WO2019010616A1 - 脉搏波传感器、传感器阵列及采用其的脉搏波测量装置 - Google Patents

脉搏波传感器、传感器阵列及采用其的脉搏波测量装置 Download PDF

Info

Publication number
WO2019010616A1
WO2019010616A1 PCT/CN2017/092400 CN2017092400W WO2019010616A1 WO 2019010616 A1 WO2019010616 A1 WO 2019010616A1 CN 2017092400 W CN2017092400 W CN 2017092400W WO 2019010616 A1 WO2019010616 A1 WO 2019010616A1
Authority
WO
WIPO (PCT)
Prior art keywords
sensor
pulse wave
flexible piezoelectric
static pressure
flexible
Prior art date
Application number
PCT/CN2017/092400
Other languages
English (en)
French (fr)
Inventor
张劭龙
刘苏
耿兴光
张以涛
张俊
侯洁娜
张海英
Original Assignee
中国科学院微电子研究所
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 中国科学院微电子研究所 filed Critical 中国科学院微电子研究所
Priority to PCT/CN2017/092400 priority Critical patent/WO2019010616A1/zh
Publication of WO2019010616A1 publication Critical patent/WO2019010616A1/zh

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure

Definitions

  • the present disclosure belongs to the field of non-invasive detection technology for human health, and particularly relates to a device for collecting brachial artery pulse waves, and more particularly to a pulse wave sensor, a sensor array, and a pulse wave measuring device using the same.
  • Pulse waveforms reflect human health and a variety of diseases. Pulse wave measurement methods are classified into invasive and non-invasive. The invasive pulse wave measurement method causes great damage to the patient, and the non-invasive type has little damage to the patient, such as a pressure sensor, an ultrasonic sensor, a photoelectric sensor, and the like. These sensors enable non-invasive measurement of pulse waves. However, the current mainstream method of measuring pulse waves is still a pressure sensor to measure pulse waves. Some devices use a piezoresistive pressure sensor to pulse multiple points on the wrist. Some devices use strain gauges as pulse wave sensors, and some devices use MEMS piezoresistive sensors to detect pulse. The dynamic range of the above sensor is limited by the material itself, and the sensitivity is limited by the range.
  • Pressure sensors with pure piezoelectric principle have high sensitivity and the output amplitude is not affected by static pressure, but piezoelectric sensors cannot measure static pressure. Therefore, the two sensors independently used for pulse wave measurement can not effectively reflect the physical condition of the person being tested. If you want to reflect the type of disease through the pulse wave, pulse waves must be acquired over a wide range of static pressures. However, the sensitivity of current piezoresistive sensors is determined by the range in which the force is applied. This results in a small-range pressure sensor range that does not meet the test requirements. The large-range sensor output voltage has a low resolution of force, and cannot output a morphological pulse wave at low pressure.
  • the existing sensor array has two problems.
  • One problem is that the sensor array cannot meet the problem of arm shape fit of different people.
  • the difference in array fit cannot guarantee the acquisition of pulse waves.
  • the fidelity Another problem is the mutual interference between the sensors caused by the deformation of the sensor. This problem can superimpose the pulse waves collected by adjacent sensors and affect the accuracy of the pulse wave.
  • the main object of the present disclosure is to provide a pulse wave sensor, a sensor array, and a pulse wave measuring apparatus using the same, to solve at least one of the above technical problems.
  • the present disclosure provides a pulse wave sensor including a sensor skeleton and a flexible piezoelectric sensor, characterized in that:
  • the flexible piezoelectric sensor includes a flexible piezoelectric film for sensing a pulse wave and converting it into an electrical signal;
  • the sensor frame is for fixing the flexible piezoelectric sensor
  • One side of the sensor skeleton connecting the flexible piezoelectric sensor includes a downwardly concave space, and the flexible piezoelectric sensor is wholly or partially fixed around the downwardly concave space, thereby making the flexible piezoelectric sensor flexible.
  • the piezoelectric film is wholly or partially suspended.
  • the present disclosure also provides a pulse wave sensor array including an elastic buffer material and a plurality of pulse wave sensors as described above, wherein a plurality of the pulse wave sensors are distributed at intervals in the elastic buffer On the material.
  • the present disclosure also provides a pulse wave measuring apparatus characterized in that the pulse wave sensor array as described above is employed.
  • the pulse wave sensor of the present disclosure has the following beneficial effects: the sensor gives a large deformation space of the flexible film, thereby being capable of generating a stronger electrical signal, and the sensitivity is higher; the sensor overcomes the pulse in the prior art.
  • the wave acquisition device cannot accurately and comprehensively reflect the problem of the pulse information of the human body.
  • the traditional piezoresistive sensor range is inversely proportional to the sensitivity.
  • the pulse wave sensor needs to capture the weak pulse signal in a large range, while the conventional piezoresistive sensor is in a large range.
  • the sensitivity is lower, and the sensor of the present disclosure will have a static pressure signal
  • the dynamic pulse wave pressure signal is measured separately, the piezoelectric pressure film is used to measure the dynamic pressure fluctuation, and the piezoresistive sensor measures the static pressure, so that the dynamic sensitivity is not affected by the static pressure range, and the pulse wave can be highly sensitive under a wide range of static pressure;
  • the sensor of the present disclosure adopts a skeleton with a long curved surface shape and an elastic buffer material as a support, so that the array can satisfy the wrist characteristics of different groups of people and achieve a good fit to the arm surface.
  • FIG. 1 is a schematic structural view of a pulse wave sensor of the present disclosure
  • FIG. 2 is a side elevational view of the pulse wave sensor array structure of the present disclosure
  • 3A-3C are schematic diagrams showing the positional relationship between the downwardly concave space on the sensor skeleton of the present disclosure and the flexible film of the flexible piezoelectric sensor, respectively;
  • FIG. 4 is a schematic view showing the positional relationship between the pulse wave measuring device and the radial artery of the present disclosure
  • Fig. 5 is a front elevational view showing the positional relationship between the pulse wave sensor array structure of the present disclosure and the radial artery.
  • the present disclosure is to solve the problem that the pulse wave collecting device in the prior art cannot accurately and comprehensively reflect the pulse information of the human body.
  • Traditional piezoresistive sensor ranges are inversely proportional to sensitivity. Pulse wave sensors need to capture weak pulse signals over a wide range of ranges, while conventional piezoresistive sensors have lower sensitivity over a wide range of ranges.
  • the static pressure signal is measured separately from the dynamic pulse wave pressure signal, the dynamic pressure fluctuation is measured by the piezoelectric film, and the static pressure is measured by the piezoresistive sensor, thereby improving the sensitivity of the piezoelectric thin film sensor and making the pulse
  • the wave signal is sharper and the static pressure is accurately measured over a wide pressure range.
  • the present disclosure provides a structure for mitigating mutual interference between sensors and adapting to different groups of people's arms, in view of the problem of sensor state mutual influence and arm-fitting in existing sensor arrays.
  • the present disclosure discloses a pulse wave sensor including a sensor skeleton and a flexible piezoelectric sensor for sensing a pulse wave; a sensor skeleton for fixing The flexible piezoelectric sensor; the side of the sensor skeleton connecting the flexible piezoelectric sensor comprises a downwardly concave space, and the flexible piezoelectric sensor is fully or partially fixed around the downwardly concave space, the flexible pressure
  • the sensitive area of the electric sensor that is, the flexible piezoelectric film is completely or partially suspended, so that it can be bent into the downwardly concave space when subjected to an external force without bending out to the downwardly concave space, so that the phenomenon It is possible to prevent the piezoelectric induction of the flexible piezoelectric film from generating opposite polarities; in addition, the presence of the downwardly concave space also gives the flexible piezoelectric film a larger deformation space, thereby generating a stronger electrical signal.
  • the flexible piezoelectric sensor is a piezoelectric pressure sensor, and the piezoelectric material thereof includes, for example, but not limited to, PVDF (polyvinylidene fluoride), PZT (lead zirconate titanate piezoelectric ceramic), BaTiO 3 , and the like.
  • the flexible piezoelectric sensor is further provided with a contact, and one side of the contact is connected with the skin to be tested, and is used for fitting the surface of the arm and conducting the pulse wave to be tested, and detecting the other side of the contact with the flexible piezoelectric sensor.
  • the unit usually the flexible piezoelectric film
  • the unit is connected or in contact, and transmits the pulse wave to be measured to the detecting unit of the flexible piezoelectric sensor.
  • the pulse wave sensor further comprises a static pressure sensor, wherein the static pressure sensor is used to measure a static pressure applied to the pulse wave sensor; the static pressure sensor is also fixed on the sensor frame.
  • the static pressure sensor may be a piezoresistive sensor, such as but not limited to a MEMS sensor, a piezoresistive film sensor, and a strain gauge sensor.
  • the static pressure sensor is also provided with a contact, and the contact of the static pressure sensor is used to conduct the static pressure to the detection unit of the static pressure sensor.
  • the materials of the contacts of the two sensors include, but are not limited to, materials such as silica gel, foam, sponge, etc., and the Shore A hardness of the contacts is, for example, between 1 and 80 degrees.
  • the sensor skeleton can be designed as a go-go shape, a long strip shape, a button shape or other shapes, preferably a spherical shape, a cylinder or a long strip curved into a curved surface.
  • the pulse wave sensor formed by the sensor skeleton may be distributed in a dot matrix form, for example, a 5 ⁇ 5 dot matrix on the wrist to be tested; when it is a long curved curved surface
  • the bonding surface is a circular arc surface or a hyperboloid shape, so that the pulse wave sensor formed by the sensor skeleton can be similar to a half bracelet. The shape surrounds the wrist being tested.
  • the flexible piezoelectric sensor is disposed on the side of the sensor frame close to the skin, and the static pressure sensor is disposed on the opposite side of the sensor frame and the flexible piezoelectric sensor.
  • the present disclosure also discloses a pulse wave sensor array including an elastic cushioning material and a plurality of the above-described pulse wave sensors, wherein the plurality of pulse wave sensors are distributed on the elastic cushioning material at intervals.
  • the elastic cushioning material includes, for example, but not limited to, a urethane sponge, a slow rebound memory foam, etc., and the pulse wave sensor array can be attached to the arms of different people.
  • the number of the pulse wave sensors is, for example, five, or may be three, four, six, seven, eight, nine, ten A, along the measured wrists are equally spaced apart.
  • the first sensor is attached to the lateral side of the wrist to the side of the palm, and the remaining sensors are sequentially arranged in the direction of the elbow of the arm.
  • the static pressure sensor senses the static pressure transmitted from the elastic buffer material above the sensor array, and the flexible piezoelectric sensor is used to measure the radial artery pulse, which is finally realized at different pressures. Detection of brachial artery pulse signals by a lower pulse wave sensor array.
  • the present disclosure also discloses a pulse wave measuring apparatus including the pulse wave sensor array and the pressurizing device as described above, wherein the pressurizing device uses, for example, an inflatable bandage, or an inflatable balloon Wait.
  • the pulse wave sensor of the present disclosure includes a sensor backbone, a flexible piezoelectric sensor, a flexible piezoelectric sensor contact, a static pressure sensor, a static pressure sensor contact.
  • the concave side of the sensor frame is connected to the flexible piezoelectric sensor for supporting the flexible piezoelectric sensor; the other side of the sensor frame is connected with the static pressure sensor for supporting the static pressure sensor.
  • the other side of the flexible piezoelectric sensor is connected to the flexible contact for sensing the pulse wave transmitted by the contact.
  • the other side of the contact is attached to the skin for adhering to the arm surface and conducting pulse waves.
  • the other side of the static pressure sensor is connected to a pressurizing device for detecting the overall pressure experienced by the sensor structure.
  • the static pressure sensor is a piezoresistive sensor, including but not limited to a MEMS sensor, a piezoresistive film sensor, and a strain gauge sensor.
  • the flexible piezoelectric sensor is a piezoelectric pressure sensor, and the piezoelectric material includes but is not limited to materials such as PVDF, PZT, and BaTiO 3 .
  • the material of the contacts includes but is not limited to materials such as silicone, foam and sponge.
  • the pulse wave sensor array of the present disclosure comprises a porous elastic buffer material and five pulse wave sensors, the porous elastic buffer material is connected to five sensors, and the porous elastic buffer material is connected to one side of the static pressure sensor structure. It is used for absorption buffer and reduces vibration interference between sensors and external impact interference.
  • the porous elastic cushioning material allows the sensor array to fit the arms of different people.
  • the porous elastic cushioning material is not limited to a urethane sponge, a slow rebound memory foam, or the like.
  • Each sensor is sequentially spaced along the wrist at equal intervals.
  • the first sensor is placed close to the palm side of the wrist, and the second to fifth sensors are sequentially arranged from the side of the wrist. This distribution can be applied to no With the length of the arm of the crowd, increase the length of the radial artery fluctuation detection.
  • the pulse wave sensor of the present disclosure includes a sensor skeleton 1, a flexible piezoelectric sensor 2, a contact 3 of a flexible piezoelectric sensor, a static pressure sensor 4, and a contact 5 of a static pressure sensor.
  • the contact 3 of the flexible piezoelectric sensor is in contact with the skin 12, the material property of the contact 3 of the flexible piezoelectric sensor enables it to fit the skin, and the contact 3 of the flexible piezoelectric sensor has a certain elastic deformation to make the arm radial artery 10
  • the pulse wave is transmitted to the flexible piezoelectric sensor 2.
  • the flexible piezoelectric sensor is attached to the sensor frame 1 in a curved state, and converts the pulse wave fluctuations transmitted by the contacts 3 of the flexible piezoelectric sensor into electrical signals, and the converted electrical signals are output through the two poles of the flexible piezoelectric sensor 2.
  • the flexible piezoelectric sensor 2 can output an electrical signal.
  • the sensor frame 1 has a long curved shape, and one side of the flexible piezoelectric sensor 2 is supported.
  • the side of the sensor frame 1 connected to the flexible piezoelectric sensor 2 includes a downwardly concave space 8, the flexible piezoelectric sensor 2 is laid flat above the downwardly concave space 8, and the edge is fixed at the periphery of the downwardly concave space 8, as shown in Fig. 3A, which is fixed at all sides, and is concave downward at this time.
  • the flexible film above the space 8 is suspended.
  • the suspended structure converts the forward pressure received by the flexible film of the flexible piezoelectric sensor 2 into a pulling force to the periphery, thereby greatly increasing the pressure of the flexible film, thereby causing a larger piezoelectric signal, thereby Increased sensor sensitivity.
  • the other side of the sensor frame 1 is fixed with a static pressure sensor 4, and the other side of the static pressure sensor 4 is connected to a pressurizing device 9 for detecting the overall pressure experienced by the sensor structure.
  • the sensor array comprises a porous elastic buffer material 7 and five of the aforementioned pulse wave sensors 6-1, 6-2, 6-3, 6-4, 6-5.
  • the sensor array is laid flat on the wrist to be tested. Due to the characteristics of the elastic cushioning material 7, the five sensors 6-1, 6-2, 6-3, 6-4, 6-5 can be attached according to the measured hand type. The wrist surface of the arm.
  • the elastic buffer material 7 can also absorb the extra impact, reduce the influence of the pulse beat point under a certain sensor on the adjacent sensor, and reduce mutual interference between the sensors.
  • the sensor array is used to detect pulse pulsations of the iliac artery 10 near the tibia 11 at different pressures.
  • Each sensor is sequentially spaced along the wrist at equal intervals.
  • the first sensor 6-1 is adjacent to the palm side of the wrist, and the second to fifth sensors 6-2, 6-3, 6-4, 6-5 are sequentially arranged from the side of the wrist horizontal arm. This distribution can be applied to different groups of arm lengths, increasing the length of the radial artery 10 fluctuation detection.
  • the static pressure sensor 4 senses the static pressure transmitted from the elastic buffer material 1 above the sensor, and the flexible piezoelectric sensor 2 is used to measure the radial artery pulse, and finally realizes under different pressures.
  • the sensor array detects the brachial artery pulse signal.
  • the flexible film of the flexible piezoelectric sensor 2 may be fixed only on both sides (FIG. 3B); or three-sidedly fixed (FIG. 3C), in which the hatched portion indicates a downwardly concave space. 8 overlapping portion with the flexible film; or completely suspended above the downwardly concave space 8 by the projecting jig; these do not affect the realization of the technical effects of the present disclosure.
  • a reinforcing rib or a guide strip may be provided on the flexible film to be bent as far as possible in a certain direction to avoid malfunction.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physiology (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Physics & Mathematics (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

提供一种脉搏波传感器、传感器阵列及采用其的脉搏波测量装置。该脉搏波传感器包括传感器骨架（1）、柔性压电传感器（2）和静态压力传感器（4），其中：柔性压电传感器（2）包括柔性压电薄膜，用于感测脉搏波并将其转化成电信号；传感器骨架（1）用于固定；传感器骨架（1）连接柔性压电传感器（2）的一侧包含一向下凹的空间（8），从而柔性压电传感器（2）的柔性压电薄膜是全部或部分悬空的。该脉搏波传感器将静态压力信号与动态脉搏波压力信号分开测量，利用压电薄膜测量动态压力波动，压阻式静态压力传感器测量静态压力，从而动态灵敏度不受静态压力量程影响，能够在宽范围静态压力下，对脉搏波保持高灵敏度。另外该脉搏波传感器采用柔性骨架，组成的阵列可以满足不同人群手腕特征，实现对手臂表面良好的贴合。

Description

脉搏波传感器、传感器阵列及采用其的脉搏波测量装置 技术领域
本公开属于人体健康状态无创检测技术领域，具体地涉及一种用于采集桡动脉脉搏波的装置，更具体地涉及一种脉搏波传感器、传感器阵列及采用其的脉搏波测量装置。
背景技术
脉搏波形可以反映人体健康程度以及多种疾病。脉搏波测量方法分为侵入和非侵入。侵入式脉搏波测量方法对病人造成极大伤害，非侵入式对病人伤害小，比如压力传感器、超声传感器、光电传感器等。这些传感器都可实现非侵入式测量脉搏波。但是目前主流的测量脉搏波的方法依旧是压力传感器测脉搏波。有些设备利用薄膜压阻式压力传感器对腕部多点进行脉搏采集，有些设备采用了应变计作为脉搏波传感器，还有一些设备采用MEMS压阻传感器检测脉搏。上述传感器动态范围由于受材料本身限制，灵敏度受到量程制约，相同供电和灵敏度下，测力量程越大，对力的分辨率越低，输出电压越低。后续的放大电路也只是单纯放大，放大倍数过高在大压力下电压输出容易饱和。另外从静态压力中提取动态脉搏波增加了后续处理电路和算法复杂度。
单纯的压电原理的压力传感器尽管具有很高的灵敏度且输出幅值不会受静态压力影响，但是压电传感器不能测量静态压力。因此这两种传感器独立的用于脉搏波测量都不能有效反映被测人的身体状况。如果想通过脉搏波反映疾病类型，必须在宽范围静态压力采集脉搏波。但是当前的压阻式传感器的灵敏度由施加力的量程决定。这就导致了小量程压力传感器量程不能满足测试要求，大量程传感器输出电压对力的分辨能力较低，在低压力下不能输出有形态意义的脉搏波。
另外，现有的传感器阵列存在两个问题，一个问题是传感器阵列不能满足不同人群手臂外形贴合问题，阵列贴合度差无法保障采集脉搏波 的保真度；另一个问题是传感器形变带来的传感器间相互干扰问题，该问题可使相邻传感器采集的脉搏波相互叠加，影响脉搏波准确性。
因此有必要研究一种既能测量大静态压力，同时又保持高灵敏度、动态测量范围广泛的脉搏波传感器，并组成能够减轻传感器间干扰，与手臂贴合的传感器。
发明内容
有鉴于此，本公开的主要目的在于提供一种脉搏波传感器、传感器阵列及采用其的脉搏波测量装置，以解决上述技术问题中的至少之一。
为了实现上述目的，作为本公开的一个方面，本公开提供了一种脉搏波传感器，包括传感器骨架和柔性压电传感器，其特征在于：
所述柔性压电传感器包括柔性压电薄膜，用于感测脉搏波并将其转化成电信号；
所述传感器骨架用于固定所述柔性压电传感器；以及
所述传感器骨架连接所述柔性压电传感器的一侧包含一向下凹的空间，所述柔性压电传感器全部或部分固定在该向下凹的空间的四周，从而所述柔性压电传感器的柔性压电薄膜是全部或部分悬空的。
作为本公开的另一个方面，本公开还提供了一种脉搏波传感器阵列，包括弹性缓冲材料和若干如上所述的脉搏波传感器，其中若干所述脉搏波传感器以一定间隔分布在所述弹性缓冲材料上。
作为本公开的再一个方面，本公开还提供了一种脉搏波测量装置，其特征在于，其中采用如上所述的脉搏波传感器阵列。
基于上述技术方案可知，本公开的脉搏波传感器具有如下有益效果：该传感器给柔性薄膜较大的变形空间，从而能够产生更强的电信号，灵敏度更高；该传感器克服了现有技术中脉搏波采集装置无法精准、全面地反映出人体的脉象信息的问题，传统压阻式传感器量程与灵敏度成反比，脉搏波传感器需要在大量程范围捕捉微弱脉搏信号，而传统压阻传感器在大量程范围中灵敏度较低，而本公开的传感器将静态压力信号与 动态脉搏波压力信号分开测量，利用压电薄膜测量动态压力波动，压阻式传感器测量静态压力，从而动态灵敏度不受静态压力量程影响，能够在宽范围静态压力下，对脉搏波保持高灵敏度；本公开的传感器采用长条形曲面形状的骨架及弹性缓冲材料作为支撑，从而组成的阵列可以满足不同人群手腕特征，实现对手臂表面良好的贴合。
附图说明
图1是本公开的脉搏波传感器的结构原理图；
图2是本公开的脉搏波传感器阵列结构的侧视示意图；
图3A-3C分别是本公开的传感器骨架上向下凹的空间与柔性压电传感器的柔性薄膜之间的位置关系示意图；
图4是本公开的脉搏波测量装置与桡动脉的位置关系示意图；
图5是本公开的脉搏波传感器阵列结构与桡动脉的位置关系的正视图。
在上图中，附图标记含义如下：
1、传感器骨架
2、柔性压电传感器     3、柔性压电传感器的触点
4、静态压力传感器     5、静态压力传感器的触点
6、传感器单元
6-1、第一传感器单元
6-2、第二传感器单元
6-3、第三传感器单元
6-4、第四传感器单元
6-5、第五传感器单元
7、弹性缓冲材料
8、向下凹的空间
9、加压装置
10、桡动脉            11、桡骨
12、皮肤
具体实施方式
为使本公开的目的、技术方案和优点更加清楚明白，以下结合具体实施例，并参照附图，对本公开作进一步的详细说明。
本公开是为了解决现有技术中的脉搏波采集装置无法精准、全面地反映出人体的脉象信息的问题。传统压阻式传感器量程与灵敏度成反比，脉搏波传感器需要在大量程范围捕捉微弱脉搏信号，而传统压阻传感器在大量程范围中灵敏度较低。为了解决此问题，本公开中将静态压力信号与动态脉搏波压力信号分开测量，利用压电薄膜测量动态压力波动，压阻式传感器测量静态压力，从而提高了压电薄膜传感器的灵敏度，使得脉搏波信号更加清晰，并且在大压力范围下准确测量静态压力。
此外，本公开针对现有传感器阵列中传感器状态相互影响问题和手臂贴服问题，提供了一种减轻传感器间相互干扰，又能适应不同人群手臂的结构。
具体地，作为本公开的一个方面，本公开公开了一种脉搏波传感器，所述脉搏波传感器包括传感器骨架和柔性压电传感器，柔性压电传感器用于感测脉搏波；传感器骨架用于固定该柔性压电传感器；所述传感器骨架连接所述柔性压电传感器的一侧包含一向下凹的空间，该柔性压电传感器全部或部分固定在该向下凹的空间的四周时，该柔性压电传感器的敏感区域，即柔性压电薄膜是全部或部分悬空的，从而在受到外力时能够向该向下凹的空间内弯曲，而不会出现向向下凹的空间外弯曲的现象，这样可以避免柔性压电薄膜的压电感应产生相反的极性；此外，向下凹的空间的存在也使柔性压电薄膜有更大的形变空间，从而产生更强的电信号。
其中，该柔性压电传感器为压电式压力传感器，其压电材料例如包括但不限于PVDF(聚偏氟乙烯)、PZT(锆钛酸铅压电陶瓷)、BaTiO3等。
其中，柔性压电传感器上还设置有触点，触点一侧与待测的皮肤相连，用于贴合手臂表面和传导待测的脉搏波，触点另一侧与柔性压电传感器的检测单元(通常即为该柔性压电薄膜)相连或相接触，将待测的脉搏波传导到柔性压电传感器的检测单元上。
其中，该脉搏波传感器还包括静态压力传感器，其中该静态压力传感器用于测量施加在该脉搏波传感器上的静态压力；该静态压力传感器也固定于该传感器骨架上。
其中，静态压力传感器可以为压阻式传感器，例如包括但不限于MEMS传感器、压阻膜传感器、应变计式传感器。
其中，静态压力传感器上也设置有触点，静态压力传感器的触点用于将承受的静态压力传导到静态压力传感器的检测单元上。
其中，两种传感器的触点的材质包括但不限于硅胶、泡棉、海绵等材料，触点的邵氏硬度A例如在1-80度之间。
其中，传感器骨架可以设计成围棋棋子形状、长条形状、纽扣形状或其它形状，优选为球缺、圆柱体或弯曲成曲面的长条形体。当其为球缺或圆柱体形状时，通过该传感器骨架形成的脉搏波传感器可以以点阵形式，例如5×5的点阵形式分布在被测手腕上；当其为弯曲成曲面的长条形体时，优选为能够与手腕部被测部位贴合的长条状曲面形状，例如贴合面为圆弧面或双曲面形状，从而通过该传感器骨架形成的脉搏波传感器可以以类似于半边手镯的形状环绕着被测手腕。
其中，为了保证测量精度，柔性压电传感器设置于传感器骨架靠近贴合皮肤的一面，静态压力传感器设置于传感器骨架与柔性压电传感器相反的另一面。
作为本公开的另一个方面，本公开还公开了一种脉搏波传感器阵列，包括弹性缓冲材料和若干上述的脉搏波传感器，其中该若干脉搏波传感器以一定间隔分布在该弹性缓冲材料上。
该弹性缓冲材料例如包括但不限于聚氨酯海绵、慢回弹记忆海绵等，可以使该脉搏波传感器阵列贴合不同人群的手臂。
该若干脉搏波传感器例如为5个，也可以是3、4、6、7、8、9、10 个，沿被测的腕部等间距依次排开。作为优选，其中的第一传感器贴于腕横纹靠近手掌一侧，其余的传感器依次向手臂的肘部方向排列。
当外界有加压装置对该脉搏波传感器阵列施加压力时，静态压力传感器感受来自传感器阵列上方的弹性缓冲材料传递的静态压力，柔性压电传感器用于测量桡动脉脉博，最终实现在不同压力下脉搏波传感器阵列对桡动脉脉搏信号的检测。
作为本公开的再一个方面，本公开还公开了一种脉搏波测量装置，包括如上所述的脉搏波传感器阵列和加压装置，其中加压装置例如采用可充气的绷带，或者可膨胀的气囊等。
在一些具体实施例中，本公开的脉搏波传感器，包括传感器骨架、柔性压电传感器、柔性压电传感器触点、静态压力传感器、静态压力传感器触点。其中传感器骨架凹侧与柔性压电传感器相连，用于支撑该柔性压电传感器；传感器骨架另一侧与静态压力传感器相连，用于支撑该静态压力传感器。柔性压电传感器另一侧与柔性触点相连，用于感受触点所传导的脉搏波。触点另一侧与皮肤相连，用于贴合手臂表面和传导脉搏波。静态压力传感器另一侧与加压装置相连，用于检测此传感器结构所受到的整体压力。其中静态压力传感器为压阻式传感器，包括但不限于MEMS传感器、压阻膜传感器、应变计式传感器。柔性压电传感器为压电式压力传感器，压电材料包括但不限于PVDF、PZT、BaTiO3等材料。触点的材质包括但不限于硅胶、泡棉和海绵等材质。
在一些具体实施例中，本公开的脉搏波传感器阵列，包括一个多孔弹性缓冲材料和五个脉搏波传感器，多孔弹性缓冲材料与五个传感器连接，多孔弹性缓冲材料与静态压力传感器结构一侧相连，用于吸收缓冲，减少传感器间震动干扰和外界冲击干扰。另外，多孔弹性缓冲材料可以使传感器阵列贴合不同人群手臂。多孔弹性缓冲材料不局限于聚氨酯海绵、慢回弹记忆海绵等。
每个传感器沿腕部等间距依次排开。第一传感器贴近腕横纹手掌一侧，第二至五传感器从腕横纹手臂一侧依次排开。该分布可以适用于不 同人群手臂长度，增大桡动脉波动探测长度。
下面结合附图对本公开的几个具体实施方式进行进一步阐述说明。
如图1-5所示，本公开的脉搏波传感器包括传感器骨架1、柔性压电传感器2、柔性压电传感器的触点3、静态压力传感器4及静态压力传感器的触点5。柔性压电传感器的触点3与皮肤12接触，柔性压电传感器的触点3的材料特性使其能够贴合皮肤，柔性压电传感器的触点3拥有一定弹性形变可使手臂桡动脉10的脉搏波传递给柔性压电传感器2。柔性压电传感器以弯曲状态贴合在传感器骨架1上，它将柔性压电传感器的触点3传导的脉搏波波动转化为电信号，通过柔性压电传感器2的两极将转化的电信号输出。当桡动脉10跳动给皮肤12一个力，这个力被柔性压电传感器的触点3接收并传递给柔性压电传感器2，柔性压电传感器2即可输出电信号。
如图4、5所示，传感器骨架1为长条状的曲面形状，其一侧为柔性压电传感器2提供支撑，如图3A所示，传感器骨架1连接柔性压电传感器2的一侧包含一个向下凹的空间8，柔性压电传感器2平铺在向下凹的空间8上方，边缘固定在向下凹的空间8周边，如图3A所示为四周均固定，此时向下凹的空间8上方的柔性薄膜悬空。此悬空结构使得柔性压电传感器2的柔性薄膜所受到的正向压力转换为向四周的拉扯力，从而极大提高了柔性薄膜所承受的压强，因此使其产生更大的压电信号，从而提高了传感器灵敏度。传感器骨架1另一侧固定静态压力传感器4，静态压力传感器4另一侧与加压装置9相连，用于检测此传感器结构所受到的整体压力。
传感器阵列包括多孔的弹性缓冲材料7和五个上述的脉搏波传感器6-1、6-2、6-3、6-4、6-5。该传感器阵列平铺在被测手腕上，由于弹性缓冲材料7的特性，五个传感器6-1、6-2、6-3、6-4、6-5可以根据被测人手型贴附在手臂的手腕表面。当脉搏跳动时弹性缓冲材料7还可以吸收多余的冲击，减少某一传感器下的脉搏跳动点对临近传感器的影响，减少传感器间相互干扰。
如图4所示，该传感器阵列用于探测桡骨11附近桡动脉10在不同压力下的脉搏跳动。每个传感器沿腕部等间距依次排开。第一传感器6-1贴近腕横纹手掌一侧，第二至五传感器6-2、6-3、6-4、6-5从腕横纹手臂一侧依次排开。该分布可以适用于不同人群手臂长度，增大桡动脉10波动探测长度。当外界有加压装置9对传感器阵列施加压力时，静态压力传感器4感受来自传感器上方弹性缓冲材料1传递的静态压力，柔性压电传感器2用于测量桡动脉脉博，最终实现在不同压力下传感器阵列探测桡动脉脉搏信号。
作为上述实施方式的变种，如图3B、3C所示，柔性压电传感器2的柔性薄膜可以只有两面固定(图3B)；或者三面固定(图3C)，其中斜线部分表示向下凹的空间8与柔性薄膜的重叠部位；或者通过伸出的夹具完全悬置于该向下凹的空间8上方；这些均不影响本公开的技术效果的实现。此外，为了防止柔性压电传感器2的柔性薄膜的折叠和变形，可以在该柔性薄膜上设置加强筋或导向条使其尽量向固定的某些方向弯曲，从而避免其误动作。
以上所述的具体实施例，对本公开的目的、技术方案和有益效果进行了进一步详细说明，应理解的是，以上所述仅为本公开的具体实施例而已，并不用于限制本公开，凡在本公开的精神和原则之内，所做的任何修改、等同替换、改进等，均应包含在本公开的保护范围之内。

Claims (13)

  1. 一种脉搏波传感器，包括传感器骨架和柔性压电传感器，其特征在于：
    所述柔性压电传感器包括柔性压电薄膜，用于感测脉搏波并将其转化成电信号；
    所述传感器骨架用于固定所述柔性压电传感器；以及
    所述传感器骨架连接所述柔性压电传感器的一侧包含一向下凹的空间，所述柔性压电传感器全部或部分固定在该向下凹的空间的四周，从而所述柔性压电传感器的柔性压电薄膜是全部或部分悬空的。
  2. 如权利要求1所述的脉搏波传感器，其特征在于，所述柔性压电传感器为压电式压力传感器，其压电材料选自聚偏氟乙烯、锆钛酸铅压电陶瓷或BaTiO3。
  3. 如权利要求1所述的脉搏波传感器，其特征在于，所述柔性压电传感器上还设置有触点，触点一侧与待测的皮肤相连，用于贴合手臂表面和传导待测的脉搏波，触点另一侧与所述柔性压电传感器的柔性压电薄膜相连或相接触，将待测的脉搏波传导到所述柔性压电传感器的柔性压电薄膜上。
  4. 如权利要求1所述的脉搏波传感器，其特征在于，所述脉搏波传感器还包括静态压力传感器，其中所述静态压力传感器用于测量施加在所述脉搏波传感器上的静态压力。
  5. 如权利要求4所述的脉搏波传感器，其特征在于，所述静态压力传感器为MEMS传感器、压阻膜传感器或应变计式传感器。
  6. 如权利要求4所述的脉搏波传感器，其特征在于，所述柔性压电传感器和/或静态压力传感器上设置有触点。
  7. 如权利要求6所述的脉搏波传感器，其特征在于，所述触点的材质为硅胶、泡棉或海绵。
  8. 如权利要求1所述的脉搏波传感器，其特征在于，所述传感器骨架为球缺、圆柱体或弯曲成曲面的长条形体。
  9. 一种脉搏波传感器阵列，包括弹性缓冲材料和若干如权利要求1至8任意一项所述的脉搏波传感器，其中若干所述脉搏波传感器以一定间隔分布在所述弹性缓冲材料上。
  10. 如权利要求9所述的脉搏波传感器阵列，其特征在于，所述弹性缓冲材料为聚氨酯海绵或慢回弹记忆海绵。
  11. 如权利要求9所述的脉搏波传感器阵列，其特征在于，所述脉搏波传感器的个数为3、4、5、6、7、8、9或10个。
  12. 如权利要求9所述的脉搏波传感器阵列，其特征在于，所述若干脉搏波传感器中的第一传感器设置于被测手腕的手掌根部横纹处，其余的传感器向被测手腕的肘部方向依次排列。
  13. 一种脉搏波测量装置，其特征在于，其中采用如权利要求9至12任意一项所述的脉搏波传感器阵列。
PCT/CN2017/092400 2017-07-10 2017-07-10 脉搏波传感器、传感器阵列及采用其的脉搏波测量装置 WO2019010616A1 (zh)

Priority Applications (1)

Application Number Priority Date Filing Date Title
PCT/CN2017/092400 WO2019010616A1 (zh) 2017-07-10 2017-07-10 脉搏波传感器、传感器阵列及采用其的脉搏波测量装置

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CN2017/092400 WO2019010616A1 (zh) 2017-07-10 2017-07-10 脉搏波传感器、传感器阵列及采用其的脉搏波测量装置

Publications (1)

Publication Number Publication Date
WO2019010616A1 true WO2019010616A1 (zh) 2019-01-17

Family

ID=65000954

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2017/092400 WO2019010616A1 (zh) 2017-07-10 2017-07-10 脉搏波传感器、传感器阵列及采用其的脉搏波测量装置

Country Status (1)

Country Link
WO (1) WO2019010616A1 (zh)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN114199423A (zh) * 2021-11-09 2022-03-18 大连理工大学 一种双激发压力记忆装置
US11712206B2 (en) 2020-05-11 2023-08-01 Samsung Electronics Co., Ltd. Apparatus and method for estimating bio-information, and bio-signal measuring sensor

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP3547381B2 (ja) * 2000-09-05 2004-07-28 岸野 雅方 圧脈波検出具
CN103519793A (zh) * 2013-10-22 2014-01-22 詹北斗 多段复合式中医脉象采集装置
CN105640513A (zh) * 2015-12-31 2016-06-08 中国科学院微电子研究所 脉搏波阵列式传感器采集系统及方法
CN105813550A (zh) * 2013-12-11 2016-07-27 皇家飞利浦有限公司 用于测量对象的脉搏波的系统和方法
CN106108865A (zh) * 2016-04-18 2016-11-16 北京百脉智连科技有限公司 一种可标定静态力的脉象传感器及脉象采集装置

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP3547381B2 (ja) * 2000-09-05 2004-07-28 岸野 雅方 圧脈波検出具
CN103519793A (zh) * 2013-10-22 2014-01-22 詹北斗 多段复合式中医脉象采集装置
CN105813550A (zh) * 2013-12-11 2016-07-27 皇家飞利浦有限公司 用于测量对象的脉搏波的系统和方法
CN105640513A (zh) * 2015-12-31 2016-06-08 中国科学院微电子研究所 脉搏波阵列式传感器采集系统及方法
CN106108865A (zh) * 2016-04-18 2016-11-16 北京百脉智连科技有限公司 一种可标定静态力的脉象传感器及脉象采集装置

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11712206B2 (en) 2020-05-11 2023-08-01 Samsung Electronics Co., Ltd. Apparatus and method for estimating bio-information, and bio-signal measuring sensor
CN114199423A (zh) * 2021-11-09 2022-03-18 大连理工大学 一种双激发压力记忆装置

Similar Documents

Publication Publication Date Title
CN109222918B (zh) 脉搏波传感器、传感器阵列及采用其的脉搏波测量装置
Meng et al. Kirigami‐inspired pressure sensors for wearable dynamic cardiovascular monitoring
CN106725363B (zh) 脉搏波采集装置和脉搏波采集标定方法
CN109222917B (zh) 脉搏波传感器、传感器阵列及脉搏波测量方法
EP3281606B1 (en) Ferroelectric composite material-based artificial electronic skin
WO2020024428A1 (zh) 脉搏检测装置及其制作方法
CN103300835B (zh) 一种高精度人体脉动测量系统
Khan et al. Design analysis and human tests of foil-based wheezing monitoring system for asthma detection
US20190209031A1 (en) Blood pressure measuring device, blood pressure measuring method and recording medium having blood pressure measuring program recorded therein
WO2011147221A1 (zh) 双感测脉诊仪
US9320489B1 (en) Apparatus for detection of cardiac acoustic signals
CN107041751A (zh) 一种呼吸状态检测系统及无线无源的声表面波传感器
US20240090775A1 (en) Physiological parameter sensing systems and methods
WO2019010616A1 (zh) 脉搏波传感器、传感器阵列及采用其的脉搏波测量装置
TW201740876A (zh) 可捲曲生物統計量測設備
CN206593752U (zh) 接触式声音探测传感器以及接触式声音传感装置
CN109222919A (zh) 脉搏波传感器、传感器阵列及采用其的脉搏波测量装置
CN105167764A (zh) 血压测量设备及方法
Chang et al. Heartbeat monitoring technique based on corona-poled PVDF film sensor for smart apparel application
WO2019010610A1 (zh) 脉搏波传感器、传感器阵列及采用其的脉搏波测量装置
WO2019010615A1 (zh) 脉搏波传感器、传感器阵列及脉搏波测量方法
CN112120679A (zh) 一种脉搏检测设备及其制作方法
CN216978189U (zh) 压力传感器及检测装置
WO2018094737A1 (zh) 脉搏波采集装置和脉搏波采集标定方法
CN205054204U (zh) 血压测量设备

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 17917807

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 17917807

Country of ref document: EP

Kind code of ref document: A1