Wearable device, blood pressure measurement method and related apparatus

Abstract

The present application relates to the field of data processing, and discloses a wearable device, a blood pressure measurement method and a related apparatus. The method comprises: acquiring pressure data sets respectively collected by at least one sensor array; on the basis of the pressure data sets collected by the at least one sensor array, determining an effective pressure sensing unit from among absolute pressure sensing units comprised in the at least one sensor array; on the basis of pressure data collected by the effective pressure sensing unit in the at least one sensor array, determining arterial pressure data respectively corresponding to at least one artery blood vessel; and on the basis of the arterial pressure data corresponding to the at least one artery blood vessel, determining the blood pressure of a user. The arterial pressure data can represent the pressure actually borne by a corresponding artery blood vessel during blood pressure measurement, so that the accuracy of a blood pressure result determined on the basis of the arterial pressure data corresponding to the artery blood vessel is high.

Description

Wearable device, blood pressure measurement method and related device

[0001] This application claims priority to Chinese patent application No. 202311635159.6, filed on November 30, 2023, entitled “Wearable device, blood pressure measurement method and related device”, the entire contents of which are incorporated by reference into this application. Technical Field

[0002] The present application relates to the field of data processing, and in particular to a wearable device, a blood pressure measurement method, and related devices. Background Art

[0003] Blood pressure is a key health monitoring indicator that reflects a person's health. Blood pressure refers to the lateral pressure exerted by the pulsating blood flow on the vessel walls, that is, the pressure perpendicular to the vessel walls. The peak pressure is the systolic pressure, also known as the high pressure, and the trough pressure is the diastolic pressure, also known as the low pressure. Currently, blood pressure is typically measured using an upper arm or wrist sphygmomanometer. For example, with an upper arm sphygmomanometer, the user wears the cuff at heart height. The cuff's bladder is inflated to a pressure exceeding the systolic pressure, obstructing blood flow in the upper arm. The bladder is then gradually deflated, collecting pressure data within the cuff during deflation. This pressure data represents the actual pressure experienced by the arterial vessels during the pressurization process. This pressure data includes the arterial pulse wave signal (also known as dynamic pressure) and the corresponding external pressure signal (also known as static pressure). The user's blood pressure is then determined based on these dynamic and static pressures.

[0004] Among them, the width of the airbag has a decisive influence on the accuracy of blood pressure measurement. For wrist sphygmomanometers, the width of the airbag must be at least 60 mm to ensure that the collected pressure data accurately represents the actual pressure borne by the artery during the pressurization process, thereby ensuring the accuracy of the measurement data. However, with the advancement and development of science and technology, more and more wearable devices are equipped with blood pressure measurement functions. In addition, due to the pursuit of portability and compactness of wearable devices, the width of the wearable strip of wearable devices is usually narrow (usually around 30 mm), which leads to the width of the airbag inside the wearable strip being narrow (also called a narrow airbag). When the narrow airbag is inflated, the cross-section of the narrow airbag is close to a circle, resulting in compression loss, making the collected pressure data higher than the actual pressure borne by the artery, resulting in a higher blood pressure in the final calculation. In other words, when measuring blood pressure through a narrow airbag, the gas pressure inside the narrow airbag cannot accurately represent the actual pressure borne by the artery during the pressurization process, resulting in inaccurate blood pressure results.

[0005] Summary of the Invention

[0006] This application provides a wearable device, a blood pressure measurement method, and related devices, which can solve the problem of inaccurate blood pressure measurement results in related technologies. The technical solution is as follows:

[0007] In a first aspect, a wearable device is provided, which includes a wearable strap, an inflation component, at least one sensor array and a processor, wherein the inflation component includes an air pump and an airbag; the airbag is located on the inner side of the wearable strap and is distributed along the length of the wearable strap, and the air pump is used to inflate and pressurize the airbag and then deflate and decompress it during the process of measuring the user's blood pressure; the at least one sensor array is located on a side of the airbag away from the wearable strap, and when the user wears the wearable device, the at least one sensor array corresponds to the position of at least one artery of the user; the sensor array includes a plurality of absolute pressure sensing units, and the size of the absolute pressure sensing unit in a first direction is not greater than the diameter of the corresponding artery, and the first direction is perpendicular to the flow direction of the corresponding artery; the sensor array is used to collect the pressure borne by the corresponding artery during the process of measuring the user's blood pressure, and the processor is used to determine the user's blood pressure based on the pressure data set collected by the at least one sensor array.

[0008] Because the sensor array includes multiple absolute pressure sensing units, the pressure measured by these absolute pressure sensing units is relative to vacuum pressure. Therefore, the pressure measured by these absolute pressure sensing units is unaffected by changes in atmospheric pressure and accurately reflects the actual pressure conditions. Because at least one sensor array is located on the side of the airbag away from the wearable strap, when a user wears the wearable device, the sensor array can contact the user's skin and collect pressure data at the contact location. This pressure data is relative to vacuum pressure. Compared to methods that collect pressure data inside the airbag, the pressure data collected in this application can accurately represent the actual pressure experienced by the corresponding contact location, thereby ensuring the accuracy of the ultimately determined user blood pressure.

[0009] Optionally, the column direction of the sensor array is the same as the flow direction of the corresponding arterial blood vessel, the multiple absolute pressure sensing units are arranged in M ​​rows and N columns, and the distance between two adjacent absolute pressure sensing units in the same row is not greater than the diameter of the corresponding arterial blood vessel, M is an integer greater than or equal to 1, and N is an integer greater than 1.

[0010] For any artery corresponding to a sensor array, the absolute pressure sensing unit located directly above the artery is at the shortest distance from the artery. Therefore, the pulse wave signal intensity directly above the artery is the highest, and the pulse wave signal intensity gradually decays from directly above the artery toward both sides. If the size of the absolute pressure sensing unit in the first direction is larger than the diameter of the corresponding artery, the pressure data collected by the absolute pressure sensing units in the sensor array will have a small difference, making it difficult to determine the arterial pressure data corresponding to the artery based on the pressure data collected by the absolute pressure sensing units. In the present application, the size of the absolute pressure sensing unit in the first direction is no larger than the diameter of the corresponding artery. This allows the fidelity of the signal details of the pressure data set collected by the sensor array to be higher, facilitates determination of the arterial pressure data corresponding to the artery, and makes the final determined blood pressure more accurate.

[0011] Optionally, the absolute pressure sensing units in two adjacent rows of the plurality of absolute pressure sensing units are arranged in a staggered manner.

[0012] For any artery corresponding to a sensor array, the absolute pressure sensing unit located directly above the artery will capture the strongest pulse wave signal. However, two adjacent absolute pressure sensing units in the same row are typically spaced apart, and the row direction of the sensor array is perpendicular to the flow direction of the corresponding artery. Therefore, the artery may be located within the spacing between two adjacent absolute pressure sensing units in a row of the sensor array. In this case, the two adjacent absolute pressure sensing units cannot be located directly above the artery, and thus cannot capture a pulse wave signal with optimal signal strength. However, because the absolute pressure sensing units in two adjacent rows of the multiple absolute pressure sensing units included in the sensor array are staggered, the sensor array can effectively capture a pulse wave signal with optimal signal strength, thereby ensuring the accuracy of the ultimately determined user blood pressure.

[0013] Optionally, the at least one sensor array includes a first array and / or a second array, the first array corresponds to the radial artery and the second array corresponds to the ulnar artery.

[0014] Optionally, a size of the sensor array in the first direction is greater than three times the diameter of the corresponding arterial blood vessel.

[0015] Because the absolute pressure sensing units in two adjacent rows of the multiple absolute pressure sensing units included in the sensor array may be arranged in an staggered manner, or the number of absolute pressure sensing units included in each row of the sensor array is different and / or the spacing between adjacent absolute pressure sensing units in the same row is different, in this case, the sensor array is not a regular rectangle, that is, the sensor array has multiple sizes in the first direction. At this time, the size of the sensor array in the first direction being greater than three times the diameter of the corresponding arterial blood vessel can be understood as the smallest size of the multiple sizes of the sensor array in the first direction being greater than three times the diameter of the corresponding arterial blood vessel.

[0016] Optionally, the wearable device further comprises a memory for storing a computer program for executing the blood pressure measurement method provided in the second aspect below. The processor is configured to execute the computer program stored in the memory to implement the blood pressure measurement method described in the second aspect below.

[0017] Optionally, the wearable device may further include a communication bus, which is used to establish a connection between the processor and the memory.

[0018] In a second aspect, a blood pressure measurement method using the wearable device described in the first aspect is provided, the method comprising: obtaining a pressure data set respectively collected by the at least one sensor array, the pressure data set being collected by a plurality of absolute pressure sensing units included in the corresponding sensor array during the process of inflation and pressurization or deflation and decompression of the airbag; based on the pressure data set collected by the at least one sensor array, determining an effective pressure sensing unit from the absolute pressure sensing units included in the at least one sensor array, the pressure data collected by the effective pressure sensing unit being able to effectively characterize the pulsation of the user's arterial blood vessels; based on the pressure data collected by the effective pressure sensing units in the at least one sensor array, determining arterial pressure data corresponding to the at least one arterial blood vessel, the arterial pressure data characterizing the actual pressure borne by the corresponding arterial blood vessel during the blood pressure measurement process; and determining the user's blood pressure based on the arterial pressure data corresponding to the at least one arterial blood vessel.

[0019] The present application takes into account that the size of the arterial blood vessels is relatively small relative to the size of the sensor array. Therefore, the present application determines the absolute pressure sensing unit (also known as the effective pressure sensing unit) that can effectively characterize the pulsation of the user's arterial blood vessels from the multiple absolute pressure sensing units included in the sensor array, and then determines the arterial pressure data corresponding to the arterial blood vessels based on the pressure data collected by the effective pressure sensing unit, thereby ensuring the accuracy of the arterial pressure data finally determined. Since the arterial pressure data can characterize the actual pressure that the corresponding arterial blood vessels bear during the blood pressure measurement process, the accuracy of the blood pressure result determined based on the arterial pressure data corresponding to the arterial blood vessels is higher. In addition, when the arterial pressure data corresponding to at least two arterial blood vessels are determined, the present application can also determine the user's blood pressure based on the arterial pressure data corresponding to the at least two arterial blood vessels, thereby further improving the accuracy of the blood pressure measurement.

[0020] During the user's blood pressure measurement, the airbag in the wearable device can be inflated and pressurized at a target rate and then deflated and decompressed, or inflated and pressurized and then deflated and decompressed at a target rate, or inflated and pressurized at a target rate and then deflated and decompressed at a target rate. In other words, during at least one of the two processes of inflation and deflation, the airbag in the wearable device experiences a pressure change at the target rate, and the at least one sensor array can collect a pressure data set during the process of the airbag pressure changing at the target rate.

[0021] Among them, the target rate is set in advance, and the upper limit of the target rate value range is related to the sampling frequency of the sensor array and the user's heart rate. The higher the sampling frequency of the sensor array and / or the higher the user's heart rate, the higher the upper limit of the target rate value range. In other words, the sampling frequency of the sensor array and the user's heart rate are proportional to the upper limit of the target rate value range.

[0022] Optionally, the pressure data set includes multiple sets of pressure data collected by multiple absolute pressure sensing units included in the corresponding sensor array, and each set of pressure data includes pressure data at multiple moments.

[0023] In other words, for any sensor array, the pressure data set collected by the sensor array includes multiple sets of pressure data, which correspond one-to-one to the multiple absolute pressure sensing units included in the sensor array, and each set of pressure data is the pressure data collected by the corresponding absolute pressure sensing unit at multiple moments.

[0024] Optionally, the wearable device determines multiple groups of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array based on the first pressure data set, and determines valid pressure sensing units in the first sensor array from the multiple groups of candidate pressure sensing units.

[0025] Among them, the above-mentioned first pressure data set is a pressure data set collected by a first sensor array, and the first sensor array is any one of the at least one sensor array included in the wearable device. The multiple groups of candidate pressure sensing units correspond one-to-one to multiple first moments. The positions of the same group of candidate pressure sensing units are continuous and the difference between the pressure data collected at the corresponding first moments is within the pressure fluctuation range. The first moment is one of the multiple moments, and the first artery is the artery corresponding to the first sensor array.

[0026] Optionally, the wearable device stores the coordinates of each absolute pressure sensing unit in the first sensor array. In this case, the continuous positions of the same group of candidate pressure sensing units refer to the continuity of the abscissas and / or ordinates of the same group of candidate pressure sensing units. In addition, if the difference between the pressure data collected at the same time by the same group of candidate pressure sensing units is within the pressure fluctuation range, it indicates that the difference in the pressure data collected by the same group of candidate pressure sensing units is small.

[0027] In actual applications, the pressure at the position where the airbag contacts the skin is much greater than the pressure at the position where the airbag does not contact the skin, and the difference in pressure data at the position where the airbag contacts the skin is relatively small. Therefore, if the positions of the same group of candidate pressure sensing units are continuous and the difference in the collected pressure data is small, it means that the group of candidate pressure sensing units may be located at the position where the airbag contacts the skin. In this case, the pressure data collected by the group of candidate pressure sensing units is valid, so that the accuracy and reliability of the user's blood pressure determined subsequently can be guaranteed.

[0028] Optionally, the implementation process of determining the effective pressure sensing unit in the first sensor array from the multiple groups of candidate pressure sensing units includes: determining at least one first sensing unit from the multiple groups of candidate pressure sensing units, and based on the first pressure data set, determining at least one second sensing unit from the absolute pressure sensing units included in the first sensor array, the positions of the at least one second sensing unit are continuous, and the intersection of the at least one first sensing unit and the at least one second sensing unit is used as the effective pressure sensing unit in the first sensor array.

[0029] Based on the dynamic pressure collected by each absolute pressure sensing unit in the first sensor array, the maximum peak-to-peak value corresponding to each absolute pressure sensing unit in the first sensor array is determined to obtain multiple maximum peak-to-peak values. Based on the multiple maximum peak-to-peak values, at least one second candidate sensing unit is determined. The positions of the at least one second candidate sensing unit are continuous, and the differences between the corresponding maximum peak-to-peak values ​​are within the peak-to-peak value fluctuation range. Based on the at least one second candidate sensing unit, at least one second sensing unit is determined.

[0030] For any artery corresponding to a sensor array, the pulse wave signal strength is greatest directly above the artery, and the pulse wave signal strength gradually decays from directly above the artery toward both sides. Therefore, if the positions of at least one second candidate sensor unit are continuous and the corresponding peak-to-peak values ​​differ slightly, it indicates that the at least one second candidate sensor unit is likely located near the artery. In this case, the pressure data collected by the at least one second candidate sensor unit is valid, or in other words, the data collected by the group of candidate pressure sensor units is pressure data that can represent arterial pulsation, thus ensuring the accuracy and reliability of the user's blood pressure subsequently determined.

[0031] In addition, since the first sensing unit is located at the position where the airbag contacts the skin, the second sensing unit is located around the arterial blood vessel, and the effective pressure sensing unit in the first sensor array is the intersection of the at least one first sensing unit and the at least one second sensing unit, the effective pressure sensing unit is an absolute pressure sensing unit located at the position where the airbag contacts the skin and around the arterial blood vessel. In this case, the arterial pressure data determined in the subsequent steps based on the pressure data collected by the effective pressure sensing unit is accurate and valid, thereby further ensuring the accuracy and reliability of the user's blood pressure determined subsequently.

[0032] Optionally, based on the pressure data collected by the effective pressure sensing unit in the second sensor array, the arterial pressure data corresponding to the second arterial vessel is determined, and the second sensor array is any one of the at least one sensor array, and the second arterial vessel is the arterial vessel corresponding to the second sensor array.

[0033] There are multiple implementations for determining the arterial pressure data corresponding to the second arterial vessel based on the pressure data collected by the effective pressure sensing units in the second sensor array, two of which are described below.

[0034] In a first implementation, the pressure data is pressure data collected by the effective pressure sensing unit at multiple time instants, and the arterial pressure data is arterial pressure data corresponding to each of the multiple time instants. In this case, for any one of the multiple time instants, the average or maximum value of the pressure data collected by the effective pressure sensing unit at that time instant is used as the arterial pressure data corresponding to that time instant. Arterial pressure data corresponding to each of the multiple time instants can be obtained in the same manner.

[0035] In a second implementation, pressure data collected by an effective pressure sensing unit in the second sensor array is determined as arterial pressure data corresponding to the second arterial vessel.

[0036] Optionally, based on the pressure data collected by the effective pressure sensing units in the second sensor array, the maximum peak-to-peak value corresponding to each effective pressure sensing unit is determined to obtain at least one maximum peak-to-peak value, and the pressure data collected by the effective pressure sensing unit corresponding to the largest maximum peak-to-peak value among the at least one maximum peak-to-peak value is used as the arterial pressure data corresponding to the second arterial vessel.

[0037] In actual applications, before determining the arterial pressure data corresponding to the at least one arterial vessel based on the pressure data collected by the effective pressure sensing units in the at least one sensor array, the wearable device can also determine the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit in the target sensor array. The tissue attenuation coefficient indicates the attenuation of the pulse wave of the target arterial vessel by the human tissue. The target arterial vessel is the arterial vessel corresponding to the target sensor array, and the target sensor array is any one of the at least one sensor array. Based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit, the pressure data collected by the at least one effective pressure sensing unit is corrected.

[0038] That is to say, the present application takes into account the attenuation of the pulse wave of the target artery by human tissue, and corrects the pressure data collected by the effective pressure sensing unit by calculating the tissue attenuation coefficient, so that the pressure data collected by the corrected effective pressure sensing unit can accurately reflect the pulsation of the artery, thereby ensuring the accuracy and reliability of the user's blood pressure finally determined.

[0039] Determine the distance between the at least one effective pressure sensing unit and the target artery, and determine a unit attenuation coefficient. The unit attenuation coefficient refers to the attenuation of the pulse wave of the target artery by a unit thickness of human tissue. Based on the unit attenuation coefficient and the distance between the at least one effective pressure sensing unit and the target artery, determine the tissue attenuation coefficient corresponding to each of the at least one effective pressure sensing units.

[0040] Optionally, a distance between a first effective pressure sensing unit and a target artery is determined to determine a unit attenuation coefficient. The first effective pressure sensing unit is any one of the at least one effective pressure sensing unit. A value obtained by multiplying the unit attenuation coefficient by the distance between the first effective pressure sensing unit and the target artery is used as the tissue attenuation coefficient corresponding to the first effective pressure sensing unit. Each of the at least one first effective pressure sensing unit is processed in the same manner to determine the tissue attenuation coefficient corresponding to each of the at least one effective pressure sensing units.

[0041] Based on the pressure data collected by the effective pressure sensing units in the target sensor array, the primary pressure sensing unit and the secondary pressure sensing unit among the effective sensing units of the target sensor array are determined. The primary pressure sensing unit is the absolute pressure sensing unit with the highest signal strength among the effective sensing units of the target sensor array, and the signal strength of the secondary pressure sensing unit is less than the signal strength of the primary pressure sensing unit. Based on the primary pressure sensing unit and the secondary pressure sensing unit among the effective sensing units, the distance between the first effective pressure sensing unit and the target artery is determined, as well as the unit attenuation coefficient.

[0042] Based on the pressure data collected by the effective pressure sensing units in the target sensor array, a maximum peak-to-peak value corresponding to each effective pressure sensing unit is determined to obtain at least one maximum peak-to-peak value. The effective pressure sensing unit corresponding to the largest maximum peak-to-peak value among the at least one maximum peak-to-peak values ​​is used as the primary pressure sensing unit. The effective pressure sensing unit corresponding to the largest peak-to-peak value among the at least one maximum peak-to-peak values ​​that is not equal to the largest maximum peak-to-peak value and whose difference is greater than a maximum peak-to-peak value difference threshold is used as the secondary pressure sensing unit.

[0043] When the first effective pressure sensing unit is the primary pressure sensing unit, the methods of determining the distance between the first effective pressure sensing unit and the target artery and determining the unit attenuation coefficient are different from those when the first effective pressure sensing unit is the secondary pressure sensing unit, and will be introduced separately below.

[0044] In the case where the first effective pressure sensing unit is the primary pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, as well as the distance between the target secondary pressure sensing unit and the target artery are determined based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, and the distance between the first effective pressure sensing unit and the target secondary pressure sensing unit in the first direction. The target secondary pressure sensing unit is any secondary pressure sensing unit in the target sensor array. The unit attenuation coefficient is determined based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, as well as the distance between the target secondary pressure sensing unit and the target artery.

[0045] In the case where the first effective pressure sensing unit is a secondary pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, and the distance between the main pressure sensing unit and the target artery are determined based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the main pressure sensing unit, and the distance between the first effective pressure sensing unit and the main pressure sensing unit in the first direction. The unit attenuation coefficient is determined based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the main pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, and the distance between the main pressure sensing unit and the target artery.

[0046] For any one of the at least one effective pressure sensing unit, the pressure data of the effective pressure sensing unit is respectively subtracted from the tissue attenuation coefficient corresponding to the effective pressure sensing unit in a plurality of absolute pressures to obtain a plurality of corrected static pressures, and the pressure data of the effective pressure sensing unit is respectively added to the tissue attenuation coefficient corresponding to the effective pressure sensing unit in a plurality of dynamic pressures to obtain a plurality of corrected dynamic pressures. The plurality of corrected static pressures and the plurality of corrected dynamic pressures are used as the first pressure data of the effective pressure sensing unit to correct the pressure data collected by the effective pressure sensing unit. Each of the at least one effective pressure sensing unit is processed in the same manner to correct the pressure data collected by each of the at least one effective pressure sensing unit.

[0047] For the pressure applied by the airbag (i.e., static pressure), the pressure applied by the airbag first reaches the absolute pressure sensing unit, and then is attenuated by human tissue before reaching the target artery. The static pressure borne by the target artery is smaller than the static pressure collected by the absolute pressure sensing unit. Therefore, by subtracting the tissue attenuation coefficient corresponding to the effective pressure sensing unit from the multiple static pressures, the static pressure can be corrected.

[0048] For the pulse wave generated by the target artery, after being emitted from the target artery, the pulse wave is attenuated by human tissue before reaching the absolute pressure sensing unit. The dynamic pressure generated by the target artery is greater than the dynamic pressure collected by the absolute pressure sensing unit. Therefore, by adding the tissue attenuation coefficient corresponding to the effective pressure sensing unit to the multiple dynamic pressures, the dynamic pressure can be corrected.

[0049] When the number of the at least one arterial vessel is one, the wearable device can directly determine the user's blood pressure based on the arterial pressure data corresponding to the arterial vessel according to a relevant algorithm.

[0050] When the number of the at least one artery is at least two, that is, the at least one artery includes at least two arteries, in this case, there are multiple ways to determine the user's blood pressure based on the arterial pressure data corresponding to the at least two arteries, two of which are introduced below.

[0051] In a first implementation, the arterial pressure data includes static pressures corresponding to multiple moments and dynamic pressures corresponding to each static pressure. The static pressures represent the pressure applied by the airbag, and the dynamic pressures represent the pulsation of the corresponding artery under the pressure of the static pressures. Different weights are assigned to the at least two arteries. In this case, the dynamic pressures corresponding to the same moment in the arterial pressure data of the at least two arteries are multiplied by their respective weights and then added together to obtain a plurality of superimposed dynamic pressures. The static pressures corresponding to the same moment in the dynamic pressure data of the at least two arteries are multiplied by their respective weights and then added together to obtain a plurality of superimposed static pressures. The plurality of superimposed dynamic pressures and the plurality of superimposed static pressures are used as the superimposed arterial pressure data. Based on the superimposed arterial pressure data, the user's blood pressure is determined according to a relevant algorithm.

[0052] In a second implementation, the arterial pressure data includes multiple static pressures and a dynamic pressure corresponding to each static pressure. The static pressure represents the pressure applied by the balloon, and the dynamic pressure represents the pulsation of the corresponding artery under the pressure of the static pressure. In this case, the wearable device can superimpose the dynamic pressures in the arterial pressure data corresponding to the at least two arteries, based on the static pressures in the arterial pressure data corresponding to the at least two arteries, to obtain superimposed arterial pressure data. Based on this superimposed arterial pressure data, the wearable device can determine the user's blood pressure according to a relevant algorithm.

[0053] When the at least two arteries are the ulnar and radial arteries, due to the different depths of the ulnar and radial arteries in human tissue, the irregularities of the human wrist bones, and the influence of the user's wearing style, the pulse wave signal within the airbag, obtained by superimposing the pulse pulsations of the ulnar and radial arteries in the time domain, cannot accurately represent the pulsation of the user's arterial vessels during pressurization, resulting in significant error and further reducing the accuracy of the blood pressure results. The present application can superimpose the arterial pressure data corresponding to the at least two arteries in the static pressure dimension, thereby fundamentally avoiding the problem of large pulse wave signal errors caused by simple superposition in the time domain and further improving the accuracy of blood pressure measurements.

[0054] In a third aspect, a blood pressure measurement device is provided, which is included in the wearable device described in the first aspect, and has the function of implementing the blood pressure measurement method described in the second aspect. The blood pressure measurement device includes at least one module configured to implement the blood pressure measurement method described in the second aspect.

[0055] In a fourth aspect, a computer-readable storage medium is provided, wherein the storage medium stores instructions. When the instructions are executed on a computer, the computer executes the steps of the blood pressure measurement method described in the second aspect.

[0056] In a fifth aspect, a computer program product comprising instructions is provided. When the instructions are executed on a computer, the computer is caused to perform the steps of the blood pressure measurement method described in the first aspect. Alternatively, a computer program is provided. When the computer program is executed on a computer, the computer is caused to perform the steps of the blood pressure measurement method described in the second aspect.

[0057] The technical effects obtained in the above-mentioned third, fourth and fifth aspects are similar to the technical effects obtained by the corresponding technical means in the first and second aspects, and will not be repeated here. BRIEF DESCRIPTION OF THE DRAWINGS

[0058] FIG1 is a schematic diagram of a pressure distribution provided in an embodiment of the present application;

[0059] FIG2 is a schematic diagram of a wrist blood pressure monitor provided in an embodiment of the present application;

[0060] FIG3 is a schematic diagram of a wearable device provided in an embodiment of the present application;

[0061] FIG4 is a schematic diagram of a sensor array provided in an embodiment of the present application;

[0062] FIG5 is a schematic diagram of another sensor array provided in an embodiment of the present application;

[0063] FIG6 is a schematic diagram of a sensor array a provided in an embodiment of the present application;

[0064] FIG7 is a schematic diagram of another sensor array a provided in an embodiment of the present application;

[0065] FIG8 is a schematic diagram of an absolute pressure sensing unit provided in an embodiment of the present application;

[0066] FIG9 is a schematic diagram of another absolute pressure sensing unit provided in an embodiment of the present application;

[0067] FIG10 is a schematic diagram of a sensor array arrangement provided in an embodiment of the present application;

[0068] FIG11 is a schematic diagram of a distance between two adjacent absolute pressure sensing units provided in an embodiment of the present application;

[0069] FIG12 is a schematic diagram of another sensor array arrangement provided in an embodiment of the present application;

[0070] FIG13 is a schematic diagram of the flow direction of an arterial vessel provided in an embodiment of the present application;

[0071] FIG14 is a schematic diagram of a first array and a second array provided in an embodiment of the present application;

[0072] FIG15 is a schematic structural diagram of another wearable device provided in an embodiment of the present application;

[0073] FIG16 is a flow chart of a blood pressure measurement method provided in an embodiment of the present application;

[0074] FIG17 is a schematic diagram of first pressure data provided in an embodiment of the present application;

[0075] FIG18 is a schematic diagram of a pulse wave signal of an arterial blood vessel provided in an embodiment of the present application;

[0076] FIG19 is a schematic diagram of a primary pressure sensing unit and a secondary pressure sensing unit provided in an embodiment of the present application;

[0077] FIG20 is a schematic diagram of superimposed arterial pressure data provided in an embodiment of the present application;

[0078] FIG21 is a schematic structural diagram of a blood pressure measurement device provided in an embodiment of the present application. DETAILED DESCRIPTION

[0079] In order to make the objectives, technical solutions and advantages of the embodiments of the present application clearer, the implementation methods of the present application will be further described in detail below with reference to the accompanying drawings.

[0080] For ease of understanding, before explaining in detail the blood pressure measurement method provided in the embodiment of the present application, the application scenarios involved in the embodiment of the present application are first introduced.

[0081] Blood pressure refers to the lateral pressure exerted by pulsating blood flow on the vessel walls, that is, the pressure perpendicular to the vessel walls. Peak pressure is systolic pressure, also known as high pressure, and trough pressure is diastolic pressure, also known as low pressure. Blood pressure is a key indicator in health monitoring, used to assess a person's health and the progress of critically ill patients' conditions. For example, blood pressure can reflect the normality of several indicators, including cardiac function, blood flow, blood volume, and vasomotor function. Abnormally high or low blood pressure indicates a possible abnormality in any of these indicators. A sudden drop in blood pressure may be caused by insufficient blood volume, abnormal vasodilation, or severe cardiac impairment. Furthermore, chronically high or low blood pressure can cause significant damage to blood vessels and multiple organs throughout the body. Therefore, regular blood pressure monitoring is crucial. It allows for early detection of chronic conditions like hypertension, allowing for timely intervention to prevent worsening conditions. It also helps to detect and prevent premature hypotension. For patients with hypertension, regular blood pressure monitoring helps doctors tailor treatment plans based on the results, ultimately achieving better outcomes.

[0082] Currently, blood pressure is typically measured using an upper arm or wrist blood pressure monitor. For example, with an upper arm blood pressure monitor, the user wears the cuff at heart height. The cuff's airbag is then inflated and pressurized to exceed systolic pressure, blocking blood flow in the upper arm. The airbag is then gradually deflated, collecting pressure data from the deflation process. This pressure data represents the actual pressure experienced by the artery during the pressurization process. This pressure data includes the arterial pulse wave signal (also known as dynamic pressure) and the corresponding external pressurization signal (also known as static pressure). The user's blood pressure is then determined based on this dynamic and static pressures.

[0083] The width of the airbag has a crucial impact on the accuracy of blood pressure measurements. For wrist blood pressure monitors, the airbag width must be at least the standard width (60 mm) to ensure that the collected pressure data accurately represents the actual pressure experienced by the arterial vessels during pressurization, thereby ensuring the accuracy of the measurement data. However, with the advancement and development of technology, more and more wearable devices are equipped with blood pressure measurement functions. Due to the pursuit of portability and compactness, the width of the wearable straps of wearable devices is generally narrow (usually around 30 mm), resulting in a narrower airbag width within the strap (also known as a narrow airbag / narrow-width airbag). When the narrow airbag is inflated, its cross-section approaches a circle, resulting in compression loss, causing the collected pressure data to be higher than the actual pressure experienced by the arterial vessels. Furthermore, as shown in Figure 1, the pressure distribution at the point of contact between the narrow airbag and the skin is uneven compared to that of a standard-width airbag. In this case, the pressure at the point of contact between the narrow airbag and the skin differs significantly from the gas pressure within the airbag, resulting in an inflated blood pressure. That is, when measuring blood pressure through a narrow balloon, the gas pressure inside the narrow balloon cannot accurately represent the actual pressure that the artery is subjected to during the pressurization process, resulting in inaccurate blood pressure results.

[0084] Also, referring to FIG2 , for a wrist blood pressure monitor, the pulse wave signal included in the pressure data inside the airbag collected by the wrist blood pressure monitor is actually the pulse wave signal of the ulnar artery and the radial artery acting on the airbag. For ease of description, the pulse wave signal included in the pressure data within the airbag will be referred to as the "in-airbag pulse wave signal." Specifically, referring to FIG2 , the in-airbag pulse wave signal is actually the time-domain superposition of the ulnar and radial artery pulse wave signals. Ideally, the waveforms of the ulnar and radial artery pulse wave signals should be similar, and the mean arterial pressure (MAP) corresponding to the ulnar and radial arteries should also be close to the user's MAP. However, due to the different depths of the ulnar and radial arteries within human tissue, irregularities in the human wrist bones, and the influence of the user's wearing style, the narrow airbag applies different pressures to the ulnar and radial arteries at the same time. In this case, the in-airbag pulse wave signal, obtained by the time-domain superposition of the ulnar and radial artery pulse pulsations, cannot accurately represent the pulsation of the user's arterial blood vessels during pressurization and has significant errors. This problem further reduces the accuracy of the blood pressure results.

[0085] Based on the above problems, an embodiment of the present application provides a wearable device, which includes a wearable strap, an inflatable component, at least one sensor array and a processor, wherein the inflatable component includes an air pump and an airbag. Since the sensor array includes a plurality of absolute pressure sensing units, the pressure measured by the absolute pressure sensing unit is relative to the vacuum pressure. Therefore, the pressure measured by the absolute pressure sensing unit is not affected by changes in atmospheric pressure and can accurately reflect the actual pressure situation. Since the at least one sensor array is located on the side of the airbag away from the wearable strap, in this case, when the user wears the wearable device, the sensor array can contact the user's skin and collect pressure data at the contact position. The pressure data is relative to the vacuum pressure. Compared with the method of collecting pressure data inside the airbag, the pressure data collected by the embodiment of the present application can accurately represent the actual pressure borne by the corresponding contact position, thereby ensuring the accuracy of the user's blood pressure finally determined. Furthermore, since the embodiment of the present application takes into account that the size of the arterial blood vessels is relatively small relative to the size of the sensor array, the embodiment of the present application can determine the absolute pressure sensing unit (also known as the effective pressure sensing unit) that can effectively characterize the pulsation of the user's arterial blood vessels from the multiple absolute pressure sensing units included in the sensor array, and then determine the arterial pressure data corresponding to the arterial blood vessels based on the pressure data collected by the effective pressure sensing unit, thereby ensuring the accuracy of the arterial pressure data finally determined. Since the arterial pressure data can characterize the actual pressure that the corresponding arterial blood vessels bear during the blood pressure measurement process, the accuracy of the blood pressure result determined based on the arterial pressure data corresponding to the arterial blood vessels is higher. In addition, when the arterial pressure data corresponding to at least two arterial blood vessels are determined, the embodiment of the present application can also determine the user's blood pressure based on the arterial pressure data corresponding to the at least two arterial blood vessels, thereby further improving the accuracy of the blood pressure measurement.

[0086] Please refer to Figure 3, which is a schematic diagram of a wearable device provided in an embodiment of the present application. The wearable device includes a wearable strap 01, an inflation assembly including an air pump (not shown in Figure 3) and an airbag 02, at least one sensor array 03 (two sensor arrays are schematically represented in Figure 3 as the at least one sensor array), and a processor (not shown in Figure 3).

[0087] The airbag 02 is located on the inner side of the wearable strip 01 and is distributed along the length of the wearable strip 01. The air pump is used to inflate and pressurize the airbag 02 and then deflate and decompress it during the process of measuring the user's blood pressure. The at least one sensor array 03 is located on the side of the airbag 02 away from the wearable strip 01. When the user wears the wearable device, the at least one sensor array corresponds to the position of at least one artery of the user.

[0088] For example, please refer to Figure 4. If the at least one sensor array includes sensor array 03a and sensor array 03b, sensor array 03a and sensor array 03b are located on the side of the airbag 02 away from the wearing band 01, and, please refer to Figure 5, when the user wears the wearable device, the sensor array 03a corresponds to the position of the user's artery 1, and the sensor array 03b corresponds to the position of the user's artery 2.

[0089] It should be noted that, when the wearable band 01 and the airbag 02 are two independent components, the airbag 02 is located inside the wearable band 01. Of course, in actual applications, the wearable band 01 and the airbag 02 can also be a single unit, with the airbag 02 located inside the wearable band. When the user wears the wearable device, the at least one sensor array 03 is located on the side of the wearable band 01 that can contact the user's skin.

[0090] In some embodiments, for any one of the at least one sensor arrays 03, the sensor array 03 includes a plurality of absolute pressure sensing units, each having a dimension in a first direction no greater than the diameter of the corresponding artery, the first direction being perpendicular to the flow direction of the corresponding artery. The sensor array 03 is configured to collect the pressure experienced by the corresponding artery during blood pressure measurement of the user, and the processor is configured to determine the user's blood pressure based on the pressure dataset collected by the at least one sensor array 03.

[0091] For example, referring to FIG6 , if the at least one sensor array 03 includes sensor array a, which includes multiple absolute pressure sensing units ( FIG6 schematically illustrates these multiple absolute pressure sensing units using seven absolute pressure sensing units), and referring to FIG6 and FIG7 , the absolute pressure sensing units have a dimension in a first direction that is perpendicular to the flow direction of the corresponding arterial vessel no greater than the diameter of the corresponding arterial vessel. Sensor array a is used to collect the pressure of the corresponding arterial vessel during a user's blood pressure measurement.

[0092] In practical applications, for any artery corresponding to a sensor array, the absolute pressure sensing unit located directly above the artery is at the shortest distance from the artery. Therefore, the pulse wave signal intensity directly above the artery is the highest, and the pulse wave signal intensity gradually decays from directly above the artery toward both sides. Referring to FIG8 , if the size of the absolute pressure sensing unit in the first direction is larger than the diameter of the corresponding artery, the pressure data collected by the absolute pressure sensing units in the sensor array will have a small difference, making it difficult to determine the arterial pressure data corresponding to the artery based on the pressure data collected by the absolute pressure sensing units. In the embodiment of the present application, referring to FIG9 , the size of the absolute pressure sensing unit in the first direction is no larger than the diameter of the corresponding artery. This ensures that the fidelity of the signal details of the pressure data set collected by the sensor array is higher, facilitating the determination of the arterial pressure data corresponding to the artery, and ultimately more accurate blood pressure determination.

[0093] In practical applications, the diameter of a standard human artery is approximately 2 mm to 3 mm. In this case, the diameter of the artery can be any value between 2 mm and 3 mm. For example, the diameter of the artery can be 3 mm. Furthermore, the diameter can be adjusted according to different needs in different situations, and this embodiment of the present application is not limited thereto.

[0094] In some embodiments, for any sensor array 03, the column direction of the sensor array 03 is the same as the flow direction of the corresponding arterial blood vessel, the multiple absolute pressure sensing units are arranged in M ​​rows and N columns, and the distance between two adjacent absolute pressure sensing units in the same row is no greater than the diameter of the corresponding arterial blood vessel, M is an integer greater than or equal to 1, and N is an integer greater than 1.

[0095] It should be noted that the arrangement of the multiple absolute pressure sensing units included in the sensor array 03 is related to the width of the wearable device's airbag, the location and diameter of the arterial blood vessels, and the size of the absolute pressure sensing units. Technicians can adjust the arrangement of the multiple absolute pressure sensing units based on actual needs. For example, if the size of the absolute pressure sensing unit is 1 mm and the diameter of the arterial blood vessels is 3 mm, the multiple absolute pressure sensing units can be arranged in 1 row of 24 columns, 4 rows of 9 columns, or 4 rows of 6 columns. This embodiment of the present application does not limit this arrangement.

[0096] For example, referring to FIG10 , if the at least one sensor array 03 includes sensor array a, the column direction of sensor array a aligns with the flow direction of the corresponding arterial blood vessel, and the seven absolute pressure sensing units of sensor array a are arranged in a row of seven columns. Referring to FIG11 , the distance between two adjacent absolute pressure sensing units in the same row of sensor array a is no greater than the diameter of the corresponding arterial blood vessel.

[0097] Optionally, for any sensor array 03 , the absolute pressure sensing units in two adjacent rows of the multiple absolute pressure sensing units included in the sensor array 03 are arranged in a staggered manner.

[0098] For example, if the at least one sensor array 03 includes a sensor array b, please refer to FIG. 12 . The absolute pressure sensing units in two adjacent rows of the plurality of absolute pressure sensing units included in the sensor array b are arranged in a staggered manner.

[0099] Based on the above description, for any artery corresponding to a sensor array 03, the absolute pressure sensing unit located directly above the artery has the highest pulse wave signal strength. However, there is typically a certain distance between two adjacent absolute pressure sensing units in the same row, and the row direction of the sensor array 03 is perpendicular to the flow direction of the corresponding artery. Therefore, referring to FIG13 , the artery may be located within the distance between two adjacent absolute pressure sensing units in the Xth row of the sensor array 03. In this case, the two adjacent absolute pressure sensing units cannot be located directly above the artery, and thus cannot collect a pulse wave signal with the optimal signal strength. However, because the absolute pressure sensing units in two adjacent rows of the multiple absolute pressure sensing units included in the sensor array 03 are staggered, there is an absolute pressure sensing unit located directly above the artery in the row above and / or below the Xth row. This effectively ensures that the sensor array 03 can collect a pulse wave signal with the optimal signal strength, thereby ensuring the accuracy of the ultimately determined user blood pressure.

[0100] In some embodiments, referring to FIG. 14 , the at least one sensor array 03 includes a first array and / or a second array, the first array corresponds to the radial artery, and the second array corresponds to the ulnar artery.

[0101] Optionally, for any sensor array 03, the size of the sensor array 03 in the first direction is greater than three times the diameter of the corresponding arterial blood vessel. In other words, the sensor array 03 includes at least three absolute pressure sensing units in the first direction.

[0102] It should be noted that, since the absolute pressure sensing units in two adjacent rows of the multiple absolute pressure sensing units included in the sensor array may be arranged in an interlaced manner, or the number of absolute pressure sensing units included in each row of the sensor array is different and / or the spacing between adjacent absolute pressure sensing units in the same row is different, in this case, the sensor array is not a regular rectangle, that is, the sensor array has multiple sizes in the first direction. At this time, the size of the sensor array 03 in the first direction being greater than three times the diameter of the corresponding arterial blood vessel can be understood as the smallest size among the multiple sizes of the sensor array in the first direction being greater than three times the diameter of the corresponding arterial blood vessel.

[0103] In some embodiments, the above-mentioned wearable device is capable of obtaining the pressure data sets collected by the at least one sensor array 03 respectively, and then based on the pressure data sets collected by the at least one sensor array 03, determining the effective pressure sensing unit from the absolute pressure sensing units included in the at least one sensor array 03, and based on the pressure data collected by the effective pressure sensing units in the at least one sensor array 03, determining the arterial pressure data corresponding to the at least one arterial vessel respectively, and determining the user's blood pressure based on the arterial pressure data corresponding to the at least one arterial vessel.

[0104] It should be noted that when the wearable device includes at least two sensor arrays, the arrangement of the at least two sensor arrays, the number of absolute pressure sensing units in the sensor array, and the spacing between the absolute pressure sensing units can be the same or different, and the embodiments of the present application do not limit this.

[0105] The wearable device provided in the embodiments of the present application can be worn on any part of the user where blood pressure can be measured, such as the wrist, leg, upper arm, etc., and the embodiments of the present application do not limit this. In the case where the wearable device is worn on the user's wrist to measure blood pressure, the wearable device can be an electronic device capable of measuring blood pressure, such as a watch, a bracelet, or a wrist electronic blood pressure monitor. In this case, the wearable strip can also be called a wristband, and the embodiments of the present application do not limit this.

[0106] Those skilled in the art should understand that the above-mentioned wearable devices are only examples. Other existing or future wearable devices that are applicable to the embodiments of the present application should also be included in the scope of protection of the embodiments of the present application and are incorporated herein by reference.

[0107] It should be noted that the application scenarios and wearable devices described in the embodiments of the present application are intended to more clearly illustrate the technical solutions of the embodiments of the present application, and do not constitute a limitation on the technical solutions provided in the embodiments of the present application. Ordinary technicians in this field can know that with the evolution of technology and the emergence of new application scenarios, the technical solutions provided in the embodiments of the present application are also applicable to similar technical problems.

[0108] Please refer to Figure 15, which is a schematic diagram of the structure of another wearable device according to an embodiment of the present application. The wearable device can be the wearable device described above. The wearable device includes at least one processor 1501, a communication bus 1502, a memory 1503, and at least one communication interface 1504.

[0109] Processor 1501 may be a general-purpose central processing unit (CPU), a network processor (NP), a microprocessor, or one or more integrated circuits for implementing the solution of the present application, such as an application-specific integrated circuit (ASIC), a programmable logic device (PLD), or a combination thereof. The PLD may be a complex programmable logic device (CPLD), a field-programmable gate array (FPGA), a generic array logic (GAL), or any combination thereof.

[0110] Communication bus 1502 is used to transmit information between the above components. Communication bus 1502 can be divided into address bus, data bus, control bus, etc. For ease of illustration, only one thick line is used in the figure, but this does not mean that there is only one bus or one type of bus.

[0111] The memory 1503 may be a read-only memory (ROM), a random access memory (RAM), an electrically erasable programmable read-only memory (EEPROM), an optical disc (including a compact disc read-only memory (CD-ROM), a compact disc, a laser disc, a digital versatile disc, a Blu-ray disc, etc.), a magnetic disk storage medium or other magnetic storage device, or any other medium that can be used to carry or store desired program code in the form of instructions or data structures and can be accessed by a computer, but is not limited thereto. The memory 1503 may exist independently and be connected to the processor 1501 via the communication bus 1502. The memory 1503 may also be integrated with the processor 1501.

[0112] In some embodiments, the wearable device may further include at least one communication interface 1504, which uses any transceiver-like device for communicating with other devices or communication networks. The communication interface 1504 includes a wired communication interface and may also include a wireless communication interface. The wired communication interface may be, for example, an Ethernet interface. The Ethernet interface may be an optical interface, an electrical interface, or a combination thereof. The wireless communication interface may be a wireless local area network (WLAN) interface, a cellular network communication interface, or a combination thereof.

[0113] As an embodiment, the wearable device may include multiple processors, such as processor 1501 and processor 1505 shown in FIG15 . Each of these processors may be a single-core processor or a multi-core processor. The processor herein may refer to one or more devices, circuits, and / or processing cores for processing data (such as computer program instructions).

[0114] In a specific implementation, as an embodiment, the wearable device may further include an output device and an input device. The output device communicates with the processor 1501 and can display information in a variety of ways. For example, the output device can be a liquid crystal display (LCD), a light emitting diode (LED) display device, a cathode ray tube (CRT) display device, or a projector. The input device communicates with the processor 1501 and can receive user input in a variety of ways. For example, the input device can be a touch screen device or a sensor device.

[0115] In some embodiments, the memory 1503 is used to store program code 1510 for executing the solution of the present application, and the processor 1501 can execute the program code 1510 stored in the memory 1503. The program code 1510 may include one or more software modules. The wearable device can implement the blood pressure measurement method provided in the embodiment of Figure 16 below through the processor 1501 and the program code 1510 in the memory 1503.

[0116] FIG16 is a flow chart of a blood pressure measurement method provided in an embodiment of the present application, which is applied to the wearable device described above. Referring to FIG16 , the method includes the following steps.

[0117] Step 1601: Obtain a pressure data set collected by at least one sensor array included in the wearable device, where the pressure data set is collected by multiple absolute pressure sensing units included in the corresponding sensor array during the airbag inflation and pressurization or deflation and decompression process.

[0118] During the user's blood pressure measurement, the airbag in the wearable device can be inflated and pressurized at a target rate and then deflated and decompressed, or inflated and pressurized and then deflated and decompressed at a target rate, or inflated and pressurized at a target rate and then deflated and decompressed at a target rate. In other words, during at least one of the two processes of inflation and deflation, the airbag in the wearable device experiences a pressure change at the target rate, and the at least one sensor array can collect a pressure data set during the process of the airbag pressure changing at the target rate.

[0119] Among them, the target rate is set in advance, and the upper limit of the target rate value range is related to the sampling frequency of the sensor array and the user's heart rate. The higher the sampling frequency of the sensor array and / or the higher the user's heart rate, the higher the upper limit of the target rate value range. In other words, the sampling frequency of the sensor array and the user's heart rate are proportional to the upper limit of the target rate value range.

[0120] Step 1602: Based on the pressure data set collected by at least one sensor array, determine an effective pressure sensing unit from the absolute pressure sensing units included in the at least one sensor array, and the pressure data collected by the effective pressure sensing unit can effectively represent the pulsation condition of the user's arterial blood vessels.

[0121] In some embodiments, the pressure data set includes multiple sets of pressure data collected by multiple absolute pressure sensing units included in the corresponding sensor array, and each set of pressure data includes pressure data at multiple moments.

[0122] In other words, for any sensor array, the pressure data set collected by the sensor array includes multiple sets of pressure data, which correspond one-to-one to the multiple absolute pressure sensing units included in the sensor array, and each set of pressure data is the pressure data collected by the corresponding absolute pressure sensing unit at multiple moments.

[0123] In one possible implementation, the wearable device determines, based on the first pressure data set, multiple groups of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array, and determines valid pressure sensing units in the first sensor array from the multiple groups of candidate pressure sensing units.

[0124] Among them, the above-mentioned first pressure data set is a pressure data set collected by a first sensor array, and the first sensor array is any one of the at least one sensor array included in the wearable device. The multiple groups of candidate pressure sensing units correspond one-to-one to multiple first moments. The positions of the same group of candidate pressure sensing units are continuous and the difference between the pressure data collected at the corresponding first moments is within the pressure fluctuation range. The first moment is one of the multiple moments, and the first artery is the artery corresponding to the first sensor array.

[0125] In some embodiments, the wearable device stores the coordinates of each absolute pressure sensing unit in the first sensor array. In this case, the continuous positions of the same group of candidate pressure sensing units refer to the continuity of the horizontal coordinates and / or the continuity of the vertical coordinates of the same group of candidate pressure sensing units. In addition, if the difference between the pressure data collected at the same time by the same group of candidate pressure sensing units is within the pressure fluctuation range, it indicates that the pressure data collected by the same group of candidate pressure sensing units have a small difference.

[0126] It should be noted that the pressure fluctuation range is pre-set. For example, the pressure fluctuation range can be set to -5 mmHg to 5 mmHg, and can be adjusted according to different needs in different situations.

[0127] In actual applications, the pressure at the position where the airbag contacts the skin is much greater than the pressure at the position where the airbag does not contact the skin, and the difference in pressure data at the position where the airbag contacts the skin is relatively small. Therefore, if the positions of the same group of candidate pressure sensing units are continuous and the difference in the collected pressure data is small, it means that the group of candidate pressure sensing units may be located at the position where the airbag contacts the skin. In this case, the pressure data collected by the group of candidate pressure sensing units is valid, so that the accuracy and reliability of the user's blood pressure determined subsequently can be guaranteed.

[0128] The implementation process of determining multiple groups of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array based on the first pressure data set includes: determining multiple first moments from multiple moments, and for any one of the multiple first moments, determining a group of candidate pressure sensing units corresponding to the first moment from the absolute pressure sensing units included in the first sensor array based on the multiple first pressure data and the positions of the multiple absolute pressure sensing units included in the first sensor array, wherein the multiple first pressure data correspond one-to-one to the multiple absolute pressure sensing units included in the first sensor array, and the first pressure data is pressure data collected by the corresponding absolute pressure sensing unit at the first moment. Each of the multiple first moments is processed in the same manner to determine the candidate pressure sensing units corresponding to each of the multiple first moments.

[0129] It should be noted that the pressure data collected by the absolute pressure sensing unit at the first moment includes static pressure and dynamic pressure. The static pressure represents the pressure applied by the airbag at the first moment, and the dynamic pressure represents the pulsation of the corresponding arterial blood vessel under the pressure of the static pressure. In this case, the first pressure data may also be the static pressure collected by the corresponding absolute pressure sensing unit at the first moment. In other words, the pressure data (raw pressure data) collected by the absolute pressure sensing unit at the first moment consists of the static pressure and dynamic pressure at the first moment. In this case, the first pressure data may be the raw pressure data collected at the first moment or the static pressure at the first moment, and this embodiment of the application does not limit this.

[0130] Since the first pressure data set may be collected during the airbag inflation and pressurization process or during the airbag deflation and decompression process, if the first pressure data set is collected during the airbag inflation and pressurization process, at least one pressure data whose pressure data is a reference pressure value can be determined from the first pressure data set, and the earliest moment corresponding to the at least one pressure data is used as the first starting moment, and the moment later than the first starting moment among the multiple moments is used as the multiple first moments. If the first pressure data set is collected during the airbag deflation and decompression process, at least one pressure data whose pressure data is a reference pressure value can be determined from the first pressure data set, and the latest moment corresponding to the at least one pressure data is used as the first starting moment, and the moment earlier than the first starting moment among the multiple moments is used as the multiple first moments. Of course, in actual applications, multiple first moments can also be determined from multiple moments in time by other methods. For example, some or all of the multiple moments can be directly used as the multiple first moments, and this embodiment of the present application is not limited to this.

[0131] In actual applications, when the pressure applied by the airbag to the artery is too small or too large, the absolute pressure sensing unit cannot clearly collect the pulse wave data of the artery. Therefore, the reference pressure value is the pressure value at which the absolute pressure sensing unit can clearly collect the pulse wave data of the artery. The reference pressure value is set by technicians based on experience. For example, the reference pressure value can be set to 80 mmHg, and can be adjusted according to different needs in different situations.

[0132] Since the reference pressure value is the pressure value at which the absolute pressure sensing unit can clearly collect the pulse wave data of the arterial blood vessel, if the pressure data collected by an absolute pressure sensing unit in the first sensor array reaches the reference pressure value, it means that the absolute pressure sensing unit in the first sensor array that is closer to the arterial blood vessel can collect the pulse wave signal. In this case, the accuracy of the determined candidate pressure sensing unit can be guaranteed.

[0133] Optionally, the implementation process of determining a group of candidate pressure sensing units corresponding to the first moment from the absolute pressure sensing units included in the first sensor array based on multiple first pressure data and the positions of multiple absolute pressure sensing units included in the first sensor array includes: based on multiple first pressure data and the positions of multiple absolute pressure sensing units included in the first sensor array, determining at least one group of first pressure sensing units from the absolute pressure sensing units included in the first sensor array, the positions of the same group of first pressure sensing units being continuous and the difference between the collected first pressure data being within the pressure fluctuation range, and selecting a group of pressure sensing units from the at least one group of first pressure sensing units as a group of candidate pressure sensing units corresponding to the first moment based on the first pressure data of the at least one group of first pressure sensing units.

[0134] In one possible implementation, based on the first pressure data of each group of first pressure sensing units, the first average values ​​corresponding to each group of first pressure sensing units are determined to obtain at least one first average value, which is the average value of the first pressure data of the corresponding group of first pressure sensing units. A group of first pressure sensing units corresponding to the largest first average value among the at least one first average value is used as a target pressure sensing unit group. In the target pressure sensing unit group, the first pressure sensing units whose first pressure data are less than a first pressure threshold are deleted, and the deleted target pressure sensing unit group is used as a group of candidate pressure sensing units corresponding to the first moment. The first pressure threshold is the product of the first average value corresponding to the target pressure sensing unit group and the pressure ratio.

[0135] The pressure ratio is pre-set, for example, it can be set to 75%, and can be adjusted according to different needs in different situations.

[0136] For example, if the first sensor array includes 48 absolute pressure sensing units arranged in 24 rows and 2 columns, the 48 units are absolute pressure sensing units 1-24 corresponding to the first column and absolute pressure sensing units 1-24 corresponding to the second column. Taking absolute pressure sensing units 1-24 corresponding to the first column as an example, please refer to FIG17 . FIG17 shows first pressure data collected by the 24 absolute pressure sensing units at time A among multiple first moments. The abscissa of FIG17 represents absolute pressure sensing units 1-24, and the ordinate represents first pressure data. As can be seen from FIG17 , the first pressure data of absolute pressure sensing unit 5-16 is greater than the first pressure threshold. Therefore, absolute pressure sensing unit 5-16 is a candidate pressure sensing unit corresponding to time A.

[0137] In some embodiments, the implementation process of determining the valid pressure sensing unit in the first sensor array from the multiple groups of candidate pressure sensing units includes: determining at least one first sensing unit from the multiple groups of candidate pressure sensing units, and based on the first pressure data set, determining at least one second sensing unit from the absolute pressure sensing units included in the first sensor array, the positions of the at least one second sensing unit are continuous, and the intersection of the at least one first sensing unit and the at least one second sensing unit is used as the valid pressure sensing unit in the first sensor array.

[0138] It should be noted that the position continuity of the at least one second sensing unit refers to the continuity of the horizontal coordinate and / or the continuity of the vertical coordinate of the at least one second sensing unit.

[0139] Optionally, each candidate pressure sensing unit in the multiple groups of candidate pressure sensing units, or the intersection of the multiple groups of candidate pressure sensing units, can be used as the at least one first sensing unit. Of course, in actual applications, the at least one first sensing unit can also be determined by other methods, which are not limited in this embodiment of the present application.

[0140] In some embodiments, the first pressure data set includes pressure data collected by each absolute pressure sensing unit in the first sensor array, the pressure data including a static pressure and a dynamic pressure corresponding to the static pressure, the static pressure representing the pressure applied by the airbag, and the dynamic pressure representing the pulsation of the corresponding artery under the compression of the static pressure. In this case, based on the dynamic pressure collected by each absolute pressure sensing unit in the first sensor array, a maximum peak-to-peak value corresponding to each absolute pressure sensing unit in the first sensor array is determined to obtain multiple maximum peak-to-peak values. Based on the multiple maximum peak-to-peak values, at least one second candidate sensing unit is determined, wherein the positions of the at least one second candidate sensing unit are continuous and the difference between the corresponding maximum peak-to-peak values ​​is within a peak-to-peak fluctuation range. Based on the at least one second candidate sensing unit, at least one second sensing unit is determined.

[0141] The peak-to-peak value fluctuation range is set in advance and can be adjusted according to different needs in different situations.

[0142] For any absolute pressure sensing unit in the first sensor array, multiple peak-to-peak values ​​of the dynamic pressure of the absolute pressure sensing unit are determined, and the multiple peak-to-peak values ​​correspond one-to-one to the multiple arterial pulsation cycles included in the dynamic pressure. The largest peak-to-peak value among the multiple peak-to-peak values ​​is used as the corresponding maximum peak-to-peak value of the absolute pressure sensing unit.

[0143] It should be noted that the dynamic pressure collected by the effective pressure sensing unit is actually the pulse wave signal of the arterial blood vessel. Please refer to Figure 18, which is a schematic diagram of a pulse wave signal of an arterial blood vessel. The pulse wave signal includes multiple arterial pulsation cycles, and the peak-to-peak value in the dynamic pressure is the difference between the maximum dynamic pressure and the minimum dynamic pressure in an arterial pulsation cycle.

[0144] In some embodiments, the at least one second candidate sensor unit can be directly determined as the at least one second sensor unit. In other embodiments, for the at least one second candidate sensor unit, the second candidate sensor units whose maximum peak-to-peak value is less than a maximum peak-to-peak value threshold can also be deleted, and the at least one second candidate sensor unit after deletion is used as the at least one second candidate sensor unit, where the maximum peak-to-peak value threshold is the product of the average value of the maximum peak-to-peak value corresponding to the at least one second candidate sensor unit and the peak-to-peak value ratio.

[0145] The peak-to-peak ratio is pre-set, for example, it can be set to 75%, and can be adjusted according to different needs in different situations.

[0146] Based on the above description, for any artery corresponding to a sensor array, the pulse wave signal strength is greatest directly above the artery, and the pulse wave signal strength gradually decays from directly above the artery toward both sides. Therefore, if the positions of at least one second candidate sensor unit are continuous and the corresponding peak-to-peak values ​​differ slightly, it indicates that the at least one second candidate sensor unit is likely located near the artery. In this case, the pressure data collected by the at least one second candidate sensor unit is valid, or in other words, the data collected by the group of candidate pressure sensor units is pressure data that can represent arterial pulsation, thus ensuring the accuracy and reliability of the user's blood pressure subsequently determined.

[0147] In addition, since the first sensing unit is located at the position where the airbag contacts the skin, the second sensing unit is located around the arterial blood vessel, and the effective pressure sensing unit in the first sensor array is the intersection of the at least one first sensing unit and the at least one second sensing unit, the effective pressure sensing unit is an absolute pressure sensing unit located at the position where the airbag contacts the skin and around the arterial blood vessel. In this case, the arterial pressure data determined in the subsequent steps based on the pressure data collected by the effective pressure sensing unit is accurate and valid, thereby further ensuring the accuracy and reliability of the user's blood pressure determined subsequently.

[0148] In summary, the embodiments of the present application can determine the absolute pressure sensing units located at the point where the airbag contacts the skin based on the pressure data collected by the first sensor array. Furthermore, based on the dynamic pressure collected by the first sensor array, they can determine the absolute pressure sensing units located around the artery, thereby further determining the effective pressure sensing units located at the point where the airbag contacts the skin and around the artery. Of course, in practical applications, if the first sensor array has a small number of rows, it is not necessary to determine the absolute pressure sensing units located at the point where the airbag contacts the skin in the first sensor array. Instead, it is sufficient to determine the absolute pressure sensing units located around the artery based on the dynamic pressure collected by the first sensor array, and use these absolute pressure sensing units located around the artery as the effective pressure sensing units.

[0149] If the number of rows in the first sensor array is small, it means that the width of the first sensor array should be smaller than the width of the airbag in the wearable device. In this case, it can be considered that the absolute pressure sensing units in the first sensor array are all located at the contact position between the airbag and the skin. Therefore, the absolute pressure sensing units located around the arterial blood vessels can be directly determined based on the dynamic pressure collected by the first sensor array, and the absolute pressure sensing units around the arterial blood vessels can be used as effective pressure sensing units.

[0150] Step 1603: Based on the pressure data collected by the effective pressure sensing units in at least one sensor array, determine the arterial pressure data corresponding to the at least one arterial blood vessel, where the arterial pressure data represents the actual pressure borne by the corresponding arterial blood vessel during the blood pressure measurement process.

[0151] Based on the pressure data collected by the effective pressure sensing unit in the second sensor array, the arterial pressure data corresponding to the second arterial vessel is determined, the second sensor array is any one of the at least one sensor array, and the second arterial vessel is the arterial vessel corresponding to the second sensor array.

[0152] There are multiple implementations for determining the arterial pressure data corresponding to the second arterial vessel based on the pressure data collected by the effective pressure sensing units in the second sensor array, two of which are described below.

[0153] In a first implementation, the pressure data is pressure data collected by the effective pressure sensing unit at multiple time instants, and the arterial pressure data is arterial pressure data corresponding to each of the multiple time instants. In this case, for any one of the multiple time instants, the average or maximum value of the pressure data collected by the effective pressure sensing unit at that time instant is used as the arterial pressure data corresponding to that time instant. Arterial pressure data corresponding to each of the multiple time instants can be obtained in the same manner.

[0154] In a second implementation, pressure data collected by an effective pressure sensing unit in the second sensor array is determined as arterial pressure data corresponding to the second arterial vessel.

[0155] Optionally, based on the pressure data collected by the effective pressure sensing units in the second sensor array, the maximum peak-to-peak value corresponding to each effective pressure sensing unit is determined to obtain at least one maximum peak-to-peak value, and the pressure data collected by the effective pressure sensing unit corresponding to the largest maximum peak-to-peak value among the at least one maximum peak-to-peak value is used as the arterial pressure data corresponding to the second arterial vessel.

[0156] Optionally, the pressure data is pressure data collected by the effective pressure sensing unit at multiple moments, and the pressure data includes a static pressure and a dynamic pressure corresponding to the static pressure. The static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation of the corresponding artery under the pressure of the static pressure. In other words, the pressure data includes multiple static pressures and multiple dynamic pressures, and the multiple static pressures and the multiple dynamic pressures correspond to the multiple moments in time.

[0157] In this case, based on the pressure data collected by the effective pressure sensing units in the second sensor array, the implementation process of determining the maximum peak-to-peak value corresponding to each effective pressure sensing unit includes: for any effective pressure sensing unit in the second sensor array, determining multiple peak-to-peak values ​​of the dynamic pressure of the effective pressure sensing unit, the multiple peak-to-peak values ​​corresponding one-to-one to the multiple arterial pulsation cycles included in the dynamic pressure, and the largest peak-to-peak value among the multiple peak-to-peak values ​​as the corresponding maximum peak-to-peak value of the effective pressure sensing unit. The effective pressure sensing units in the second sensor array are processed in the same manner to determine the maximum peak-to-peak value corresponding to each effective pressure sensing unit. Of course, in actual applications, the maximum peak-to-peak value corresponding to each effective pressure sensing unit can also be determined by other methods, and the embodiments of the present application do not limit this.

[0158] Based on the above description, the wearable device can use the pressure data collected by the effective pressure sensing unit with the largest MAP among the effective pressure sensing units as the arterial pressure data corresponding to the second artery. Of course, in actual applications, the pressure data collected by any effective pressure sensing unit in the second sensor array can also be determined as the arterial pressure data corresponding to the second artery.

[0159] In actual applications, before determining the arterial pressure data corresponding to the at least one arterial vessel based on the pressure data collected by the effective pressure sensing units in the at least one sensor array, the wearable device can also determine the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit in the target sensor array. The tissue attenuation coefficient indicates the attenuation of the pulse wave of the target arterial vessel by the human tissue. The target arterial vessel is the arterial vessel corresponding to the target sensor array, and the target sensor array is any one of the at least one sensor array. Based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit, the pressure data collected by the at least one effective pressure sensing unit is corrected.

[0160] That is to say, the embodiment of the present application takes into account the attenuation of the pulse wave of the target artery by human tissue, and corrects the pressure data collected by the effective pressure sensing unit by calculating the tissue attenuation coefficient, so that the pressure data collected by the corrected effective pressure sensing unit can accurately reflect the pulsation of the artery, thereby ensuring the accuracy and reliability of the user's blood pressure finally determined.

[0161] In some embodiments, the process of determining the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in the target sensor array includes: determining the distance between the at least one effective pressure sensing unit and the target artery, determining the unit attenuation coefficient, which refers to the attenuation of the pulse wave of the target artery by human tissue of unit thickness, and based on the unit attenuation coefficient and the distance between the at least one effective pressure sensing unit and the target artery, determining the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit.

[0162] Optionally, a distance between a first effective pressure sensing unit and a target artery is determined to determine a unit attenuation coefficient. The first effective pressure sensing unit is any one of the at least one effective pressure sensing unit. A value obtained by multiplying the unit attenuation coefficient by the distance between the first effective pressure sensing unit and the target artery is used as the tissue attenuation coefficient corresponding to the first effective pressure sensing unit. Each of the at least one first effective pressure sensing unit is processed in the same manner to determine the tissue attenuation coefficient corresponding to each of the at least one effective pressure sensing units.

[0163] In some embodiments, based on the pressure data collected by the effective pressure sensing units in the target sensor array, the primary pressure sensing unit and the secondary pressure sensing unit among the effective sensing units of the target sensor array are determined, the primary pressure sensing unit is the absolute pressure sensing unit with the largest signal strength among the effective sensing units of the target sensor array, and the signal strength of the secondary pressure sensing unit is less than the signal strength of the primary pressure sensing unit. Based on the primary pressure sensing unit and the secondary pressure sensing unit among the effective sensing units, the distance between the first effective pressure sensing unit and the target arterial blood vessel is determined, as well as the unit attenuation coefficient.

[0164] Optionally, based on pressure data collected by effective pressure sensing units in the target sensor array, a maximum peak-to-peak value corresponding to each effective pressure sensing unit is determined to obtain at least one maximum peak-to-peak value, and the effective pressure sensing unit corresponding to the largest maximum peak-to-peak value among the at least one maximum peak-to-peak values ​​is used as the primary pressure sensing unit. The effective pressure sensing unit corresponding to the largest peak-to-peak value among the at least one maximum peak-to-peak values ​​that is not equal to the largest maximum peak-to-peak value and whose difference is greater than a maximum peak-to-peak value difference threshold is used as the secondary pressure sensing unit.

[0165] Of course, in practical applications, the primary and secondary pressure sensing units can also be determined in other ways. For example, the effective pressure sensing unit with the largest average value of pressure data collected by the effective pressure sensing units in the target sensor array can be used as the primary pressure sensing unit. In another example, the effective pressure sensing units in the effective pressure sensing units of the target sensor array other than the primary pressure sensing unit can be used as the secondary pressure sensing units. This embodiment of the present application is not limited to this.

[0166] The maximum peak-to-peak value difference threshold is set in advance. For example, the maximum peak-to-peak value difference threshold can be set to 2, and can be adjusted according to requirements in different situations.

[0167] It should be noted that the above-mentioned implementation method of determining the maximum peak-to-peak value corresponding to each effective pressure sensing unit based on the pressure data collected by the effective pressure sensing units in the target sensor array is similar to the implementation method of determining the maximum peak-to-peak value corresponding to each effective pressure sensing unit based on the pressure data collected by the effective pressure sensing units in the second sensor array mentioned above. For details, please refer to the relevant content above and will not be repeated here.

[0168] In actual applications, the wearable device includes a narrow airbag and a pressure sensor for collecting the gas pressure inside the airbag. In this case, after determining the primary pressure sensing unit among the valid sensing units, the mean arterial pressure (MAP) corresponding to the primary pressure sensing unit can also be determined based on the pressure data collected by the primary pressure sensing unit. The MAP corresponding to the pressure sensor can also be determined based on the pressure data collected by the pressure sensor according to a relevant algorithm. If the MAP corresponding to the primary pressure sensing unit is greater than or equal to the MAP corresponding to the pressure sensor, the process returns to step 1601, i.e., re-measures the user's blood pressure. If the MAP corresponding to the primary pressure sensing unit is less than the MAP corresponding to the pressure sensor, the process continues with the step of determining the secondary pressure sensing unit.

[0169] Based on the above description, when the narrow airbag is inflated, the pressure data collected by the air pressure sensor is higher than the actual pressure borne by the arterial blood vessels. Therefore, under normal circumstances, the MAP corresponding to the main pressure sensing unit should be smaller than the MAP corresponding to the air pressure sensor. If the MAP corresponding to the main pressure sensing unit is greater than or equal to the MAP corresponding to the air pressure sensor, it means that the measurement result of the wearable device is incorrect and needs to be remeasured.

[0170] In some embodiments, the pressure data collected by the master pressure sensing unit is pressure data collected by the master pressure sensing unit at multiple moments, and the pressure data includes a static pressure and a dynamic pressure corresponding to the static pressure. In this case, the static pressure corresponding to the first dynamic pressure among the dynamic pressures of the master pressure sensing unit is used as the MAP corresponding to the master pressure sensing unit. The first dynamic pressure is the dynamic pressure corresponding to the maximum peak-to-peak value among the dynamic pressures of the master pressure sensing unit.

[0171] Based on the above description, the peak-to-peak value in the dynamic pressure is the difference between the maximum dynamic pressure and the minimum dynamic pressure in an arterial pulsation cycle. Therefore, the dynamic pressure corresponding to the maximum peak-to-peak value is either the maximum dynamic pressure or the minimum dynamic pressure corresponding to the maximum peak-to-peak value in the corresponding arterial pulsation cycle, or the maximum dynamic pressure of the two dynamic pressures, or the minimum dynamic pressure of the two dynamic pressures, or the average value of the maximum peak-to-peak value in the corresponding arterial pulsation cycle, or the dynamic pressure corresponding to the midpoint of the corresponding arterial pulsation cycle, etc. Of course, in actual applications, the dynamic pressure corresponding to the maximum peak-to-peak value can also be determined by other methods, and this application is not limited to this.

[0172] When the first effective pressure sensing unit is the primary pressure sensing unit, the methods of determining the distance between the first effective pressure sensing unit and the target artery and determining the unit attenuation coefficient are different from those when the first effective pressure sensing unit is the secondary pressure sensing unit, and will be introduced separately below.

[0173] In the case where the first effective pressure sensing unit is the primary pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, as well as the distance between the target secondary pressure sensing unit and the target artery are determined based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, and the distance between the first effective pressure sensing unit and the target secondary pressure sensing unit in the first direction. The target secondary pressure sensing unit is any secondary pressure sensing unit in the target sensor array. The unit attenuation coefficient is determined based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, as well as the distance between the target secondary pressure sensing unit and the target artery.

[0174] In some embodiments, the wearable device stores the distance between any two absolute pressure sensing units in the target sensor array in the first direction. If the first effective pressure sensing unit is the primary pressure sensing unit, the wearable device can determine the distance between the first effective pressure sensing unit and the target artery, and the distance between the target secondary pressure sensing unit and the target artery based on the ratio of the MAP corresponding to the target secondary pressure sensing unit to the MAP corresponding to the first effective pressure sensing unit, and the distance between the first effective pressure sensing unit and the target secondary pressure sensing unit in the first direction, according to relevant formulas such as trigonometric functions.

[0175] It should be noted that the implementation method of determining the MAP corresponding to the target secondary pressure sensing unit is similar to the implementation method of determining the MAP corresponding to the primary pressure sensing unit mentioned above. For details, please refer to the relevant content above and will not be repeated here.

[0176] Based on the above description, since the absolute pressure sensing unit located directly above the artery has the strongest pulse wave signal, and the primary pressure sensing unit is the absolute pressure sensing unit with the strongest signal among the valid sensing units in the target sensor array, referring to FIG19 , the primary pressure sensing unit can be considered to be the absolute pressure sensing unit located directly above the target artery in the target sensor array. The distance between the primary pressure sensing unit and the target artery is distance 1. The secondary pressure sensing unit is the absolute pressure sensing unit located farther from the target artery, and the distance between the secondary pressure sensing unit and the target artery is distance 2. The ratio of the MAP corresponding to the secondary pressure sensing unit to the MAP corresponding to the primary pressure sensing unit can represent the ratio between distance 1 and distance 2. Therefore, based on the ratio of the MAP corresponding to the secondary pressure sensing unit to the MAP corresponding to the primary pressure sensing unit, as well as the distance between the primary and secondary pressure sensing units in the first direction (i.e., distance 3 in FIG19 ), distance 1 and distance 3 can be determined using relevant formulas such as trigonometric functions.

[0177] In other embodiments, if the first effective pressure sensing unit is the primary pressure sensing unit, the wearable device may also determine the distance between the first effective pressure sensing unit and the target artery, and the distance between the target secondary pressure sensing unit and the target artery based on the ratio of the MAP corresponding to the target secondary pressure sensing unit to the MAP corresponding to the first effective pressure sensing unit, the maximum peak-to-peak value corresponding to the target secondary pressure sensing unit and the maximum peak-to-peak value corresponding to the first effective pressure sensing unit, and the distance between the first effective pressure sensing unit and the target secondary pressure sensing unit in the first direction, according to relevant formulas such as trigonometric functions. Of course, in actual applications, the distance between the first effective pressure sensing unit and the target artery, and the distance between the target secondary pressure sensing unit and the target artery may also be determined by other methods, and the embodiments of the present application are not limited to this.

[0178] In actual applications, during the propagation of the pulse wave signal, not all human tissues between the absolute pressure sensing unit and the target artery attenuate the signal. Human tissues with a certain thickness do not affect the signal strength, and the thickness of the human tissue that does not attenuate the signal is related to factors such as the user's age, weight, and gender. Therefore, in some embodiments, the wearable device can also correct the distance between the first effective pressure sensing unit and the target artery, as well as the distance between the target secondary pressure sensing unit and the target artery, that is, obtain the user's basic information, which includes at least one of gender, height data, and weight data, and based on the basic information, correct the distance between the first effective pressure sensing unit and the target artery, as well as the distance between the target secondary pressure sensing unit and the target artery.

[0179] Optionally, the user can input at least one of his / her gender, height data and weight data into the wearable device, so that the wearable device can obtain the basic information of the user.

[0180] Based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, and the distance between the target secondary pressure sensing unit and the target artery, the process of determining the unit attenuation coefficient includes: dividing the MAP difference by the distance difference to obtain the unit attenuation coefficient, the MAP difference being the difference between the MAP of the first effective pressure sensing unit and the MAP of the target secondary pressure sensing unit, the distance difference being the difference between a first distance and a second distance, the first distance being the distance between the first effective pressure sensing unit and the target artery, and the second distance being the distance between the target secondary pressure sensing unit and the target artery.

[0181] In the case where the first effective pressure sensing unit is a secondary pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, and the distance between the main pressure sensing unit and the target artery are determined based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the main pressure sensing unit, and the distance between the first effective pressure sensing unit and the main pressure sensing unit in the first direction. The unit attenuation coefficient is determined based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the main pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, and the distance between the main pressure sensing unit and the target artery.

[0182] The method for determining the distance between the first effective pressure sensing unit and the target artery, as well as the distance between the main pressure sensing unit and the target artery based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the main pressure sensing unit, and the distance between the first effective pressure sensing unit and the main pressure sensing unit in the first direction is similar to the method for determining the distance between the first effective pressure sensing unit and the target artery, as well as the distance between the target secondary pressure sensing unit and the target artery based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, and the distance between the first effective pressure sensing unit and the target secondary pressure sensing unit in the first direction in the above text. For details, please refer to the relevant content above and will not be repeated here.

[0183] The implementation method of determining the unit attenuation coefficient based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the main pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, and the distance between the main pressure sensing unit and the target artery is similar to the implementation method of determining the unit attenuation coefficient based on the pressure data collected by the first effective pressure sensing unit, the pressure data collected by the target secondary pressure sensing unit, the distance between the first effective pressure sensing unit and the target artery, and the distance between the target secondary pressure sensing unit and the target artery. For details, please refer to the relevant content above and will not be repeated here.

[0184] In some embodiments, the pressure data includes multiple static pressures and dynamic pressures corresponding to each static pressure. In this case, the process of correcting the pressure data collected by the at least one effective pressure sensing unit based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit includes: for any one of the at least one effective pressure sensing unit, subtracting the tissue attenuation coefficient corresponding to the effective pressure sensing unit from the pressure data of the effective pressure sensing unit from the multiple absolute pressures to obtain multiple corrected static pressures; adding the tissue attenuation coefficient corresponding to the effective pressure sensing unit to the pressure data of the effective pressure sensing unit from the multiple dynamic pressures to obtain multiple corrected dynamic pressures; and using the multiple corrected static pressures and the multiple corrected dynamic pressures as the first pressure data of the effective pressure sensing unit to correct the pressure data collected by the effective pressure sensing unit. Each of the at least one effective pressure sensing unit is processed in the same manner to correct the pressure data collected by each of the at least one effective pressure sensing unit.

[0185] For the pressure applied by the airbag (i.e., static pressure), the pressure applied by the airbag first reaches the absolute pressure sensing unit, and then is attenuated by human tissue before reaching the target artery. The static pressure borne by the target artery is smaller than the static pressure collected by the absolute pressure sensing unit. Therefore, by subtracting the tissue attenuation coefficient corresponding to the effective pressure sensing unit from the multiple static pressures, the static pressure can be corrected.

[0186] For the pulse wave generated by the target artery, after being emitted from the target artery, the pulse wave is attenuated by human tissue before reaching the absolute pressure sensing unit. The dynamic pressure generated by the target artery is greater than the dynamic pressure collected by the absolute pressure sensing unit. Therefore, by adding the tissue attenuation coefficient corresponding to the effective pressure sensing unit to the multiple dynamic pressures, the dynamic pressure can be corrected.

[0187] Step 1604: Determine the user's blood pressure based on the arterial pressure data corresponding to the at least one arterial vessel.

[0188] When the number of arterial vessels is different, the implementation methods for determining the user's blood pressure based on the arterial pressure data corresponding to the at least one arterial vessel are different, which will be introduced below respectively.

[0189] When the number of the at least one arterial vessel is one, the wearable device can directly determine the user's blood pressure based on the arterial pressure data corresponding to the arterial vessel according to a relevant algorithm.

[0190] When the number of the at least one artery is at least two, that is, the at least one artery includes at least two arteries, in this case, there are multiple ways to determine the user's blood pressure based on the arterial pressure data corresponding to the at least two arteries, two of which are introduced below.

[0191] In a first implementation, the arterial pressure data includes static pressures corresponding to multiple moments and dynamic pressures corresponding to each static pressure. The static pressures represent the pressure applied by the airbag, and the dynamic pressures represent the pulsation of the corresponding artery under the pressure of the static pressures. Different weights are assigned to the at least two arteries. In this case, the dynamic pressures corresponding to the same moment in the arterial pressure data of the at least two arteries are multiplied by their respective weights and then added together to obtain a plurality of superimposed dynamic pressures. The static pressures corresponding to the same moment in the dynamic pressure data of the at least two arteries are multiplied by their respective weights and then added together to obtain a plurality of superimposed static pressures. The plurality of superimposed dynamic pressures and the plurality of superimposed static pressures are used as the superimposed arterial pressure data. Based on the superimposed arterial pressure data, the user's blood pressure is determined according to a relevant algorithm.

[0192] For example, if there are two arteries, namely artery 1 and artery 2, the weight corresponding to artery 1 is weight 1, and the weight corresponding to artery 2 is weight 2. The arterial pressure data corresponding to artery 1 and artery 2 respectively include static pressures corresponding to two moments, namely time 1 and time 2, and dynamic pressures corresponding to each static pressure. Taking time 1 as an example, the static pressure corresponding to artery 1 at time 1 is static pressure 11, and the dynamic pressure corresponding to time 1 is dynamic pressure 11. The static pressure corresponding to artery 2 at time 1 is static pressure 21, and the dynamic pressure corresponding to time 1 is dynamic pressure 21.

[0193] In this case, the static pressure 11 is multiplied by weight 1, the static pressure 21 is multiplied by weight 2, and the weighted static pressure 11 and the weighted static pressure 12 are added together to obtain the superimposed static pressure corresponding to time 1. The dynamic pressure 11 is multiplied by weight 1, the dynamic pressure 21 is multiplied by weight 2, and the weighted dynamic pressure 11 and the weighted dynamic pressure 12 are added together to obtain the superimposed dynamic pressure corresponding to time 1.

[0194] In a second implementation, the arterial pressure data includes multiple static pressures and a dynamic pressure corresponding to each static pressure. The static pressure represents the pressure applied by the balloon, and the dynamic pressure represents the pulsation of the corresponding artery under the pressure of the static pressure. In this case, in some embodiments, the wearable device can superimpose the dynamic pressures in the arterial pressure data corresponding to the at least two arteries, based on the static pressures in the arterial pressure data corresponding to the at least two arteries, to obtain superimposed arterial pressure data. Based on this superimposed arterial pressure data, the wearable device can determine the user's blood pressure according to a relevant algorithm.

[0195] Optionally, the at least two arterial vessels correspond to different weights respectively. In this case, among the dynamic pressures of the arterial pressure data corresponding to the at least two arterial vessels, the dynamic pressures corresponding to the same static pressure are multiplied by their respective corresponding weights and then added to obtain a plurality of superimposed dynamic pressures. The plurality of superimposed dynamic pressures and the static pressures corresponding to the plurality of superimposed dynamic pressures are used as the superimposed arterial pressure data.

[0196] It should be noted that the sum of the weights corresponding to the at least two arterial vessels is 1.

[0197] For example, if the number of arteries is 2, the two arteries are artery 1 and artery 2, the weight corresponding to artery 1 is weight 1, and the weight corresponding to artery 2 is weight 2; the arterial pressure data corresponding to artery 1 includes static pressure 11 and dynamic pressure 11 corresponding to the static pressure 11, and the arterial pressure data corresponding to artery 2 includes static pressure 21 and dynamic pressure 21 corresponding to the static pressure 21.

[0198] If the static pressure 11 is equal to the static pressure 21, the dynamic pressure 11 is multiplied by the weight 1, the dynamic pressure 21 is multiplied by the weight 2, and the weighted dynamic pressure 11 and the weighted dynamic pressure 12 are added together to obtain the superimposed dynamic pressure corresponding to the static pressure 11 (or static pressure 21).

[0199] In the case where the at least two arteries are the ulnar and radial arteries, based on the above description, due to the different depths of the ulnar and radial arteries in human tissue, the irregularities of the human wrist bones, and the influence of the user's wearing method, the pulse wave signal within the airbag, obtained by superimposing the pulse pulsations of the ulnar and radial arteries in the time domain, cannot accurately represent the pulsation of the user's arterial vessels during pressurization, and has a large error, further reducing the accuracy of the blood pressure results. Referring to Figure 20, the embodiment of the present application can superimpose the arterial pressure data corresponding to the at least two arteries in the static pressure dimension, thereby fundamentally avoiding the problem of large errors in the pulse wave signal caused by simple superposition in the time domain, further improving the accuracy of blood pressure measurement.

[0200] Because the sensor array includes multiple absolute pressure sensing units, the pressure measured by the absolute pressure sensing units is relative to vacuum pressure. Therefore, the pressure measured by the absolute pressure sensing units is not affected by changes in atmospheric pressure and can accurately reflect the actual pressure conditions. Because the at least one sensor array is located on the side of the airbag away from the wearable band, in this case, when the user wears the wearable device, the sensor array can contact the user's skin and collect pressure data at the contact position. This pressure data is relative to vacuum pressure. Compared with the method of collecting pressure data inside the airbag, the pressure data collected by the embodiment of the present application can accurately represent the actual pressure experienced by the corresponding contact position, thereby ensuring the accuracy of the user's blood pressure determined. In addition, because the embodiment of the present application takes into account the relatively small size of the artery relative to the size of the sensor array, the embodiment of the present application can determine the absolute pressure sensing unit (also known as the effective pressure sensing unit) that can effectively represent the pulsation of the user's artery from the multiple absolute pressure sensing units included in the sensor array. Based on the pressure data collected by the effective pressure sensing unit, the arterial pressure data corresponding to each artery is determined, thereby ensuring the accuracy of the arterial pressure data determined. Because arterial pressure data can represent the actual pressure experienced by the corresponding artery during blood pressure measurement, the blood pressure result determined based on the arterial pressure data corresponding to that arterial vessel is more accurate. Furthermore, when arterial pressure data corresponding to at least two arteries is determined, embodiments of the present application can also determine the user's blood pressure based on the arterial pressure data corresponding to at least two arteries, thereby further improving the accuracy of blood pressure measurement.

[0201] When two adjacent rows of absolute pressure sensing units within the sensor array are staggered, this effectively ensures that the sensor array can capture pulse wave signals with optimal signal strength, thereby ensuring the accuracy of the ultimately determined user's blood pressure. This embodiment of the present application takes into account the attenuation of the pulse wave of the target arterial vessel by human tissue and corrects the pressure data collected by the effective pressure sensing units by calculating the tissue attenuation coefficient. This corrected pressure data collected by the effective pressure sensing units accurately reflects the pulsation of the arterial vessel, thereby ensuring the accuracy and reliability of the ultimately determined user's blood pressure.

[0202] Figure 21 is a structural schematic diagram of a blood pressure measurement device provided in an embodiment of the present application. The blood pressure measurement device can be implemented by software, hardware, or a combination of both to become part or all of the above-mentioned wearable device. The device includes: an acquisition module 2101, a first determination module 2102, a second determination module 2103, and a third determination module 2104.

[0203] Acquisition module 2101 is configured to acquire pressure datasets collected by at least one sensor array. These pressure datasets are collected by the multiple absolute pressure sensing units included in the corresponding sensor array during the airbag inflation or deflation process. The detailed implementation process is described in the corresponding embodiments above and will not be repeated here.

[0204] The first determination module 2102 is configured to determine, based on the pressure data set collected by the at least one sensor array, an effective pressure sensing unit from the absolute pressure sensing units included in the at least one sensor array, wherein the pressure data collected by the effective pressure sensing unit can effectively represent the pulsation of the user's arterial blood vessels. The detailed implementation process is referred to the corresponding content in the above embodiments and is not repeated here.

[0205] The second determination module 2103 is configured to determine arterial pressure data corresponding to at least one artery based on the pressure data collected by the effective pressure sensing units in the at least one sensor array. The arterial pressure data represents the actual pressure experienced by the corresponding artery during the blood pressure measurement. The detailed implementation process is described in detail in the respective embodiments above and will not be further elaborated here.

[0206] The third determining module 2104 is configured to determine the user's blood pressure based on the arterial pressure data corresponding to at least one arterial vessel. Detailed implementation procedures are described in the corresponding embodiments above and will not be repeated here.

[0207] Optionally, the pressure data set includes multiple sets of pressure data collected by multiple absolute pressure sensing units, and each set of pressure data includes pressure data at multiple moments;

[0208] The first determining module 2102 is specifically configured to:

[0209] determining, based on the first pressure data set, a plurality of candidate groups of pressure sensing units from the absolute pressure sensing units included in the first sensor array;

[0210] The first pressure data set is a pressure data set collected by a first sensor array, the first sensor array is any one of the at least one sensor array, the multiple groups of candidate pressure sensing units correspond one-to-one to multiple first moments, positions of the candidate pressure sensing units in the same group are continuous, and differences between pressure data collected at corresponding first moments are within a pressure fluctuation range, the first moment is one of the multiple moments, and the first artery is the artery corresponding to the first sensor array;

[0211] From the plurality of groups of candidate pressure sensing units, valid pressure sensing units in the first sensor array are determined.

[0212] Optionally, the device further comprises:

[0213] a fourth determining module, configured to determine a tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in a target sensor array, the tissue attenuation coefficient indicating attenuation of a pulse wave of a target artery by human tissue, the target artery being an artery corresponding to the target sensor array, the target sensor array being any one of the at least one sensor array;

[0214] The correction module is used to correct the pressure data collected by the at least one effective pressure sensing unit based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit.

[0215] Optionally, the fourth determining module is specifically configured to:

[0216] determining a distance between at least one active pressure sensing unit and a target arterial vessel;

[0217] Determine a unit attenuation coefficient, which refers to the attenuation of the pulse wave of the target artery by a unit thickness of human tissue;

[0218] Based on the unit attenuation coefficient and the distance between the at least one effective pressure sensing unit and the target arterial blood vessel, the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit is determined.

[0219] Optionally, the arterial pressure data includes a plurality of static pressures and a dynamic pressure corresponding to each static pressure, and the at least one arterial vessel includes at least two arterial vessels, the static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation of the corresponding arterial vessel under the pressure of the static pressure;

[0220] The third determining module 2104 is specifically configured to:

[0221] superimposing the dynamic pressures in the arterial pressure data corresponding to the at least two arterial vessels according to the static pressures in the arterial pressure data corresponding to the at least two arterial vessels to obtain superimposed arterial pressure data;

[0222] The user's blood pressure is determined based on the superimposed arterial pressure data.

[0223] In the embodiment of the present application, since the sensor array includes multiple absolute pressure sensing units, the pressure measured by the absolute pressure sensing units is relative to vacuum pressure. Therefore, the pressure measured by the absolute pressure sensing units is not affected by changes in atmospheric pressure and can accurately reflect the actual pressure conditions. Since the at least one sensor array is located on the side of the airbag away from the wearable band, in this case, when the user wears the wearable device, the sensor array can contact the user's skin and collect pressure data at the contact position. This pressure data is relative to vacuum pressure. Compared with the method of collecting pressure data inside the airbag, the pressure data collected by the embodiment of the present application can accurately represent the actual pressure at the corresponding contact position, thereby ensuring the accuracy of the user's blood pressure. In addition, since the embodiment of the present application takes into account the relatively small size of the artery relative to the size of the sensor array, the embodiment of the present application can determine the absolute pressure sensing unit (also known as the effective pressure sensing unit) that can effectively represent the pulsation of the user's artery from the multiple absolute pressure sensing units included in the sensor array. Based on the pressure data collected by the effective pressure sensing unit, the arterial pressure data corresponding to each artery is determined, thereby ensuring the accuracy of the final arterial pressure data. Because arterial pressure data can represent the actual pressure experienced by the corresponding artery during blood pressure measurement, the blood pressure result determined based on the arterial pressure data corresponding to that arterial vessel is more accurate. Furthermore, when arterial pressure data corresponding to at least two arteries is determined, embodiments of the present application can also determine the user's blood pressure based on the arterial pressure data corresponding to the at least two arteries, thereby further improving the accuracy of blood pressure measurement.

[0224] It should be noted that the blood pressure measurement device provided in the above embodiment is merely illustrated by the division of the aforementioned functional modules when performing blood pressure measurement. In actual applications, the aforementioned functions can be assigned to different functional modules as needed, i.e., the internal structure of the device can be divided into different functional modules to perform all or part of the functions described above. Furthermore, the blood pressure measurement device provided in the above embodiment and the blood pressure measurement method embodiment are based on the same concept. The specific implementation process is detailed in the method embodiment and will not be repeated here.

[0225] An embodiment of the present application also provides a computer-readable storage medium, which stores instructions. When the instructions are executed on a computer, the computer executes the steps of the blood pressure measurement method described in the above embodiment, or executes the steps of the blood pressure measurement method described in the above embodiment.

[0226] The present application also provides a computer program product comprising instructions that, when executed on a computer, cause the computer to perform the steps of the blood pressure measurement method described in the above embodiment. Alternatively, the present application also provides a computer program that, when executed on a computer, causes the computer to perform the steps of the blood pressure measurement method described in the above embodiment.

[0227] In the above embodiments, all or part of the embodiments can be implemented by software, hardware, firmware, or any combination thereof. When implemented using software, all or part of the embodiments can be implemented in the form of a computer program product. The computer program product includes one or more computer instructions. When the computer instructions are loaded and executed on a computer, all or part of the processes or functions described in the embodiments of the present application are generated. The computer can be a general-purpose computer, a special-purpose computer, a computer network, or other programmable device. The computer instructions can be stored in a computer-readable storage medium, or transmitted from one computer-readable storage medium to another computer-readable storage medium. For example, the computer instructions can be transmitted from one website, computer, server, or data center to another website, computer, server, or data center via a wired (e.g., coaxial cable, optical fiber, digital subscriber line (DSL)) or wireless (e.g., infrared, wireless, microwave, etc.) method. The computer-readable storage medium can be any available medium that can be accessed by a computer, or a data storage device such as a server or data center that includes one or more available media integrated therein. The available medium may be a magnetic medium (e.g., a floppy disk, a hard disk, or a magnetic tape), an optical medium (e.g., a digital versatile disc (DVD)), or a semiconductor medium (e.g., a solid state disk (SSD)). It is worth noting that the computer-readable storage medium mentioned in the embodiments of the present application may be a non-volatile storage medium, in other words, a non-transient storage medium.

[0228] It should be understood that the "plurality" mentioned herein refers to two or more. In the description of the embodiments of the present application, unless otherwise specified, " / " means or, for example, A / B can mean A or B; "and / or" in this article is merely a description of the association relationship of associated objects, indicating that there can be three relationships, for example, A and / or B can mean: A exists alone, A and B exist at the same time, and B exists alone. In addition, in order to facilitate a clear description of the technical solutions of the embodiments of the present application, in the embodiments of the present application, words such as "first" and "second" are used to distinguish between identical or similar items with substantially the same functions and effects. Those skilled in the art will understand that words such as "first" and "second" do not limit the quantity and execution order, and words such as "first" and "second" do not necessarily limit them to be different.

[0229] It should be noted that the information (including but not limited to user device information, user personal information, etc.), data (including but not limited to data used for analysis, stored data, displayed data, etc.), and signals involved in the embodiments of this application are all authorized by the user or fully authorized by all parties, and the collection, use, and processing of relevant data must comply with the relevant laws, regulations, and standards of the relevant countries and regions. For example, the pressure data sets collected by at least one sensor array involved in the embodiments of this application were all obtained with full authorization.

[0230] The above description is an embodiment provided for this application and is not intended to limit this application. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principles of this application should be included in the scope of protection of this application.

Claims

1. A wearable device, characterized in that: The wearable device includes a wearable strap, an inflatable component, at least one sensor array and a processor, and the inflatable component includes an air pump and an air bag; The airbag is located inside the wearing band, and the airbag is distributed along the length direction of the wearing band. The air pump is used to inflate and pressurize the airbag and then deflate and decompress it during the process of measuring the blood pressure of the user; The at least one sensor array is located on a side of the airbag away from the wearable band, and when the user wears the wearable device, the at least one sensor array corresponds to a position of at least one artery of the user; The sensor array includes a plurality of absolute pressure sensing units, wherein the size of the absolute pressure sensing units in a first direction is not greater than the diameter of the corresponding arterial blood vessel, and the first direction is perpendicular to the flow direction of the corresponding arterial blood vessel; The sensor array is used to collect the pressure of the corresponding arterial blood vessels during the process of measuring the blood pressure of the user, and the processor is used to determine the blood pressure of the user based on the pressure data set collected by the at least one sensor array.

2. The wearable device according to claim 1, wherein: The column direction of the sensor array is the same as the flow direction of the corresponding arterial blood vessel, the multiple absolute pressure sensing units are arranged in M ​​rows and N columns, and the distance between two adjacent absolute pressure sensing units in the same row is no greater than the diameter of the corresponding arterial blood vessel, M is an integer greater than or equal to 1, and N is an integer greater than 1.

3. The wearable device according to claim 2, characterized in that: The absolute pressure sensing units in two adjacent rows of the plurality of absolute pressure sensing units are arranged in a staggered manner.

4. The wearable device according to claim 1, wherein: The at least one sensor array includes a first array and / or a second array, the first array corresponds to the radial artery and the second array corresponds to the ulnar artery.

5. The wearable device according to claim 1, wherein: The dimension of the sensor array in the first direction is greater than three times the diameter of the corresponding arterial blood vessel.

6. A blood pressure measurement method using the wearable device according to any one of claims 1 to 5, characterized in that: The method comprises: Acquire a pressure data set respectively collected by the at least one sensor array, wherein the pressure data set is collected by a plurality of absolute pressure sensing units included in the corresponding sensor array during the process of inflation and pressurization or deflation and decompression of the airbag; Based on the pressure data set collected by the at least one sensor array, determining an effective pressure sensing unit from the absolute pressure sensing units included in the at least one sensor array, wherein the pressure data collected by the effective pressure sensing unit can effectively represent the pulsation of the arterial blood vessels of the user; Determine arterial pressure data corresponding to the at least one arterial blood vessel based on pressure data collected by effective pressure sensing units in the at least one sensor array, wherein the arterial pressure data represents the pressure actually borne by the corresponding arterial blood vessel during the blood pressure measurement process; The blood pressure of the user is determined based on the arterial pressure data corresponding to the at least one arterial blood vessel.

7. The method according to claim 6, characterized in that The pressure data set includes multiple groups of pressure data collected by the multiple absolute pressure sensing units, each group of pressure data includes pressure data at multiple moments; The determining of effective pressure sensing units from absolute pressure sensing units included in the at least one sensor array based on the pressure data set collected by the at least one sensor array comprises: Based on the first pressure data set, determining a plurality of groups of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array; The first pressure data set is a pressure data set collected by the first sensor array, the first sensor array is any one of the at least one sensor array, the multiple groups of candidate pressure sensing units correspond one-to-one to multiple first moments, the positions of the same group of candidate pressure sensing units are continuous and the difference between the pressure data collected at the corresponding first moments is within the pressure fluctuation range, the first moment is one of the multiple moments, and the first arterial blood vessel is the arterial blood vessel corresponding to the first sensor array; From the multiple groups of candidate pressure sensing units, valid pressure sensing units in the first sensor array are determined.

8. The method according to claim 6, characterized in that Before determining the arterial pressure data respectively corresponding to the at least one arterial blood vessel based on the pressure data collected by the effective pressure sensing units in the at least one sensor array, the method further comprises: Determine a tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in a target sensor array, wherein the tissue attenuation coefficient indicates attenuation of a pulse wave of a target artery by human tissue, wherein the target artery is an artery corresponding to the target sensor array, and the target sensor array is any one of the at least one sensor array; Based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit, the pressure data collected by the at least one effective pressure sensing unit is corrected.

9. The method according to claim 8, characterized in that The step of determining a tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in the target sensor array comprises: determining a distance between the at least one active pressure sensing unit and the target arterial vessel; Determining a unit attenuation coefficient, wherein the unit attenuation coefficient refers to the attenuation of the pulse wave of the target artery by a unit thickness of human tissue; Based on the unit attenuation coefficient and the distance between the at least one effective pressure sensing unit and the target arterial blood vessel, the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit is determined.

10. The method according to claim 6, characterized in that The arterial pressure data includes a plurality of static pressures and a dynamic pressure corresponding to each static pressure, the at least one arterial blood vessel includes at least two arterial blood vessels, the static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation of the corresponding arterial blood vessel under the pressure of the static pressure; The determining the blood pressure of the user based on the arterial pressure data respectively corresponding to the at least one arterial blood vessel comprises: According to the static pressures in the arterial pressure data corresponding to the at least two arterial vessels, the dynamic pressures in the arterial pressure data corresponding to the at least two arterial vessels are superimposed to obtain superimposed arterial pressure data; Based on the superimposed arterial pressure data, the blood pressure of the user is determined.

11. A blood pressure measuring device, characterized in that: The wearable device according to any one of claims 1 to 5, wherein the device comprises: an acquisition module, configured to acquire a pressure data set respectively acquired by the at least one sensor array, wherein the pressure data set is acquired by a plurality of absolute pressure sensing units included in the corresponding sensor array during the process of inflation and pressurization or deflation and decompression of the airbag; A first determination module is configured to determine, based on the pressure data set collected by the at least one sensor array, an effective pressure sensing unit from the absolute pressure sensing units included in the at least one sensor array, wherein the pressure data collected by the effective pressure sensing unit can effectively represent the pulsation of the arterial blood vessels of the user; A second determination module is used to determine arterial pressure data corresponding to the at least one arterial blood vessel based on the pressure data collected by the effective pressure sensing unit in the at least one sensor array, wherein the arterial pressure data represents the pressure actually borne by the corresponding arterial blood vessel during the blood pressure measurement process; The third determination module is used to determine the blood pressure of the user based on the arterial pressure data corresponding to the at least one arterial blood vessel.

12. The device according to claim 11, characterized in that The pressure data set includes multiple groups of pressure data collected by the multiple absolute pressure sensing units, each group of pressure data includes pressure data at multiple moments; The first determining module is specifically used for: Based on the first pressure data set, determining a plurality of groups of candidate pressure sensing units from the absolute pressure sensing units included in the first sensor array; The first pressure data set is a pressure data set collected by the first sensor array, the first sensor array is any one of the at least one sensor array, the multiple groups of candidate pressure sensing units correspond one-to-one to multiple first moments, the positions of the same group of candidate pressure sensing units are continuous and the difference between the pressure data collected at the corresponding first moments is within the pressure fluctuation range, the first moment is one of the multiple moments, and the first arterial blood vessel is the arterial blood vessel corresponding to the first sensor array; From the multiple groups of candidate pressure sensing units, valid pressure sensing units in the first sensor array are determined.

13. The device according to claim 11, characterized in that The device also includes: The fourth determination module is used to determine the tissue attenuation coefficient corresponding to at least one effective pressure sensing unit in the target sensor array. The tissue attenuation coefficient indicates the attenuation of the pulse wave of the target artery by the human tissue, wherein the target artery is the artery corresponding to the target sensor array, and the target sensor array is any one of the at least one sensor array; A correction module is used to correct the pressure data collected by the at least one effective pressure sensing unit based on the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit.

14. The device according to claim 13, characterized in that The fourth determination module is specifically used for: determining a distance between the at least one active pressure sensing unit and the target arterial vessel; Determining a unit attenuation coefficient, wherein the unit attenuation coefficient refers to the attenuation of the pulse wave of the target artery by a unit thickness of human tissue; Based on the unit attenuation coefficient and the distance between the at least one effective pressure sensing unit and the target arterial blood vessel, the tissue attenuation coefficient corresponding to the at least one effective pressure sensing unit is determined.

15. The device according to claim 11, characterized in that The arterial pressure data includes a plurality of static pressures and a dynamic pressure corresponding to each static pressure, the at least one arterial blood vessel includes at least two arterial blood vessels, the static pressure represents the pressure applied by the airbag, and the dynamic pressure represents the pulsation of the corresponding arterial blood vessel under the pressure of the static pressure; The third determination module is specifically used for: According to the static pressures in the arterial pressure data corresponding to the at least two arterial vessels, the dynamic pressures in the arterial pressure data corresponding to the at least two arterial vessels are superimposed to obtain superimposed arterial pressure data; Based on the superimposed arterial pressure data, the blood pressure of the user is determined.

16. A computer-readable storage medium, characterized in that: The storage medium stores instructions, and when the instructions are executed on the computer, the computer executes the steps of any one of the methods described in claims 6-10.

17. A computer program, characterized in that The computer program comprises instructions, and when the instructions are executed on the computer, the computer is caused to execute the steps of the method according to any one of claims 6 to 10.

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