: the limb pressure module in the host controls the airbag structure cuff to rapidly decompress at an average speed of V22, and the blood flow through the sensing control module controls the blood flow through the sensing device to end the sensing, and the measurement ends.

[0104] The advantages of the measurement system of the embodiment of the present disclosure are illustrated below by comparing the data in the specific measurement process of the embodiment and the comparative example.

[0105] Example 1

[0106] use Figures 4 to 6 The blood pressure measurement system shown measures the blood pressure of a user.

[0107] Pressurization process: The first air pump 31 in the pressure-applying device 30 inflates the first airbag cuff 1 to increase its internal pressure, and the average pressurization speed V1 may be 10 mmHg / s. At the same time, the second air pump 51 inflates and pressurizes the second airbag cuff 2 at the same speed until the pressure inside the second airbag cuff 2 reaches 70 mmHg.

[0108] During the process of pressurizing the first airbag cuff 1, the pressure oscillation wave signals in the first airbag cuff 1 and the second airbag cuff 2 are collected. The controller 40 receives a series of pressure oscillation wave signals sent by the first sensor device 10, and statistically calculates and obtains the first target signal, that is, the pressure oscillation wave signal with the largest oscillation wave amplitude. When it is detected that the amplitude of the pressure oscillation wave signal in the first airbag cuff 1 is weakened to half of the maximum amplitude, the static pressure value in the first airbag cuff 1 at this time is obtained and used as the predicted systolic pressure SYS1, and the pressure threshold for stopping pressurization is set based on the predicted systolic pressure SYS1, such as a pressure value 30 mmHg higher than the predicted systolic pressure SYS1. When the pressure in the first airbag cuff 1 reaches the pressure threshold, the first airbag cuff 1 is stopped from being inflated. At this time, the pressure of the first airbag cuff 1 on the user's limbs is the greatest. The controller 40 calculates the diastolic pressure DIA according to the principle of oscillometric blood pressure measurement based on a series of pressure oscillation wave signals. In some embodiments, when the second sensor device 20 fails to detect the third target signal (the pressure oscillation wave signal in the second airbag cuff 2 completely disappears), the controller 40 controls the first air pump 31 to stop inflating the first airbag cuff 1 .

[0109] Decompression process: Open the slow release valve 32 to discharge the gas in the first airbag cuff 1 to reduce the pressure inside it. The speed of pressure reduction can be an average of 4 mmHg / s (the first average speed of decompression V21 = 4 mmHg / s). During the decompression period, the second air pressure sensing device detects the second target signal in the second airbag cuff 2 in real time, that is, the first pressure oscillation wave signal. The first pressure oscillation wave signal refers to the first pressure oscillation wave signal among the two or more consecutive pressure oscillation wave signals detected. The static pressure in the first airbag cuff 1 corresponding to the starting time of the first pressure oscillation wave signal is obtained, that is, the systolic pressure SYS2 of the auscultatory method, and is output as the systolic pressure. When it is determined that the second target signal is detected, the first quick release valve 33 and the second quick release valve 53 are opened to exhaust the first airbag cuff 1 and the second airbag cuff 2 to reduce the pressure. The speed of pressure reduction can be an average of 80 mmHg / s (the second average speed of decompression V22 = 80 mmHg / s).

[0110] For the subject A whose blood pressure measurement results are systolic pressure 130 mmHg and diastolic pressure 80 mmHg, the systolic pressure SYS1 is predicted to be 130 mmHg, and the maximum pressure of the first airbag cuff 1 is 160 mmHg.

[0111] The time for blood pressure measurement is calculated as follows:

[0112] 1. Duration of the pressurization process: 0-160mmHg, pressurization speed is 10mmHg / s, and the pressurization time is 160 / 10=16s;

[0113] 2. Depressurization time:

[0114] The time taken to reduce the blood pressure to 125 mmHg at a rate of 4 mmHg / s is (160-125) / 4=8.75 s;

[0115] The time taken to reduce blood pressure to 0 mmHg at a rate of 80 mmHg / s is: 125 / 80≈1.56 s;

[0116] Therefore, the total time for blood pressure measurement is approximately: 16s+8.75s+1.56s≈26s.

[0117] The above process is used to measure the blood pressure of subject B. The blood pressure measurement results are systolic pressure 180 mmHg and diastolic pressure 80 mmHg, the predicted systolic pressure SYS1 is 180 mmHg, the maximum pressurization height is 210 mmHg, and the measurement time is 32 seconds.

[0118] Comparative Example 1

[0119] A blood pressure measurement system uses the oscillometric principle of the pressurization process. The pressure increase rate during the pressurization process is 5 mmHg / s. When the pressure in the cuff rises to 30 mmHg higher than the systolic pressure, inflation is stopped and exhaust and pressure reduction begin. The pressure reduction rate is 80 mmHg / s.

[0120] For subject A whose blood pressure measurement results are systolic pressure 130 mmHg and diastolic pressure 80 mmHg, the measurement time is 34 seconds.

[0121] For subject B, whose blood pressure measurement results are systolic pressure 180 mmHg and diastolic pressure 80 mmHg, the measurement time is 44 seconds.

[0122] Comparative Example 2

[0123] A blood pressure measurement system uses the oscillometric principle of the blood pressure reduction process. The pressure increase rate during the pressurization process is 13 mmHg / s. When the pressure in the cuff rises to 30 mmHg above the systolic pressure, inflation is stopped and exhaust and pressure reduction begin. The pressure reduction rate is 5 mmHg / s.

[0124] For subject A, whose blood pressure measurement results are systolic pressure 130 mmHg and diastolic pressure 80 mmHg, the measurement time is 33 seconds.

[0125] For subject B, whose blood pressure measurement results are systolic pressure 180 mmHg and diastolic pressure 80 mmHg, the measurement time is 47 seconds.

[0126] Comparative Example 3

[0127] A blood pressure measurement system uses the principle of auscultatory pulse waves. The pressure increase rate during the pressurization process is 13 mmHg / s. When the pressure increases to 30 mmHg above the systolic pressure, the pressure is stopped. The pressure reduction rate during the depressurization process is 4 mmHg / s. During the depressurization process, the human body pressure oscillation wave signal is collected. When the pressure drops to 20 mmHg below the diastolic pressure, the pressure is reduced at 80 mmHg / s until it drops to 0. The systolic and diastolic pressures are calculated to complete the measurement.

[0128] For subject A whose blood pressure measurement results are systolic pressure 130 mmHg and diastolic pressure 80 mmHg, the measurement time is 38 seconds.

[0129] For subject B, whose blood pressure measurement results are systolic pressure 180 mmHg and diastolic pressure 80 mmHg, the measurement time is 54 seconds.

[0130] The blood pressure measurement time of Example 1 and the three comparative examples is compared as follows:

[0131]

[0132] It can be seen from the data in the table that as the pressure difference between systolic pressure and diastolic pressure increases, the blood pressure measurement method of the present invention has a shorter measurement time than the oscillometric method and the stethoscope-like method.

[0133] Clinical accuracy comparison experiment of Example 1 and three comparative examples:

[0134] According to the ISO 81060-22018 version of the clinical test standard for sphygmomanometers, 85 people were tested, and the auscultation value of the mercury sphygmomanometer was used as a reference. The clinical accuracy level was compared as follows:

[0135]

[0136] It can be seen from the data in the table that this embodiment combines the advantages of the oscillometric method and the quasi-auscultation method, which not only improves the accuracy of systolic and diastolic blood pressure measurement in non-invasive blood pressure measurement, but also significantly reduces the measurement time and improves the measurement comfort.

[0137] Example 2

[0138] Different from the first embodiment, in this embodiment, the second sensor device 20 is a photoelectric sensor device (the light source is green light). The second sensor device 20 is fixed to the downstream of the first airbag cuff 1 along the blood flow direction of the brachial artery of the upper arm, and is used to pick up the blood flow oscillation changes when the blood circulates in the blood vessel.

[0139] See also Figure 7 For example, the measurement process is as follows:

[0140] Pressurization process: The first air pump 31 inflates and pressurizes the first airbag cuff 1, and the pressurization speed is 8mmHg / pulse (the first pressurization average speed V11 = 8mmHg / pulse). When the air pressure in the first airbag cuff 1 reaches 80mmHg, the first airbag cuff 1 is continuously inflated and pressurized at the second pressurization average speed V12 of 13mmHg / pulse, so that the limb artery is gradually compressed and closed until the artery is completely blocked. The overall pressurization average speed V1 is greater than the first pressurization average speed V11, and less than the second pressurization average speed V12.

[0141] During the pressurization process, the pressure oscillation wave signal in the first airbag cuff 1 and the blood flow signal in the photoelectric sensor device are collected. When the blood flow change oscillation signal in the photoelectric sensor device completely disappears, the current value of the air pressure signal in the first airbag cuff 1 at this time is used as the predicted systolic pressure SYS1. After continuing to pressurize for 25 mmHg, the pressurization is stopped. The diastolic pressure DIA is calculated according to the oscillometric principle; the calculation method of the above-calculated "estimated high pressure" is: 3*PP-2*DIA; where PP is the static pressure value in the first airbag cuff 1 corresponding to the pressure oscillation wave signal with the largest amplitude, that is, the estimated average pressure. DIA is the estimated diastolic pressure, which is the static pressure value in the first airbag cuff 1 corresponding to the pressure oscillation wave signal with an amplitude equal to 70% of the maximum amplitude during the process of the pressure oscillation wave signal in the first airbag cuff 1 changing from weak to strong.

[0142] Decompression process: Open the slow release valve 32 to exhaust and decompress the first airbag cuff 1, and the decompression speed is 4mmHg / pulse. During the decompression period, the second target signal is collected through the photoelectric sensor device, and the static pressure value in the first airbag cuff 1 corresponding to the start time of the second target signal is 130mmHg, that is, the systolic pressure SYS2 of the quasi-auscultation method is 130mmHg, and the weighted average of the systolic pressure SYS2 of the quasi-auscultation method and the predicted systolic pressure SYS1 is calculated to obtain the output systolic pressure: SYS = (2*SYS1+8*SYS2) / 10, where the weight is 2:8. Afterwards, the first airbag cuff 1 is exhausted and decompressed through the first quick release valve, and the average decompression speed is 80mmHg / pulse.

[0143] During the whole process, the relationship between the cuff pressure and time in the first airbag cuff 1 is as follows: Figure 7 shown.

[0144] For subject A whose blood pressure measurement result is 130 / 80 mmHg, the predicted systolic pressure SYS1 is 135 mmHg, the maximum pressurization height is 160 mmHg, the systolic pressure SYS2 of the auscultatory method is 130 mmHg, the final calculated output systolic pressure SYS is 131 mmHg, and the diastolic DIA is 80 mmHg. The measurement time is calculated as follows:

[0145] 1. During the pressurization process, 8mmHg / pulse speed is used for pressurization from 0 to 80mmHg, and 13mmHg / pulse speed is used for pressurization from 80 to 160mmHg. The pressurization time is 80 / 8+(160-80) / 13≈16.15s;

[0146] 2. When the pressure of the first airbag cuff 1 reaches 160 mmHg, it is reduced to 125 mmHg at a rate of 4 mmHg / pulse, and the pressure reduction time is (160-125) / 4=8.75 s;

[0147] 3. Finally, the blood pressure is rapidly reduced at a rate of 80 mmHg / pulse to end the measurement. The rapid blood pressure reduction time is: 125 / 80≈1.56s.

[0148] Therefore, the total time for blood pressure measurement is about 26s.

[0149] For subject B whose blood pressure measurement result is 180 / 80 mmHg, the predicted systolic pressure SYS1 is 185 mmHg, the maximum pressurization height is 210 mmHg, the systolic pressure SYS2 of the auscultatory method is 180 mmHg, the final calculated output systolic pressure SYS is 181 mmHg, and the diastolic pressure is 80 mmHg. The measurement time is calculated as follows:

[0150] 1. During the pressurization process, 8mmHg / pulse speed is used for pressurization from 0 to 80mmHg, and 13mmHg / pulse speed is used for pressurization from 80 to 210mmHg. The pressurization time is 80 / 8+(210-80) / 13=20s;

[0151] 2. When the pressure of the first airbag cuff 1 reaches 210 mmHg, it is reduced to 175 mmHg at a rate of 4 mmHg / pulse, and the pressure reduction time is (210-175) / 4=8.75 s;

[0152] 3. Finally, the blood pressure is rapidly reduced at a rate of 80 mmHg / pulse to end the measurement. The time for rapid blood pressure reduction is: 175 / 80≈2.19s.

[0153] Therefore, the total time for blood pressure measurement is about 31s.

[0154] Comparison of Example 2 with three comparative examples shows that the overall measurement time is as follows:

[0155]

[0156] It can be seen from the data in the table that as the pressure difference between systolic pressure and diastolic pressure increases, the blood pressure measurement time of the present invention is shortened more and more obviously compared with the oscillometric method and the stethoscope-like method.

[0157] Clinical accuracy comparison experiment of Example 2 and three comparative examples

[0158] According to the ISO 81060-22018 version of the clinical test standard for sphygmomanometers, 85 people were tested, and the auscultation value of the mercury sphygmomanometer was used as a reference. The clinical accuracy level was compared as follows:

[0159]

[0160] It can be seen from the data in the table that this embodiment combines the advantages of the oscillometric method and the quasi-auscultation method, which not only improves the accuracy of systolic and diastolic blood pressure measurement in non-invasive blood pressure measurement, but also significantly reduces the measurement time and improves the measurement comfort.

[0161] Example 3

[0162] In this embodiment:

[0163] The airbag structure cuff is a first airbag cuff 1 that can wrap around the arm, and is used to apply pressure to the upper arm at an average speed V1, press the blood vessels in the arm, and block the blood flow;

[0164] The second sensing device 20 uses a Doppler pulse probe or a radar probe, which acts below the first airbag cuff 1 to pick up the blood flow oscillation changes when the blood circulates in the blood vessel; different from Example 1, in this embodiment, the blood flow passes through the sensing control module as a photoelectric drive circuit; the blood flow passes through the sensing sensing module as a photoelectric collection circuit, which is used to collect the blood flow change oscillation signal when the blood circulates from the photoelectric sensing device.

[0165] The blood flow sensing control module is a Doppler driving circuit or a radar driving circuit; the blood flow sensing module is a Doppler signal acquisition circuit or a radar signal acquisition circuit, which is used to collect the pulse wave oscillation signal when the blood is circulating from the Doppler pulse probe or the radar probe.

[0166] For subject A whose blood pressure measurement result is 130 / 80 mmHg, the measurement method is as follows:

[0167] S1, pressurization process: the first air pump 31 in the pressure-applying device 30 pressurizes the first airbag cuff 1 at an average speed V1 of 8 mmHg / s, so that the limb artery is gradually pressurized and closed until the artery is completely blocked.

[0168] At the same time, the pressure shock wave signal in the first airbag cuff 1 and the blood flow signal in the Doppler pulse probe or radar probe are collected. When the pressure shock wave signal intensity in the first airbag cuff 1 decreases from strong to half of the maximum pressure shock wave signal intensity, or the blood flow change shock signal in the Doppler pulse probe or radar probe disappears completely, the current value of the air pressure signal in the first airbag cuff 1 is used as the predicted systolic pressure SYS1; after continuing to pressurize for 20 mmHg, stop pressurizing, and the maximum pressurization height is about 160 mmHg. Calculate the diastolic pressure DIA according to the oscillometric principle;

[0169] S2, slow pressure reduction process: the first airbag cuff 1 reduces the pressure at an average speed V21 of 8 mmHg / s through the slow release valve 32 in the main unit 3. During this period, the Doppler signal acquisition circuit or the radar signal acquisition circuit collects the pulse oscillation signal in the Doppler pulse probe or the radar probe in real time. When the Doppler pulse probe or the radar probe continuously extracts 2 or more blood flow signals, the air pressure in the first airbag cuff 1 corresponding to the starting moment of the first blood flow signal is the stethoscope-like systolic pressure SYS2. At this time, the air pressure slowly decreases to about 125 mmHg.

[0170] S3, rapid decompression process: the first airbag cuff 1 reduces the pressure at an average speed V22 of 25 mmHg / s through the first quick release valve 33, and the measurement ends.

[0171] For a subject whose blood pressure measurement result is 130 / 80 mmHg, the predicted systolic pressure SYS1 is 140 mmHg, the maximum pressurization height is 160 mmHg, the final calculated output systolic pressure SYS is 130 mmHg, and the diastolic pressure is 80 mmHg. The measurement time is calculated as follows:

[0172] During the pressurization process, the pressure is increased at a rate of 8 mmHg / s from 0 to 160 mmHg. When the pressure of the first airbag cuff 1 reaches 160 mmHg, it is reduced to 125 mmHg at a rate of 8 mmHg / s, and finally reduced rapidly at a rate of 25 mmHg / s to end the measurement. The time used for this blood pressure measurement is: 160 / 8+(160-125) / 8+125 / 25≈29 s;

[0173] For a subject whose blood pressure measurement result is 180 / 80 mmHg, the predicted systolic pressure SYS1 is 190 mmHg, the maximum pressurization height is 210 mmHg, the final calculated output systolic pressure SYS is 180 mmHg, and the diastolic pressure is 80 mmHg. The measurement time is calculated as follows:

[0174] During the pressurization process, 0-210 mmHg is rapidly pressurized at a speed of 8 mmHg / s. When the pressure of the first airbag cuff 1 reaches 210 mmHg, it is reduced to 175 mmHg at a speed of 8 mmHg / s, and finally rapidly reduced at a speed of 25 mmHg / s to end the measurement. The time used for this blood pressure measurement is: 210 / 8+(210-175) / 8+175 / 25≈38 s.

[0175] Taking subjects with blood pressure of 130 / 80 mmHg and 180 / 80 mmHg as an example, compared with the three comparative examples, the measurement time of Example 3 is significantly shortened, and the measurement comfort is improved.

[0176] Example 4

[0177] In this embodiment:

[0178] The airbag structure cuff is an airbag wristband that can wrap around the wrist and is used to apply pressure to the wrist at an average speed V1 to press the blood vessels in the wrist and block blood flow;

[0179] The second sensor device 20 is a photoelectric sensor device, which acts on the finger, and the light source is red light or infrared light, which is used to pick up the blood flow oscillation changes when the blood circulates in the blood vessels.

[0180] The pressure-applying device 30 includes a first air pump 31, a first quick-release valve 33, an airbag wristband and a slow-release valve 32, so as to realize the inflation or deflation of the airbag wristband, thereby pressurizing or reducing the pressure on the limbs; the limb pressure sensing module, i.e., the first air pressure sensor 11, is used to sense the air pressure signal from the airbag wristband and collect the pressure shock wave signal. The design is consistent with that in Example 1.

[0181] The blood flow sensing control module is a photoelectric drive circuit; the blood flow sensing module is a photoelectric collection circuit, which is used to collect blood flow change oscillation signals during blood circulation from the photoelectric sensor device.

[0182] Taking the blood pressure measurement result of subject A as 130 / 80 mmHg as an example, the measurement method is as follows:

[0183] S1, pressurization process; the first air pump 31 in the pressure-applying device 30 pressurizes the airbag wristband at an average speed V11 of 10 mmHg / s (the average speed of the low-pressure section of V1). When the air pressure in the airbag wristband reaches 80 mmHg, the airbag wristband continues to be pressurized at an average speed V12 of 20 mmHg / s (the average speed of the high-pressure section of V1), so that the wrist artery is gradually pressurized and closed until the artery is completely blocked.

[0184] At the same time, the pressure shock wave signal in the airbag wristband and the blood flow signal in the photoelectric sensor device are collected. When the pressure shock wave signal in the airbag wristband decreases from strong to half of the maximum pressure shock wave signal, or the blood flow change shock signal in the photoelectric sensor device disappears completely, the current value of the air pressure signal in the airbag wristband is used as the predicted systolic pressure SYS1; after continuing to pressurize for 30mmHg, stop pressurizing. At this time, the maximum pressurization height is about 160mmHg. Calculate the diastolic pressure DIA according to the oscillometric principle;

[0185] S2, slow pressure reduction process; the airbag wristband slowly reduces the pressure at an average speed V21 of 5mmHg / pulse through the slow release valve 32 in the host 3. During this period, the photoelectric collection circuit collects the blood flow oscillation signal in the photoelectric sensor device in real time. When the photoelectric sensor device continuously extracts 2 or more blood flow passing signals, the air pressure in the airbag wristband corresponding to the starting moment of the first blood flow passing signal is the systolic pressure SYS. At this time, the air pressure slowly decreases to about 125mmHg.

[0186] S3, rapid depressurization process: the airbag wristband rapidly depressurizes at an average speed V22 of 50 mmHg / s through the first quick release valve 31, and the measurement ends.

[0187] For a subject whose blood pressure measurement result is 130 / 80 mmHg, the predicted systolic pressure SYS1 is 130 mmHg, the maximum pressurization height is 160 mmHg, the final calculated output systolic pressure SYS is 130 mmHg, and the diastolic pressure is 80 mmHg. The measurement time is calculated as follows:

[0188] During the pressurization process, 0-80mmHg is pressurized at a speed of 10mmHg / s, and 80-160mmHg is pressurized at a speed of 20mmHg / s. When the pressure of the airbag wristband reaches 160mmHg, it is reduced to 125mmHg at a speed of 5mmHg / s, and finally at a speed of 50mmHg / s to end the measurement. The time used for this blood pressure measurement is: 80 / 10+(160-80) / 20+(160-125) / 5+125 / 50≈22s;

[0189] For a subject whose blood pressure measurement result is 180 / 80 mmHg, the predicted systolic pressure SYS1 is 180 mmHg, the maximum pressurization height is 210 mmHg, the final calculated output systolic pressure SYS is 180 mmHg, and the diastolic pressure is 80 mmHg. The measurement time is calculated as follows:

[0190] During the pressurization process, 0-100mmHg is pressurized at a speed of 10mmHg / s, and 100-210mmHg is pressurized at a speed of 20mmHg / s. When the pressure of the airbag wristband reaches 210mmHg, it is reduced to 175mmHg at a speed of 5mmHg / s, and finally reduced rapidly at a speed of 50mmHg / s to end the measurement. The time used for this blood pressure measurement is: 100 / 10+(210-100) / 20+(210-175) / 5+175 / 50≈26s;

[0191] Taking subjects with blood pressure of 130 / 80 mmHg and 180 / 80 mmHg as an example, compared with the three comparative examples, the measurement time of Example 4 is significantly shortened, and the measurement comfort is improved.

[0192] Example 5

[0193] In this embodiment:

[0194] The airbag structure cuff is a first airbag cuff 1 that can wrap around the arm, and is used to apply pressure to the upper arm at an average speed V1, press the blood vessels in the arm, and block the blood flow;

[0195] The second sensor device 20 is a piezoelectric sensor device, which is located downstream of the first airbag cuff 1 along the blood flow direction of the arm artery, and is used to pick up the blood flow oscillation changes when the blood circulates in the blood vessel.

[0196] The pressure-applying device 30 is composed of a first air pump 31, a first quick-release valve 33 and a slow-release valve 32, and is used to inflate or deflate the first airbag cuff 1, thereby increasing or decreasing the pressure on the arm; the limb pressure sensing module, namely the first air pressure sensor 11, is used to sense the air pressure signal from the first airbag cuff 1 and collect the pressure oscillation wave signal. The design is consistent with that in Example 1.

[0197] The blood flow sensing control module is a piezoelectric driving circuit; the blood flow sensing sensor module is a piezoelectric acquisition circuit, which is used to collect blood flow change oscillation signals during blood circulation from the piezoelectric sensor device.

[0198] Taking the measurement of a subject with systolic blood pressure of 130 mmHg and diastolic blood pressure of 80 mmHg as an example, the measurement method is as follows:

[0199] S1, pressurization process; the first air pump in the pressure device pressurizes the first airbag cuff 1 at an average speed V11 of 15 mmHg / s (the average speed of the low-pressure section of V1). When the air pressure in the first airbag cuff 1 reaches 80 mmHg, the first airbag cuff 1 continues to be pressurized at an average speed V12 of 25 mmHg / pulse (the average speed of the high-pressure section of V1), so that the limb artery is gradually pressurized and closed until the artery is completely blocked.

[0200] At the same time, the pressure shock wave signal in the first airbag cuff 1 and the blood flow signal in the piezoelectric sensor device are collected. When the pressure shock wave signal intensity in the first airbag cuff 1 decreases from strong to half of the maximum pressure shock wave signal intensity, or the blood flow change shock signal in the piezoelectric sensor device disappears completely, the current value of the air pressure signal in the first airbag cuff 1 is used as the predicted systolic pressure SYS1; after continuing to pressurize for 25mmHg, stop pressurizing, and the maximum pressurization height is about 160mmHg. Calculate the diastolic pressure DIA according to the oscillometric principle;

[0201] S2, slow blood pressure reduction process; the first airbag cuff 1 slowly reduces the pressure at an average speed V21 of 2mmHg / pulse through the slow release valve in the main unit. During this period, the piezoelectric acquisition circuit collects the blood flow oscillation signal in the piezoelectric sensor device in real time. When the piezoelectric sensor device continuously extracts 2 or more blood flow passing signals, the air pressure in the first airbag cuff 1 corresponding to the starting moment of the first blood flow passing signal is the predicted systolic pressure SYS2. At this time, the air pressure slowly decreases to about 125mmHg.

[0202] S3, rapid depressurization process: the first airbag cuff 1 passes through the quick release valve 1 and rapidly depressurizes at an average speed V22 of 100 mmHg / s, and the measurement ends.

[0203] For a subject whose blood pressure measurement result is 130 / 80 mmHg, the predicted systolic pressure SYS1 is 135 mmHg, the maximum pressurization height is 160 mmHg, the final calculated output systolic pressure SYS is 130 mmHg, and the diastolic pressure is 80 mmHg. The measurement time is calculated as follows:

[0204] During the pressurization process, 0-80mmHg is pressurized at a speed of 15mmHg / s, and 80-160mmHg is pressurized at a speed of 25mmHg / s. When the pressure of the first airbag cuff 1 reaches 160mmHg, it is reduced to 125mmHg at a speed of 2mmHg / s, and finally at a speed of 100mmHg / s to end the measurement. The time used for this blood pressure measurement is: 80 / 15+(160-80) / 25+(160-125) / 2+125 / 100≈27s;

[0205] For a subject whose blood pressure measurement result is 180 / 80 mmHg, the predicted systolic pressure SYS1 is 185 mmHg, the maximum pressurization height is 210 mmHg, the final calculated output systolic pressure SYS is 180 mmHg, and the diastolic pressure is 80 mmHg. The measurement time is calculated as follows:

[0206] During the pressurization process, 0-80mmHg is pressurized at 15mmHg / pulse speed, and 80-210mmHg is pressurized at 25mmHg / pulse speed. When the pressure of the first airbag cuff 1 reaches 210mmHg, it is reduced to 175mmHg at a rate of 2mmHg / s, and finally reduced rapidly at a rate of 100mmHg / s to end the measurement. The time used for this blood pressure measurement is: 80 / 15+(210-80) / 25+(210-175) / 2+175 / 100≈30s;

[0207] Taking subjects with blood pressure of 130 / 80 mmHg and 180 / 80 mmHg as an example, compared with the three comparative examples, the measurement time of Example 5 is significantly shortened, and the measurement comfort is improved.

[0208] Example 6

[0209] In this embodiment:

[0210] A mechanical strap and a piezoelectric sensor are used to replace the airbag cuff, and the piezoelectric sensor is placed between the mechanical strap and the upper arm. The mechanical strap is wrapped around the upper arm and can apply pressure to the upper arm at an average speed of V1, pressing the blood vessels in the arm and blocking blood flow.

[0211] The second sensor device 20 is a photoelectric sensor device, which is stably fixed downstream of the mechanical strap along the blood flow direction of the arm artery, and is used to pick up the blood flow oscillation changes when the blood circulates in the blood vessel.

[0212] The pressure-applying device 30 includes a servo driver (not shown) and a servo motor (not shown), which are used to control the mechanical strap to apply pressure or reduce pressure on the arm; the limb pressure sensing module is a piezoelectric sensor, which is used to collect pressure signals and pressure oscillation wave signals from the piezoelectric sensing device.

[0213] The blood flow sensing control module is a photoelectric drive circuit; the blood flow sensing module is a photoelectric collection circuit, which is used to collect blood flow change oscillation signals during blood circulation from the photoelectric sensor device.

[0214] Taking the blood pressure measurement of a subject with a systolic blood pressure of 130 mmHg and a diastolic blood pressure of 80 mmHg as an example, the measurement method is as follows:

[0215] S1, pressurization process; the servo driver and servo motor control the mechanical strap to apply pressure to the arm at an average speed V11 of 15 mmHg / s (the average speed of the low-pressure section of V1). When the pressure sensed by the piezoelectric sensor reaches 80 mmHg, pressure is continued to be applied to the arm at an average speed V12 of 35 mmHg / s (the average speed of the high-pressure section of V1), so that the limb artery is gradually compressed and closed until the artery is completely blocked.

[0216] At the same time, the pressure shock wave signal sensed by the piezoelectric sensor and the blood flow signal in the photoelectric sensor are collected. When the pressure shock wave signal intensity sensed by the piezoelectric sensor decreases from strong to half of the maximum pressure shock wave signal intensity, or the blood flow change shock signal in the photoelectric sensor disappears completely, the current value sensed by the piezoelectric sensor at this time is used as the predicted systolic pressure SYS1; after continuing to pressurize for 25mmHg, stop pressurizing, and the maximum pressurization height is about 160mmHg. Calculate the diastolic pressure DIA according to the oscillometric principle;

[0217] S2, slow blood pressure reduction process; the mechanical strap slowly relaxes the pressure at an average speed V21 of 1 mmHg / s. During this period, the photoelectric collection circuit collects the blood flow oscillation signal in the photoelectric sensor device in real time. When the photoelectric sensor device continuously extracts 2 or more blood flow signals, the pressure sensed by the piezoelectric sensor device corresponding to the starting moment of the first blood flow signal is the systolic pressure SYS2 by the auscultation method. At this time, the applied pressure has been slowly reduced to about 125 mmHg.

[0218] S3, rapid blood pressure reduction process: the mechanical strap is quickly loosened at an average speed of 120 mmHg / s V22, and the measurement is completed.

[0219] For a subject whose blood pressure measurement result is 130 / 80 mmHg, the predicted systolic pressure SYS1 is 135 mmHg, the maximum pressurization height is 160 mmHg, the final calculated output systolic pressure SYS is 130 mmHg, and the diastolic pressure is 80 mmHg. The measurement time is calculated as follows:

[0220] During the pressurization process, 0-100mmHg is pressurized at a speed of 15mmHg / s, and 100-160mmHg is pressurized at a speed of 35mmHg / s. When the pressure of the piezoelectric sensor reaches 160mmHg, it is reduced to 125mmHg at a speed of 2mmHg / s, and finally at a speed of 120mmHg / s to end the measurement. The time used for this blood pressure measurement is: 100 / 15+(160-100) / 35+(160-125) / 2+125 / 120≈27s;

[0221] For a subject whose blood pressure measurement result is 180 / 80 mmHg, the predicted systolic pressure SYS1 is 185 mmHg, the maximum pressurization height is 210 mmHg, the systolic pressure SYS is 180 mmHg, and the diastolic pressure is 80 mmHg. The measurement time is calculated as follows:

[0222] During the pressurization process, 0-100mmHg is pressurized at 15mmHg / pulse speed, and 100-210mmHg is pressurized at 35mmHg / pulse speed. When the pressure of the piezoelectric sensor reaches 210mmHg, it is reduced to 175mmHg at a rate of 2mmHg / s, and finally the strap is quickly loosened at a rate of 120mmHg / s to end the measurement. The time used for this blood pressure measurement is: 100 / 15+(210-100) / 35+(210-175) / 2+175 / 120≈29s;

[0223] Taking subjects with blood pressure of 130 / 80 mmHg and 180 / 80 mmHg as an example, compared with the three comparative examples, the measurement time of Example 6 is significantly shortened, and the measurement comfort is improved.

[0224] The above is only a specific implementation of the present disclosure, but the protection scope of the present disclosure is not limited thereto. Any technician familiar with the technical field can easily think of various equivalent modifications or replacements within the technical scope disclosed in the present disclosure, and these modifications or replacements should be included in the protection scope of the present disclosure. Therefore, the protection scope of the present disclosure should be based on the protection scope of the claims.

Claims

1. A blood pressure measurement system, characterized in that: include: A pressure-applying device for applying pressure to a user's limb; A first sensor device, used to obtain a pressure signal; A second sensor device, used to obtain a second target signal; as well as A controller programmed to: Controlling the pressure applying device to incrementally apply pressure to the user's limb so that the target artery is blocked; Controlling the first sensor device to at least obtain a plurality of pressure oscillation wave signals generated by the pulsation of a target artery during the process of applying pressure to a user's limb; Obtain a first target signal based on the multiple pressure oscillation wave signals, and obtain diastolic pressure based on the first target signal; Controlling the pressure applying device to apply pressure to the user's limbs in a decreasing manner; Controlling the second sensing device to detect a second target signal in the process of gradually applying pressure to the user's limb, and obtaining the pressure applied to the user's limb from the first sensing device when the second target signal is detected, wherein the second target signal is used to indicate a state transition of the target artery in the user's limb from occlusion to flow; as well as The systolic blood pressure is obtained based on at least the pressure applied to the user's limb when the second target signal is detected.

2. The blood pressure measurement system according to claim 1, characterized in that: The controller is programmed to control: The pressure applying device, in the process of gradually applying pressure to the user's limb, reduces the pressure at a first average pressure reduction speed and then reduces the pressure at a second average pressure reduction speed; The second sensing device detects the second target signal during the process of reducing the pressure: detecting the second target signal during the process of reducing the pressure at the first average pressure reduction speed; The second average pressure reduction speed is greater than the first average pressure reduction speed.

3. The blood pressure measurement system according to claim 2, characterized in that: The controller is programmed to control the pressure applying device to switch to reducing pressure at the second pressure reducing average speed in response to confirming detection of the second target signal.

4. The blood pressure measurement system according to claim 1, characterized in that: The controller is programmed to control: The pressure applying device, in the process of incrementally applying pressure to the user's limb: first applies pressure at a first average pressure application speed and then applies pressure at a second average pressure application speed; Wherein, the first average pressurization speed is smaller than the second average pressurization speed.

5. The blood pressure measurement system according to claim 1, characterized in that: The controller is programmed to control the second sensor device to detect a third target signal during the process of the pressure applying device applying pressure, and to control the pressure applying device: Applying the pressure is stopped in response to the failure to detect the third target signal, or in response to the first sensing device detecting that the applied pressure reaches a preset threshold, wherein the preset threshold is set based on the first target signal.

6. The blood pressure measurement system according to claim 5, characterized in that: The third target signal is a fluctuation signal obtained from downstream of the artery to which pressure is applied during the process of incrementally applying pressure to the user's limbs. The fluctuation signal is an air pressure signal, a photoelectric signal, an electromagnetic wave signal, an ultrasonic signal or a piezoelectric signal, and the fluctuation signal reflects changes in blood flow.

7. The blood pressure measurement system according to claim 1, characterized in that: The first target signal is a predetermined pressure oscillation wave signal obtained based on multiple pressure oscillation wave signals, and / or the second target signal is: the first fluctuation signal detected in the process of reducing the pressure applied to the user's limbs, the fluctuation signal is an air pressure signal, a photoelectric signal, an electromagnetic wave signal, an ultrasonic signal or a piezoelectric signal, and the fluctuation signal is used to reflect changes in blood flow.

8. The blood pressure measurement system according to claim 7, characterized in that: The first fluctuation signal is the first fluctuation signal of at least two consecutive fluctuation signals detected for the first time.

9. The blood pressure measurement system according to claim 1, characterized in that: The controller further calculates a predicted systolic pressure based on the first target signal, and the systolic pressure is calculated based on the pressure applied to the user's limb when the second target signal is detected and the predicted systolic pressure.

10. The blood pressure measurement system according to claim 1, characterized in that: The process in which the controller calculates and obtains the systolic pressure based on at least the second target signal includes extracting the pressure applied to the user's limb corresponding to the moment when the second target signal is detected.

11. The blood pressure measurement system according to claim 1, characterized in that: The second sensing device is used to detect the second target signal downstream of the location where the target artery is occluded.

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