Blood pressure measurement method and system

Abstract

A blood pressure measurement method and system. The measurement method comprises: (S10) incrementally applying pressure to the limb of a user, so as to block a target artery; (S20) during the process of applying the pressure to the limb of the user, at least obtaining a plurality of pressure oscillation wave signals generated by the pulsation of the target artery; (S30) obtaining a first target signal on the basis of the plurality of pressure oscillation wave signals, and obtaining a diastolic blood pressure on the basis of the first target signals; (S40) decrementally applying pressure to the limb of the user; (S50) during the process of decrementally applying the pressure to the limb of the user, detecting a second target signal and obtaining the pressure applied to the limb of the user of when the second target signal is detected, wherein the second target signal is used for representing a state transition of the target artery from blockage to flow; and (S60) obtaining a systolic blood pressure at least on the basis of the pressure applied to the limb of the user of when the second target signal is detected.

Description

Blood pressure measurement method and system Technical Field

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

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

[0003] 1) The Korotkoff sound auscultation method uses an inflated cuff to compress the arteries in the limbs. As the cuff pressure decreases, the arteries gradually open from complete blockage to full opening. A stethoscope is used to identify the changes in the sound during the transition from blocked blood flow to unblocked blood flow. The corresponding air pressure within the cuff is then used to determine the systolic and diastolic blood pressures.

[0004] 2) Oscillometry: An inflatable cuff is used to compress the limb arteries to block arterial blood flow. During the pressurization process, the pressure oscillation waves in the cuff are detected and collected. During the depressurization process, the pressure oscillation waves in the cuff are detected. The systolic and diastolic blood pressures are calculated based on the pressure oscillation waves.

[0005] Figure 1 shows the pulse (pressure oscillation signal) amplitude as a function of cuff pressure during the pressurization process, and the corresponding cuff pressure (cuff pressure) as a function of time. As the cuff pressure slowly increases from 0 mmHg, the pulse amplitude gradually increases. When the cuff pressure equals the mean pressure (Pm), the arterial wall is unloaded, and the amplitude reaches its maximum. Once the cuff pressure exceeds the mean pressure (Pm), the amplitude gradually decreases. When the cuff pressure continues to increase to exceed the systolic pressure (Ps), the pressure oscillation signal is sufficient for oscillometric calculation of the systolic pressure, allowing the cuff to be rapidly deflated to terminate the measurement. During the cuff pressure increase process, the recorded pulse oscillation amplitude exhibits a parabolic envelope. Based on large-scale population statistics, different manufacturers have identified the envelopes of systolic pressure (Ps) and diastolic pressure (Pd), as well as the pulse shape characteristics, for different blood pressure groups and developed statistical models. The algorithms associated with these models are embedded in the electronic blood pressure monitor's memory and applied to calculate systolic and diastolic pressures during individual blood pressure measurements.

[0006] As shown in FIG2 , FIG2 is a schematic diagram showing the change of the amplitude of the pulse (pressure oscillation wave signal) with the airbag cuff pressure during the depressurization process and the corresponding change of the cuff pressure (airbag cuff pressure) with time.

[0007] The cuff is first rapidly inflated. When the cuff pressure exceeds the systolic pressure (Ps), arterial blood flow is blocked, and small oscillations appear within the cuff due to the impact of the proximal pulse. The pressure oscillation signal is then collected after the cuff pressure is slowly depressurized. When the cuff pressure falls below the systolic pressure (Ps), the pulse amplitude gradually increases. When the cuff pressure equals the mean arterial pressure (Pm), the arterial wall is unloaded, and the pulse amplitude reaches its maximum. After the cuff pressure falls below the mean arterial pressure, the pulse amplitude gradually decreases. After the cuff pressure is slowly depressurized until the pressure falls below the diastolic pressure (Pd), the oscillation signal is no longer collected, and the cuff can be rapidly deflated to terminate the measurement. During the slow decrease in cuff pressure, the collected pulse pressure oscillation amplitude exhibits a parabolic envelope. Based on a large number of population statistics, different manufacturers can find the envelope curves of 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 applied to the blood pressure measurement process of individual users to calculate systolic and diastolic blood pressure.

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

[0009] 1. The mercury sphygmomanometer using the Korotkoff sound auscultation method is the gold standard for blood pressure measurement. However, 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 is poor.

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

[0012] Furthermore, calculating systolic and diastolic blood pressure using the pressure-increasing or pressure-decreasing oscillometric methods requires collecting sufficient pulse signals to plot the envelope curves. Therefore, the pressure increase or decrease rate during measurement must be kept relatively constant. Generally, the pressure change rate during measurement is limited to approximately 4-6 mmHg per second or per pulse, and the maximum pressure increase or decrease is approximately 20-30 mmHg higher than the systolic pressure. Furthermore, the rapid decrease or increase in pressure during pressure-increasing or pressure-decreasing measurements also takes time, resulting in a relatively long measurement time for an oscillometric electronic blood pressure monitor. For example, for a user with a systolic blood pressure of 130 mmHg, the entire measurement process takes approximately 30 seconds. Higher blood pressure requires a higher pressure increase, and the measurement time increases. When the user's systolic blood pressure reaches 200 mmHg, the entire measurement takes nearly a minute, resulting in prolonged pressure on the user's arm and poor comfort.

[0013] 3. Some products simply combine the oscillometric pressure measurement process with the pressure relief process to improve measurement accuracy. However, because the oscillometric principle requires that the measurement process cover the entire pressure range from systolic to diastolic pressure with sufficient pulse signals, combining the pressure and pressure relief measurement processes results in prolonged compression on the user's arm, resulting in poor comfort.

[0014] Summary of the Invention

[0015] The present invention aims to provide a blood pressure measurement method and system that can improve the accuracy of blood pressure measurement.

[0016] In a first aspect, a blood pressure measurement method is provided, comprising:

[0017] Incrementally applying pressure to the user's limb to occlude the target artery;

[0018] Obtaining at least a plurality of pressure oscillation wave signals generated by the pulsation of a target artery during the process of applying pressure to the user's limb;

[0019] 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;

[0020] Applying decreasing pressure to the user's limbs;

[0021] Detecting a second target signal during the process of gradually applying pressure to the user's limb and obtaining the pressure applied to the user's limb when the second target signal is detected, wherein the second target signal is used to indicate a state transition of the target artery from occlusion to flow; and

[0022] 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.

[0023] In one possible implementation, the process of gradually applying pressure to the user's limb includes: reducing the pressure at a first average pressure reduction rate and then reducing the pressure at a second average pressure reduction rate;

[0024] Detecting the second target signal during the pressure reduction process includes: detecting the second target signal during the pressure reduction process at the first pressure reduction average speed;

[0025] The second average pressure reduction speed is greater than the first average pressure reduction speed.

[0026] In combination with the foregoing possible implementation manner, in another possible implementation manner, in response to confirming that the second target signal is detected, the process switches to a process of reducing the pressure at a second average pressure reduction speed.

[0027] In combination with the above possible implementations, in another possible implementation:

[0028] Incrementally applying pressure to the user's limb includes: 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.

[0029] In combination with the above possible implementations, in another possible implementation, a third target signal is detected during the process of applying pressure, and applying pressure is stopped in response to not detecting the third target signal; or, applying pressure is stopped in response to reaching a preset pressure threshold, and the preset threshold is set based on the first target signal.

[0030] 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. 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.

[0031] 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 gradually applying pressure to the user's limb, 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.

[0032] 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.

[0033] In combination with the above possible implementation methods, in another possible implementation method, the measurement method also includes calculating the predicted systolic pressure based on the first target signal, and calculating 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.

[0034] In combination with the above possible implementations, in another possible implementation, the systolic pressure is calculated based on at least the second target signal, and the pressure applied to the user's limb corresponding to the moment when the second target signal is detected is extracted based on the moment when the second target signal is detected.

[0035] In combination with the foregoing possible implementation manner, in another possible implementation manner, the second target signal is detected downstream of the location where the target artery is blocked.

[0036] In a second aspect, a blood pressure measurement system is provided, comprising a pressure-applying device, a first sensing device, a second sensing device and a controller; the pressure-applying device is used to apply pressure to a user's limb; the first sensing device is used to obtain a pressure signal; the second sensing device is used to obtain a second target signal; the controller is programmed to perform: controlling the pressure-applying device to incrementally apply pressure to the user's limb so that the target artery is blocked; controlling the first sensing 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 the diastolic pressure based on the first target signal; controlling the pressure-applying device to incrementally apply pressure to the user's limb; controlling the second sensing 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 sensing device when the second target signal is detected, wherein the second target signal is used to characterize the transition of the target artery in the user's limb from a blocked to a flowing state; and obtaining the systolic pressure based at least on the pressure applied to the user's limb when the second target signal is detected.

[0037] In one possible implementation, the controller is programmed to control:

[0038] The pressure applying device reduces the pressure at a first average pressure reduction rate and then reduces the pressure at a second average pressure reduction rate during the process of gradually applying pressure to the user's limb;

[0039] The second sensing device detects the second target signal during the pressure reduction process: detecting the second target signal during the pressure reduction process at the first average pressure reduction rate;

[0040] The second average pressure reduction speed is greater than the first average pressure reduction speed.

[0041] In combination with the above possible implementation manner, in another possible implementation manner, the controller is programmed to control the pressure applying device: in response to confirming that the second target signal is detected, switch to reducing the pressure at a second average pressure reduction speed.

[0042] In combination with the above possible implementations, in another possible implementation, the controller is programmed to control the pressure-applying device to apply pressure to the user's limbs in an incremental manner: 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.

[0043] In combination with the above possible implementation manner, in another possible implementation manner, the controller is programmed to control the second sensing device to detect the third target signal during the process of the pressure applying device applying pressure, and to control the pressure applying device:

[0044] Applying the pressure is stopped in response to not detecting the third target signal, or in response to the first sensing device detecting that the applied pressure reaches a preset threshold, where the preset threshold is set based on the first target signal.

[0045] 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. 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.

[0046] 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 limb, 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.

[0047] 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.

[0048] 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.

[0049] In combination with the above possible implementations, in another possible implementation, the process of the controller calculating 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.

[0050] In combination with the foregoing possible implementation manner, in another possible implementation manner, the second sensing device is used to detect a second target signal downstream of a location where the target artery is blocked.

[0051] The blood pressure measurement method provided by the present invention utilizes the oscillometric method to obtain signals and calculate diastolic pressure during the process of applying pressure to the limbs, and to obtain systolic pressure by picking up signals indicating the transition from closed to open blood vessels during the process of lowering blood pressure. This improves the measurement accuracy of systolic and diastolic pressures without significantly increasing the measurement time. BRIEF DESCRIPTION OF THE DRAWINGS

[0052] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the following briefly introduces the drawings required for use in the embodiments of the present invention. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without any creative work.

[0053] FIG1 is a schematic diagram showing the change of pulse amplitude with air bag cuff pressure in blood pressure measurement using the pressure oscillometric method and the corresponding change of cuff pressure with time.

[0054] FIG2 is a schematic diagram showing the change of pulse amplitude with air bag cuff pressure and the corresponding change of cuff pressure with time when measuring blood pressure using the step-down oscillometric method.

[0055] FIG3 is a flow chart of a blood pressure measurement method according to an embodiment of the present invention.

[0056] FIG4 is a schematic structural diagram of a blood pressure measurement system according to an embodiment of the present invention.

[0057] FIG5 is another structural schematic diagram of the blood pressure measurement system in FIG4 .

[0058] FIG6 is a schematic diagram of the detailed structure of the blood pressure measurement system in FIG5 .

[0059] FIG7 is a schematic diagram showing changes in the pressure in the first airbag cuff over time using a blood pressure measurement method according to an embodiment of the present invention.

[0060] FIG8 is a schematic diagram showing changes in the pressure in the first airbag cuff over time using a blood pressure measurement method according to another embodiment of the present invention. DETAILED DESCRIPTION

[0061] To make the objectives, technical solutions, and advantages of the embodiments of the present invention more clear, the technical solutions in the embodiments of the present invention will be clearly and completely described below in conjunction with the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. All other embodiments obtained by ordinary technicians in this field based on the embodiments of the present invention without making any creative efforts shall fall within the scope of protection of the present invention.

[0062] The features and exemplary embodiments of various aspects of the present invention will be described in detail below. In the detailed description below, many specific details are set forth in order to provide a comprehensive understanding of the present invention. However, it will be apparent to those skilled in the art that the present invention can be implemented without the need for some of these specific details. The following description of the embodiments is merely intended to provide a better understanding of the present invention by illustrating examples of the present invention. The present invention is in no way limited to any specific structure and configuration set forth below, but rather encompasses any modification, replacement, and improvement of parts, components, and connection modes without departing from the spirit of the present invention. In the accompanying drawings and the following description, well-known structures and techniques are not shown to avoid unnecessary ambiguity in the present invention.

[0063] 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 thorough understanding of embodiments of the present invention.

[0064] The blood pressure measurement method provided by the present invention includes obtaining diastolic pressure during the process of applying pressure to a user's limb, and obtaining systolic pressure based on at least a signal obtained during the process of reducing pressure on the user's limb, thereby improving the accuracy of blood pressure measurement. The method primarily comprises: incrementally applying pressure to the user's limb using a pressure-applying device, such as an air bag and an air pump, to occlude a target artery; obtaining, via a pressure sensor, multiple pressure oscillation wave signals as the target artery pulsates during the process of applying pressure to the user's limb; obtaining a first target signal (e.g., the pressure oscillation wave signal with the largest pulse amplitude detected during oscillometric blood pressure measurement) based on the multiple pressure oscillation wave signals, and obtaining diastolic pressure based on the first target signal. Subsequently, the pressure applied to the user's limb is gradually reduced, and a second target signal is detected during the pressure reduction process, along with the pressure applied to the user's limb at the time the signal is detected. The second target signal is used to indicate a transition from an occluded state to a flowing state in the target artery, and the systolic pressure is obtained based on at least the pressure applied to the user's limb at the time the signal is detected.

[0065] 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 airbag 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 on this basis obtaining a more accurate diastolic pressure; in addition, the systolic pressure is obtained based on at least a second target signal representing the transition of the target artery from blocked to flowing state. Compared with the traditional oscillometric method of obtaining the average pressure and then using the amplitude coefficient method to calculate the systolic pressure, it is more suitable for different individuals and the systolic pressure obtained is more accurate.

[0066] Refer to FIG3 , which is a flow chart of a blood pressure measurement method according to an embodiment of the present invention.

[0067] In this embodiment, the blood pressure measurement method includes the following steps:

[0068] S10. Incrementally apply pressure to the user's limb to occlude the target artery.

[0069] Specifically, an airbag cuff can be wrapped around the user's upper arm and inflated using an air pump. During inflation, the pressure in the cuff gradually increases at an average pressure rate V1. As the cuff gradually expands, it compresses the brachial artery, and when the cuff is sufficiently inflated, it can occlude the brachial artery.

[0070] S20. Obtain at least a plurality of pressure oscillation wave signals generated by the pulsation of a target artery during the process of applying pressure to the user's limbs.

[0071] The pressure within the cuff can be considered the pressure applied to the brachial artery. Furthermore, due to the force exerted by the arterial pulsation on the cuff, a pressure oscillation wave corresponding to the pulse is generated within the cuff. The cuff can be connected to a pressure sensor via a tube. During the application of pressure to the user's limb, the pressure sensor can read the real-time pressure signal within the cuff. This real-time pressure signal can be separated into a static pressure signal and a pressure oscillation wave signal corresponding to the pulse. The static pressure signal refers to the pressure signal that rises or falls smoothly over time as the cuff is inflated or deflated.

[0072] S30. Obtain a first target signal based on the multiple pressure oscillation wave signals, and obtain the diastolic pressure based on the first target signal.

[0073] The static pressure signal is the pressure signal within the cuff that varies gently over time and can be considered the pressure applied to the brachial artery. The pressure oscillation wave signal represents the brachial artery pulsation. Its oscillation wave amplitude exhibits the following variation pattern: During pressurization, before the cuff pressure reaches the mean arterial pressure (PM), the oscillation wave amplitude gradually increases with increasing pressure. When the cuff pressure equals the mean arterial pressure (PM), the arterial wall is unloaded, and the oscillation wave amplitude reaches its maximum. After the cuff pressure reaches the mean arterial pressure (PM), the oscillation wave amplitude gradually decreases with increasing pressure. As the cuff pressure gradually increases, the amplitudes of multiple pressure oscillation wave signals form a parabolic envelope. The pressure oscillation wave signal with the largest amplitude is the first target signal.

[0074] After obtaining the first target signal, the amplitude of the pressure oscillation wave signal corresponding to the diastolic pressure can be further calculated based on the pre-set amplitude coefficient. However, this amplitude may not completely match a pressure oscillation wave signal. The first pressure oscillation wave signal slightly smaller than this 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 also be inferred by jointly inferring two oscillation wave signals with adjacent amplitudes of the pressure oscillation wave signal corresponding to the diastolic pressure, calculating the proportional relationship between the amplitudes of the diastolic pressure corresponding to the two adjacent oscillation wave signals, and using this proportional relationship to interpolate the airbag cuff static pressure values ​​corresponding to the starting points of the two oscillation wave signals to calculate the diastolic pressure value.

[0075] S40: Apply pressure to the user's limbs in a decreasing manner.

[0076] The cuff can be deflated using a valve with a controllable deflation rate to gradually reduce the cuff's pressure, thereby gradually decreasing the pressure on the brachial artery until blood circulation is restored within the artery. As shown in Figure 7 , the pressure within the cuff is reduced at a first average pressure reduction rate, V11.

[0077] S50 . Detect a second target signal during the pressure reduction process and obtain the pressure applied to the user's limb when the signal is detected, wherein the second target signal is used to represent a state transition of the target artery from occlusion to flow.

[0078] 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 transitions from being blocked to recirculating, and a pulse is regenerated downstream of the blocked artery. A pressure oscillation wave signal can also be detected downstream. Specifically, a small airbag and a pressure sensor or other detection device can be used to detect the pressure oscillation wave signal in the artery downstream of the airbag cuff. The first pressure oscillation wave signal detected is the second target signal. Alternatively, Korotkoff sounds can be detected in the artery of the airbag cuff. These Korotkoff sound signals are the second target signal.

[0079] S60 : Obtaining the systolic pressure based on at least the pressure applied to the user's limb when the signal is detected (the systolic pressure SYS2 according to the auscultation-like method).

[0080] When blood resumes circulating in the brachial artery, the intravascular pressure equals the cuff pressure. By detecting changes in brachial artery blood flow and the corresponding time of these changes, the static pressure of the cuff at that moment can be determined, which is the systolic pressure.

[0081] Electronic blood pressure monitors using the stethoscopic pulse wave method use a method similar to the Korotkoff sound auscultation method. During use, a pulse wave sensor is placed some distance downstream of the Korotkoff sound cuff in the direction of blood flow. After rapidly inflating the cuff to a pressure 20-30 mmHg above the subject's systolic pressure, it is slowly deflated to reduce blood pressure. During the blood pressure measurement process, a distinct pulse oscillation signal is generated at the moment when the artery is completely compressed and blood flow is released. The downstream pulse wave sensor detects this change in blood flow, and the pressure within the cuff at that moment is the systolic pressure. The inflated cuff then continues to slowly deflate, and the pulse wave sensor gradually and steadily detects the pulse signal. When the artery is fully opened and blood flow is normal, the pressure within the cuff is the diastolic pressure. After detecting the diastolic pressure, the cuff can be rapidly deflated to terminate the measurement. However, the pulse signal changes little from the moment blood flow is released to the moment when the artery is fully opened, resulting in large errors in the diastolic pressure calculation. Furthermore, when calculating systolic and diastolic blood pressure using a stethoscope-like method, the pressure relief rate must be limited to 5 mmHg per second or per pulse to ensure measurement accuracy, and may even need to be controlled to 2-3 mmHg per second or per pulse. Furthermore, the pressure application process means the arm is under pressure for a long time during the entire measurement process, resulting in poor comfort.

[0082] During the inflation process of an airbag cuff, the air pump generally delivers pressurized gas at a constant rate. During the initial inflation phase, the cuff expands in volume as the air inside it increases, resulting in a relatively slow increase in pressure. At the end of the inflation phase, the cuff's volume no longer increases significantly with the increase in air inside it, causing the pressure to increase rapidly. Compared to the rapid pressure increase phase, the initial, slower pressure increase phase takes longer, allowing more pressure oscillation wave signals to be collected during this phase. This allows for a more ideal pressure oscillation wave signal and its amplitude envelope curve, resulting in a more accurate diastolic pressure. Furthermore, during the process of deflation of the cuff to reduce pressure on the user's limb, only the second target signal generated when the target artery transitions from blocked to unblocked is used to determine the systolic pressure. Once the systolic pressure is determined, both the systolic and diastolic pressures can be output. Compared to systolic pressure obtained using mean pressure Pm and an amplitude coefficient derived from statistical data, the present invention's method of obtaining systolic pressure using a stethoscope-like method is more adaptable to different user types and offers higher accuracy for individual patients. The measurement method of the present invention takes less time than the traditional oscillometric method of simply superimposing the pressure measurement process and the pressure reduction measurement process, while the latter will cause the user's limb to be under pressure for a long time and poor comfort.

[0083] 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 may easily cause numbness, swelling, or even pain.

[0084] Compared with the prior art, the embodiments of the present invention have at least one of the following beneficial effects:

[0085] 1. Improved the accuracy of diastolic and systolic blood pressure measurements:

[0086] The present invention adopts a method that combines the auscultation-like method and the oscillometric method. During the process of applying pressure on the limbs, the sufficient pulse signal in the low-pressure section of the oscillometric method is fully utilized to calculate only the diastolic pressure, thereby ensuring the measurement accuracy of the diastolic pressure. At the same time, during the process of releasing pressure on the limbs, the auscultation-like pulse wave method principle is adopted. Compared with the oscillometric method principle based on statistics, the auscultation-like method fully reflects the state of individual blood flow when it is flushed, has better individual adaptability, and higher systolic pressure accuracy.

[0087] 2. Reduced non-invasive blood pressure measurement time:

[0088] The method of the present invention can accelerate the pressurization speed in the high pressure range; since the systolic pressure does not need to be calculated during the pressurization measurement process, the pressurization speed in the high pressure range can be accelerated to more than 10 mmHg / s, and the pressurization time is shortened;

[0089] The present invention predicts the cuff pressure height when the systolic blood pressure is unknown, so that the maximum pressure height will only be slightly higher than the systolic blood pressure of the subject, and the pressure is increased to the required height according to different blood pressure levels, thereby reducing unnecessary arm compression time;

[0090] 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 known 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 stethoscope-like 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 saves about 10 seconds of pressure relief time. For hypertensive patients with a large difference between systolic and diastolic blood pressure, the saved measurement time will be more obvious. For subjects with a systolic / diastolic blood pressure of 180 / 80 mmHg, the present invention can save about 20 seconds in the pressure relief process alone.

[0091] 3. Improves the comfort of the subject throughout the blood pressure measurement process:

[0092] Compared with the existing blood pressure measurement principle, the present invention significantly shortens the overall blood pressure measurement time, shortens the time the limbs are compressed, 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, or even pain, in the arm during the measurement process, and improving the comfort of blood pressure measurement.

[0093] In some embodiments, in step S10, incrementally applying pressure to the user's limb to occlude the target artery specifically includes: first applying pressure at a first average pressure rate V11 and then applying pressure at a second average pressure rate V12. The first average pressure rate V11 is lower than the second average pressure rate V12. As shown in FIG8 , FIG8 is a schematic diagram of the change in pressure within the airbag cuff over time when pressure is applied to the user's limb using the first average pressure rate V11 and the second average pressure rate V12. The second average pressure rate V12 is higher than the first average pressure rate V11. During the pressurization process at the first average pressurization rate, the pressure growth in the airbag cuff may be nonlinear (e.g., the pressure growth curve is parabolic); during the pressurization process at the second average pressurization rate, the pressure growth may also be nonlinear (e.g., the pressure growth curve is parabolic); the overall pressure growth curve of the pressurization at the first average pressurization rate and the second average pressurization rate may be two adjacent curves in a parabolic curve, e.g., the pressure growth curve corresponding to the first average pressurization rate may be a relatively gentle section of the parabolic curve (a section with a slower slope growth), while the pressure growth curve corresponding to the first average pressurization rate may be a relatively steep section of the parabolic curve (a section with a faster slope growth).

[0094] In some optional embodiments, pressure is applied at a second average pressure rate in response to the pressure increasing to a predetermined pressure at the first average pressure rate. For example, a pressure threshold for switching the pressure rate is set after the average pressure Pm is calculated based on the first target signal. This pressure threshold can be greater than Pm by a predetermined value. When the pressure in the cuff reaches this pressure threshold, the pressure rate is increased.

[0095] Furthermore, in some embodiments, in step S10, a third target signal is detected during the application of pressure to the user's limb, and the application of pressure is stopped in response to the failure to detect the third target signal. The third target signal is a fluctuating signal generated during the incremental application of pressure to the user's limb. The fluctuating signal represents changes in blood flow in the detected area caused by the pulse, such as a pressure oscillation wave signal. When the fluctuating signal is not detected, it indicates that the target artery has been compressed and blocked, and the application of pressure can then be stopped, and the process of reducing pressure can be initiated. For example, a second airbag cuff can be used downstream of the airbag cuff in conjunction with a pressure sensor to detect the pressure oscillation wave signal. In some optional embodiments, the third target signal can also be a fluctuating signal of other signals, such as a photoelectric signal, an electromagnetic wave signal, an ultrasonic signal, or a piezoelectric signal. Specifically, the fluctuating signal can be obtained downstream of the target artery during the incremental application of pressure to the user's limb using a photoelectric sensor, an airbag pulse sensor, a radar sensor, a Doppler sensor, or a piezoelectric pulse sensor.

[0096] In other embodiments, in step S10, the application of pressure can also be stopped in response to reaching a preset pressure threshold, and the preset threshold is set based on the first target signal. As shown in Figures 7 and 8, Figure 7 is a schematic diagram of the change in pressure over time in the airbag cuff using the blood pressure measurement method of an embodiment of the present invention. 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 application of pressure can be stopped and the process of reducing pressure can be started. Specifically, the first target signal is the pressure oscillation wave signal with the largest amplitude value obtained during 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.

[0097] 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 rate and then reducing the pressure at a second average pressure reduction rate. The second average pressure reduction rate is greater than the first average pressure reduction rate, which allows the airbag cuff to be deflated quickly and reduces 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 rate. Further, in some embodiments, in step S50, in response to confirming that the second target signal is detected, the pressure is switched to being reduced at the second average pressure reduction rate. After the second target signal is detected, the user's systolic blood pressure can be calculated. Therefore, once the second target signal is detected, the airbag cuff can be quickly deflated at the second average pressure reduction rate to remove pressure from the user's limbs as soon as possible.

[0098] In some embodiments, in step S50, the second target signal is the first fluctuation signal detected during the process of reducing pressure on the user's limb. This fluctuation signal represents changes in blood flow at the detected site caused by the pulse, such as a pressure oscillation signal. The pressure oscillation signal of the target artery is detected downstream of the occluded artery using a second airbag cuff and a pressure sensor. During the process of reducing pressure on the user's limb, after the artery transitions from closed to open, the pressure oscillation can propagate downstream. The moment the first pressure oscillation signal is detected can be considered the moment the artery transitioned from closed to open. Specifically, the starting point of the first pressure oscillation signal is used as the moment the artery transitioned from closed to open. The static pressure of the airbag cuff at that moment can be subsequently 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 fluctuation signal can be obtained downstream of the target artery during the process of gradually reducing pressure on the user's limb using a photoelectric sensor, an airbag pulse sensor, a radar sensor, a Doppler sensor, or a piezoelectric pulse sensor.

[0099] Furthermore, in some embodiments, in step S50, the first fluctuation signal is the first 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 of two consecutive pressure oscillation wave signals detected for the first time. To avoid interference, whether the two detected pressure oscillation wave signals are continuous can be determined based on the user's heart rate. In some optional embodiments, the first fluctuation signal is the first of three consecutive fluctuation signals detected for the first time.

[0100] In some embodiments, in step S50, the second target signal may 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.

[0101] In some embodiments, in step S60, a predicted systolic pressure SYS1 is further calculated 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 (the auscultation-like systolic pressure SYS2) and the predicted systolic pressure. Calculating the predicted systolic pressure based on the first target signal may be calculating the systolic pressure as the predicted systolic pressure based on the mean pressure Pm using an amplitude coefficient method. Calculating 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 may be calculating an average or weighted average of the two.

[0102] 4 to 6 , the present invention provides a blood pressure measurement system.

[0103] The blood pressure measurement system includes a main unit, an airbag cuff, and a blood flow sensing device. The main unit is equipped 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.

[0104] The limb pressure module is used to apply pressure to or release pressure on the limb by the airbag structure cuff; the airbag structure cuff can be wrapped around the arm to apply pressure to the arm, pressurize the blood vessels in the arm, and block 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 the airbag cuff, respectively, so as to apply pressure to or release pressure on the limb;

[0105] The limb pressure sensing module is used to sense the air pressure signal and collect the pulse wave signal from the airbag 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 airbag cuff 1;

[0106] The blood flow sensing device is located downstream of the arterial occlusion point of the airbag cuff and is used to detect changes in blood flow within the blood vessel. The blood flow sensing device utilizes a second airbag cuff 2 filled with a predetermined amount of gas. The second airbag cuff 2 is stably fixed downstream of the arterial occlusion point of the first airbag cuff 1 and is used to detect changes in the blood pulse during blood flow within the blood vessel. The second airbag cuff 2 can be smaller than the first airbag cuff 1 and is used to detect blood flow signals, not to completely occlude the artery.

[0107] The blood flow sensing module is used to collect blood circulation 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 changes from the second airbag cuff 2;

[0108] 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 are used to inflate or quickly deflate the blood flow sensing device (i.e., the second airbag cuff 2) to pressurize or quickly relieve pressure on the limb.

[0109] The blood pressure calculation module is used to calculate the systolic pressure and diastolic pressure based on 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 specifically be a single-chip microcomputer, used to calculate the systolic pressure and diastolic pressure based on the signals collected by the limb pressure sensing module (first air pressure sensor 11) and the blood flow through the induction sensing module.

[0110] 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. When the pulse wave signal intensity decreases from strong to a certain level or the current air pressure in the airbag structure cuff exceeds the estimated high pressure, or the blood flow sensing module fails to 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.

[0111] During the process of the airbag structure cuff relieving pressure on the limb through the limb pressure module, the blood flow passes through the induction sensor module to detect the pulse oscillation signal when the blood flow is rushed out, and the blood pressure calculation module uses the current signal collected by the corresponding limb pressure sensor 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.

[0112] 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.

[0113] The certain degree mentioned herein is 30-70% of the maximum pulse wave signal intensity.

[0114] In some embodiments, a blood pressure measurement system includes a pressure-applying device 30, a first sensing device 10, a second sensing device 20, and a controller. The pressure-applying device 30 is used to apply pressure to a user's limb in a controlled manner, such as by applying pressure incrementally or incrementally. The first sensing device 10 is used to obtain a pressure signal; the second sensing device 20 is used to obtain a second target signal. The controller 40 can be programmed to control the operation of the aforementioned devices and calculate the user's systolic and diastolic blood pressures after obtaining the corresponding signals.

[0115] 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 each 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 when the internal air is inflated and pressurized, thereby blocking blood flow. In addition to being used to compress the limbs, the first airbag cuff 1 is also used to convert the pulse signal into an air pressure signal, so it is also 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. Second sensing device 20 includes a second air pressure sensor 21, a second airbag cuff 2, and a second pipeline connecting the two. Second air pressure sensor 21 can pick up the air pressure signal within second airbag cuff 2 through the second pipeline. Second airbag cuff 2 is stably fixed downstream of the arterial occlusion point of first airbag cuff 1 and is used to pick up pulse changes during blood circulation within the blood vessel. The air pressure signal from second airbag cuff 2 can reflect the arterial pulsation condition.

[0116] 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.

[0117] In addition to airbag cuffs and air pumps, other mechanical structures can also be used to achieve pressure and pressure reduction on the limb. For example, in some embodiments, the pressure-applying device can be a ring or C-shaped hoop with a variable diameter. This uses a mechanical structure rather than pressurized gas to change the hoop's diameter. As the hoop's diameter decreases, it gradually compresses the user's limb, effectively applying increasing pressure to the limb. As the hoop's diameter increases, it gradually reduces the pressure on the user's limb.

[0118] First sensing device 10 and second sensing device 20 are devices for collecting external signals, and they perform signal collection operations according to instructions from controller 40. In some embodiments, first sensing device 10 can also be a strain sensor used in conjunction with a mechanical pressure device, and second sensing device 20 can be a photoelectric sensor, a radar sensor, a Doppler sensor, or a piezoelectric pulse sensor.

[0119] The controller 40 may be a single-chip microcomputer including a memory and a processor. The controller 40 can send control signals to the pressure-applying device 30 using a pre-set program, causing it to apply or release pressure to the limb as instructed. The controller 40 also calculates the signals collected by the first sensing device 10 and the second sensing device 20 according to the pre-set program to obtain diastolic and systolic pressures.

[0120] After receiving a user instruction and initiating the measurement process, the blood pressure measurement system can automatically execute the blood pressure measurement method described in the aforementioned embodiment. For example, the method for measuring blood pressure using the aforementioned blood pressure measurement system includes the following steps:

[0121] S1, Pressurization Process: The limb pressure module inflates the airbag cuff at an average pressure velocity V1. The limb pressure sensing module collects pulse wave signals from the airbag cuff. Simultaneously, the blood flow sensing control module controls the on and off of the blood flow sensing device. When the blood flow sensing device is on, it senses blood flow within the blood vessels. The blood flow sensing module collects the blood flow signals sensed by the blood flow sensing device.

[0122] During the pressurization process, the pulse wave signal in the airbag cuff and the blood flow signal at the location where the blood flows through the sensing device are simultaneously collected. In the blood pressure calculation module, when the pulse wave signal strength in the airbag cuff is analyzed to decrease from strong to half of the maximum pulse wave signal strength, or when the blood flow signal at the location where the blood flows through the sensing device disappears completely, the air pressure signal in the airbag cuff at this time is used as the predicted systolic pressure SYS1. After that, the limb pressure module stops pressurizing, and the blood pressure calculation module calculates the diastolic pressure DIA using the oscillometric method.

[0123] S2, slow decompression process: the airbag structure cuff slowly decompresses at the first average pressure reduction speed V21 through the limb pressure module. At the same time, the blood flow passes through the sensing module to collect the blood flow signal in the sensing device in real time. When the blood flow passes through the sensing 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 by the stethoscope method, and the slow decompression is stopped at this time.

[0124] S3, rapid decompression process: the limb pressure module in the host controls the airbag structure cuff to quickly 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 sensing, and the measurement ends.

[0125] The advantages of the blood pressure measurement method and system of the embodiment of the present invention are illustrated below by comparing the data during the specific measurement process of the embodiment and the comparative example.

[0126] Example 1

[0127] The blood pressure measurement system shown in FIG4 to FIG6 is used to measure the user's blood pressure.

[0128] During the pressurization process, the first air pump 31 in the pressurization device 30 inflates the first airbag cuff 1, increasing its internal pressure. The average pressurization rate V1 can be 10 mmHg / s. Simultaneously, the second air pump 51 inflates the second airbag cuff 2 at the same rate until the pressure inside the cuff reaches 70 mmHg.

[0129] During the pressurization process of 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 transmitted by the first sensing device 10 and statistically calculates the first target signal, i.e., the pressure oscillation wave signal with the largest oscillation amplitude. When the amplitude of the pressure oscillation wave signal in the first airbag cuff 1 is detected to have weakened to half of its 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. A 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 this pressure threshold, inflation of the first airbag cuff 1 is stopped. At this time, the pressure exerted by the first airbag cuff 1 on the user's limb is at its maximum. The controller 40 calculates the diastolic pressure DIA based on the series of pressure oscillation wave signals according to the principle of oscillometric blood pressure measurement. In some embodiments, when the second sensing 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 .

[0130] Decompression process: The slow-release valve 32 is opened to expel gas from the first airbag cuff 1 to reduce its internal pressure. The pressure reduction rate can be an average of 4 mmHg / s (first average pressure reduction rate V21 = 4 mmHg / s). During the decompression process, the second air pressure sensing device detects the second target signal, i.e., the first pressure oscillation wave signal, from the second airbag cuff 2 in real time. The first pressure oscillation wave signal refers to the first of two or more consecutive pressure oscillation wave signals detected. The static pressure in the first airbag cuff 1 corresponding to the starting moment of the first pressure oscillation wave signal is obtained, i.e., the stethoscope-like systolic pressure SYS2, and output as the systolic pressure. When the second target signal is detected, the first and second quick-release valves 33 and 53 are opened to expel gas from the first and second airbag cuffs 1 and 2 and reduce their pressure. The pressure reduction rate can be an average of 80 mmHg / s (second average pressure reduction rate V22 = 80 mmHg / s).

[0131] For subject A, whose blood pressure measurement results are systolic pressure 130 mmHg and diastolic pressure 80 mmHg, the predicted systolic pressure SYS1 is 130 mmHg, and the maximum pressure of the first airbag cuff 1 is 160 mmHg. The blood pressure measurement time is calculated as follows:

[0132] 1. Pressurization process time: 0-160mmHg adopts 10mmHg / s speed for pressurization, and the pressurization time is 160 / 10=16s;

[0133] 2. Depressurization process time:

[0134] The time taken to reduce blood pressure to 125 mmHg at a rate of 4 mmHg / s is (160-125) / 4=8.75 seconds.

[0135] The time taken to reduce blood pressure to 0 mmHg at a rate of 80 mmHg / s is: 125 / 80≈1.56s;

[0136] Therefore, the total time for blood pressure measurement is approximately: 16s+8.75s+1.56s≈26s.

[0137] 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 pressure height is 210 mmHg, and the measurement takes 32 seconds.

[0138] Comparative Example 1

[0139] A certain 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 stops and exhaust and pressure reduction begin. The pressure reduction rate is 80 mmHg / s.

[0140] For subject A whose blood pressure measurement results are systolic pressure 130 mmHg and diastolic pressure 80 mmHg, the measurement time is 34 seconds.

[0141] For subject B, whose blood pressure measurement results are systolic pressure 180 mmHg and diastolic pressure 80 mmHg, the measurement time is 44 seconds.

[0142] Comparative Example 2

[0143] A certain 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 stops and exhaust and pressure reduction begin. The pressure reduction rate is 5 mmHg / s.

[0144] For subject A whose blood pressure measurement results are systolic pressure 130 mmHg and diastolic pressure 80 mmHg, the measurement time is 33 seconds.

[0145] For subject B, whose blood pressure measurement results are systolic pressure 180 mmHg and diastolic pressure 80 mmHg, the measurement time is 47 seconds.

[0146] Comparative Example 3

[0147] A certain blood pressure measurement system uses a stethoscope-like pulse wave principle. During pressurization, the pressure increases at a rate of 13 mmHg / s. Pressurization stops when the pressure reaches 30 mmHg above the systolic pressure. During depressurization, the pressure decreases at a rate of 4 mmHg / s. During the depressurization process, the system collects the body's pressure oscillation wave signal. When the pressure drops 20 mmHg below the diastolic pressure, it begins decreasing at a rate of 80 mmHg / s until it reaches zero. Systolic and diastolic pressures are then calculated to complete the measurement.

[0148] For subject A whose blood pressure measurement results are systolic pressure 130 mmHg and diastolic pressure 80 mmHg, the measurement time is 38 seconds.

[0149] For subject B, whose blood pressure measurement results are systolic pressure 180 mmHg and diastolic pressure 80 mmHg, the measurement time is 54 seconds.

[0150] The comparison of blood pressure measurement time between Example 1 and the three comparative examples is as follows:

[0151] 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.

[0152] Comparative experiment on clinical accuracy of Example 1 and three comparative examples:

[0153] Based on the ISO 81060-2 (2018) clinical testing standard for sphygmomanometers, 85 people were tested, using mercury sphygmomanometer auscultation values ​​as a reference. The clinical accuracy levels were compared as follows:

[0154] As can be seen from the data in the table, this embodiment combines the advantages of the oscillometric method and the stethoscope-like 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.

[0155] Example 2

[0156] Unlike Example 1, in this embodiment, the second sensor 20 is a photoelectric sensor (with a green light source). The second sensor 20 is fixed downstream of the first airbag cuff 1 along the brachial artery blood flow direction, and is used to pick up blood flow oscillation changes during blood circulation in the blood vessel.

[0157] Referring to FIG7 , taking a subject with a blood pressure test result of 130 / 80 mmHg and a heart rate of 60 beats / min as an example, the measurement process is as follows:

[0158] Pressurization process: The first air pump 31 inflates and pressurizes the first airbag cuff 1 at a rate of 8 mmHg / pulse (first average pressurization rate V11 = 8 mmHg / pulse). When the air pressure in the first airbag cuff 1 reaches 80 mmHg, the first airbag cuff 1 is further inflated and pressurized at a second average pressurization rate V12 of 13 mmHg / pulse, gradually pressurizing and closing the limb artery until the artery is completely blocked. The overall average pressurization rate V1 is greater than the first average pressurization rate V11 and less than the second average pressurization rate V12.

[0159] During the pressurization process, the pressure oscillation signal from the first airbag cuff 1 and the blood flow signal from 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 is used as the predicted systolic pressure SYS1. After continuing to pressurize for 25 mmHg, pressurization is stopped. The diastolic pressure DIA is calculated using the oscillometric principle. The "estimated high pressure" is calculated as follows: 3*PP-2*DIA; where PP is the static pressure value in the first airbag cuff 1 corresponding to the pressure oscillation signal with the maximum amplitude, i.e., 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 signal with an amplitude equal to 70% of the maximum amplitude during the process of the pressure oscillation signal in the first airbag 1 increasing from weak to strong.

[0160] Pressure reduction process: Slow-release valve 32 is opened to deflate first airbag cuff 1 and reduce pressure at a rate of 4 mmHg / pulse. During the pressure reduction process, the photoelectric sensor device collects a second target signal. The static pressure in first airbag cuff 1 corresponding to the start of the second target signal is 130 mmHg, indicating a systolic pressure SYS2 of 130 mmHg, as measured by the sternoscopic method. The weighted average of the systolic pressure SYS2 and the predicted systolic pressure SYS1 is calculated to obtain the output systolic pressure: SYS = (2*SYS1+8*SYS2) / 10, where the weighting is 2:8. Subsequently, the first quick-release valve is used to deflate first airbag cuff 1 at an average rate of 80 mmHg / pulse.

[0161] During the entire process, the relationship between the cuff pressure in the first airbag cuff 1 and time is shown in FIG7 .

[0162] For subject A, whose blood pressure measurement result is 130 / 80 mmHg, the predicted systolic pressure SYS1 is 135 mmHg, the maximum pressure height is 160 mmHg, the systolic pressure SYS2 of the stethoscope method is 130 mmHg, the final calculated systolic pressure SYS is 131 mmHg, and the diastolic DIA is 80 mmHg. The measurement time is calculated as follows:

[0163] 1. During the pressurization process, 8mmHg / pulse rate is used for pressurization from 0 to 80mmHg, and 13mmHg / pulse rate is used for pressurization from 80 to 160mmHg. The pressurization time is 80 / 8 + (160-80) / 13 ≈ 16.15s;

[0164] 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. The pressure reduction time is (160-125) / 4=8.75 seconds.

[0165] 3. Finally, rapidly reduce blood pressure at a rate of 80 mmHg / pulse to end the measurement. The rapid blood pressure reduction time is: 125 / 80 ≈ 1.56 seconds.

[0166] Therefore, the total time for blood pressure measurement is about 26 seconds.

[0167] For subject B, whose blood pressure measurement result is 180 / 80 mmHg, the predicted systolic pressure SYS1 is 185 mmHg, the maximum pressure height is 210 mmHg, the systolic pressure SYS2 of the stethoscope 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:

[0168] 1. During the pressurization process, 8 mmHg / pulse rate is used for pressurization from 0 to 80 mmHg, and 13 mmHg / pulse rate is used for pressurization from 80 to 210 mmHg. The pressurization time is 80 / 8 + (210-80) / 13 = 20 seconds.

[0169] 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. The pressure reduction time is (210-175) / 4=8.75 seconds.

[0170] 3. Finally, the blood pressure is rapidly lowered at a rate of 80 mmHg / pulse to end the measurement. The rapid blood pressure reduction time is: 175 / 80≈2.19s.

[0171] Therefore, the total time for blood pressure measurement is about 31 seconds.

[0172] Comparing Example 2 with the three comparative examples, the overall measurement time comparison is as follows:

[0173] It can be seen from the data in the table that as the pressure difference between systolic and diastolic pressure increases, the blood pressure measurement time of the present invention is shortened more significantly compared with the oscillometric method and the stethoscope-like method.

[0174] Comparative Experiment on Clinical Accuracy of Example 2 and Three Comparative Examples

[0175] Based on the ISO 81060-2 (2018) clinical testing standard for sphygmomanometers, 85 people were tested, using mercury sphygmomanometer auscultation values ​​as a reference. The clinical accuracy levels were compared as follows:

[0176] As can be seen from the data in the table, this embodiment combines the advantages of the oscillometric method and the stethoscope-like 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.

[0177] Example 3

[0178] In this embodiment:

[0179] 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 to press the blood vessels in the arm and block blood flow;

[0180] The second sensing device 20 uses a Doppler pulse probe or a radar probe, which acts below the first airbag cuff 1 and is used to pick up the blood flow oscillation changes during blood circulation in the blood vessels; different from Example 1, in this embodiment, the blood flow passing through the sensing control module is a photoelectric driving circuit; the blood flow passing through the sensing sensing module is a photoelectric collection circuit, which is used to collect the blood flow change oscillation signal during blood circulation from the photoelectric sensing device.

[0181] 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 during blood circulation from the Doppler pulse probe or the radar probe.

[0182] For subject A, whose blood pressure is 130 / 80 mmHg, the measurement method is as follows:

[0183] 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.

[0184] Simultaneously, the pressure oscillation wave signal in the first airbag cuff 1 and the blood flow signal from the Doppler pulse probe or radar probe are collected. When the pressure oscillation wave signal intensity in the first airbag cuff 1 decreases from strong to half of the maximum pressure oscillation wave signal intensity, or when the blood flow change oscillation signal in the Doppler pulse probe or radar probe completely disappears, 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, the pressurization is stopped. At this time, the maximum pressurization height is approximately 160 mmHg. The diastolic pressure DIA is calculated according to the oscillometric principle.

[0185] 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 two 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 systolic pressure SYS2 of the stethoscope method. At this time, the air pressure slowly decreases to about 125 mmHg.

[0186] S3, rapid decompression process: the first airbag cuff 1 decompresses at an average speed V22 of 25 mmHg / s through the first quick release valve 33, and the measurement ends.

[0187] For a subject with a blood pressure measurement result of 130 / 80 mmHg, the predicted systolic pressure SYS1 is 140 mmHg, the maximum pressure 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, 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 at a rate of 8 mmHg / s to 125 mmHg. Finally, the pressure is rapidly reduced at a rate of 25 mmHg / s to end the measurement. The time taken for this blood pressure measurement is: 160 / 8 + (160-125) / 8 + 125 / 25 ≈ 29 seconds;

[0189] For a subject with a blood pressure measurement result of 180 / 80 mmHg, the predicted systolic pressure SYS1 is 190 mmHg, the maximum pressure 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, the pressure is increased rapidly at a rate of 8 mmHg / s from 0 to 210 mmHg. When the pressure in the first cuff reaches 210 mmHg, it is reduced at a rate of 8 mmHg / s to 175 mmHg. Finally, the pressure is rapidly reduced at a rate of 25 mmHg / s to end the measurement. The time taken for this blood pressure measurement is: 210 / 8 + (210-175) / 8 + 175 / 25 ≈ 38 seconds.

[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 3 is significantly shortened, and the measurement comfort is improved.

[0192] Example 4

[0193] In this embodiment:

[0194] 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, pressing the blood vessels in the wrist and blocking blood flow;

[0195] The second sensor device 20 is a photoelectric sensor device, which acts on the finger. 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.

[0196] The pressure-applying device 30 comprises a first air pump 31, a first quick-release valve 33, an airbag wristband, and a slow-release valve 32. This allows the airbag wristband to be inflated or deflated, thereby increasing or decreasing pressure on the limb. The limb pressure sensing module, namely the first air pressure sensor 11, is used to sense air pressure signals from the airbag wristband and collect pressure oscillation wave signals. This design is consistent with that of Example 1.

[0197] 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.

[0198] Taking subject A, whose blood pressure is 130 / 80 mmHg, as an example, the measurement method is as follows:

[0199] 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.

[0200] Simultaneously, the pressure oscillation wave signal from the airbag wristband and the blood flow signal from the photoelectric sensor are collected. When the pressure oscillation wave signal in the airbag wristband decreases from strong to half of the maximum pressure oscillation wave signal, or when the blood flow change oscillation signal in the photoelectric sensor 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 30 mmHg, the pressurization is stopped. At this time, the maximum pressurization height is about 160 mmHg. The diastolic pressure DIA is calculated according to the oscillometric principle.

[0201] S2, slow blood pressure reduction process; the airbag wristband slowly reduces the pressure at an average rate 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 two 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.

[0202] S3, rapid decompression process: the airbag wristband passes through the first quick release valve 31 and rapidly decompresses at an average speed V22 of 50 mmHg / s, and the measurement ends.

[0203] For a subject with a blood pressure measurement result of 130 / 80 mmHg, the predicted systolic pressure SYS1 is 130 mmHg, the maximum pressure 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, the pressure is increased at a rate of 10 mmHg / s from 0 to 80 mmHg, and at a rate of 20 mmHg / s from 80 to 160 mmHg. When the pressure of the airbag wristband reaches 160 mmHg, it is reduced at a rate of 5 mmHg / s to 125 mmHg, and finally at a rate of 50 mmHg / s to end the measurement. The time taken for this blood pressure measurement is: 80 / 10 + (160-80) / 20 + (160-125) / 5 + 125 / 50 ≈ 22 seconds;

[0205] For a subject with a blood pressure measurement result of 180 / 80 mmHg, the predicted systolic pressure SYS1 is 180 mmHg, the maximum pressure 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, the pressure is increased at a rate of 10 mmHg / s from 0 to 100 mmHg, and at a rate of 20 mmHg / s from 100 to 210 mmHg. When the pressure of the airbag wristband reaches 210 mmHg, it is reduced at a rate of 5 mmHg / s to 175 mmHg, and finally at a rate of 50 mmHg / s to end the measurement. The time taken for this blood pressure measurement is: 100 / 10 + (210-100) / 20 + (210-175) / 5 + 175 / 50 ≈ 26 seconds;

[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 4 is significantly shortened, and the measurement comfort is improved.

[0208] Example 5

[0209] In this embodiment:

[0210] 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 to press the blood vessels in the arm and block blood flow;

[0211] The second sensor device 20 is a piezoelectric sensor device, which is located downstream of the first airbag cuff 1 along the direction of blood flow in the arm artery and is used to pick up blood flow oscillation changes during blood circulation in the blood vessels.

[0212] The pressure-applying device 30 comprises 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 pressure on the arm. The limb pressure sensing module, namely the first air pressure sensor 11, is used to sense air pressure signals from the first airbag cuff 1 and collect pressure oscillation wave signals. This design is consistent with that of Example 1.

[0213] 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 sensing device.

[0214] Taking the 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 first air pump in the pressure-applying device pressurizes the first airbag cuff 1 at an average speed V11 of 15 mmHg / s (the average speed of the low-pressure segment 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 segment of V1), so that the limb artery is gradually pressurized and closed until the artery is completely blocked.

[0216] Simultaneously, the pressure oscillation wave signal in the first airbag cuff 1 and the blood flow signal in the piezoelectric sensor device are collected. When the pressure oscillation wave signal in the first airbag cuff 1 decreases from strong to half of the maximum pressure oscillation wave signal, or when the blood flow change oscillation signal in the piezoelectric sensor device completely disappears, 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 25 mmHg, the pressurization is stopped. At this time, the maximum pressurization height is about 160 mmHg. The diastolic pressure DIA is calculated according to the oscillometric principle.

[0217] 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 sensing device in real time. When the piezoelectric sensing device continuously extracts two 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.

[0218] S3, rapid decompression process: the first airbag cuff 1 passes through the quick release valve 1 and rapidly decompresses at an average speed V22 of 100 mmHg / s, and the measurement ends.

[0219] For a subject with a blood pressure measurement result of 130 / 80 mmHg, the predicted systolic pressure SYS1 is 135 mmHg, the maximum pressure 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, the pressure is increased at a rate of 15 mmHg / s from 0 to 80 mmHg and at a rate of 25 mmHg / s from 80 to 160 mmHg. When the pressure of the first cuff 1 reaches 160 mmHg, it is reduced at a rate of 2 mmHg / s to 125 mmHg, and finally at a rate of 100 mmHg / s to end the measurement. The time taken for this blood pressure measurement is: 80 / 15 + (160-80) / 25 + (160-125) / 2 + 125 / 100 ≈ 27 seconds;

[0221] For a subject with a blood pressure measurement result of 180 / 80 mmHg, the predicted systolic pressure SYS1 is 185 mmHg, the maximum pressure 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:

[0222] During the pressurization process, the pressure is increased at 15 mmHg / pulse rate from 0 to 80 mmHg, and at 25 mmHg / pulse rate from 80 to 210 mmHg. When the pressure of the first cuff reaches 210 mmHg, it is reduced at a rate of 2 mmHg / s to 175 mmHg, and finally at a rapid rate of 100 mmHg / s to end the measurement. The time taken for this blood pressure measurement is: 80 / 15 + (210-80) / 25 + (210-175) / 2 + 175 / 100 ≈ 30 seconds;

[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 5 is significantly shortened, and the measurement comfort is improved.

[0224] Example 6

[0225] In this embodiment:

[0226] The pneumatic cuff is replaced with a mechanical strap and piezoelectric sensor, placed between the strap and the upper arm. The strap wraps around the upper arm and applies pressure at an average velocity of V1, compressing the blood vessels and blocking blood flow.

[0227] The second sensing device 20 is a photoelectric sensing 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 vessels.

[0228] 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.

[0229] 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.

[0230] Taking the blood pressure 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:

[0231] S1, pressurization process; the servo drive 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), causing the limb artery to gradually be compressed and closed until the artery is completely blocked.

[0232] At the same time, the pressure oscillation wave signal sensed by the piezoelectric sensor and the blood flow signal in the photoelectric sensor are collected. When the pressure oscillation wave signal intensity sensed by the piezoelectric sensor decreases from strong to half of the maximum pressure oscillation wave signal intensity, or when the blood flow change oscillation signal in the photoelectric sensor disappears completely, the current value sensed by the piezoelectric sensor is used as the predicted systolic pressure SYS1; after continuing to pressurize for 25 mmHg, the pressurization is stopped. At this time, the maximum pressurization height is about 160 mmHg. The diastolic pressure DIA is calculated according to the oscillometric principle.

[0233] 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 two 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 measured by the stethoscope. At this time, the applied pressure has slowly decreased to about 125 mmHg.

[0234] S3, rapid blood pressure reduction process: the mechanical strap is quickly loosened at an average speed of 120 mmHg / s V22, and the measurement ends.

[0235] For a subject with a blood pressure measurement result of 130 / 80 mmHg, the predicted systolic pressure SYS1 is 135 mmHg, the maximum pressure 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:

[0236] During the pressurization process, the pressure is increased at a rate of 15 mmHg / s from 0 to 100 mmHg and at a rate of 35 mmHg / s from 100 to 160 mmHg. When the pressure of the piezoelectric sensor reaches 160 mmHg, it is reduced at a rate of 2 mmHg / s to 125 mmHg, and finally at a rate of 120 mmHg / s to end the measurement. The time taken for this blood pressure measurement is: 100 / 15 + (160-100) / 35 + (160-125) / 2 + 125 / 120 ≈ 27 seconds;

[0237] For a subject with a blood pressure measurement result of 180 / 80 mmHg, the predicted systolic pressure SYS1 is 185 mmHg, the maximum pressure 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:

[0238] During the pressurization process, the pressure is increased at 15 mmHg / pulse rate from 0-100 mmHg, and at 35 mmHg / pulse rate from 100-210 mmHg. When the pressure of the piezoelectric sensor reaches 210 mmHg, it is reduced to 175 mmHg at a rate of 2 mmHg / s. Finally, the cuff is quickly loosened at a rate of 120 mmHg / s to end the measurement. The time taken for this blood pressure measurement is: 100 / 15 + (210-100) / 35 + (210-175) / 2 + 175 / 120 ≈ 29 seconds;

[0239] 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.

[0240] The above description is merely a specific embodiment of the present invention, but the scope of protection of the present invention is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in the present invention, and such modifications or substitutions are intended to be within the scope of protection of the present invention. Therefore, the scope of protection of the present invention shall be subject to the scope of protection of the claims.

Claims

1. A blood pressure measurement method, characterized in that: include: incrementally applying pressure to the user's limb so that the target artery is occluded; 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; Obtaining a first target signal based on the multiple pressure oscillation wave signals, and obtaining diastolic pressure based on the first target signal; Applying decreasing pressure to the user's limbs; Detecting a second target signal during the process of gradually applying pressure to the user's limb and obtaining the pressure applied to the user's limb when the second target signal is detected, wherein the second target signal is used to indicate a state transition of the target artery 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 method according to claim 1, characterized in that: The process of gradually applying pressure to the user's limbs includes: reducing the pressure at a first average pressure reduction rate and then reducing the pressure at a second average pressure reduction rate; The detecting the second target signal in the process of reducing the pressure comprises: detecting the second target signal in 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 method according to claim 2, characterized in that: In response to confirming that the second target signal is detected, switching to a process of reducing the pressure at the second pressure reduction average speed.

4. The blood pressure measurement method according to claim 1, characterized in that: The incrementally applying pressure to the user's limb includes: 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.

5. The blood pressure measurement method according to claim 1, characterized in that: A third target signal is detected during the process of applying pressure, and applying pressure is stopped in response to failure to detect the third target signal; or, applying pressure is stopped in response to reaching a preset pressure threshold, wherein the preset threshold is set based on the first target signal.

6. The blood pressure measurement method 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 method 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 gradually 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 is used to reflect changes in blood flow.

8. The blood pressure measurement method 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 method according to claim 1, characterized in that: The method further includes calculating a predicted systolic blood pressure based on the first target signal, and calculating the systolic blood pressure based on the pressure applied to the user's limb when the second target signal is detected and the predicted systolic blood pressure.

10. The blood pressure measurement method according to claim 1, characterized in that: The calculating and obtaining the systolic pressure based at least on the second target signal is to extract the pressure applied to the user's limb corresponding to the moment when the second target signal is detected.

11. The blood pressure measurement method according to claim 1, characterized in that: The second target signal is detected downstream of the location where the target artery is occluded.

12. 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.

13. The blood pressure measurement system according to claim 12, 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.

14. The blood pressure measurement system according to claim 13, 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.

15. The blood pressure measurement system according to claim 12, 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.

16. The blood pressure measurement system according to claim 12, 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.

17. The blood pressure measurement system according to claim 16, 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.

18. The blood pressure measurement system according to claim 12, 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.

19. The blood pressure measurement system according to claim 18, characterized in that: The first fluctuation signal is the first fluctuation signal of at least two consecutive fluctuation signals detected for the first time.

20. The blood pressure measurement system according to claim 12, 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.

21. The blood pressure measurement system according to claim 12, 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.

22. The blood pressure measurement system according to claim 12, 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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