CN214073368U - Miniature ultrasonic blood pressure detection device - Google Patents

Abstract

This specification discloses a miniature ultrasonic blood pressure measurement device, includes: at least one body pressure electric material sensor, wherein the body pressure electric material sensor is used for realizing conversion of electric energy and mechanical energy and transmitting and receiving ultrasonic waves, and one side of the body pressure electric material sensor, which transmits and receives the ultrasonic waves, faces to a detection object; the bulk piezoelectric material sensor is at least provided with a first electrode leading-out end and a second electrode leading-out end; the first circuit board is arranged below the bulk piezoelectric material sensor, and an acoustic barrier layer is arranged between the bulk piezoelectric material sensor and the first circuit board so as to prevent the ultrasonic waves of the bulk piezoelectric material sensor from propagating to the first circuit board; and the controller is electrically connected with the first electrode leading-out end and the second electrode leading-out end of the body voltage material sensor through the first circuit board. The miniature ultrasonic blood pressure detection device that this specification provided has miniaturized, low-cost advantage, can satisfy the requirement of wearable application scene, is applicable to wearable product.

Description

Miniature ultrasonic blood pressure detection device

Technical Field

The specification relates to the technical field of medical monitoring, in particular to a miniature ultrasonic blood pressure detection device.

Background

Blood pressure is gaining more and more attention as an important index of physical health condition, and particularly in wearable markets, people show strong demands for portable blood pressure monitoring products. In recent years, various blood pressure detection products are also emerging on the market, and mainly there are cuff type sphygmomanometers, optical PPG sphygmomanometers, PPG + ECG method sphygmomanometers, and ultrasonic sphygmomanometers in development stage. However, the cuff-type sphygmomanometer cannot completely meet the requirements of wearable products on volume and comfort level, and cannot continuously monitor blood pressure, the precision of the optical PPG and PPG + ECG sphygmomanometer is too low, and the ultrasonic sphygmomanometer has the advantages of comfort in use, continuous monitoring and accurate measurement. The core component of the ultrasonic sphygmomanometer is an ultrasonic transducer, and the traditional ultrasonic transducer is large in size, high in cost and not suitable for wearable products.

SUMMERY OF THE UTILITY MODEL

In view of the defects of the prior art, an object of the present specification is to provide a miniature ultrasonic blood pressure detection device, which has the advantages of miniaturization and low cost, can meet the requirements of wearable application scenarios, and is suitable for wearable products.

In order to achieve the above object, an embodiment of the present specification provides a miniature ultrasonic blood pressure monitor, including:

at least one body piezoelectric material sensor, wherein the body piezoelectric material sensor is used for converting electric energy and mechanical energy and transmitting and receiving ultrasonic waves, and one side of the body piezoelectric material sensor, which transmits and receives the ultrasonic waves, faces to a detection object; the bulk piezoelectric material sensor is at least provided with a first electrode leading-out end and a second electrode leading-out end;

the first circuit board is arranged below the bulk piezoelectric material sensor, and an acoustic barrier layer is arranged between the bulk piezoelectric material sensor and the first circuit board so as to prevent the ultrasonic waves of the bulk piezoelectric material sensor from propagating to the first circuit board; and the number of the first and second groups,

and the controller is electrically connected with the first electrode leading-out end and the second electrode leading-out end of the bulk voltage material sensor through the first circuit board.

In a preferred embodiment, a protective frame structure is provided on the periphery of the bulk piezoelectric material sensor.

In a preferred embodiment, the bulk piezoelectric material sensor has a detection surface and an electrical installation surface opposite to the detection surface; the electrical installation surface faces the first circuit board.

In a preferred embodiment, the first electrode terminal and the second electrode terminal are both provided on an electrical mounting surface of the bulk piezoelectric material sensor.

In a preferred embodiment, the bulk piezoelectric material sensor includes a first electrode, a second electrode, and a bulk piezoelectric material disposed between the first electrode and the second electrode, the first electrode being in electrical communication with the first electrode terminal, and the second electrode being in electrical communication with the second electrode terminal.

In a preferred embodiment, the bulk piezoelectric material sensor is further provided with an acoustic matching layer, and the acoustic matching layer is disposed on a surface of the bulk piezoelectric material sensor facing the detection object.

In a preferred embodiment, an impedance value of the acoustic matching layer is between an acoustic impedance value of the bulk piezoelectric material sensor and an acoustic impedance value of the detection target.

As a preferred embodiment, the body pressure piezoelectric material sensor is further provided with a skin coupling layer, and the skin coupling layer is arranged on the acoustic matching layer; when the detection device detects, the skin coupling layer is directly contacted with the skin of the detection object.

In a preferred embodiment, the first circuit board is a flexible circuit board.

As a preferred embodiment, the miniature ultrasonic blood pressure monitor further comprises a reinforcing layer disposed under the flexible circuit board to support the bulk piezoelectric material sensor on the flexible circuit board.

In a preferred embodiment, the acoustic barrier layer is a void space layer.

In a preferred embodiment, the acoustic impedance value of the acoustic impedance layer is greater than 100 times the acoustic impedance value of the bulk piezoelectric material sensor, or less than 1/100 times the acoustic impedance value of the bulk piezoelectric material sensor.

In a preferred embodiment, the length of the bulk piezoelectric material sensor is at least greater than the diameter of the artery of the detection object.

In a preferred embodiment, the bulk piezoelectric material in the bulk piezoelectric material sensor is a piezoelectric material having a piezoelectric or ferroelectric effect.

Has the advantages that: according to the miniature ultrasonic blood pressure detection device provided by the embodiment of the specification, the body pressure electric material sensor, the first circuit board, the acoustic barrier layer and the controller are arranged, so that one surface of the body pressure electric material sensor, which transmits and receives ultrasonic waves, faces a detection object, and the acoustic barrier layer is arranged between the body pressure electric material sensor and the first circuit board, so that the ultrasonic waves of the piezoelectric material sensor can be prevented from being transmitted to the first circuit board, the ultrasonic waves are transmitted to the detection object, and the ultrasonic blood pressure detection of the detection object is realized. The miniature ultrasonic blood pressure detection device provided by the embodiment of the specification has the advantages of simple structure, excellent performance, small size, low cost and mass production, can meet the requirements of wearable application scenes, and is suitable for wearable products.

Specific embodiments of the present specification are disclosed in detail with reference to the following description and the accompanying drawings, which specify the manner in which the principles of the specification may be employed. It should be understood that the embodiments of the present description are not so limited in scope.

Features that are described and/or illustrated with respect to one embodiment may be used in the same way or in a similar way in one or more other embodiments, in combination with or instead of the features of the other embodiments.

It should be emphasized that the term "comprises/comprising" when used herein, is taken to specify the presence of stated features, integers, steps or components but does not preclude the presence or addition of one or more other features, integers, steps or components.

Drawings

In order to more clearly illustrate the embodiments of the present specification or the technical solutions in the prior art, the drawings needed to be used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present specification, and other drawings can be obtained by those skilled in the art without inventive exercise.

Fig. 1 is a schematic structural diagram of a miniature ultrasonic blood pressure measurement device provided in an embodiment of the present disclosure;

FIG. 2 is an expanded view of the structure of FIG. 1;

FIG. 3 is a cross-sectional view taken along line A-A of FIG. 1;

FIG. 4 is a schematic structural diagram of another miniature ultrasonic blood pressure measurement device provided in the embodiments of the present disclosure;

FIG. 5 is an expanded view of the structure of FIG. 4;

FIG. 6 is a cross-sectional view taken along line B-B of FIG. 4;

fig. 7 is a schematic structural view of a sensor surface of a bulk piezoelectric material provided in an embodiment of the present disclosure;

fig. 8 is a schematic bottom view of fig. 7, i.e., a schematic structural view of an electrical mounting surface;

fig. 9 is a schematic structural diagram of another miniature ultrasonic blood pressure measurement device provided in the embodiments of the present disclosure.

Description of reference numerals:

1. a first circuit board; 101. a first surface; 102. a second surface; 2. a bulk piezoelectric material sensor; 201. an electrical mounting surface; 202. detecting a surface; 203. a side surface; 3. a first enclosure frame; 4. a second enclosure frame; 5. an adhesive layer; 6. a through hole; 7. soldering points of solder paste; 8. a controller; 9. a reinforcing layer; 10. a first electrode; 11. a second electrode; 12. an acoustic matching layer; 13. a first electrode lead-out terminal; 14. a skin coupling layer; 15. and a protective frame structure.

Detailed Description

In order to make those skilled in the art better understand the technical solutions in the present specification, the technical solutions in the embodiments of the present specification will be clearly and completely described below with reference to the drawings in the embodiments of the present specification, and it is obvious that the described embodiments are only a part of the embodiments of the present specification, and not all of the embodiments. All other embodiments obtained by a person of ordinary skill in the art based on the embodiments in the present specification without any creative effort shall fall within the protection scope of the present specification.

It will be understood that when an element is referred to as being "disposed on" another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may be present. The terms "vertical," "horizontal," "left," "right," and the like as used herein are for illustrative purposes only and do not represent the only embodiments.

Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. The terminology used in the description of the invention herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. As used herein, the term "and/or" includes any and all combinations of one or more of the associated listed items.

In this specification, a component of an embodiment of the present invention is defined as "lower" in a direction toward or facing a user, and "upper" in a direction away from the user in a normal use state.

Specifically, when the miniature ultrasonic blood pressure detection device of the embodiment of the present invention is configured on wearable devices such as a bracelet and a watch, the direction in which the wearable device contacts or faces the skin of the user is defined as "down", and the direction opposite to this, or the direction away from the user is defined as "up".

More specifically, an upward direction illustrated in fig. 1 to 7 and 9 is defined as "up", and a downward direction illustrated in fig. 1 to 7 and 9 is defined as "down".

It should be noted that the definitions of the directions in the present specification are only for convenience of describing the technical solution of the present invention, and do not limit the directions of the micro-ultrasonic blood pressure monitor according to the embodiments of the present invention in other scenes that may cause the orientation of the components to be reversed or the positions to be changed, including but not limited to use, testing, transportation, and manufacturing.

The ultrasonic ranging technology is based on the principle that an ultrasonic transducer is used for transmitting ultrasonic pulse signals, receiving reflected ultrasonic pulses, and calculating the position of a reflecting interface according to the time delay of the received pulse signals to realize the ranging function. The technology is widely applied to the fields of medical treatment, military affairs and industrial detection. Attaching an ultrasonic transducer to the surface of human skin, emitting ultrasonic pulses towards an artery, receiving reflected echo signals, monitoring artery diameter information, and calculating the blood pressure according to the diameter information. This technique is reported in a large number of documents, such as Jan M MeindersandArnold P G Hoeks, "Simultaneous assessment of diameter and pressure waves in the cardiac identity", and the like. The relationship between the artery diameter and the blood pressure is supported by a clear mathematical physical model, but the indirect blood pressure measurement method of estimating the blood pressure based on the diameter has inherent errors which are derived from the blood vessel elasticity estimation error and the blood vessel section area error, and the method needs to be calibrated regularly.

The blood flow rate also reflects the blood pressure information, and the blood pressure estimation by detecting the blood flow rate is also a feasible method. The method utilizes an ultrasonic Doppler velocity measurement technology, utilizes an ultrasonic transducer to emit ultrasonic pulses and receive pulse signals reflected by blood, can obtain blood flow velocity information according to a Doppler velocity measurement principle, and then obtains blood flow information by combining the diameter of a blood vessel.

The core component of the blood pressure detection technology based on ultrasonic waves is an ultrasonic transducer which mainly comprises a piezoelectric ultrasonic transducer, a capacitive ultrasonic transducer and a magnetostrictive ultrasonic transducer, wherein the piezoelectric ultrasonic transducer has the advantages of simple structure, excellent performance and most extensive application. The traditional piezoelectric ultrasonic transducer comprises a sound absorption backing, an electrode layer, a piezoelectric layer, an acoustic matching layer, an acoustic lens layer and other structures, is large in size and high in cost, and cannot be directly applied to wearable products. Therefore, the embodiment of the specification provides a miniature ultrasonic blood pressure detection device, which has the advantages of miniaturization and low cost, can meet the requirements of wearable application scenes, and is suitable for wearable products.

Please refer to fig. 1 to 9. The miniature ultrasonic blood pressure detection device provided by the embodiment of the specification can comprise a body pressure and electric material sensor 2, a first circuit board 1, an acoustic barrier layer and a controller 8. Wherein at least one of the bulk piezoelectric material sensors 2. The bulk piezoelectric material sensor 2 is used for conversion of electric energy and mechanical energy, and transmission and reception of ultrasonic waves. The side of the bulk piezoelectric material sensor 2 that transmits and receives ultrasonic waves faces the detection object. The bulk piezoelectric material sensor 2 is provided with at least a first electrode lead-out terminal 13 and a second electrode lead-out terminal. The first circuit board 1 is disposed below the bulk piezoelectric material sensor 2. An acoustic barrier layer is arranged between the body pressure electric material sensor 2 and the first circuit board 1 to prevent the ultrasonic waves of the body pressure electric material sensor from propagating to the first circuit board. The controller 8 is electrically connected with the first electrode leading-out terminal 13 and the second electrode leading-out terminal of the body pressure electric material sensor 2 through the first circuit board 1.

According to the miniature ultrasonic blood pressure detection device provided by the embodiment of the specification, the body pressure electric material sensor, the first circuit board, the acoustic barrier layer and the controller are arranged, so that one surface of the body pressure electric material sensor, which transmits and receives ultrasonic waves, faces a detection object, and the acoustic barrier layer is arranged between the body pressure electric material sensor and the first circuit board, so that the ultrasonic waves of the piezoelectric material sensor can be prevented from being transmitted to the first circuit board, the ultrasonic waves are transmitted to the detection object, and the ultrasonic blood pressure detection of the detection object is realized. The miniature ultrasonic blood pressure detection device provided by the embodiment of the specification has the advantages of simple structure, excellent performance, small size, low cost and mass production, can meet the requirements of wearable application scenes, and is suitable for wearable products.

In the present embodiment, the bulk piezoelectric material sensor 2 may include a first electrode 10, a second electrode 11, and a bulk piezoelectric material. The bulk piezoelectric material is disposed between the first electrode 10 and the second electrode 11. The first electrode 10 is in electrical communication with a first electrode lead 13, and the second electrode 11 is in electrical communication with a second electrode lead. The first electrode 10 and the second electrode 11 are located on the upper and lower surfaces of the bulk piezoelectric material sensor 2 and are not coplanar, for example, the first electrode 10 is on the upper surface of the bulk piezoelectric material sensor 2, and the second electrode 11 is on the lower surface of the bulk piezoelectric material sensor 2.

Specifically, the bulk piezoelectric material sensor 2 has a detection surface 202 and an electrical mounting surface 201 opposite to the detection surface 202. The electrical mounting surface 201 faces the first circuit board 1 and is a lower surface of the body pressure sensor 2, and the body pressure sensor 2 receives an electrical signal of an external circuit through the electrical mounting surface 201. The detection surface 202 faces the detection target and is the upper surface of the bulk piezoelectric material sensor 2.

In the present embodiment, the first electrode lead 13 and the second electrode lead may be provided on different surfaces of the bulk piezoelectric material sensor 2. In a preferred embodiment, the first electrode lead 13 and the second electrode lead are both provided on the electrical mounting surface 201 of the bulk piezoelectric material sensor 2. As shown in fig. 8, the first electrode lead 13 and the second electrode 11 are provided on the same surface of the bulk piezoelectric material sensor 2. Namely, the first electrode lead-out terminal 13 and the second electrode 11 are both disposed on the electrical mounting surface 201. Through setting up first electrode leading-out end 13, can make first electrode 10 pass through electrical property installation face 201 and first circuit board 1 electric connection to only can realize first electrode 10, second electrode 11 simultaneously and first circuit board 1 electric connection through electrical property installation face 201, and need not to consider the problem with detection face 202 and first circuit board 1 electric connection, can make the structure simpler, satisfy the requirement of wearable product to the miniaturization. That is, the first circuit board 1 is only required to be disposed on one side of the bulk piezoelectric material sensor 2 (the electrical mounting surface 201), so that the first electrode 10 and the second electrode 11 can be electrically connected to an external circuit. Of course, in other embodiments, the first electrode 10 and the second electrode 11 may be disposed on both sides of the bulk piezoelectric material sensor 2, and the two electrode layers are disposed with circuit boards for electrical connection with external circuits; or, the first electrode 10 or the second electrode 11 and the second electrode 11 or the first electrode 10 share the first circuit board 1 by means of wire bonding. In the preferred embodiment, the circuit boards in the whole miniature ultrasonic blood pressure detection device are relatively few, the circuit structure is compact, the complexity of acoustic matching of the miniature ultrasonic blood pressure detection device can be simplified, narrow sound beams can be easily obtained, and the resolution of ultrasonic distance measurement is improved.

Specifically, in a manner of disposing the terminals of the two electrode layers on the same plane, reference may be made to two manners described below:

first, as shown in fig. 7, the first electrode lead 13 is electrically connected to the first electrode 10 via a conductive material provided on the side surface 203 of the bulk piezoelectric material sensor 2.

In a second mode, as shown in fig. 3 and 6, the first electrode terminal 13 is electrically connected to the first electrode 10 through the through hole 6. The through hole 6 penetrates the bulk piezoelectric material sensor 2. The walls of the through-hole 6 are coated with a conductive material. Of course, the through hole 6 may be filled with a conductive material. Specifically, the conductive material at the upper end of the through hole 6 is electrically connected to the first electrode 10, and the conductive material at the lower end of the through hole 6 is electrically connected to the first electrode terminal 13.

In the present embodiment, the piezoelectric material in the body piezoelectric material sensor 2 can be selected from piezoelectric materials having piezoelectric and ferroelectric effects, such as lead titanate PT, lead zirconate titanate PZT, barium titanate BT, PVDF organic polymers, etc., so that the body piezoelectric material sensor 2 can realize interconversion between electric energy and mechanical energy. Preferably, the body pressure piezoelectric material sensor 2 is made of lead zirconate titanate PZT, which can realize ultrasonic blood pressure detection and is low in cost. The material of the first electrode 10 and the second electrode 11 may be conductive metal such as nickel, aluminum, silver, copper, gold, etc., or conductive material such as silver paste, anisotropic conductive film ACF, etc., for transmitting the transmission excitation signal and receiving signal. Applying an alternating current to the first electrode 10 and the second electrode 11 may place the bulk piezoelectric material sensor 2 in an operating state. Under the working state, the body pressure electric material sensor 2 converts the alternating current signal into mechanical vibration, so that stable ultrasonic waves are generated, ultrasonic signals can be emitted to a human body, the ultrasonic signals reflected by the human body are received, and the reflected ultrasonic signals are converted into electric signals.

In the present embodiment, since the acoustic impedance value of the piezoelectric material is often much larger than that of the human tissue, and the mechanical vibration generated by the piezoelectric material sensor 2 under the electric excitation cannot penetrate into the skin tissue quickly, and cannot directly form a high-intensity narrow acoustic pulse, the piezoelectric material sensor 2 is further provided with the acoustic matching layer 12. As shown in fig. 9, the acoustic matching layer 12 is provided on the surface of the bulk piezoelectric material sensor 2 facing the detection target.

Specifically, the impedance value of the acoustic matching layer 12 is between the acoustic impedance value of the bulk piezoelectric material sensor 2 and the acoustic impedance value of the detection target. The acoustic matching layer 12 is made of a material with low acoustic attenuation and moderate acoustic impedance, for example, epoxy resin, plastic, rubber, etc. may be used. To adjust the acoustic impedance value, solid particles such as metal tungsten, aluminum, zirconia, alumina, or the like may be incorporated in the acoustic matching layer 12. When a single acoustic matching layer 12 is provided, the thickness of the acoustic matching layer 12 is an odd number times the wavelength of 1/4.

In the present embodiment, since the elastic modulus of the acoustic matching layer 12 is much larger than that of the skin, a large amount of air gaps are generated when the acoustic matching layer 12 is directly attached to the skin, and therefore the bulk piezoelectric material sensor 2 is further provided with the skin coupling layer 14. As shown in fig. 9, the skin coupling layer 14 is disposed on the acoustic matching layer 12. When the detection device detects, the skin coupling layer 14 is directly contacted with the skin of the detection object. The skin coupling layer 14 may be made of a highly elastic solid material having an elastic modulus of less than 1 MPa. The elastic modulus of the skin coupling layer 14 is close to that of the skin, and the skin coupling layer 14 is directly contacted with the skin, so that a bonded air gap can be eliminated, and the ultrasonic penetration rate is enhanced. The skin coupling layer 14 may be made of rubber, silicone, Polydimethylsiloxane (PDMS), or other materials.

In this embodiment, the acoustic barrier layer may be a void spacer layer. The gap spacer layer may be vacuum or filled with air, nitrogen, or other gas, so as to ensure that the ultrasonic signal is better emitted from the detection surface 202 to the detection object. The material of the acoustic barrier layer may be a material having an acoustic impedance different from that of the bulk piezoelectric material sensor 2 by a predetermined value, such as epoxy, plastic, silicone rubber, or the like. By providing an acoustic barrier layer of suitable thickness, transmitted acoustic energy away from the detection surface 202 can be attenuated. The material of the acoustic barrier layer may also be an acoustically absorptive material to absorb and attenuate transmitted acoustic energy away from the detection surface 202. An acoustic barrier layer with a larger difference between the acoustic impedance and the bulk piezoelectric material sensor 2 and the first circuit board 1 can be arranged below the electrode layer on the lower surface of the bulk piezoelectric material sensor 2, and the acoustic barrier layer is selected to have a proper thickness to inhibit the backward propagation of the acoustic wave and also reduce the interference of the backward reflected acoustic wave on useful signals.

Preferably, the acoustic impedance value of the acoustic barrier layer is greater than 100 times the acoustic impedance value of the bulk piezoelectric material sensor 2, or less than 1/100 times the acoustic impedance value of the bulk piezoelectric material sensor 2.

In a preferred embodiment, the acoustic barrier layer may be located between the first electrode 10 or the second electrode 11 and the first circuit board 1. The first electrode 10 or the second electrode 11 is connected to the first circuit board 1 at multiple points for electrical connection and multi-point support. The first electrode terminal 13 and the second electrode terminal can be electrically connected to the first circuit board 1 through the solder paste 7 with a predetermined height, so as to electrically connect the first electrode 10 and the first circuit board 1, and the second electrode 11 and the first circuit board 1, as shown in fig. 3 and 6. The solder paste spot 7 may have a predetermined height of 20 to 60 μm in the vertical and vertical directions. The bulk piezoelectric material sensor 2 and the first circuit board 1 may be connected by an SMT (Surface Mounted Technology) process. The predetermined height of the solder paste spot 7 is a height after reflow (after reflow).

At this time, the area without the solder paste welding spot 7 between the piezoelectric material sensor 2 and the first circuit board 1 is filled with the air with the preset height to form an acoustic barrier layer. Solder paste solder joint 7 forms unsettled bearing structure, and the bottom surface electrode lower surface of body pressure electric material sensor 2 does not contact with other structures by a large scale, only contacts with first circuit board 1 point, can form the effect of cavity backing to improve signal strength, avoid the ultrasonic wave formation of downside reflection to disturb simultaneously. Meanwhile, a multi-point supporting structure can be adopted, so that the bending strength is improved, the reliability is improved, and meanwhile, the supporting points play a role in electrical connection.

In another possible embodiment, the first circuit board 1 may be located between the first electrode 10 or the second electrode 11 and the acoustic barrier layer, i.e. the acoustic barrier layer is provided on the second surface 102 of the first circuit board 1.

In the present embodiment, the first circuit board 1 is provided with a conductive circuit for electrically connecting the transducer with the circuit system. The first circuit board 1 may be a flexible circuit board FPC. Specifically, the first circuit board 1 has a first surface 101 and a second surface 102 opposite to each other. As shown in fig. 3 and 6, the first surface 101 and the second surface 102 are opposite to each other in the up-down direction. And the first surface 101 is located above the second surface 102. Of course, the first surface 101 is not limited to be located above the second surface 102, and the first surface 101 may also be located below the second surface 102, which is not specified in this application.

In order to improve reliability, the detection device may further comprise a stiffening layer 9. The stiffening layer 9 is disposed under the flexible circuit board to support the bulk piezoelectric material sensor 2 on the flexible circuit board. The reinforcing layer 9 may be made of stainless steel. The stiffening layer 9 may be arranged on the second surface 102 of the first circuit board 1 by means of a connection. The connection may be glue. Of course, the connecting portion is not limited to glue, and may be made of other materials, which is not limited in this specification.

In the present embodiment, the length of the bulk piezoelectric material sensor 2 is at least longer than the diameter of the artery to be detected, and is used to form a uniform ultrasonic beam, which is convenient for the user to align the bulk piezoelectric material sensor 2 with the blood vessel. The measurement of the diameter of blood vessels by means of ultrasound technology requires that the ultrasound beam must radiate the cross section of the blood vessel. When the blood pressure detection device is manufactured by using the ultrasonic transducer, the ultrasonic transducer needs to be arranged in an array form in a large area so as to ensure that the diameter of the blood vessel is irradiated by the acoustic beam. The body piezoelectric material sensor in the miniature ultrasonic blood pressure monitoring device in the embodiment directly adopts the single body piezoelectric material sensor 2 to emit uniform plane wave sound beams, so that the full coverage of the section of a blood vessel is realized, the sensitivity of diameter measurement to the relative position of the transducer is reduced, and the diameter measurement precision is ensured. The diameter of the human radial artery ranges from 2 to 3mm, the planar beam width must be larger than the diameter of the artery, and the larger the beam width, the easier it is for the user to align the piezo-electric material sensor 2 with the artery vessel. For example, the planar beam width can be 3-20mm, the length of the corresponding bulk piezoelectric material sensor 2 can be 3-20mm, the acoustic wavelength is far smaller than the length of the transducer, the diffraction effect is weak, and the beam width is close to the length of the transducer. When the width dimension of the bulk piezoelectric material sensor 2 is larger than 1mm, a uniform unidirectional plane beam can be obtained. The manufacturing cost of the micro ultrasonic wave of the piezoelectric material sensor is lower than that of a blood pressure measuring device manufactured by an array type PMUT ultrasonic transducer.

In this embodiment, the controller 8 may be disposed on the first surface 101 of the first circuit board 1 and electrically connected to the first circuit board 1. The first surface 101 of the first circuit board 1 is provided with a conductive circuit, and the controller 8 can be electrically connected with the bulk voltage material sensor 2 through the conductive circuit. The controller 8 may include a signal transmitting unit and a signal receiving unit to control the bulk piezoelectric material sensor 2 to transmit a signal and control the bulk piezoelectric material sensor 2 to transmit the received signal to the controller 8. Specifically, the controller 8 may control the external circuit to apply an alternating current to the bulk piezoelectric material sensor 2, so that the bulk piezoelectric material sensor 2 may emit an ultrasonic signal, which reaches a blood vessel to be measured in a human body through the skin by the detection surface 202, and the ultrasonic signal returns to the bulk piezoelectric material sensor 2 after being reflected by the blood vessel to be measured, and the bulk piezoelectric material sensor 2 may convert the received ultrasonic signal into an electrical signal and transmit the electrical signal to the controller 8.

As shown in fig. 9, in the present embodiment, a protection frame structure 15 is provided on the periphery of the bulk piezoelectric material sensor 2. The bulk piezoelectric material sensor 2 further includes a side surface 203 between the electrical mounting surface 201 and the detection surface 202. The protective frame structure 15 can fix the side 203, so that the body piezoelectric material sensor 2 can vibrate better to generate ultrasonic waves. The protective frame structure 15 can also protect the side surface 203 to prevent the side surface 203 from colliding.

In one possible embodiment, as shown in fig. 1 to 3, the protective frame structure 15 includes a first enclosure frame 3 disposed on the first surface 101. The first enclosure frame 3 is disposed on the peripheral side of the side surface 203, and a space is provided between the first enclosure frame 3 and the side surface 203. The bezel structure 15 further includes an adhesive layer 5 disposed in the spaced-apart space. The adhesive layer 5 is connected to the side surface 203, the first enclosure 3 and the first surface 101, respectively. The adhesive layer 5 may be glue. Of course, the adhesive layer 5 is not limited to glue, and may be other materials, which is not limited in this specification. The protective frame structure has low cost.

In this embodiment, the detection device can be manufactured by the following steps. First, the piezoelectric material sensor 2 is manufactured, and solder paste is applied to the first electrode lead 13 and the second electrode lead. The first circuit board 1 and the controller 8 are manufactured at the same time, and the controller 8 is connected with the first surface 101 of the first circuit board 1 by using an SMT process. The first enclosure frame 3 can be connected with the first surface 101, the electric mounting surface 201 of the piezoelectric material sensor 2 is connected with the first surface 101 of the first circuit board 1 through the first electrode leading-out terminal 13 and the second electrode leading-out terminal by using an SMT process, and finally the side surface 203 of the piezoelectric material sensor 2 is subjected to glue dispensing protection, so that the first enclosure frame 3 can prevent glue from overflowing due to cross flow before curing, and therefore the first circuit board 1 is prevented from being polluted.

In another possible embodiment, as shown in fig. 4 to 6, the protective frame structure 15 includes a second enclosure frame 4 disposed on the first surface 101. The second surrounding frame 4 is disposed on the peripheral side of the side surface 203, and the second surrounding frame 4 is attached to the side surface 203. Specifically, the second enclosure frame 4 may be made of epoxy resin. The protection frame structure is manufactured by adopting a customized die machine, so that labor can be saved, and the packaging precision is improved.

In this embodiment, the detection device can be manufactured by the following steps. First, the body pressure sensor 2 may be manufactured by open-molding (open-molding), in which the second surrounding frame 4 is closely attached to the side surface 203 of the body pressure sensor 2, the electrical mounting surface 201 and the detection surface 202 of the body pressure sensor 2 are exposed, and the electrical mounting surface 201 may be exposed by grinding. And the first electrode lead 13 and the second electrode lead are brushed with solder paste. The first circuit board 1 and the controller 8 are manufactured at the same time, and the controller 8 is connected with the first surface 101 of the first circuit board 1 by using an SMT process. Then, the electrical mounting surface 201 of the bulk piezoelectric material sensor 2 is connected to the first surface 101 of the first circuit board 1 through the first electrode lead 13 and the second electrode lead by using the SMT process.

In the present embodiment, the thickness of each layer of the detection device can be determined according to the operating frequency, and for example, when the operating frequency is 10M, the thickness of the corresponding bulk piezoelectric material sensor 2 is about 0.2mm, and the thickness of the single-layer acoustic matching layer 12 is 1/4 wavelengths. The thicknesses of the acoustic barrier layer, the first circuit board 1 and the reinforcing layer can be selected according to the process feasibility. The total thickness of the whole detection device can be controlled within 2 mm.

In one possible embodiment, the body piezoelectric material sensor 2 may have a length of 7 mm and a width of 2 mm. The controller 8 may be 4 mm long and 4 mm wide. The first circuit board 1 may have a length of 14 mm and a width of 4.8 mm. Of course, in other embodiments, the sizes of the body pressure material sensor 2, the controller 8, and the first circuit board 1 may be adjusted as needed, and the present specification is not limited to the only one.

In a preferred embodiment, the thickness of the bulk piezoelectric material sensor 2 may be 300 micrometers, the thickness of the first circuit board 1 may be 100 micrometers, and the total thickness of the reinforcing layer 9 and the connecting portion may be 140 micrometers in a direction along the electrical mounting surface 201 to the detection surface 202, i.e., in the up-down direction in the drawing. The total thickness of the transducer may thus be 560 microns. This embodiment may also provide a transducer with an overall thickness of less than 560 microns. The thickness of the first enclosure frame 3 may be 200 microns, the thickness of the second enclosure frame 4 may be 290 microns, and the thickness of the controller 8 may be 360 microns. Of course, in other embodiments, the specific size of the thickness of each of the aforementioned components may be adjusted according to needs, and this specification is not limited to this.

The miniature ultrasonic blood pressure detection device provided by the specification can be manufactured by directly utilizing the traditional machining process, the manufacturing process is simple, the cost is low, the mass production is easy, meanwhile, the electromechanical coupling coefficient of the piezoelectric material is high, the sensitivity is high, the skin penetrability is strong, and a good blood pressure detection effect is achieved.

It should be noted that, in the description of the present specification, the terms "first", "second", and the like are used for descriptive purposes only and for distinguishing similar objects, and no order is present therebetween, and no indication or suggestion of relative importance is to be made. Further, in the description of the present specification, "a plurality" means two or more unless otherwise specified.

Any numerical value recited herein includes all values from the lower value to the upper value, in increments of one unit, provided that there is a separation of at least two units between any lower value and any higher value. For example, if it is stated that the number of a component or a value of a process variable (e.g., temperature, pressure, time, etc.) is from 1 to 90, preferably from 20 to 80, and more preferably from 30 to 70, it is intended that equivalents such as 15 to 85, 22 to 68, 43 to 51, 30 to 32 are also expressly enumerated in this specification. For values less than 1, one unit is suitably considered to be 0.0001, 0.001, 0.01, 0.1. These are only examples of what is intended to be explicitly recited, and all possible combinations of numerical values between the lowest value and the highest value that are explicitly recited in the specification in a similar manner are to be considered.

Unless otherwise indicated, all ranges include the endpoints and all numbers between the endpoints. The use of "about" or "approximately" with a range applies to both endpoints of the range. Thus, "about 20 to about 30" is intended to cover "about 20 to about 30", including at least the endpoints specified.

The term "consisting essentially of …" describing a combination shall include the identified element, ingredient, component or step as well as other elements, ingredients, components or steps that do not materially affect the basic novel characteristics of the combination. The use of the terms "comprising" or "including" to describe combinations of elements, components, or steps herein also contemplates embodiments that consist essentially of such elements, components, or steps. By using the term "may" herein, it is intended to indicate that any of the described attributes that "may" include are optional.

A plurality of elements, components, parts or steps can be provided by a single integrated element, component, part or step. Alternatively, a single integrated element, component, part or step may be divided into separate plural elements, components, parts or steps. The disclosure of "a" or "an" to describe an element, ingredient, component or step is not intended to foreclose other elements, ingredients, components or steps.

It is to be understood that the above description is intended to be illustrative, and not restrictive. Many embodiments and many applications other than the examples provided will be apparent to those of skill in the art upon reading the above description. The disclosures of all articles and references, including patent applications and publications, are hereby incorporated by reference for all purposes.

Claims (14)

1. A miniature ultrasonic blood pressure monitor, comprising:

at least one body piezoelectric material sensor, wherein the body piezoelectric material sensor is used for converting electric energy and mechanical energy and transmitting and receiving ultrasonic waves, and one side of the body piezoelectric material sensor, which transmits and receives the ultrasonic waves, faces to a detection object; the bulk piezoelectric material sensor is at least provided with a first electrode leading-out end and a second electrode leading-out end;

the first circuit board is arranged below the bulk piezoelectric material sensor, and an acoustic barrier layer is arranged between the bulk piezoelectric material sensor and the first circuit board so as to prevent the ultrasonic waves of the bulk piezoelectric material sensor from propagating to the first circuit board; and the number of the first and second groups,

and the controller is electrically connected with the first electrode leading-out end and the second electrode leading-out end of the bulk voltage material sensor through the first circuit board.

2. The miniature ultrasonic blood pressure measuring device of claim 1, wherein a protective frame structure is disposed around the bulk piezoelectric material sensor.

3. The miniature ultrasonic blood pressure monitor of claim 1, wherein said bulk piezoelectric material sensor has a sensing surface and an electrical mounting surface opposite said sensing surface; the electrical installation surface faces the first circuit board.

4. The miniature ultrasonic blood pressure monitor of claim 3, wherein said first electrode lead and said second electrode lead are both disposed on an electrical mounting surface of said bulk piezoelectric material sensor.

5. The miniature ultrasonic blood pressure monitor of claim 1, wherein said bulk piezoelectric material sensor has a first electrode, a second electrode and a bulk piezoelectric material, said bulk piezoelectric material being disposed between said first electrode and said second electrode, said first electrode being in electrical communication with said first electrode lead and said second electrode being in electrical communication with said second electrode lead.

6. The miniature ultrasonic blood pressure measuring device according to claim 1, wherein said bulk piezoelectric material sensor is further provided with an acoustic matching layer, said acoustic matching layer being provided on a surface of said bulk piezoelectric material sensor facing said measurement object.

7. The miniature ultrasonic blood pressure measuring device of claim 6, wherein the impedance value of said acoustic matching layer is between the acoustic impedance value of said bulk piezoelectric material sensor and the acoustic impedance value of said subject.

8. The miniature ultrasonic blood pressure measuring device of claim 6, wherein said body pressure piezoelectric material sensor is further provided with a skin coupling layer, said skin coupling layer being disposed on said acoustic matching layer; when the detection device detects, the skin coupling layer is directly contacted with the skin of the detection object.

9. The miniature ultrasonic blood pressure monitor of claim 1, wherein said first circuit board is a flexible circuit board.

10. The miniature ultrasonic blood pressure monitor of claim 9, further comprising a stiffening layer disposed under said flexible circuit board to support said bulk piezoelectric material sensor on said flexible circuit board.

11. The miniature ultrasonic blood pressure monitor of claim 1 wherein said acoustic barrier layer is a void spacer layer.

12. The miniature ultrasonic blood pressure device of claim 1 wherein the acoustic impedance value of said acoustic barrier layer is greater than 100 times the acoustic impedance value of said bulk piezoelectric material sensor or less than 1/100 times the acoustic impedance value of said bulk piezoelectric material sensor.

13. The miniature ultrasonic blood pressure monitor of claim 1, wherein the length of said bulk piezoelectric material sensor is at least greater than the diameter of an artery of said subject.

14. The miniature ultrasonic blood pressure monitor of any one of claims 1-13, wherein the bulk piezoelectric material in said bulk piezoelectric material sensor is a piezoelectric material having piezoelectric or ferroelectric effect.

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