Ultrasonic array sensor, ultrasonic detection device and equipment and blood vessel measurement method

Abstract

The embodiment of the invention discloses an ultrasonic array sensor, an ultrasonic detection device, ultrasonic detection equipment and a blood vessel measurement method, relates to the technical field of ultrasonic detection, and solves the problem that the detection value is inaccurate when the blood vessel diameter and the blood flow velocity are simultaneously detected by the existing ultrasonic technology. The ultrasonic array sensor comprises a packaging structure with a first surface and a plurality of ultrasonic transducer groups arranged in the packaging structure. And each ultrasonic transducer group comprises a plurality of ultrasonic transducers which are positioned on the same plane and are distributed at intervals. The plurality of ultrasonic transducer groups comprise a first ultrasonic transducer group, a second ultrasonic transducer group and a third ultrasonic transducer group which are arranged opposite to the first surface; and the plurality of ultrasonic transducers in the second ultrasonic transducer group are respectively positioned on the midpoints of connecting lines for correspondingly connecting the plurality of ultrasonic transducers in the first ultrasonic transducer group and the plurality of ultrasonic transducers in the third ultrasonic transducer group. And the distance L between the first ultrasonic transducer group and the third ultrasonic transducer group meets the following formula: L = 2d1 * tani + 2d2 * tangamma.

Description

Technical Field

[0001] The present application relates to the field of ultrasonic detection technology, and in particular to an ultrasonic array sensor, an ultrasonic detection device and equipment, and a blood vessel measurement method. Background Art

[0002] Blood flow volume refers to the amount of blood flowing through a certain cross section of a blood vessel per unit time. Therefore, blood flow is closely related to the diameter of the artery and the flow velocity of the artery. The changes in blood flow in time and space can contain rich information about a person's cardiovascular condition.

[0003] At present, blood flow is mainly detected by photoplethysmographic (PPG), thermal analysis, edge field capacitor, ultrasound and other methods. Among them, photoplethysmographic, thermal analysis and edge field capacitor can only measure the blood flow in blood vessels with a depth of a few millimeters. In addition, photoplethysmographic and edge field capacitor can only detect the estimated value of blood volume change, and thermal analysis can only detect the relative time average of blood flow velocity. The estimated value of blood volume change and the relative time average of blood flow velocity are meaningless for the clinical diagnosis of cardiovascular disease. Ultrasound technology has higher penetration ability and will not cause harm to the human body within the safety intensity. It can detect blood flow in deeper blood vessels. However, the existing ultrasound technology has the problem of inaccurate detection values ​​when simultaneously detecting blood vessel diameter and blood flow velocity. Summary of the invention

[0004] The embodiments of the present application provide an ultrasonic array sensor, an ultrasonic detection device and equipment, and a blood vessel measurement method, which solve the problem that the existing ultrasonic technology simultaneously detects blood vessel diameter and blood flow velocity and the detection values ​​are inaccurate.

[0005] In order to achieve the above objectives, this application adopts the following technical solutions:

[0006] In a first aspect, an embodiment of the present application provides an ultrasonic array sensor. The ultrasonic array sensor includes a packaging structure and a plurality of ultrasonic transducer groups. The packaging structure has a first surface, and the first surface is used to fit with the skin. For example, the first surface of the packaging structure fits with the skin above the artery to be measured. Multiple ultrasonic transducer groups are respectively detected and arranged in the packaging structure, and each ultrasonic transducer group includes multiple ultrasonic transducers located in the same plane, and the multiple ultrasonic transducers are arranged at intervals. In addition, the multiple ultrasonic transducer groups include a first ultrasonic transducer group, a second ultrasonic transducer group and a third ultrasonic transducer group, and the first ultrasonic transducer group, the second ultrasonic transducer group and the third ultrasonic transducer group are arranged relative to the first surface. The multiple ultrasonic transducers in the second ultrasonic transducer group are respectively located at the midpoint of the connecting line correspondingly connecting the multiple ultrasonic transducers in the first ultrasonic transducer group and the multiple ultrasonic transducers in the third ultrasonic transducer group. The value range of the angle between the plane where the first ultrasonic transducer group is located and the first surface, and the value range of the angle between the plane where the second ultrasonic transducer group is located and the first surface are both 0-10°. The range of the angle between the surface where the third ultrasonic transducer group is located and the first surface is greater than 10°. The spacing L between the multiple ultrasonic transducers in the first ultrasonic transducer group and the multiple ultrasonic transducers in the third ultrasonic transducer group satisfies: L=2d1·tani+2d2·tanγ. Among them, i is the incident angle of the ultrasonic signal emitted by the ultrasonic transducer in the third ultrasonic transducer group, γ is the refraction angle of the ultrasonic signal emitted by the ultrasonic transducer in the third ultrasonic transducer group incident in the biological tissue, d1 is the designed distance between the third ultrasonic transducer group and the skin, and d2 is the distance between the skin and the artery to be measured.

[0007] When the ultrasonic array sensor of the embodiment of the present application is used to detect arterial blood vessels, the first surface of the packaging structure is attached to the skin. The angle between the plane where the multiple ultrasonic transducers in the first ultrasonic transducer group are located and the skin can be 0-10°. The angle between the plane where the multiple ultrasonic transducers in the second ultrasonic transducer group are located and the skin can be 0-10°. The angle between the surface where the multiple ultrasonic transducers in the third ultrasonic transducer group are located and the skin can be greater than 10°. The multiple ultrasonic transducers in the first ultrasonic transducer group, the multiple ultrasonic transducers in the second ultrasonic transducer group, and the multiple ultrasonic transducers in the third ultrasonic transducer group can all be arranged crosswise with the arterial blood vessels to be measured. In addition, the third ultrasonic transducer group can increase the Doppler angle, so that the blood flow rate can be accurately measured without focusing ultrasound. When the ultrasonic array sensor performs echo detection, the ultrasonic signals emitted by the multiple ultrasonic transducers in the first ultrasonic transducer group are controlled, and the ultrasonic signals can be received by the artery to be measured after being reflected by the artery to be measured. At the same time, the ultrasonic signals emitted by the multiple ultrasonic transducers in the second ultrasonic transducer group are controlled, and the ultrasonic signals can be received by the artery to be measured after being reflected by the artery to be measured. Then, according to the ultrasonic signals received by the first ultrasonic transducer group and the ultrasonic signals received by the second ultrasonic transducer group, multiple pulsation amplitudes and multiple depths of the artery to be measured can be obtained. Afterwards, the position of the artery to be measured can be determined according to the multiple pulsation amplitudes and multiple depths of the artery. On this basis, data detection is performed on the artery to be measured, and its detection data (such as blood vessel diameter and blood flow velocity) is more accurate. Furthermore, since the multiple ultrasonic transducers in the second ultrasonic transducer group are respectively located at the midpoint of the connecting line correspondingly connecting the multiple ultrasonic transducers in the first ultrasonic transducer group and the multiple ultrasonic transducers in the third ultrasonic transducer group, and the spacing L between the multiple ultrasonic transducers in the first ultrasonic transducer group and the multiple ultrasonic transducers in the third ultrasonic transducer group satisfies: L=2d1·tani+2d2·tanγ. Therefore, when the ultrasonic array sensor performs penetration detection, after the ultrasonic signals emitted by the multiple ultrasonic transducers in the third ultrasonic transducer group are controlled, the ultrasonic signals are reflected by the artery to be measured and can be received by the multiple ultrasonic transducers in the first ultrasonic transducer group. When the ultrasonic array sensor performs data detection on the artery to be measured, the multiple ultrasonic transducers in the second ultrasonic transducer group can be controlled to perform echo detection, and the first ultrasonic transducer group and the third ultrasonic transducer group can be controlled to perform penetration detection at the same time. According to the multiple ultrasonic signals received by the second ultrasonic transducer group, the current section diameter and the current Doppler angle of the artery to be measured can be obtained. According to the multiple ultrasonic signals received by the first ultrasonic transducer group and the current Doppler angle, the current blood flow velocity of the blood in the arterial vessel to be measured is obtained. Therefore, the detection values ​​of the current blood vessel diameter and the current blood flow velocity measured simultaneously are relatively accurate, and the condition of the arterial vessel can be understood according to the detection values.

[0008] Based on this, the above-mentioned first ultrasonic transducer group, the second ultrasonic transducer group and the third ultrasonic transducer group constitute an ultrasonic transducer detection unit. In some embodiments of the present application, the above-mentioned multiple ultrasonic transducer groups may include only one ultrasonic transducer detection unit, and the structure of the ultrasonic array sensor is relatively simple. In some other embodiments of the present application, the above-mentioned multiple ultrasonic transducer groups include multiple ultrasonic transducer detection units, and the multiple ultrasonic transducer detection units are all arranged relative to the first surface. The plane where the third ultrasonic transducer group in the multiple ultrasonic transducer detection units is located has different angles with the first surface. Thereby, the multiple ultrasonic transducer detection units can be respectively applied to the arterial blood vessels to be measured at different depths for measurement, so as to increase the blood vessel depth range that can be detected by the ultrasonic array sensor.

[0009] It should be noted that, in some embodiments of the present application, the above-mentioned packaging structure can be a flexible substrate, so that it is suitable for application in wearable smart devices. In addition, the above-mentioned ultrasonic array sensor can also be used as a flexible ultrasonic patch. In some embodiments of the present application, the above-mentioned packaging structure can also be a rigid shell, which can be applied to medical ultrasonic detection equipment. And the above-mentioned multiple ultrasonic transducers can specifically be piezoelectric ceramics.

[0010] In the second aspect, the embodiment of the present application also provides an ultrasonic detection device, which can be an ultrasonic probe, an ultrasonic patch with a hard back plate, or a component used to fit the skin in a wearable smart device, such as a wristband of a smart bracelet. The ultrasonic detection device includes a support and an ultrasonic array sensor of the above embodiment, and the ultrasonic array sensor is arranged on the support. Since the ultrasonic array sensor in the ultrasonic detection device of the embodiment of the present application has the same structure as the ultrasonic array sensor described in the above embodiment, both can solve the same technical problems and obtain the same technical effects, which will not be repeated here.

[0011] In the third aspect, the embodiments of the present application also provide an ultrasonic detection device. The ultrasonic detection device includes a signal generating circuit and the ultrasonic detection device described in the above embodiments. Among them, the signal generating circuit can be used to emit a pulse wave or a continuous wave. The ultrasonic detection device is electrically connected to the signal generating circuit. The ultrasonic detection device can receive the pulse wave or continuous wave emitted by the signal generating circuit, and convert the electrical signal of the pulse wave or continuous wave into an ultrasonic signal to be emitted. Since the ultrasonic detection device in the ultrasonic detection device of the embodiment of the present application has the same structure as the ultrasonic detection device described in the above embodiments, both can solve the same technical problems and obtain the same technical effects, which will not be repeated here.

[0012] In a fourth aspect, the present application also provides a blood vessel measurement method using the ultrasonic detection device described in the above embodiment. The blood vessel measurement method includes the following steps:

[0013] Blood vessel positioning stage: Control the ultrasonic array sensor in the ultrasonic detection equipment to perform the first echo mode. The first echo mode is that the first ultrasonic transducer group sends out an ultrasonic signal and receives the ultrasonic signal reflected by the arterial blood vessel to be measured, and the second ultrasonic transducer group sends out an ultrasonic signal and receives the ultrasonic signal reflected by the arterial blood vessel to be measured. According to the ultrasonic signals received by the first ultrasonic transducer group and the second ultrasonic transducer group in the ultrasonic array sensor, multiple pulsation amplitudes and multiple depths of the arterial blood vessel to be measured are obtained. According to the multiple pulsation amplitudes and multiple depths of the arterial blood vessel to be measured, the position of the arterial blood vessel to be measured is determined.

[0014] For example, according to the ultrasonic transducers corresponding to the larger pulsation amplitudes among the multiple pulsation amplitudes of the artery to be measured, the position of the artery to be measured is directly below the position of these ultrasonic transducers. Then, the depth position of the artery to be measured can be determined in combination with the detection depths of these ultrasonic transducers. Thus, the position of the artery to be measured is determined.

[0015] Blood vessel measurement stage: Control the ultrasonic array sensor to perform the second echo mode and the penetration mode simultaneously. The second echo mode is that the second ultrasonic transducer group sends out an ultrasonic signal and receives the ultrasonic signal reflected by the arterial blood vessel to be measured. The penetration mode is that the third ultrasonic transducer group sends out an ultrasonic signal, and the ultrasonic signal reflected by the arterial blood vessel to be measured is received by the first ultrasonic transducer group. According to the multiple ultrasonic signals received by the second ultrasonic transducer group, the current section diameter of the arterial blood vessel to be measured is obtained. According to the multiple ultrasonic signals received by the first ultrasonic transducer group, the current blood flow velocity of the blood in the arterial blood vessel to be measured is obtained.

[0016] Since the above-mentioned blood vessel measurement method first determines the position of the artery to be measured, and then simultaneously measures the cross-sectional diameter of the artery to be measured and the blood flow velocity of the blood in the artery to be measured, it can ensure that the measurement results of the cross-sectional diameter of the artery to be measured and the blood flow velocity of the blood in the artery to be measured are relatively accurate.

[0017] In some embodiments of the present application, after obtaining multiple pulsation amplitudes and multiple depths of the arterial blood vessel to be measured in the above-mentioned blood vessel positioning stage, the blood vessel measurement method further includes: determining the first ultrasonic transducer and the second ultrasonic transducer according to the multiple pulsation amplitudes of the arterial blood vessel to be measured. Among them, the first ultrasonic transducer is the ultrasonic transducer with the largest pulsation amplitude detected among the multiple ultrasonic transducers in the first ultrasonic transducer group. The second ultrasonic transducer is the ultrasonic transducer with the largest pulsation amplitude detected among the multiple ultrasonic transducers in the second ultrasonic transducer group. Based on the measurement data of the first ultrasonic transducer and the measurement data of the second ultrasonic transducer, the current section diameter of the arterial blood vessel to be measured and the current blood flow velocity of the blood in the arterial blood vessel to be measured can be calculated, and the detection result is more accurate.

[0018] Based on the above, in some embodiments of the present application, obtaining the current section diameter of the arterial blood vessel to be measured according to the multiple ultrasonic signals received by the second ultrasonic transducer group specifically includes:

[0019] According to the multiple ultrasonic signals received by the second ultrasonic transducer group, the chord length C1 of the second ultrasonic transducer is obtained, and the third ultrasonic transducer is determined and the chord length C2 of the third ultrasonic transducer is obtained. Among them, the third ultrasonic transducer is an ultrasonic transducer whose pulsation amplitude detected by the multiple ultrasonic circulators of the second ultrasonic transducer group is closest to the maximum pulsation amplitude (that is, the multiple pulsation amplitudes detected by the multiple ultrasonic circulators of the second ultrasonic transducer group are arranged from large to small, and the pulsation amplitude ranked second).

[0020] According to the formula The current section diameter R of the arterial blood vessel to be measured is calculated, wherein D is the distance between the center of the second ultrasonic transducer and the center of the third ultrasonic transducer.

[0021] In some embodiments of the present application, obtaining the current blood flow velocity of the blood in the arterial vessel to be measured according to the multiple ultrasonic signals received by the first ultrasonic transducer group specifically includes:

[0022] According to the multiple ultrasonic signals received by the first ultrasonic transducer group, the Doppler frequency shift f is obtained. d .

[0023] According to the formula The current blood flow velocity v of the blood in the arterial blood vessel to be measured is calculated. Wherein, f0 is the center frequency of the first ultrasonic transducer, c is the sound velocity of the ultrasonic signal in the biological tissue, and θ is the Doppler angle.

[0024] Furthermore, in some embodiments of the present application, after determining the first ultrasonic transducer and the second ultrasonic transducer in the above-mentioned blood vessel positioning stage, the method further includes:

[0025] According to the ultrasonic signal received by the first ultrasonic transducer and the ultrasonic signal received by the second ultrasonic transducer, a depth H1 of the first ultrasonic transducer and a depth H2 of the second ultrasonic transducer are obtained.

[0026] According to the formula The blood vessel angle β of the arterial blood vessel to be measured is calculated, wherein α is the refraction angle of the ultrasonic signal emitted by the second ultrasonic transducer in the biological tissue, and L is the distance between the first ultrasonic transducer group and the third ultrasonic transducer group.

[0027] According to the formula The Doppler angle θ is calculated. BRIEF DESCRIPTION OF THE DRAWINGS

[0028] In order to illustrate the technical solution of the embodiments of the present application, the drawings required for use in the embodiments of the present application will be described below.

[0029] Figure 1 This is a schematic diagram of the three-dimensional structure of the ultrasonic array sensor according to an embodiment of the present application;

[0030] Figure 2 This is a schematic diagram of an ultrasonic array sensor used to detect radial artery in an embodiment of the present application;

[0031] Figure 3 This is a cross-sectional schematic diagram of the ultrasonic array sensor of the embodiment of the present application when performing detection;

[0032] Figure 4 It is a schematic diagram of the design parameters of the ultrasonic array sensor according to the embodiment of the present application;

[0033] Figure 5 This is a schematic top view of the ultrasonic array sensor of the embodiment of the present application when performing detection;

[0034] Figure 6 This is a schematic structural diagram of an ultrasonic array sensor having two ultrasonic transducer detection units according to an embodiment of the present application;

[0035] Figure 7 This is a schematic diagram of the structure of a wristband of a smart bracelet in which the ultrasonic detection device in an embodiment of the present application is a smart bracelet;

[0036] Figure 8 The ultrasonic detection device of the embodiment of the present application is a schematic diagram of the structure of an ultrasonic probe;

[0037] Fig. 9 This is a schematic diagram of the structure of an ultrasonic detection device in an embodiment of the present application as a smart bracelet;

[0038] Fig.10 A schematic diagram of a flow chart of a blood vessel measurement method using an ultrasonic detection device according to an embodiment of the present application;

[0039] Fig.11 A schematic diagram of signals of an ultrasonic detection device according to an embodiment of the present application executing a first echo mode;

[0040] Fig.12 This is a signal schematic diagram of the ultrasonic detection device according to an embodiment of the present application executing the second echo mode and the penetration mode simultaneously;

[0041] Fig.13 It is a flow chart of the blood vessel positioning stage in the blood vessel measurement method using the ultrasonic detection device of the embodiment of the present application for detection;

[0042] Fig.14 This is one of the diagrams annotating some parameters of the ultrasonic detection equipment according to the embodiment of the present application;

[0043] Fig.15 This is a partial flow chart of S202 in the blood vessel measurement method using the ultrasonic detection device of the embodiment of the present application;

[0044] Fig.16 is a schematic cross-sectional view of the arterial blood vessel to be measured;

[0045] Fig.17 This is the second schematic diagram of some parameters of the ultrasonic detection equipment in the embodiment of the present application;

[0046] Fig.18 This is a flow chart of S203 in the blood vessel measurement method using the ultrasonic detection device of the embodiment of the present application;

[0047] Fig.19 A schematic diagram of a flow chart of calculating the Doppler angle in a blood vessel measurement method using an ultrasonic detection device according to an embodiment of the present application;

[0048] Fig. 20 This is the third diagram of the annotation of some parameters of the ultrasonic detection equipment according to the embodiment of the present application.

[0049] Figure Number:

[0050] 10-ultrasonic array sensor; 1-packaging structure; 11-first surface; 2-ultrasonic transducer group; 21-first ultrasonic transducer group; 22-second ultrasonic transducer group; 23-third ultrasonic transducer group; 2a-ultrasonic transducer; 201-first ultrasonic transducer; 202-second ultrasonic transducer; 203-third ultrasonic transducer; 2S-ultrasonic transducer detection unit; 100-ultrasonic detection device; 20-support member; 20a-wristband body; 20b-probe housing; 200-signal generating circuit; 1000-ultrasonic detection equipment; 2000-skin; 3000-biological tissue; 4000-arterial blood vessel to be tested. DETAILED DESCRIPTION

[0051] In order to make the objectives, technical solutions and advantages of the present application clearer, the present application will be further described in detail below in conjunction with the accompanying drawings.

[0052] In the following, the terms "first", "second", etc. are used for descriptive purposes only and are not to be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Thus, a feature defined as "first", "second", etc. may explicitly or implicitly include one or more of the features. In the description of this application, unless otherwise specified, "plurality" means two or more.

[0053] In addition, in the present application, directional terms such as "up", "down", "left", "right", "horizontal" and "vertical" are defined relative to the orientation of the components in the drawings. It should be understood that these directional terms are relative concepts. They are used for relative description and clarification, and they may change accordingly according to the changes in the orientation of the components in the drawings.

[0054] In this application, unless otherwise clearly specified and limited, the term "connection" should be understood in a broad sense. For example, "connection" can refer to the connection of mechanical structure or physical structure. For example, it can be a fixed connection, a detachable connection, or an integrated connection; it can be directly connected or indirectly connected through an intermediate medium. It can also be understood as the physical contact and electrical conduction of components, and it can also be understood as the form in which different components in the circuit structure are connected through physical lines such as PCB copper foil or wires that can transmit electrical signals.

[0055] Ultrasound is a sound wave with a frequency higher than that audible to the human ear (20Hz~20KHz). It has high penetrating power and will not cause harm to the human body within a safe intensity. Therefore, ultrasound can be used to detect blood flow in deep blood vessels. Among them, the ultrasonic array sensor is one of the core components of ultrasonic detection. However, when the existing ultrasonic array sensor detects the blood vessel diameter and blood flow velocity at the same time, its detection value is inaccurate and cannot be used as a data reference for blood vessel conditions.

[0056] In order to solve this problem, the present application provides an ultrasonic array sensor with an improved structure. Figure 1 The ultrasonic array sensor 10 includes a packaging structure 1 and a plurality of ultrasonic transducer groups 2. The packaging structure 1 may be a rigid shell or a flexible substrate, which is not limited in the present application. The plurality of ultrasonic transducer groups 2 are spaced apart in the packaging structure 1. Figure 1 and Figure 2 As shown, the packaging structure 1 has a first surface 11, and the first surface 11 is used to fit the skin 2000. Therefore, the first surface 11 is the surface of the packaging structure 1 close to the skin 2000. The first surface 11 can be a plane or a curved surface that adapts to the skin surface, as long as it can completely fit the skin. Adapt means that the first surface is a shape that can completely fit the skin.

[0057] Each ultrasonic transducer group 2 includes a plurality of ultrasonic transducers 2a located in the same plane, and the plurality of ultrasonic transducers 2a are arranged at intervals. For example, the plurality of ultrasonic transducers 2a are arranged at intervals along a straight line. In addition, the plurality of ultrasonic transducer groups 2 include a first ultrasonic transducer group 21, a second ultrasonic transducer group 22, and a third ultrasonic transducer group 23.

[0058] The first ultrasonic transducer group 21, the second ultrasonic transducer group 22 and the third ultrasonic transducer group 23 are all arranged opposite to the first surface 11. Figure 3 As shown, the value range of the angle A between the plane where the first ultrasonic transducer group 21 is located and the first surface 11 is 0-10°. The value range of the angle B between the plane where the second ultrasonic transducer group 22 is located and the first surface 11 is also 0-10°. Therefore, after the first surface 11 of the packaging structure 1 is attached to the skin 2000, the value range of the angle between the plane where the first ultrasonic transducer group 21 is located and the skin 2000 is 0-10°, and the value range of the angle between the plane where the second ultrasonic transducer group 22 is located and the skin 2000 is 0-10°.

[0059] The angle C between the surface where the third ultrasonic transducer group 23 is located and the first surface 11 is greater than 10°. That is, after the first surface 11 of the packaging structure 1 is attached to the skin 2000, the angle between the surface where the third ultrasonic transducer group 23 is located and the skin 2000 is greater than 10°. The multiple ultrasonic transducers 2a in the second ultrasonic transducer group 22 are respectively located at the midpoint of the connecting line between the multiple ultrasonic transducers 2a in the first ultrasonic transducer group 21 and the multiple ultrasonic transducers 2a in the third ultrasonic transducer group 23. And, referring to Figure 4 and Figure 5 , the spacing L between the multiple ultrasonic transducers 2a in the first ultrasonic transducer group 21 and the multiple ultrasonic transducers 2a in the third ultrasonic transducer group 23 satisfies: L=2d1·tani+2d2·tanγ. Wherein, i is the incident angle of the ultrasonic signal emitted by the ultrasonic transducer 2a in the third ultrasonic transducer group 23. γ is the refraction angle of the ultrasonic signal emitted by the ultrasonic transducer 2a in the third ultrasonic transducer group 23 incident in the biological tissue 3000. d1 is the designed distance between the third ultrasonic transducer group 23 and the skin 2000. d2 is the distance between the skin 2000 and the arterial blood vessel 4000 to be measured. d2 can be a preset value. Therefore, the ultrasonic signals emitted by the multiple ultrasonic transducers 2a in the third ultrasonic transducer group 23 can be received by the multiple ultrasonic transducers 2a in the first ultrasonic transducer group 21.

[0060] When the ultrasonic array sensor 10 of the embodiment of the present application is used to detect the arterial blood vessel 4000 to be measured, the first surface 11 of the packaging structure 1 is attached to the skin 2000. The angle between the plane where the multiple ultrasonic transducers 2a in the first ultrasonic transducer group 21 are located and the skin 2000 can be 0-10°. The angle between the plane where the multiple ultrasonic transducers 2a in the second ultrasonic transducer group 22 are located and the skin 2000 can also be 0-10°. The angle between the surface where the multiple ultrasonic transducers 2a in the third ultrasonic transducer group 23 are located and the first surface 11 can be greater than 10°. The multiple ultrasonic transducers 2a in the first ultrasonic transducer group 21, the multiple ultrasonic transducers 2a in the second ultrasonic transducer group 22, and the multiple ultrasonic transducers 2a in the third ultrasonic transducer group 23 are in contact with the arterial blood vessel 4000 to be measured ( Figure 4The artery 4000 to be measured shown in the figure is the radial artery) can be cross-arranged. In addition, the third ultrasonic transducer group 23 can increase the Doppler angle, so that the blood flow rate can be accurately measured without focusing ultrasound. When the ultrasonic array sensor 10 performs echo detection, the ultrasonic signals emitted by the multiple ultrasonic transducers 2a in the first ultrasonic transducer group 21 are controlled, and the ultrasonic signals can be received by themselves after being reflected by the artery 4000 to be measured, and the ultrasonic signals emitted by the multiple ultrasonic transducers 2a in the second ultrasonic transducer group 22 are controlled, and the ultrasonic signals can be received by themselves after being reflected by the artery 4000 to be measured. Then, according to the ultrasonic signals received by the first ultrasonic transducer group 21 and the ultrasonic signals received by the second ultrasonic transducer group 22, multiple pulsation amplitudes and multiple depths of the artery 4000 to be measured can be obtained. Afterwards, the position of the artery 4000 to be measured can be determined according to the multiple pulsation amplitudes and multiple depths of the artery 4000 to be measured. On this basis, data detection is performed on the arterial blood vessel 4000 to be detected, and the detection data (such as blood vessel diameter and blood flow velocity) is relatively accurate. In addition, since the multiple ultrasonic transducers 2a in the second ultrasonic transducer group 22 are respectively located at the midpoint of the connecting line correspondingly connecting the multiple ultrasonic transducers 2a in the first ultrasonic transducer group 21 and the multiple ultrasonic transducers 2a in the third ultrasonic transducer group 23, and the spacing L between the multiple ultrasonic transducers 2a in the first ultrasonic transducer group 21 and the multiple ultrasonic transducers 2a in the third ultrasonic transducer group 23 satisfies: L=2d1·tani+2d2·tanγ, when the ultrasonic array sensor 10 performs penetration detection, after the ultrasonic signal emitted by the multiple ultrasonic transducers 2a in the third ultrasonic transducer group 23 is controlled, the ultrasonic signal can be received by the multiple ultrasonic transducers 2a in the first ultrasonic transducer group 21 after being reflected by the arterial blood vessel 4000 to be detected. When the ultrasonic array sensor 10 performs data detection on the arterial blood vessel 4000 to be measured, the multiple ultrasonic transducers 2a in the second ultrasonic transducer group 22 can be controlled to perform echo detection, and the first ultrasonic transducer group 21 and the third ultrasonic transducer group 23 can be controlled to perform penetration detection at the same time. According to the multiple ultrasonic signals received by the second ultrasonic transducer group 22, the current section diameter of the arterial blood vessel 4000 to be measured can be obtained. According to the multiple ultrasonic signals received by the first ultrasonic transducer group 21, the current blood flow velocity of the blood in the arterial blood vessel 4000 to be measured can be obtained. Therefore, the detection values ​​of the current blood vessel diameter and the current blood flow velocity measured simultaneously are both relatively accurate, and the condition of the arterial blood vessel 4000 to be measured can be understood based on the detection values.

[0061] It should be noted that if the packaging structure 1 is a flexible substrate, the ultrasonic array sensor 10 may be a flexible ultrasonic patch. The ultrasonic transducer 2a may be a piezoelectric ceramic. Figure 5 As shown, each ultrasonic transducer group 2 includes two or more ultrasonic transducers 2a. Figure 5 The multiple ultrasonic transducers 2a in each ultrasonic transducer group 2 shown can be arranged at equal intervals and along a straight line, and the straight lines where the multiple ultrasonic transducer groups 2 are located are parallel to each other.

[0062] In addition, in some embodiments, the number of ultrasonic transducers 2a in the first ultrasonic transducer group 21, the number of ultrasonic transducers 2a in the second ultrasonic transducer group 22, and the number of ultrasonic transducers 2a in the third ultrasonic transducer group 23 may be equal. Thus, the plurality of ultrasonic transducers 2a in the first ultrasonic transducer group 21 correspond one-to-one to the plurality of ultrasonic transducers 2a in the third ultrasonic transducer group 23. Furthermore, the plurality of ultrasonic transducers 2a in the second ultrasonic transducer group 22 may be located at the midpoint of the connecting line between the plurality of ultrasonic transducers 2a in the first ultrasonic transducer group 21 and the plurality of ultrasonic transducers 2a in the third ultrasonic transducer group 23, respectively.

[0063] Furthermore, the first ultrasonic transducer group 21, the second ultrasonic transducer group 22 and the third ultrasonic transducer group 23 constitute an ultrasonic transducer detection unit 2S. Figure 4 and Figure 5 As shown, the above-mentioned multiple ultrasonic transducer groups 2 only include one ultrasonic transducer detection unit 2S, which can achieve the detection function of the ultrasonic array sensor 10 and has a relatively simple structure.

[0064] In other embodiments of the present application, Figure 6 As shown, the plurality of ultrasonic transducer groups 2 include a plurality of ultrasonic transducer detection units 2S, and the plurality of ultrasonic transducer detection units 2S are all arranged opposite to the first surface 11. Moreover, the plane where the third ultrasonic transducer group 23 in the plurality of ultrasonic transducer detection units 2S is located has a different angle with the first surface 11. Thus, the plurality of ultrasonic transducer detection units 2S can be respectively applied to measure arterial blood vessels to be measured at different depths, so as to increase the depth range of blood vessels detectable by the ultrasonic array sensor 10.

[0065] For example, Figure 6 As shown, the multiple ultrasonic transducer groups 2 include two ultrasonic transducer detection units 2S, and the planes where the third ultrasonic transducer groups 23 in the two ultrasonic transducer detection units 2S are located have different angles with the first surface 11, which can be suitable for detecting the arterial blood vessels 4000 to be tested in a larger depth range.

[0066] The above mainly describes the main structure of the ultrasonic array sensor 10 of the embodiment of the present application. The ultrasonic array sensor 10 can be applied to various electronic devices for ultrasonic detection. Figure 7The embodiment of the present application also includes an ultrasonic detection device 100, which includes a support member 20 and the ultrasonic array sensor 10 described in the above embodiment, and the ultrasonic array sensor 10 is arranged on the support member 20.

[0067] The ultrasonic detection device 100 of the embodiment of the present application can be various electronic products, such as a wristband of a smart watch, a wristband of a smart bracelet, an ultrasonic probe, an ultrasonic patch with a hard back plate (i.e., the support member 20), etc.

[0068] For example, Figure 7 As shown, the ultrasonic detection device 100 is a wristband of a smart bracelet. Therefore, the support member 20 is a wristband body 20a, and the ultrasonic array sensor 10 can be arranged on the wristband body 20a in an area corresponding to the radial artery.

[0069] For example, Figure 8 As shown, the ultrasonic detection device 100 is an ultrasonic probe. Therefore, the support member 20 is a probe housing 20b, and the ultrasonic array sensor 10 is arranged on the probe housing 20b.

[0070] It is understandable that the ultrasonic detection device 100 needs to be used in conjunction with a signal generating circuit to emit an ultrasonic signal. Therefore, the present application also includes an ultrasonic detection device, such as Fig. 9 As shown, the ultrasonic detection device 1000 includes the ultrasonic detection device 100 and the signal generating circuit 200 described in the above embodiment. The ultrasonic detection device 100 is electrically connected to the signal generating circuit 200. The signal generating circuit 200 can emit a continuous wave or a pulse wave. The ultrasonic detection device 100 receives the continuous wave or the pulse wave emitted by the signal generating circuit 200, and can convert the electrical signal of the continuous wave or the pulse wave into an ultrasonic signal and emit it.

[0071] It should be noted that the ultrasonic detection device 1000 of the embodiment of the present application can be an ultrasonic detector or various wearable smart devices (such as smart bracelets, smart watches, etc.). The present application does not limit this. Any device that can perform ultrasonic detection can be used. Fig. 9 Taking the smart bracelet shown as an example, the signal generating circuit 200 can be integrated on the sports chip 200a of the smart bracelet. For the ultrasonic detection device 1000 being an ultrasonic detector, the signal generating circuit 200 is included in the host circuit of the ultrasonic detector.

[0072] The above is a device or apparatus using the ultrasonic array sensor 10. The present application also provides a blood vessel measurement method using the ultrasonic detection device 1000. Fig.10 The blood vessel measurement method includes a blood vessel positioning stage and a blood vessel measurement stage which are performed sequentially.

[0073] The above-mentioned stages of vascular localization include:

[0074] S101: Control the ultrasonic array sensor 10 in the ultrasonic detection device 1000 to perform the first echo mode. Fig.11 As shown, in the first echo mode, the first ultrasonic transducer group 21 sends out ultrasonic signals and receives ultrasonic signals reflected by the arterial blood vessel 4000 to be measured, and the second ultrasonic transducer group 22 sends out ultrasonic signals and receives ultrasonic signals reflected by the arterial blood vessel 4000 to be measured.

[0075] For example, the operation of controlling the first ultrasonic transducer group 21 and the second ultrasonic transducer group 22 to emit an ultrasonic signal can be a controller in the ultrasonic detection device 1000. The controller controls the signal sounding circuit to emit a continuous wave or a pulse wave, and the first ultrasonic transducer group 21 and the second ultrasonic transducer group 22 receive the continuous wave or the pulse wave, and convert it into an ultrasonic signal and emit it. In addition, the ultrasonic signal received by the first ultrasonic transducer group 21 is converted into an electrical signal and then transmitted back to the controller. The ultrasonic signal received by the second ultrasonic transducer group 22 is converted into an electrical signal and then transmitted back to the controller. Among them, the above-mentioned controller can be integrated on the motion chip 200a of the smart bracelet, and can also be integrated in the host circuit in the ultrasonic detector.

[0076] S102: Obtain multiple pulsation amplitudes and multiple depths of the arterial blood vessel 4000 to be measured according to the ultrasonic signal received by the first ultrasonic transducer group 21 and the ultrasonic signal received by the second ultrasonic transducer group 22 in the ultrasonic array sensor 10.

[0077] For example, the controller may obtain multiple pulsation amplitudes and multiple depths based on analysis of the ultrasonic signal received by the first ultrasonic transducer group 21 and the ultrasonic signal received by the second ultrasonic transducer group 22 in the ultrasonic array sensor 10 .

[0078] S103: Determine the position of the arterial blood vessel 4000 to be measured according to the multiple pulsation amplitudes and multiple depths of the arterial blood vessel 4000 to be measured.

[0079] For example, according to the ultrasonic transducers 2a corresponding to the larger pulsation amplitudes among the multiple pulsation amplitudes of the arterial blood vessel 4000 to be tested, the position of the arterial blood vessel 4000 to be tested is directly below the position of these ultrasonic transducers 2a. Then, the depth position of the arterial blood vessel 4000 to be tested can be determined in combination with the detection depths of these ultrasonic transducers 2a. Thus, the position of the arterial blood vessel 4000 to be tested is determined.

[0080] The above-mentioned vascular measurement phase includes:

[0081] S201: Control the ultrasonic array sensor 10 to perform the second echo mode and the penetration mode simultaneously. Fig.12 As shown, the second echo mode is that the second ultrasonic transducer group 22 sends out ultrasonic signals and receives ultrasonic signals reflected by the artery 4000 to be tested. The penetration mode is that the third ultrasonic transducer group 23 sends out ultrasonic signals, and the ultrasonic signals reflected by the artery 4000 to be tested are received by the first ultrasonic transducer group 21.

[0082] For example, the controller can control the second ultrasonic transducer group 22 to emit an ultrasonic signal, and the third ultrasonic transducer group 23 to emit an ultrasonic signal. That is, the controller controls the signal sound circuit to emit a continuous wave or a pulse wave, and the second ultrasonic transducer group 22 and the third ultrasonic transducer group 23 receive the continuous wave or the pulse wave, and convert it into an ultrasonic signal and then transmit it. In addition, the ultrasonic signal received by the second ultrasonic transducer group 22 is converted into an electrical signal and then transmitted back to the controller. The ultrasonic signal received by the first ultrasonic transducer group 21 is converted into an electrical signal and then transmitted back to the controller.

[0083] S202: Obtaining the current section diameter of the arterial blood vessel 4000 to be measured according to the multiple ultrasonic signals received by the second ultrasonic transducer group 22.

[0084] For example, the controller may analyze a plurality of ultrasonic signals received by the second ultrasonic transducer group 22 to obtain the current section diameter of the arterial blood vessel 4000 to be measured.

[0085] S203: Obtaining the current blood flow velocity of the blood in the arterial vessel 4000 to be measured according to the multiple ultrasonic signals received by the first ultrasonic transducer group 21 .

[0086] For example, the controller may obtain the current blood flow velocity of the blood in the arterial vessel 4000 to be measured based on the multiple ultrasonic signals received by the first ultrasonic transducer group 21 .

[0087] Furthermore, in some embodiments of the present application, reference is made to Fig.13 and Fig.14 , after S102 in the above blood vessel positioning stage, further comprising:

[0088] S104: Determine the first ultrasonic transducer 201 and the second ultrasonic transducer 202 according to the multiple pulsation amplitudes of the arterial blood vessel 4000 to be measured. The first ultrasonic transducer 201 is the ultrasonic transducer with the largest pulsation amplitude detected among the multiple ultrasonic transducers 2a in the first ultrasonic transducer group 21. The second ultrasonic transducer 202 is the ultrasonic transducer with the largest pulsation amplitude detected among the multiple ultrasonic transducers 2a in the second ultrasonic transducer group 22 (that is, the second pulsation amplitude ranked from largest to smallest among the multiple pulsation amplitudes).

[0089] For example, the controller can calculate the current section diameter of the arterial vessel 4000 to be tested and the current blood flow velocity of the blood in the arterial vessel 4000 to be tested based on the measurement data of the first ultrasonic transducer 201 and the measurement data of the second ultrasonic transducer 202, so that the detection result is more accurate.

[0090] Based on the above blood vessel measurement method, in some embodiments of the present application, such as Fig.15 , Fig.16 and Fig.17 As shown, the above S202 specifically includes:

[0091] S2021a: According to the multiple ultrasonic signals received by the second ultrasonic transducer group 22, the chord length C1 of the second ultrasonic transducer 202 is obtained, and the third ultrasonic transducer 203 is determined and the chord length C2 of the third ultrasonic transducer 203 is obtained. The third ultrasonic transducer 203 is an ultrasonic transducer whose pulsation amplitude detected by the multiple ultrasonic circulators 2a of the second ultrasonic transducer group 22 is closest to the maximum pulsation amplitude (that is, the multiple pulsation amplitudes detected by the multiple ultrasonic circulators 2a of the second ultrasonic transducer group 22 are arranged from large to small, and the pulsation amplitude ranked second).

[0092] For example, according to the multiple ultrasonic signals (i.e., echo signals) received by the first ultrasonic transducer group 21, the controller can obtain the chord length C1 of the second ultrasonic transducer 202 and the chord length C2 of the third ultrasonic transducer 203 through analysis and mathematical calculation, as shown in FIG. Fig.16 shown.

[0093] S2022a: According to the formula The current section diameter R of the arterial blood vessel 4000 to be measured is calculated. Fig.17 As shown, D is the distance between the center of the second ultrasonic transducer 202 and the center of the third ultrasonic transducer 203 .

[0094] For example, the calculation module in the controller may execute an operation of calculating the current section diameter R of the arterial blood vessel 4000 to be measured.

[0095] In some embodiments of the present application, Fig.18 As shown, the above S203 specifically includes:

[0096] S2031: Obtaining the Doppler frequency shift f according to the multiple ultrasonic signals received by the first ultrasonic transducer group 21 d .

[0097] For example, according to the multiple ultrasonic signals (i.e., echo signals) received by the first ultrasonic transducer group 21, the Doppler frequency shift f can be obtained by orthogonal demodulation and spectrum analysis of the echo signals. d .

[0098] S2032: According to the formula The current blood flow velocity v of the blood in the arterial blood vessel 4000 to be measured is calculated. Wherein, f0 is the center frequency of the first ultrasonic transducer 201, c is the sound velocity of the ultrasonic signal in the biological tissue 3000, and θ is the Doppler angle.

[0099] For example, the calculation module in the above controller can perform an operation of calculating the current blood flow velocity v.

[0100] Furthermore, in some embodiments of the present application, after S104, as Fig.19 As shown, the blood vessel positioning stage in the above blood vessel measurement method also includes:

[0101] S105: According to the ultrasonic signal received by the first ultrasonic transducer 201 and the ultrasonic signal received by the second ultrasonic transducer 202, obtain Fig. 20 The depth H1 of the first ultrasonic transducer 201 and the depth H2 of the second ultrasonic transducer 202 are shown.

[0102] S106: According to the formula The blood vessel angle β of the arterial blood vessel 4000 to be measured is calculated. Fig.14 As shown in FIG. , α is the refraction angle of the ultrasonic signal emitted by the second ultrasonic transducer 202 in the biological tissue 3000. Fig.17 As shown, L is the distance between the first ultrasonic transducer group 21 and the third ultrasonic transducer group 23 .

[0103] For example, the calculation module in the controller may perform an operation of calculating the blood vessel angle β of the arterial blood vessel 4000 to be measured.

[0104] S106: According to the formula The Doppler angle θ is calculated.

[0105] For example, the calculation module in the controller may perform an operation of calculating the Doppler angle θ.

[0106] The above is only a specific implementation of the present application, but the protection scope of the present application is not limited thereto. Any person skilled in the art who is familiar with the present technical field can easily think of changes or substitutions within the technical scope disclosed in the present application, which should be included in the protection scope of the present application. Therefore, the protection scope of the present application should be based on the protection scope of the claims.

Claims

1. An ultrasonic array sensor, characterized in that: include: A packaging structure, wherein the packaging structure has a first surface, and the first surface is used to fit the skin; A plurality of ultrasonic transducer groups, the plurality of ultrasonic transducer groups are respectively arranged in the packaging structure at intervals; each of the ultrasonic transducer groups includes a plurality of ultrasonic transducers located in the same plane, and the plurality of ultrasonic transducers are arranged at intervals; and the plurality of ultrasonic transducer groups include a first ultrasonic transducer group, a second ultrasonic transducer group, and a third ultrasonic transducer group, all of which are arranged opposite to the first surface; The angles between the plane where the first ultrasonic transducer group is located, the plane where the second ultrasonic transducer group is located, and the first surface are 0-10°; the multiple ultrasonic transducers in the second ultrasonic transducer group are respectively located at the midpoints of the connecting lines correspondingly connecting the multiple ultrasonic transducers in the first ultrasonic transducer group and the multiple ultrasonic transducers in the third ultrasonic transducer group; the angle between the surface where the third ultrasonic transducer group is located and the first surface is greater than 10°; the spacing L between the multiple ultrasonic transducers in the first ultrasonic transducer group and the multiple ultrasonic transducers in the third ultrasonic transducer group satisfies: L=2d1·tani+2d2·tanγ; wherein, i is the incident angle of the ultrasonic signal emitted by the ultrasonic transducer in the third ultrasonic transducer group, γ is the refraction angle of the ultrasonic signal emitted by the ultrasonic transducer in the third ultrasonic transducer group incident in the biological tissue, d1 is the designed distance between the third ultrasonic transducer group and the skin, and d2 is the distance between the skin and the artery to be measured.

2. The ultrasonic array sensor according to claim 1, characterized in that: The first ultrasonic transducer group, the second ultrasonic transducer group and the third ultrasonic transducer group constitute an ultrasonic transducer detection unit; The multiple ultrasonic transducer groups include multiple ultrasonic transducer detection units that are arranged opposite to the first surface, and the planes where the third ultrasonic transducer group in the multiple ultrasonic transducer detection units is located have different angles with the first surface.

3. The ultrasonic array sensor according to claim 1, characterized in that: The packaging structure is a flexible substrate or a rigid shell.

4. An ultrasonic detection device, characterized in that: include: Supports; The ultrasonic array sensor according to any one of claims 1 to 3, wherein the ultrasonic array sensor is arranged on the supporting member.

5. The ultrasonic detection device according to claim 4, characterized in that: The ultrasonic detection device is a component in an ultrasonic probe, an ultrasonic patch or a wearable intelligent device that is used to fit the skin.

6. An ultrasonic testing device, characterized in that: include: Signal generating circuit; The ultrasonic detection device described in claim 4 or 5 is electrically connected to the signal generating circuit.

7. The ultrasonic testing device according to claim 6, characterized in that: The ultrasonic detection device is an ultrasonic detector or a wearable intelligent device.

8. A blood vessel measurement method using the ultrasonic detection device as claimed in claim 6 or 7, characterized in that: The following steps are involved: Blood vessel positioning stage: controlling the ultrasonic array sensor in the ultrasonic detection device to perform a first echo mode; wherein the first echo mode is that the first ultrasonic transducer group sends out an ultrasonic signal and receives an ultrasonic signal reflected by the arterial blood vessel to be detected, and the second ultrasonic transducer group sends out an ultrasonic signal and receives an ultrasonic signal reflected by the arterial blood vessel to be detected; Obtaining multiple pulsation amplitudes and multiple depths of the arterial blood vessel to be measured according to the ultrasonic signal received by the first ultrasonic transducer group and the ultrasonic signal received by the second ultrasonic transducer group in the ultrasonic array sensor; Determining the position of the arterial blood vessel to be measured according to multiple pulsation amplitudes and multiple depths of the arterial blood vessel to be measured; Blood vessel measurement stage: control the ultrasonic array sensor to simultaneously perform the second echo mode and the penetration mode; wherein the second echo mode is that the second ultrasonic transducer group sends out an ultrasonic signal and receives the ultrasonic signal reflected by the arterial blood vessel to be measured; the penetration mode is that the third ultrasonic transducer group sends out an ultrasonic signal, and the ultrasonic signal reflected by the arterial blood vessel to be measured is received by the first ultrasonic transducer group Obtaining a current section diameter of the arterial blood vessel to be measured according to the multiple ultrasonic signals received by the second ultrasonic transducer group; The current blood flow velocity of the blood in the arterial vessel to be measured is obtained according to the multiple ultrasonic signals received by the first ultrasonic transducer group.

9. The blood vessel measurement method according to claim 8, characterized in that: After obtaining a plurality of pulse amplitudes and a plurality of depths of the arterial blood vessel to be measured in the blood vessel positioning stage, the method further includes: According to the multiple pulsation amplitudes of the arterial blood vessel to be measured, the first ultrasonic transducer and the second ultrasonic transducer are determined; wherein the first ultrasonic transducer is the ultrasonic transducer with the largest pulsation amplitude detected among the multiple ultrasonic transducers of the first ultrasonic transducer group; and the second ultrasonic transducer is the ultrasonic transducer with the largest pulsation amplitude detected among the multiple ultrasonic transducers of the second ultrasonic transducer group.

10. The blood vessel measurement method according to claim 9, characterized in that: The step of obtaining the current section diameter of the arterial blood vessel to be measured according to the plurality of ultrasonic signals received by the second ultrasonic transducer group specifically includes: According to the multiple ultrasonic signals received by the second ultrasonic transducer group, the chord length C1 of the second ultrasonic transducer is obtained, and the third ultrasonic transducer is determined and the chord length C2 of the third ultrasonic transducer is obtained; wherein the third ultrasonic transducer is an ultrasonic transducer whose pulsation amplitude is detected to be closest to the maximum pulsation amplitude among the multiple ultrasonic transducers of the second ultrasonic transducer group; According to the formula The current section diameter R of the arterial blood vessel to be measured is calculated; wherein D is the distance between the center of the second ultrasonic transducer and the center of the third ultrasonic transducer.

11. The blood vessel measurement method according to claim 9 or 10, characterized in that: The step of obtaining the current blood flow velocity of the blood in the arterial vessel to be measured according to the multiple ultrasonic signals received by the first ultrasonic transducer group specifically includes: According to the plurality of ultrasonic signals received by the first ultrasonic transducer group, a Doppler frequency shift f is obtained. d ; According to the formula The current blood flow velocity v of the blood in the arterial vessel to be measured is calculated; wherein f0 is the center frequency of the first ultrasonic transducer, c is the sound velocity of the ultrasonic signal in the biological tissue, and θ is the Doppler angle.

12. The blood vessel measurement method according to claim 11, characterized in that: After determining the first ultrasonic transducer and the second ultrasonic transducer in the blood vessel positioning stage, the method further includes: Obtaining a depth H1 of the first ultrasonic transducer and a depth H2 of the second ultrasonic transducer according to the ultrasonic signal received by the first ultrasonic transducer and the ultrasonic signal received by the second ultrasonic transducer; According to the formula Calculate and obtain the blood vessel angle β of the arterial blood vessel to be measured; wherein α is the refraction angle of the ultrasonic signal emitted by the second ultrasonic transducer in the biological tissue, and L is the distance between the first ultrasonic transducer group and the third ultrasonic transducer group; According to the formula The Doppler angle θ is calculated.

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