WO2022247018A1 - 微裂纹应变传感元件及其制备方法和应用 - Google Patents

微裂纹应变传感元件及其制备方法和应用 Download PDF

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Publication number
WO2022247018A1
WO2022247018A1 PCT/CN2021/111707 CN2021111707W WO2022247018A1 WO 2022247018 A1 WO2022247018 A1 WO 2022247018A1 CN 2021111707 W CN2021111707 W CN 2021111707W WO 2022247018 A1 WO2022247018 A1 WO 2022247018A1
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layer
sensing element
microcrack
thin film
strain sensing
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English (en)
French (fr)
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王倩
芦泽仲
王可军
高雷
樊成
张雷
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Suzhou University
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Suzhou University
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B7/00—Measuring arrangements characterised by the use of electric or magnetic techniques
    • G01B7/16—Measuring arrangements characterised by the use of electric or magnetic techniques for measuring the deformation in a solid, e.g. by resistance strain gauge
    • G01B7/18—Measuring arrangements characterised by the use of electric or magnetic techniques for measuring the deformation in a solid, e.g. by resistance strain gauge using change in resistance
    • 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 for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/0205—Simultaneously evaluating both cardiovascular conditions and different types of body conditions, e.g. heart and respiratory condition
    • 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 for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/024—Measuring pulse rate or heart rate
    • A61B5/02438—Measuring pulse rate or heart rate with portable devices, e.g. worn by the patient
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs
    • A61B5/085—Measuring impedance of respiratory organs or lung elasticity
    • A61B5/086—Measuring impedance of respiratory organs or lung elasticity by impedance pneumography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/48—Other medical applications
    • A61B5/4806—Sleep evaluation
    • A61B5/4815—Sleep quality
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6802—Sensor mounted on worn items
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6802—Sensor mounted on worn items
    • A61B5/681—Wristwatch-type devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6824—Arm or wrist
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01L—MEASURING FORCE, STRESS, TORQUE, WORK, MECHANICAL POWER, MECHANICAL EFFICIENCY, OR FLUID PRESSURE
    • G01L1/00—Measuring force or stress, in general
    • G01L1/20—Measuring force or stress, in general by measuring variations in ohmic resistance of solid materials or of electrically-conductive fluids; by making use of electrokinetic cells, i.e. liquid-containing cells wherein an electrical potential is produced or varied upon the application of stress
    • G01L1/22—Measuring force or stress, in general by measuring variations in ohmic resistance of solid materials or of electrically-conductive fluids; by making use of electrokinetic cells, i.e. liquid-containing cells wherein an electrical potential is produced or varied upon the application of stress using resistance strain gauges
    • G01L1/2287—Measuring force or stress, in general by measuring variations in ohmic resistance of solid materials or of electrically-conductive fluids; by making use of electrokinetic cells, i.e. liquid-containing cells wherein an electrical potential is produced or varied upon the application of stress using resistance strain gauges constructional details of the strain gauges
    • G01L1/2293—Measuring force or stress, in general by measuring variations in ohmic resistance of solid materials or of electrically-conductive fluids; by making use of electrokinetic cells, i.e. liquid-containing cells wherein an electrical potential is produced or varied upon the application of stress using resistance strain gauges constructional details of the strain gauges of the semi-conductor type
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0261—Strain gauges
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Measuring devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor or mobility of a limb
    • A61B5/1102—Ballistocardiography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Measuring devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor or mobility of a limb
    • A61B5/113—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor or mobility of a limb occurring during breathing
    • A61B5/1135—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor or mobility of a limb occurring during breathing by monitoring thoracic expansion
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6823—Trunk, e.g., chest, back, abdomen, hip

Definitions

  • the invention belongs to the technical field of micro-intelligent electronics, and in particular relates to a micro-crack strain sensing element and a preparation method and application thereof.
  • the technical problem to be solved by the present invention is to overcome the shortcomings of traditional mechanical quantity sensors such as insufficient sensitivity, excessive size, and insufficient mobility in the prior art; and to solve the insufficient precision of the traditional crack strain sensor preparation method, which affects the service life of the sensor And other issues.
  • the present invention provides a microcrack strain sensing element, comprising: a base layer, a metal film, a protective layer, an output electrode, and a packaging layer; the metal film is arranged on the base layer, and the metal film is composed of two The metal film is deposited with a patterned crack structure; the protective layer is set on the metal film; the output electrode is connected to the metal film for outputting electrical signals; the encapsulation layer is set on the protective layer.
  • the material of the base layer includes: polyimide (PI), polyethylene terephthalate (PET), polyvinyl chloride (PVC), nylon (PA), casting Film of polypropylene film (CPP) material.
  • PI polyimide
  • PET polyethylene terephthalate
  • PVC polyvinyl chloride
  • PA nylon
  • CPP casting Film of polypropylene film
  • the metal thin film layer is a thin film formed by depositing gold (Au) thin film and chromium (Cr) phase, wherein the metal materials replaced by gold (Au) include: platinum (Pt), silver (Ag), copper (Cu).
  • the raw material of the protective layer is formed by mixing and stirring epoxy resin A liquid and B liquid in a weight ratio of 3:1.
  • the raw material of the encapsulation layer is formed by mixing and stirring polydimethylsiloxane (PDMS) sample solution at a weight ratio of 10:1.
  • PDMS polydimethylsiloxane
  • the present invention also provides a method for preparing the microcrack strain sensing element, comprising the steps of:
  • the protective layer template is fixed on the surface of the metal film layer, and the raw material of the protective layer is brushed on the protective layer template;
  • the structure of the coating template includes a hollow part, and protruding parts are provided at both ends of the hollow part.
  • the structure of the protective layer template includes spaced rectangular hollow grooves.
  • the patterned crack structure is an array of cracks on the surface of the metal thin film layer, and the cracks are located between protective layers arranged at intervals on the surface of the metal thin film layer.
  • the invention provides the application of the microcrack strain sensing element or the method in the medical field.
  • microcrack strain sensing element and its preparation method and application according to the present invention compared with the existing mechanical quantity sensor technology, the microcrack strain sensing element has higher mechanical quantity sensing sensitivity, mobility, and Wearability and miniaturization; the controllable patterning preparation method of microcracks based on the template method has higher precision crack control than the existing crack preparation technology and will not affect the service life of the crack, and more optimized actual operation Difficulty; Microcrack strain sensing elements have been widely used in the medical field due to their high sensitivity, wearability, and miniaturization.
  • FIG. 1 is a schematic diagram of a coating template in an embodiment of the present application.
  • Fig. 2 is a schematic diagram of laser cutting of a protective layer template in an embodiment of the present application.
  • Fig. 3 is a schematic diagram of a microcrack array in an embodiment of the present application.
  • Fig. 4 is a schematic diagram of a microcrack strain sensing element in an embodiment of the present application.
  • Fig. 5 is a schematic diagram of detection of a human breathing signal in an embodiment of the present application.
  • Fig. 6 is a schematic diagram of a human pulse signal experiment in an embodiment of the present application.
  • FIG. 7 is a schematic diagram of a detection waveform of a human pulse signal in an embodiment of the present application.
  • This embodiment provides a microcrack strain sensing element, comprising: a base layer, a metal film, a protective layer, an output electrode, and a packaging layer; the metal film is arranged on the base layer, and the metal film is made of two metal materials Deposited, the metal film is provided with a patterned crack structure; the protection layer is provided on the metal film; the output electrode is connected to the metal film for outputting electrical signals; the encapsulation layer is provided on the protection layer.
  • the base layer carries the bottom of the sensor element, and needs to have mechanical properties such as flexibility, toughness, and wear resistance;
  • the material of the base layer includes: polyimide (PI), polyethylene terephthalate (PET), polyvinyl chloride (PVC), nylon (PA), cast polypropylene film (CPP) material film.
  • the metal thin film layer is sprayed on the base layer, generally two metal materials need to be deposited to ensure a good adhesion effect with the base layer, and patterned cracks will be generated on it as the core element of the sensor;
  • the metal thin film layer It is a thin film formed by depositing gold (Au) thin film and chromium (Cr) phase, wherein the metal materials replaced by gold (Au) include: platinum (Pt), silver (Ag), copper (Cu).
  • the protective layer is brushed on the metal film using a laser-cut template, and the patterning effect of cracks is controlled according to the neutral layer of the material;
  • the raw material of the protective layer is epoxy resin A liquid and B liquid according to weight It is made by mixing and stirring in a ratio of 3:1.
  • the encapsulation layer is spin-coated on the metal thin film and the protective layer to protect cracks in the cracked metal layer from being damaged by external environmental pollution;
  • the raw material of the encapsulation layer is polydimethylsiloxane (PDMS) sample liquid according to It is made by mixing and stirring at a weight ratio of 10:1.
  • PDMS polydimethylsiloxane
  • This embodiment provides a method for preparing the microcrack strain sensing element, comprising the following steps:
  • Step 1 Select a stainless steel sheet with a thickness of 3.5cm x 5.3cm x 0.01cm, and use laser cutting to cut out the shape to make a coating template. As shown in Figure 1, use the hollow part in the middle to form the expected shape during coating. The protruding part is to facilitate the formation of output electrode lines;
  • Step 2 Cut a piece of 3.5cm x 5.3cm PET film with a thickness of 0.025mm, use the KH-100E ultrasonic cleaner to clean the sample, and dry it;
  • Step 3 Take a 3.5cm x 5.3cmx 1cm glass slide, first spray a layer of alcohol on the surface of the slide, and then spread the treated PET film evenly on the surface of the slide. Note that one end of the PET film should touch the glass slide first, and then put it down slowly to prevent air bubbles. Then place the coating template made in step 1 on the PET film and fix it with transparent glue to prevent splashing during metal spraying;
  • Step 4 use the SN201102003 high-vacuum magnetron coating equipment of the Suzhou Institute of Nanotechnology, Chinese Academy of Sciences to coat a metal layer on the PET film, and the targets used are Cr and Au. Specifically, a 5nm bonding layer is first deposited with a Cr target, and then a 50nm Au layer is deposited.
  • the deposition parameters are: vacuum degree 5x10-4Pa, power 200w, sputtering rate 1A/s;
  • Step 5 Take a piece of stainless steel sheet with a thickness of 3.5cm x 5.3cm x 0.01cm, and design a hollowed-out shape with a rectangular interval according to the crack position and density requirements. As shown in Figure 2, the hollowed-out position is the position where the crack occurs. According to the designed shape Use laser cutting method to cut on stainless steel sheet, and spray release agent to prepare protective layer template;
  • Step 6 Mix epoxy resin liquid A and liquid B according to the weight ratio of the two liquids at a ratio of 3:1, put them on a DF-101S magnetic stirrer and stir for 10 minutes, then pour the sample liquid into an 80mmx80mm petri dish, and put them together Vacuumize in a vacuum drying oven for 2 hours to remove air bubbles;
  • Step 7 Put the vacuumed epoxy resin sample solution on the V-1515 heating platform, and heat it at 60°C until the sample solution is semi-cured;
  • Step 8 When the epoxy resin sample solution reaches a certain viscosity, put the protective layer template on the PET-Au layer prepared in step 4, fix it with an electromagnet, and brush the epoxy resin sample solution on the protective layer template , to be cured;
  • Step 9 After the epoxy resin is cured, remove the mold, place electrode wires on the protrusions at both ends of the PET-Au layer, and use conductive silver paste as an adhesive;
  • Step 10 Mix PDMS (Dow Corning Company) sample solution according to the ratio of sample solution to water weight ratio of 10:1, put it on a DF-101S magnetic stirrer and stir for 10 minutes, then put it into a vacuum drying oven for 2 hours;
  • PDMS Low Corning Company
  • ⁇ curvature
  • the stretching equipment is completed, or it is done manually, and other stretching equipment can also be used to perform periodic and repetitive operations, so that the microcracks shown in Figure 3 can be obtained between the two epoxy resin layers spaced apart on the surface of the metal film Array, the prepared micro-crack sensor is shown in Figure 4.
  • This embodiment provides an application of microcrack sensing elements in the field of human physiological signal detection, including:
  • micro-crack strain sensing element is closely attached to the chest cavity of the human body, the electrode wires at both ends of the sensor are connected to the multimeter, and the resistance value of the sensing element during the breathing process of the human body is recorded at a fixed frequency;
  • the recorded resistance data is processed by calculating the relative resistance value ( ⁇ R/R0), and then the respiratory waveform diagram with time as the abscissa can be obtained. According to the waveform diagram, the physiological condition or sleep quality of the human body during the recording period can be analyzed;
  • the main wave, tidal wave and resurgence wave in the pulse waveform cycle can reflect the heart rate of the patient during clinical operation in real time, so as to judge the physiological condition of the patient.
  • the method of outputting the pulse detection curve in real time in the actual usage of the flexible and controllable micro-crack sensing element in the field of human physiological signal detection can also be used to detect human breathing in real time.
  • This embodiment provides an example of applying the microcrack sensing element to medical detection.
  • micro-crack sensor sample was placed close to the subject's chest, and the two ends of the sample were connected to the Keysight 34465A multimeter to detect the real-time change of resistance with the subject's breathing, as shown in Figure 5.
  • Breathing is one of the most important physiological signals of the human body, and the information that breathing can convey can largely reflect a person's physiological health status.
  • the breathing situation of a person during an operation can reflect the physiological state of the human body in real time; the detection of the breathing data of a person during sleep can be used as an important basis for measuring the quality of human sleep.
  • the principle that the microcrack sensing element can sensitively detect the breathing signal of the human body is similar to the stretching experiment. When the human body breathes, the chest cavity will expand with the inhalation; The sensing element is subjected to tensile strain, which leads to a drastic change in resistance.
  • the flexible micro-crack strain sensing element Based on the excellent performance of the flexible micro-crack strain sensing element, it can cause obvious changes in the resistance of the sensor during the breathing process of the human body, and the micro-cracks in the breathing process of the human body can be recorded at a certain frequency.
  • the resistance value of the strain sensing element, and the recorded resistance value data is processed through the calculation of the relative resistance value ( ⁇ R/R0), and the respiratory waveform diagram with time as the abscissa can be obtained, and the record can be analyzed according to the waveform diagram The physiological condition of the human body or the quality of sleep during the time period;
  • the relative resistance data can be obtained by real-time processing and calculation, and the pulse detection curve can be output in real time as the abscissa, so that the flexible micro-crack sensor has excellent performance.
  • the real-time pulse detection ability can reflect the patient's heart rate in real time during clinical operation, so as to judge the patient's physiological condition. It has laid a solid foundation for the application of microcrack strain sensors in future intelligent medical devices.

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Abstract

本发明公开了微裂纹应变传感元件及其制备方法和应用。所述微裂纹应变传感元件包括：基底层、金属薄膜、保护层、输出电极、封装层；所述金属薄膜设于基底层上，所述金属薄膜由两种金属材料沉积而成，所述金属薄膜设有图案化裂纹结构；所述保护层设于金属薄膜上；所述输出电极连接于金属薄膜，用于输出电信号；所述封装层设于保护层上。本发明的微裂纹应变传感元件制备方法相较现有裂纹制备技术具有更高精度的裂纹可控性且不会影响裂纹的使用寿命，以及更优化的实际操作难度；微裂纹的应变传感元件的高灵敏度、可穿戴性、小型化等特点可在医学领域中得到广泛的应用。

Description

微裂纹应变传感元件及其制备方法和应用 技术领域
本发明属于微型智能电子技术领域，具体涉及微裂纹应变传感元件及其制备方法和应用。
背景技术
传统的机械量传感器很难满足低功耗，高稳定性，小型化，高精度，高移动性和其他优异性能，而这往往也是一些对传感器性能要求高的领域所需传感器的关键要素，如可穿戴电子产品领域、医学领域等，传统的可穿戴智能设备一般都是非柔性，应用仅局限于某些部位。随着柔性导电技术的发展，柔性可穿戴智能设备的出现成为了可能，柔性传感器是可穿戴智能设备的核心器件。现有的柔性微裂纹传感器的制备方法有着精度不足、影响传感器寿命等问题。
发明内容
为此，本发明所要解决的技术问题在于克服现有技术中传统机械量传感器灵敏度不足、尺寸过大、移动性不足等缺点；以及解决传统裂纹应变传感器制备方法精度不足，影响传感元件使用寿命等问题。
为解决上述技术问题，本发明提供了微裂纹应变传感元件，包括：基底层、金属薄膜、保护层、输出电极、封装层；所述金属薄膜设于基底层上，所述金属薄膜由两种金属材料沉积而成，所述金属薄膜设有图案化裂纹结构；所述保护层设于金属薄膜上；所述输出电极连接于金属薄膜，用于输出电信号；所述封装层设于保护层上。
在本发明的一个实施例中，所述基底层的材料包括：聚酰亚胺(PI)、聚乙烯对苯二甲酸脂(PET)、聚氯乙烯(PVC)、尼龙(PA)、流延聚丙烯薄膜(CPP)材料的薄膜。
在本发明的一个实施例中，所述金属薄膜层为采用金(Au)薄膜和铬(Cr)相沉积而成的薄膜，其中金(Au)替换的金属材料包括：铂(Pt)、银(Ag)、铜(Cu)。
在本发明的一个实施例中，所述保护层的原料采用环氧树脂A液与B液按照重量比3:1的比例混合搅拌而成。
在本发明的一个实施例中，所述封装层的原料采用聚二甲基硅氧烷(PDMS)样液按重量比10：1的比例混合搅拌而成。
本发明还提供了一种制备所述微裂纹应变传感元件的方法，包括如下步骤：
(1)根据所需传感元件形状制作带有相应镂空形状的镀膜模板，将镀膜模板放置于基底层上，在基底层上镀上由两种金属材料沉积而成的金属薄膜层；
(2)根据所需裂纹的密度与位置制作带有相应镂空形状的图案的保护层模板上设计，并喷涂上脱模剂；
(3)将保护层模板固定于金属薄膜层表面，并将保护层的原料刷涂在保护层模板上；
(4)待保护层固化后进行脱模，并布置输出电极，得到样片；
(5)将封装层的原料旋涂于样片表面；
(6)对金属薄膜层进行弯曲和拉伸操作以在金属薄膜层表面得到图案化裂纹结构。
在本发明的一个实施例中，所述镀膜模板的结构包括镂空部分，所述镂空部分两端设有凸出部分。
在本发明的一个实施例中，所述保护层模板的结构包括间隔的长方形状的镂空槽。
在本发明的一个实施例中，所述图案化裂纹结构为在金属薄膜层表面的裂纹阵列，所述裂纹位于在金属薄膜层表面间隔排列的保护层之间。
本发明提供所述的微裂纹应变传感元件或所述方法在医学领域的应用。
本发明的上述技术方案相比现有技术具有以下优点：
本发明所述的微裂纹应变传感元件及其制备方法和应用，所述微裂纹的应 变传感元件相较现有的机械量传感器技术具有更高的机械量感应灵敏度、可移动性、可穿戴性以及小型化；基于模板法的微裂纹的可控图案化制备方法相较现有裂纹制备技术具有更高精度的裂纹可控性且不会影响裂纹的使用寿命，以及更优化的实际操作难度；微裂纹的应变传感元件的高灵敏度、可穿戴性、小型化等特点在医学领域中得到了广泛的应用。
附图说明
为了使本发明的内容更容易被清楚的理解，下面根据本发明的具体实施例并结合附图，对本发明作进一步详细的说明，其中
图1是本申请一实施方式中一种镀膜模板示意图。
图2是本申请一实施方式中一种保护层模板激光切割示意图。
图3是本申请一实施方式中一种微裂纹阵列示意图。
图4是本申请一实施方式中一种微裂纹应变传感元件示意图。
图5是本申请一实施方式中一种人体呼吸信号检测示意图。
图6是本申请一实施方式中一种人体脉搏信号实验示意图。
图7是本申请一实施方式中一种人体脉搏信号检测波形示意图。
具体实施方式
下面结合附图和具体实施例对本发明作进一步说明，以使本领域的技术人员可以更好地理解本发明并能予以实施，但所举实施例不作为对本发明的限定。
实施例1
本实施例提供了一种微裂纹应变传感元件，包括：基底层、金属薄膜、保护层、输出电极、封装层；所述金属薄膜设于基底层上，所述金属薄膜由两种金属材料沉积而成，所述金属薄膜设有图案化裂纹结构；所述保护层设于金属薄膜上；所述输出电极连接于金属薄膜，用于输出电信号；所述封装层设于保护层上。
具体地，所述基底层承载传感元件的底部，需要具有柔性、韧性、耐磨性 等机械性能；所述基底层的材料包括：聚酰亚胺(PI)、聚乙烯对苯二甲酸脂(PET)、聚氯乙烯(PVC)、尼龙(PA)、流延聚丙烯薄膜(CPP)材料的薄膜。
具体地，所述金属薄膜层喷涂于基底层上，一般需要沉积两种金属材料以保证与基底层的良好粘合效果，其上会产生图案化裂纹作为传感器的核心要素；所述金属薄膜层为采用金(Au)薄膜和铬(Cr)相沉积而成的薄膜，其中金(Au)替换的金属材料包括：铂(Pt)、银(Ag)、铜(Cu)。
具体地，所述保护层利用激光切割的模板刷涂于金属薄膜上，根据材料中性层控制来达到控制裂纹图案化效果；所述保护层的原料采用环氧树脂A液与B液按照重量比3:1的比例混合搅拌而成。
具体地，所述封装层旋涂于金属薄膜及保护层上，保护裂纹金属层裂纹不受外界环境污染破环；所述封装层的原料采用聚二甲基硅氧烷(PDMS)样液按重量比10：1的比例混合搅拌而成。
实施例2
本实施例提供了一种制备所述微裂纹应变传感元件的方法，包括如下步骤：
步骤1：选取一块3.5cm x 5.3cm x 0.01cm厚度的不锈钢片，利用激光切割的方法切割出形状以制作镀膜模板，如图1所示，利用中间镂空部分在镀膜时形成预想的形状，两边凸出的部分是为了方便形成输出电极线；
步骤2：剪裁一片3.5cm x 5.3cm的PET薄膜，厚度为0.025mm，使用KH-100E型超声波清洗器将试样清洗干净，吹干；
步骤3：取一块3.5cm x 5.3cmx 1cm的载玻片，先在载玻片表面喷涂一层酒精，再将处理好的PET薄膜平整地铺在载玻片表面上。注意要将PET薄膜一端先接触载玻片，再缓慢放下，以防出现气泡，然后将步骤1中制作的镀膜模板放置在PET薄膜上，并用透明胶固定住，防止金属喷涂时飞溅；
步骤4：利用中科院苏州纳米所的SN201102003高真空磁控镀膜设备在PET薄膜上镀金属层，所用的靶材为Cr和Au。具体是先用Cr靶材沉积5nm的粘合层，再沉积50nm的Au层，沉积参数为：真空度5x10-4Pa，功率为200w， 溅射速率为1A/s；
步骤5：取一块3.5cm x 5.3cm x 0.01cm厚度的不锈钢片，根据裂纹位置和密度要求设计间隔长方形的镂空形状，如图2所示，镂空的位置即为裂纹产生位置，根据设计的形状利用激光切割的方法在不锈钢片上切割，并喷涂上脱模剂以制备保护层模板；
步骤6：将环氧树脂A液与B液按照两液重量比3:1的比例混合，放到DF-101S型磁力搅拌机上搅拌10min，再将样液倒入80mmx80mm的培养皿中，一起放到真空干燥箱中抽真空2h，以去除气泡；
步骤7：将抽完真空环氧树脂样液放到V-1515型加热台上，60℃加热至样液半固化状态；
步骤8：待环氧树脂样液到达一定粘度时，将保护层模板放到步骤4制备出的PET-Au层上，并利用电磁铁固定，将环氧树脂样液刷涂在保护层模板上，待固化；
步骤9：环氧树脂固化后进行脱模，在PET-Au层两端凸起处布上电极线，用导电银浆作为粘合剂；
步骤10：按照样液与水重量比10:1的比例混合PDMS(道康宁公司)样液，放到DF-101S型磁力搅拌机上搅拌10min后再放入真空干燥箱2h；
将PDMS样液加入KW-4B型旋涂仪中，旋涂到步骤9制备出的样片表面，以作封装层，保护样片不被外部环境污染；
步骤11：将步骤10制备出的样片的金属薄膜层部分在所选取固定曲率(ρ)半径的圆棒上进行反复弯曲拉伸的操作，如ρ＝2mm，此操作可以利用现有的圆棒拉伸设备完成，或手动完成，也可借助其他拉伸设备进行周期性与重复性的操作，以便能够在金属薄膜表面间隔的两块环氧树脂层之间获得如图3所示的微裂纹阵列，制备好的微裂纹传感器如图4所示。
实施例3
本实施例提供了一种将微裂纹传感元件在人体生理信号检测领域的应用， 包括：
将微裂纹应变传感元件紧贴于人体胸腔处，传感器两端电极线连接万用表，并以固定频率记录人体呼吸过程的传感元件电阻阻值；
将所记录的阻值数据通过相对阻值(ΔR/R0)的计算进行处理，便可得到以时间为横坐标的呼吸波形图，根据波形图可以分析记录时间段人体生理状况或睡眠质量；
将微裂纹传感元件贴在人体手腕处，传感器两端电极线连接万用表，并通过软件实时处理相对阻值数据，便可以时间为横坐标实时输出脉搏检测曲线图，从曲线图中可分辨出脉搏波形周期中的主波、潮波和重振波，可以实时反映临床手术时患者的心率，从而判断患者生理状况。
进一步地，所述将柔性可控微裂纹传感元件在人体生理信号检测领域的实际用法中实时输出脉搏检测曲线的方法同样可用于实时检测人体呼吸情况。
实施例4
本实施例提供了一种将微裂纹传感元件应用于医学检测的实例。
如图5所示，将微裂纹传感器样片紧贴于实验对象的胸前，并将样片两端连接Keysight 34465A型万用表以检测电阻随着实验对象呼吸产生的实时变化，如图5所示。
呼吸是人体最重要的生理信号之一，呼吸所能传递的信息很大程度上可以反映一个人的生理健康状态。例如手术过程中人的呼吸情况可以实时反映人体生理状态；检测睡眠时人的呼吸数据可以作为衡量人体睡眠质量的重要依据等。微裂纹传感元件能够灵敏检测人体呼吸信号的原理和拉伸实验类似，当人体进行呼吸时，胸腔会随着吸气膨胀；随着呼气收缩，从而导致紧贴于胸腔处的微裂纹传感元件受到拉伸应变，从而导致电阻发生剧烈变化，基于柔性微裂纹应变传感元件的优秀性能，人体呼吸过程中可以导致很明显的传感器阻值变化，按一定频率记录人体呼吸过程中微裂纹应变传感元件的电阻阻值，并将所记录的阻值数据通过相对阻值(ΔR/R0)的计算进行处理，便可得到以时间为横坐标的呼吸波形图，根据波形图可以分析记录时间段人体生理状况或睡眠质量；
将微裂纹应变传感元件贴在实验对象手腕处，如图6所示；两端连接Keysight 34465A型万用表，以检测传感器相对电阻随人体脉搏信号变化产生的波形，如图7所示；从中截取一段完整的脉搏周期，基于柔性微裂纹应变传感元件的优秀的灵敏度，可以从曲线图中很明显的分辨出一个周期脉搏波形的三个阶段：主波、潮波和重振波，如图7所示；
再通过提前编好的软件程序根据输入的柔性微裂纹传感元件电阻数据，实时处理计算得到相对阻值数据，便可以时间为横坐标实时输出脉搏检测曲线图，从而使柔性微裂纹传感器具有优秀的实时脉搏检测能力，可以实时反映临床手术时患者的心率，从而判断患者生理状况。为微裂纹应变传感器在未来智能医疗器械的应用中打下了坚实的基础。
显然，上述实施例仅仅是为清楚地说明所作的举例，并非对实施方式的限定。对于所属领域的普通技术人员来说，在上述说明的基础上还可以做出其它不同形式变化或变动。这里无需也无法对所有的实施方式予以穷举。而由此所引申出的显而易见的变化或变动仍处于本发明创造的保护范围之中。

Claims (10)

  1. 一种微裂纹应变传感元件，其特征在于，包括：
    基底层；
    金属薄膜，所述金属薄膜设于基底层上，所述金属薄膜由两种金属材料沉积而成，所述金属薄膜设有图案化裂纹结构；
    保护层，所述保护层设于金属薄膜上；
    输出电极，所述输出电极连接于金属薄膜，用于输出电信号；
    封装层，所述封装层设于保护层上。
  2. 根据权利要求1所述的微裂纹应变传感元件，其特征在于，所述基底层的材料包括：聚酰亚胺、聚乙烯对苯二甲酸脂、聚氯乙烯、尼龙、流延聚丙烯薄膜材料的薄膜。
  3. 根据权利要求1所述的微裂纹应变传感元件，其特征在于，所述金属薄膜层为采用金薄膜和铬相沉积而成的薄膜，其中金替换的金属材料包括：铂、银、铜。
  4. 根据权利要求1所述的微裂纹应变传感元件，其特征在于，所述保护层的原料采用环氧树脂A液与B液按照重量比3:1的比例混合搅拌而成。
  5. 根据权利要求1所述的微裂纹应变传感元件，其特征在于，所述封装层的原料采用聚二甲基硅氧烷样液按重量比10：1的比例混合搅拌而成。
  6. 一种制备权利要求1-5任一项所述微裂纹应变传感元件的方法，其特征在于，包括如下步骤：
    (1)根据所需传感元件形状制作带有相应镂空形状的镀膜模板，将镀膜模板放置于基底层上，在基底层上镀上由两种金属材料沉积而成的金属薄膜层；
    (2)根据所需裂纹的密度与位置制作带有相应镂空形状的图案的保护层模板上设计，并喷涂上脱模剂；
    (3)将保护层模板固定于金属薄膜层表面，并将保护层的原料刷涂在保护层模板上；
    (4)待保护层固化后进行脱模，并布置输出电极，得到样片；
    (5)将封装层的原料旋涂于样片表面；
    (6)对金属薄膜层进行弯曲和拉伸操作以在金属薄膜层表面得到图案化裂纹结构。
  7. 根据权利要求6所述的方法，其特征在于，所述镀膜模板的结构包括镂空部分，所述镂空部分两端设有凸出部分。
  8. 根据权利要求6所述的方法，其特征在于，所述保护层模板的结构包括间隔的长方形状的镂空槽。
  9. 根据权利要求6所述的方法，其特征在于，所述图案化裂纹结构为在金属薄膜层表面的裂纹阵列，所述裂纹位于在金属薄膜层表面间隔排列的保护层之间。
  10. 权利要求1-5任一项所述的微裂纹应变传感元件或权利要求6-9任一项所述的方法在医学领域的应用。
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