WO2022142910A1 - 汗液传感器以及汗液传感系统 - Google Patents

汗液传感器以及汗液传感系统 Download PDF

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Publication number
WO2022142910A1
WO2022142910A1 PCT/CN2021/133342 CN2021133342W WO2022142910A1 WO 2022142910 A1 WO2022142910 A1 WO 2022142910A1 CN 2021133342 W CN2021133342 W CN 2021133342W WO 2022142910 A1 WO2022142910 A1 WO 2022142910A1
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Prior art keywords
electrode
sweat
hole
layer
conductive
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PCT/CN2021/133342
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English (en)
French (fr)
Inventor
王书琪
张珽
刘梦愿
陆骐峰
杨显青
李连辉
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中国科学院苏州纳米技术与纳米仿生研究所
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Application filed by 中国科学院苏州纳米技术与纳米仿生研究所 filed Critical 中国科学院苏州纳米技术与纳米仿生研究所
Priority to US17/794,990 priority Critical patent/US20230098198A1/en
Priority to EP21913652.0A priority patent/EP4166939A4/en
Priority to JP2022544276A priority patent/JP7361429B2/ja
Publication of WO2022142910A1 publication Critical patent/WO2022142910A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/42—Detecting, measuring or recording for evaluating the gastrointestinal, the endocrine or the exocrine systems
    • A61B5/4261—Evaluating exocrine secretion production
    • A61B5/4266—Evaluating exocrine secretion production sweat secretion
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/02—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating impedance
    • G01N27/04—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating impedance by investigating resistance
    • G01N27/06—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating impedance by investigating resistance of a liquid
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/053—Measuring electrical impedance or conductance of a portion of the body
    • A61B5/0531—Measuring skin impedance
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14507—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue specially adapted for measuring characteristics of body fluids other than blood
    • A61B5/14517—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue specially adapted for measuring characteristics of body fluids other than blood for sweat
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14546—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring analytes not otherwise provided for, e.g. ions, cytochromes
    • 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
    • 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
    • A61B5/683—Means for maintaining contact with the body
    • A61B5/6832—Means for maintaining contact with the body using adhesives
    • A61B5/6833—Adhesive patches
    • 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
    • A61B2562/0209—Special features of electrodes classified in A61B5/24, A61B5/25, A61B5/283, A61B5/291, A61B5/296, A61B5/053
    • 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
    • A61B2562/04—Arrangements of multiple sensors of the same type
    • A61B2562/046—Arrangements of multiple sensors of the same type in a matrix array
    • 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
    • A61B2562/12—Manufacturing methods specially adapted for producing sensors for in-vivo measurements
    • A61B2562/125—Manufacturing methods specially adapted for producing sensors for in-vivo measurements characterised by the manufacture of electrodes

Definitions

  • the present application belongs to the technical field of sensors, and in particular, relates to a sweat sensor and a sweat sensing system.
  • Abnormal changes in sweat composition during human exercise are related to blood concentration levels, or can directly indicate the health of the human body.
  • Na + is the most electrolyte in human sweat, and it is an important basis for sweat secretion. Its concentration can reflect the symptoms of different types of water and salt metabolism disorders in the human body. For example, athletes, soldiers, workers, etc. will suffer from severe dehydration when working in extreme environments (severe exercise, overheated fire rescue, etc.), resulting in hypernatremia . Failure to judge and replenish water and electrolytes in a timely manner is likely to cause serious physiological threats and even death.
  • the present application provides a sweat sensor and a sweat sensor that can simultaneously detect the amount of sweat and the concentration of electrolytes in real time and continuously, and can avoid the interference of the detection of electrolyte concentration caused by the mixing of new and old sweat. sense system.
  • a sweat sensor which includes: a sweat-conducting electrode layer, including an insulating layer, a conductive electrode disposed in the insulating layer, and a first through hole, the first through hole passing through the the insulating layer and the conductive electrode; the adhesive layer is arranged on the insulating layer and has a second through hole communicating with the first through hole; the water absorption and diffusion layer is arranged on the adhesive layer, and cover the second through hole.
  • the central axis of the first through hole coincides with the central axis of the second through hole.
  • the conductive electrode includes a first electrode and a second electrode, the first electrode and the second electrode are located in the same plane, and the electrodes of the first electrode The central axis of the through hole, the central axis of the electrode through hole of the second electrode, and the central axis of the first through hole coincide.
  • the conductive electrode includes a first electrode and a second electrode, the first electrode and the second electrode are located in different planes, and the electrodes of the first electrode The central axis of the through hole, the central axis of the electrode through hole of the second electrode, and the central axis of the first through hole coincide.
  • the sweat sensor further includes: a contact layer disposed on a surface of the insulating layer facing away from the adhesive layer, the contact layer having a connection with the adhesive layer.
  • the first through hole communicates with the third through hole.
  • the central axis of the first through hole coincides with the central axis of the third through hole.
  • the material of the insulating layer and/or the contact layer is polydimethylsiloxane, silicone rubber or thermoplastic polyester.
  • a conductance square wave curve is obtained according to the conductance value of the sweat passing through the first through hole recorded by the conductive electrode,
  • the conductance square wave curve obtains the total concentration of sweat electrolyte and the total amount of sweat simultaneously; wherein, the amplitude of the conductance square wave curve is correlated with the real-time total concentration of sweat electrolyte in the through hole, and the sweat passes through the through hole.
  • the pore volume and sweating rate correlate with the time difference between the conductance square waves in the conductance square wave curve.
  • a sweat sensing system comprising: a sweat-conducting electrode layer, including an insulating layer, a plurality of conductive electrodes disposed in the insulating layer, and a plurality of first through holes, each first The through hole penetrates through the insulating layer and a corresponding one of the conductive electrodes; the adhesive layer is arranged on the insulating layer and has a plurality of second through holes, and the second through holes are one with the first through holes.
  • a water absorption and diffusion layer is arranged on the adhesive layer and covers the plurality of second through holes.
  • each conductive electrode includes a first electrode and a second electrode, the first electrode and the second electrode of each conductive electrode are located in different planes, and each conductive electrode The first electrodes of each conductive electrode are located in the same plane, the second electrodes of each conductive electrode are located in the same plane, the central axis of the electrode through hole of the first electrode of each conductive electrode, the central axis of the electrode through hole of the second electrode and the corresponding The central axes of the first through holes are coincident; the plurality of conductive electrodes are arranged in an array, the first electrodes of the conductive electrodes in the same column are connected together, and the second electrodes of the conductive electrodes in the same row are connected together.
  • the sweat sensing system further includes: a contact layer disposed on a surface of the insulating layer facing away from the adhesive layer, the contact layer There are a plurality of third through holes therein, and the third through holes communicate with the first through holes in a one-to-one correspondence.
  • the sweat sensor of the present application can simultaneously perform real-time and continuous detection of the amount of sweat and the concentration of electrolytes, and can avoid the interference of the detection of electrolyte concentration caused by the mixing of new and old sweat.
  • FIG. 1 is a schematic structural diagram of a sweat sensor according to a first embodiment of the present application.
  • FIG. 2 is a schematic diagram of a state in which the wearable device with the sweat sensor according to the first embodiment of the present application is placed on the surface of human skin;
  • 3A and 3B are schematic diagrams of the detection principle of the conductance square wave curve and the conductance square wave curve diagram obtained by the sweat sensor according to the embodiment of the present application under the microflow syringe pump test;
  • FIG. 4 is a schematic structural diagram of a sweat sensor according to a second embodiment of the present application.
  • FIG. 5 is a schematic structural diagram of a sweat sensor according to a third embodiment of the present application.
  • FIG. 6 is a schematic structural diagram of a sweat sensing system according to an embodiment of the present application.
  • the term "including” and variations thereof represent open-ended terms meaning “including but not limited to”.
  • the terms “based on”, “depending on” and the like mean “based at least in part on”, “based at least in part on”.
  • the terms “one embodiment” and “an embodiment” mean “at least one embodiment.”
  • the term “another embodiment” means “at least one other embodiment.”
  • the terms “first”, “second”, etc. may refer to different or the same objects. Other definitions, whether explicit or implicit, may be included below. The definition of a term is consistent throughout the specification unless the context clearly dictates otherwise.
  • FIG. 1 is a schematic structural diagram of a sweat sensor according to a first embodiment of the present application.
  • (B) shows a top view of the sweat sensor according to the first embodiment of the present application, note that in (B), in order to clearly show the electrode structure, the adhesive layer 3 and Water absorption and diffusion layer 4;
  • Figure (A) shows a cross-sectional view of the sweat sensor according to the first embodiment of the present application along the line a-a' in Figure (B), of course, Figure (A) The human skin system is additionally shown in .
  • the sweat sensor according to the first embodiment of the present application includes a sweat-conducting electrode layer 2 , an adhesive layer 3 and a water-absorbing and diffusing layer 4 .
  • the perspiration electrode layer 2 includes an insulating layer 21 , a conductive electrode (not marked) disposed in the insulating layer 21 , and a first through hole (not marked), wherein the first through hole penetrates the insulating layer 21 and the conductive electrode.
  • the conductive electrode includes a first electrode 221 and a second electrode 222, wherein the first electrode 221 and the second electrode 222 are located on the same plane, and the central axis of the electrode through hole (not marked) of the first electrode 221, The central axis of the electrode through hole (not marked) of the second electrode 222 coincides with the central axis of the first through hole.
  • the insulating layer 21 is primarily a flexible insulating polymer material, which may be polydimethylsiloxane, silicone rubber, thermoplastic polyester, or the like.
  • the thickness of the insulating layer 21 is between 0.1 mm and 2 mm.
  • the first electrode 221 and the second electrode 222 are embedded inside the insulating layer 21 at the middle portion in the thickness direction.
  • the first electrode 221 and the second electrode 222 can be thin-film electrodes with a certain thickness and width prepared from materials such as carbon nanotubes, graphene, carbon black, and carbon fibers, or can be metals such as gold, platinum, copper, etc. for conductivity testing, etc.
  • the thickness of the first electrode 221 and the second electrode 222 is between 0.01 mm and 1 mm, and the width (line width) of the first electrode 221 and the second electrode 222 is smaller than that of each through hole (eg, electrode through hole, first through hole, etc.) diameter of.
  • the method of embedding the first electrode 221 and the second electrode 222 in the insulating layer 21 is not specifically limited.
  • an insulating layer 21 is first prepared, the first electrode 221 and the second electrode 222 on the same level are prepared on the insulating layer 21 by screen printing or other methods, and finally an insulating layer 221 is prepared on the same level.
  • Another insulating layer 21 is prepared on the layer 21 , the first electrode 221 and the second electrode 222 , and finally the first electrode 221 and the second electrode 222 are embedded in the inner position of the insulating layer 21 .
  • a mold template in the shape of an electrode is first prepared by a machining method, and then the prepolymer of the material for making the insulating layer 21 is poured into the mold template by the method of template complexing, and then peeled off after curing and molding to form
  • There is a groove in the shape of an electrode the first electrode 221 and the second electrode 222 are prepared by filling the groove, and then another insulating layer 21 is prepared on the first electrode 221 and the second electrode 222, and finally the first electrode 221 is prepared.
  • the second electrode 222 is embedded in the inner position of the edge layer 21 .
  • a through hole 23 (which is composed of a first through hole, an electrode through hole, etc.) is prepared by laser cutting, template method or mechanical drilling method.
  • the diameter of the through hole 23 is between 0.5 mm and 2 mm; the effective test surfaces of the first electrode 221 and the second electrode 222 are exposed to the inner wall surface of the through hole 23 .
  • the inner wall of the cylinder of the through hole 23 and the surfaces of the first electrode 221 and the second electrode 222 exposed to the through hole exhibit hydrophobic properties, so the hydrophobic material can be selected according to the material of the insulating layer 21 and the properties of the electrode material, or the The hydrophobic through-holes are realized by post-treatment methods, such as treatment with silane reagents.
  • the adhesive layer 3 is provided on the insulating layer 21, and the adhesive layer 3 has a second through hole (not shown) communicating with the first through hole. That is to say, the through hole 23 penetrates through the insulating layer 21, the adhesive layer 3 and the first electrode 221 and the second electrode 222; wherein, the part of the through hole 23 in the insulating layer 21 is set as the first through hole, the through hole The part of 23 in the adhesive layer 3 is set as the second through hole, the part of the through hole 23 in the first electrode 221 is set as the electrode through hole of the first electrode 221, and the part of the through hole 23 in the second electrode 222 The part in is set as the electrode through hole of the second electrode 222 .
  • the adhesive layer 3 is a viscous film that is fixedly connected between the sweat-conducting electrode layer 2 and the water-absorbing diffusion layer 4, and includes an ultra-thin double-sided adhesive tape (with a thickness of 0.01mm to 0.05mm) with a fixed thickness, a viscoelastic polymer prepolymers, etc.
  • the adhesive layer 3 prepares a second through hole with the same size as the first through hole by laser cutting, template method or mechanical drilling method at the overlapping position of the first through hole of the sweat-guiding electrode layer 2, Sweat is allowed to flow through the first through holes and the second through holes. Further, the central axis of the first through hole coincides with the central axis of the second through hole.
  • the water absorption and diffusion layer 4 is disposed on the adhesive layer 3 and covers the second through hole.
  • the water-absorbing diffusion layer 4 is a hydrophilic material film, including but not limited to clothing fabrics, paper-based cellulose films, gels and other water-absorbing materials.
  • the water-absorbing diffusion layer 4 can use the clothing itself as the water-absorbing layer, preferably, the breathable sweat-permeable sports tights, wrist guards, palm guards, elbow guards, sweat-absorbing belts, etc., as the water-absorbing layer.
  • the thickness of the water absorption and diffusion layer 4 is not limited.
  • the water-absorbing diffusion layer 4 forms an integrated sweat sensor with the sweat-conducting electrode layer 2 through the adhesive layer 3 .
  • FIG. 2 is a schematic diagram of a state in which the wearable device having the sweat sensor according to the first embodiment of the present application is placed on the surface of human skin.
  • the sweat sensor according to the first embodiment of the present application is wrapped and fixed by a strip made of elastic fabric and elastomer material to form a wearable device; and the wearable device can be combined with sports tights, protective clothing Fabrics such as wrists, palm pads, elbow pads, sweatbands, etc. are integrated and compatible to form an elastic water-absorbing fixing strip device 41 .
  • FIG. 3A is a schematic diagram of the detection principle of the conductance square wave curve, wherein ⁇ T 1 represents the duration of the first conductance square wave, and ⁇ T 2 represents the duration of the second conductance square wave; and FIG. 3B is an embodiment according to the present application The conductance square wave plot of the sweat sensor obtained under the microfluidic syringe pump test.
  • the height or amplitude of the conductance square wave curve is correlated with the real-time sweat electrolyte total concentration in the through hole 23, and the volume of sweat droplets passing through the through hole 23 and the sweat rate appear with the next conductance square wave curve.
  • the time difference between them is correlated; therefore, the sweat sensor proposed according to the embodiments of the present application can successfully distinguish the concentration of sweat electrolytes and the amount of sweat through a real-time continuous square wave curve; The advantage of interfering with its accuracy.
  • FIG. 4 is a schematic structural diagram of a sweat sensor according to a second embodiment of the present application.
  • (B) diagram shows a top view of the sweat sensor according to the second embodiment of the present application, note that in (B) diagram, in order to clearly show the electrode structure, the adhesive layer 3 and Water absorption and diffusion layer 4;
  • (A) Figure shows a cross-sectional view of the sweat sensor according to the second embodiment of the present application along the line a-a' in Figure (B), of course, Figure (A) The human skin system is additionally shown in ;
  • (C) is a schematic structural diagram of the first electrode and the second electrode in the sweat sensor according to the second embodiment of the present application.
  • the difference from the structure of the sweat sensor of the first embodiment shown in FIG. 1 is that the first electrode 221 and the second electrode 222 are not on the same plane.
  • the second electrode 222 is above the first electrode 221 , so the electrode through hole of the second electrode 222 overlaps with the electrode through hole of the first electrode 221 up and down.
  • FIG. 5 is a schematic structural diagram of a sweat sensor according to a third embodiment of the present application.
  • (B) shows a top view of the sweat sensor according to the third embodiment of the present application, note that in (B), in order to clearly show the electrode structure, the adhesive layer 3 and Water absorption and diffusion layer 4;
  • (A) Figure shows a cross-sectional view of the sweat sensor according to the third embodiment of the present application along the line a-a' in (B) Figure, of course, (A) Figure The human skin system is additionally shown in .
  • the sweat sensor according to the third embodiment of the present application further includes a contact layer 24 , which is disposed on the back of the insulating layer 21 with adhesive On the surface of the bonding layer 3, and the contact layer 24 has a third through hole (not shown) in communication with the first through hole. Further, the central axis of the first through hole coincides with the central axis of the third through hole, that is, the through hole 23 penetrates through the contact layer 24 .
  • the function of the contact layer 24 has two aspects: first, it is convenient to adjust the thickness of the perspiration electrode layer 2; second, when the hardness of the insulating layer 21 is not suitable for direct contact with the skin, the contact layer 24 can be used to achieve good contact with the skin. attached.
  • the material of the contact layer 24 includes, but is not limited to, polydimethylsiloxane, silicone rubber, thermoplastic polyester, and the like.
  • the tight bonding of the contact layer 24 and the insulating layer 21 can be achieved by common techniques such as cross-linking and bonding.
  • FIG. 6 is a schematic structural diagram of a sweat sensing system according to an embodiment of the present application. For ease of description, FIG. 6 only shows the conductive electrodes and insulating layers.
  • a sweat sensing system includes a plurality of sweat sensors according to the second embodiment of the present application shown in FIG. 4 , and a plurality of the sweat sensor arrays are arranged.
  • the insulating layer 21, the adhesive layer 3, the water absorption and diffusion layer 4 and/or the contact layer 24 (if provided) of each sweat sensor are integrated; that is, a plurality of conductive electrodes are provided in one layer
  • a layer of adhesive layer 3 and a layer of water absorption and diffusion layer 4 are laminated on one layer of insulating layer 21 at a time, and a layer of contact layer 24 is arranged on a layer of adhesive layer 3 facing away from one layer of insulating layer 21 . on the surface.
  • each through hole 23 also penetrates one layer of adhesive layer 3 to form a plurality of second through holes, and also penetrates a layer of contact layer 24 to form a plurality of third through holes. That is to say, the first through holes (including the electrode through holes), the second through holes and the third through holes are in one-to-one correspondence and communicate with each other.
  • the first electrodes of the conductive electrodes are located in the same civilian, the second electrodes of the conductive electrodes are located in the same plane, and the first electrodes and the second electrodes are located in different planes.
  • all the first electrodes of the conductive electrodes of each column are connected together and to the column conductive terminals, and all the second electrodes of the conductive electrodes of each row are connected together and to the row conductive terminals.
  • all first electrodes of the conductive electrodes of the first column are connected together and connected to column conductive terminals 223
  • all first electrodes of the conductive electrodes of the second column are connected together and connected to column conductive terminals 224 .
  • all the first electrodes of the conductive electrodes of the third column are connected together and connected to the column conductive terminals 225; all the second electrodes of the conductive electrodes of the first row are connected together and connected to the row conductive terminals 226, the conductive electrodes of the second row All second electrodes of the electrodes are connected together and connected to row conductive terminals 227 , and all second electrodes of the third row of conductive electrodes are connected together and connected to row conductive terminals 228 .

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Abstract

一种汗液传感器和汗液传感系统，该传感器包括：导汗电极层（2），包括绝缘层（21）、设置于绝缘层（21）内的导电电极以及第一通孔，第一通孔贯穿绝缘层（21）和导电电极；粘合层（3），设置于绝缘层（21）上，且具有与第一通孔连通的第二通孔；吸水扩散层（4），设置于粘合层（3）上，且覆盖第二通孔。该汗液传感系统具有多个该汗液传感器。该汗液传感器能够同时对出汗量和电解质浓度进行实时连续检测，并且能够避免新旧汗液混合对电解质浓度检测造成干扰。

Description

汗液传感器以及汗液传感系统
本申请基于并要求于2020年12月31日递交的申请号为202011631972.2、发明名称为“汗液传感器以及汗液传感系统”的中国专利申请的优先权。
技术领域
本申请属于传感器技术领域，具体地讲，涉及一种汗液传感器以及汗液传感系统。
背景技术
人体运动过程中汗液成分的异常变化和血液浓度水平相关，或可以直接指示人体的健康状况。例如，Na +是人体汗液中最多的电解质，是汗液分泌的重要基础，它的浓度可以反映人体不同类别的水盐代谢紊乱症状。如运动员、军人、工人等在极端环境中(剧烈运动、过热的火灾抢险等)工作时会发生严重脱水情况而产生高钠血症，其汗液和血液中Na +浓度远高出正常值，如果不及时判断和补充水分和电解质，很可能引起严重的生理威胁，甚至死亡。
目前，传统的汗液传感器无法实现同时对出汗量和电解质浓度进行实时连续检测，并且无法避免新旧汗液混合对电解质浓度检测造成的干扰。
发明内容
为了解决上述现有技术中存在的技术问题，本申请提供了一种能够同时对出汗量和电解质浓度进行实时连续检测，并且能够避免新旧汗液混合对电解质浓度检测造成干扰的汗液传感器以及汗液传感系统。
根据本申请的实施例的一方面提供的汗液传感器，其包括：导汗电极层，包括绝缘层、设置于所述绝缘层内的导电电极以及第一通孔，所述第一通孔贯穿所述绝缘层和所述导电电极；粘合层，设置于所述绝缘层上，且具有与所述第一通孔连通的第二通孔；吸水扩散层，设置于所述粘合层上，且覆盖所述第二通孔。
在上述一方面提供的汗液传感器的一个示例中，所述第一通孔的中心轴线与所述第二通孔的中心轴线重合。
在上述一方面提供的汗液传感器的一个示例中，所述导电电极包括第一电极和第二电极， 所述第一电极和所述第二电极位于同一平面内，并且所述第一电极的电极通孔的中心轴线、所述第二电极的电极通孔的中心轴线以及所述第一通孔的中心轴线重合。
在上述一方面提供的汗液传感器的一个示例中，所述导电电极包括第一电极和第二电极，所述第一电极和所述第二电极位于不同平面内，并且所述第一电极的电极通孔的中心轴线、所述第二电极的电极通孔的中心轴线以及所述第一通孔的中心轴线重合。
在上述一方面提供的汗液传感器的一个示例中，所述汗液传感器还包括：接触层，设置于所述绝缘层的背向所述粘合层的表面上，所述接触层中具有与所述第一通孔连通的第三通孔。
在上述一方面提供的汗液传感器的一个示例中，所述第一通孔的中心轴线与所述第三通孔的中心轴线重合。
在上述一方面提供的汗液传感器的一个示例中，所述绝缘层和/或所述接触层的材料为聚二甲基硅氧烷、硅橡胶或热塑性聚酯。
在上述一方面提供的汗液传感器的一个示例中，当利用所述汗液传感器检测汗液时，根据所述导电电极记录的通过所述第一通孔的汗液的电导数值获取电导方波曲线，通过所述电导方波曲线同时获取汗液电解质总浓度和汗液总量；其中，所述电导方波曲线的幅值与所述通孔内实时的汗液电解质总浓度呈相关性，所述汗液通过所述通孔的体积和出汗速率与所述电导方波曲线中电导方波之间的时间差呈相关性。
根据本申请的另一方面提供的汗液传感系统，其包括：导汗电极层，包括绝缘层、设置于所述绝缘层内的多个导电电极以及多个第一通孔，每个第一通孔贯穿所述绝缘层以及相应的一个所述导电电极；粘合层，设置于所述绝缘层上且具有多个第二通孔，所述第二通孔与所述第一通孔一一对应连通；吸水扩散层，设置于所述粘合层上，且覆盖所述多个第二通孔。
在上述另一方面提供的汗液传感系统的一个示例中，每个导电电极包括第一电极和第二电极，每个导电电极的第一电极和第二电极位于不同平面内，并且各个导电电极的第一电极位于同一平面内，各个导电电极的第二电极位于同一平面内，每个导电电极的第一电极的电极通孔的中心轴线、第二电极的电极通孔的中心轴线以及相应的第一通孔的中心轴线重合；所述多个导电电极阵列排布，同一列的导电电极的第一电极连接在一起，同一行的导电电极的第二电极连接在一起。
在上述另一方面提供的汗液传感系统的一个示例中，所述汗液传感系统还包括：接触层，设置于所述绝缘层的背向所述粘合层的表面上，所述接触层中具有多个第三通孔，所述第三通孔与所述第一通孔一一对应连通。
与现有技术相比，本申请的有益效果至少在于：
本申请的汗液传感器能够同时对出汗量和电解质浓度进行实时连续检测，并且能够避免新旧汗液混合对电解质浓度检测造成干扰。
附图说明
通过结合附图进行的以下描述，本申请的实施例的上述和其它方面、特点和优点将变得更加清楚，附图中：
图1是根据本申请的第一实施例的汗液传感器的结构示意图；
图2是具有根据本申请的第一实施例的汗液传感器的可穿戴装置置于人体皮肤表面上的状态示意图；
图3A和图3B是电导方波曲线检测原理示意图以及根据本申请的实施例的汗液传感器在微流注射泵测试下获得的电导方波曲线图；
图4是根据本申请的第二实施例的汗液传感器的结构示意图；
图5是根据本申请的第三实施例的汗液传感器的结构示意图；
图6是根据本申请的实施例的汗液传感系统的结构示意图。
具体实施方式
以下，将参照附图来详细描述本申请的具体实施例。然而，可以以许多不同的形式来实施本申请，并且本申请不应该被解释为限制于这里阐述的具体实施例。相反，提供这些实施例是为了解释本申请的原理及其实际应用，从而使本领域的其他技术人员能够理解本申请的各种实施例和适合于特定预期应用的各种修改。
如本文中使用的，术语“包括”及其变型表示开放的术语，含义是“包括但不限于”。术语“基于”、“根据”等表示“至少部分地基于”、“至少部分地根据”。术语“一个实施例”和“一实施例”表示“至少一个实施例”。术语“另一个实施例”表示“至少一个其他实施例”。术语“第一”、“第二”等可以指代不同的或相同的对象。下面可以包括其他的定义，无论是明确的还是隐含的。除非上下文中明确地指明，否则一个术语的定义在整个说明书中是一致的。
图1是根据本申请的第一实施例的汗液传感器的结构示意图。其中，在图1中，(B)图示出了根据本申请的第一实施例的汗液传感器的俯视图，注意在(B)图中，为了清晰显示电极结构，未示出粘合层3和吸水扩散层4；(A)图示出了沿(B)图中的a-a’线对根据本申 请的第一实施例的汗液传感器进行剖切的剖切图，当然，(A)图中额外示出了人体皮肤系统。
参照图1，根据本申请的第一实施例的汗液传感器包括导汗电极层2、粘合层3和吸水扩散层4。
具体地，导汗电极层2包括绝缘层21、设置在绝缘层21内的导电电极(未标识)以及第一通孔(未标识)，其中，第一通孔贯穿绝缘层21和导电电极。在一个示例中，导电电极包括第一电极221和第二电极222，其中，第一电极221和第二电极222位于同一平面，并且第一电极221的电极通孔(未标识)的中心轴线、第二电极222的电极通孔(未标识)的中心轴线以及所述第一通孔的中心轴线重合。
在一个示例中，绝缘层21主要为柔性绝缘聚合物材料，其可以是聚二甲基硅氧烷、硅橡胶、热塑性聚酯等。绝缘层21的厚度在0.1mm～2mm之间。
第一电极221和第二电极222嵌入在绝缘层21内部并位于厚度方向上的中间部分。第一电极221和第二电极222可以为碳纳米管、石墨烯、碳黑、碳纤维等材料制备的具有一定厚度和宽度的薄膜电极，也可以为金、铂、铜等电导测试用金属等其他材料制成的具有一定厚度和宽度的薄膜电极。第一电极221和第二电极222的厚度在0.01mm～1mm之间，并且第一电极221和第二电极222宽度(线宽)小于各通孔(例如电极通孔、第一通孔等)的直径。
这里，不对第一电极221和第二电极222在绝缘层21中的嵌入方法做具体限定。例如，在一个示例中，首先制备一层绝缘层21，在这层绝缘层21上通过丝网印刷等方法制备出位于同一水平面上的第一电极221和第二电极222，最后在一层绝缘层21、第一电极221和第二电极222上再制备另一层绝缘层21，最终将第一电极221和第二电极222嵌入在了绝缘层21的内部位置。在另一个示例中，首先通过机械加工的方法制备电极形状的模具模板，然后采用模板复形的方法将绝缘层21的制作材料的预聚体倒入模具模板，等固化成型后揭下来后形成具有电极形状的凹槽，在凹槽中填充制备第一电极221和第二电极222，然后在第一电极221和第二电极222之上制备另一层绝缘层21，最终将第一电极221和第二电极222嵌入在了缘层21的内部位置。
在绝缘层21以及第一电极221和第二电极222的中间位置，通过激光切割、模板方法或机械打孔的方法制备出一个通孔23(其由第一通孔、电极通孔等构成)，通孔23的直径在0.5mm～2mm之间；第一电极221和第二电极222的有效测试表面暴露于通孔23内壁表面。优选的，通孔23圆柱体内壁和暴露于通孔的第一电极221和第二电极222表面呈现疏水性质，因此可通过绝缘层21的材料和电极材料的性质选择疏水性材料，也可以通过后处理的方法实现疏水性的通孔，例如采用硅烷试剂处理。
粘合层3设置在绝缘层21上，并且粘合层3具有与第一通孔连通的第二通孔(未示出)。也就是说，通孔23贯通绝缘层21、粘合层3以及第一电极221和第二电极222；其中，通孔23在绝缘层21中的部分被设定为第一通孔，通孔23在粘合层3中的部分被设定为第二通孔，通孔23在第一电极221中的部分被设定为第一电极221的电极通孔，通孔23在第二电极222中的部分被设定为第二电极222的电极通孔。
粘合层3是固定连接导汗电极层2和吸水扩散层4之间的具有粘性的薄膜，其包括采用固定厚度的超薄双面胶(厚度为0.01mm～0.05mm)、粘弹性聚合物的预聚体等。在一个示例中，粘合层3在导汗电极层2的第一通孔的重叠位置通过激光切割、模板方法或机械打孔的方法制备出和第一通孔尺寸一样的第二通孔，使汗液从第一通孔和第二通孔流过。进一步地，第一通孔的中心轴线与第二通孔的中心轴线重合。
吸水扩散层4设置于粘合层3上，且覆盖所述第二通孔。在一个示例中，吸水扩散层4为亲水性材料薄膜，包括但不限定于衣物织物、纸基纤维素类薄膜、凝胶等吸水材料。在本实施例中，吸水扩散层4可以以衣物本身为吸水层，优选的，以透气透汗运动紧身衣物、护腕、护掌、护肘、吸汗带等为吸水层。并不限定吸水扩散层4的厚度。吸水扩散层4通过粘合层3与导汗电极层2形成一体汗液传感器。
图2是具有根据本申请的第一实施例的汗液传感器的可穿戴装置置于人体皮肤表面上的状态示意图。参照图2，根据本申请的第一实施例的汗液传感器被通过弹性的织物、弹性体材料制成的条带包裹固定，以形成可穿戴装置；而该可穿戴装置可以与运动紧身衣物、护腕、护掌、护肘、吸汗带等织物集成兼容，形成弹性吸水固定条带装置41。
当根据本申请的实施例的汗液传感器设置于人体皮肤1上时，皮肤下皮12内的汗腺14分泌出汗液13，汗液13从汗腺14分泌出时具有一定的压强，最大可以达到70000Nm -2，足以将汗液14泵入通孔23并被吸水扩散层4迅速吸收走；当汗液13通过通孔23的内壁时，暴露于通孔23内的平行电极(即第一电极221和第二电极222)会记录下实时通过汗液液体或汗液液滴的电导数值。如图3A图是电导方波曲线检测原理的示意图，其中，ΔT 1表示第一个电导方波持续时间，ΔT 2表示第二个电导方波持续时间；而图3B是根据本申请的实施例的汗液传感器在微流注射泵测试下获得的电导方波曲线图。
参照图3B，电导方波曲线的高度或幅值与通孔23内实时的汗液电解质总浓度呈相关性，而汗液液滴通过通孔23的体积和出汗速率与下一个电导方波曲线出现之间的时间差呈相关性；因此，根据本申请的实施例提出的汗液传感器可以通过一条实时连续的电导方波曲线，将汗液电解质浓度和出汗量成功区分出来；同时具有不被新旧汗液混合干扰其准确性的优点。
图4是根据本申请的第二实施例的汗液传感器的结构示意图。其中，在图4中，(B)图示出了根据本申请的第二实施例的汗液传感器的俯视图，注意在(B)图中，为了清晰显示电极结构，未示出粘合层3和吸水扩散层4；(A)图示出了沿(B)图中的a-a’线对根据本申请的第二实施例的汗液传感器进行剖切的剖切图，当然，(A)图中额外示出了人体皮肤系统；(C)图示出了根据本申请的第二实施例的汗液传感器中的第一电极和第二电极的结构示意图。
参照图4，与图1所示的第一实施例的汗液传感器的结构不同之处在于：第一电极221和第二电极222不在同一平面上。例如，第二电极222在第一电极221的上方，因此第二电极222的电极通孔与第一电极221的电极通孔上下重叠。
图5是根据本申请的第三实施例的汗液传感器的结构示意图。其中，在图5中，(B)图示出了根据本申请的第三实施例的汗液传感器的俯视图，注意在(B)图中，为了清晰显示电极结构，未示出粘合层3和吸水扩散层4；(A)图示出了沿(B)图中的a-a’线对根据本申请的第三实施例的汗液传感器进行剖切的剖切图，当然，(A)图中额外示出了人体皮肤系统。
参照图5，与图1所示的第一实施例的汗液传感器的结构不同之处在于：根据本申请的第三实施例的汗液传感器还包括接触层24，设置于绝缘层21的背向粘合层3的表面上，并且接触层24中具有与第一通孔连通的第三通孔(未示出)。进一步地，所述第一通孔的中心轴线与所述第三通孔的中心轴线重合，也就是说，通孔23贯穿接触层24。
接触层24的作用有两个方面：一、方便调节导汗电极层2的厚度；二、当绝缘层21的硬度不适于与皮肤直接接触，可通过接触层24来实现与皮肤的良好接触贴附。接触层24的材料包括但不限定于聚二甲基硅氧烷、硅橡胶、热塑性聚酯等。接触层24和绝缘层21的紧密结合可以通过常用的交联粘合等技术来实现。
图6是根据本申请的实施例的汗液传感系统的结构示意图。为了便于描述介绍，图6仅示出了导电电极和绝缘层。
参照图6，根据本申请的实施例的汗液传感系统包括多个图4所示的根据本申请的第二实施例的汗液传感器，多个所述汗液传感器阵列排布。
在这种情况下，各个汗液传感器的绝缘层21、粘合层3、吸水扩散层4和/或接触层24(如果设置有)连成一体；也就是说，多个导电电极设置于一层绝缘层21内，一层粘合层3和一层吸水扩散层4一次层叠于一层绝缘层21上，而一层接触层24设置于一层绝缘层21的背向一层粘合层3的表面上。
当然，各个通孔23也贯穿一层粘合层3以形成多个第二通孔，并且也贯穿一层接触层 24以形成多个第三通孔。也就是说，第一通孔(包括各电极通孔)、第二通孔以及第三通孔一一对应并连通。
在多个所述汗液传感器阵列分布的情况下，各导电电极的第一电极位于同一平民，而各导电电极的第二电极位于同一平面，并且第一电极和第二电极位于不同平面。因此，每一列的导电电极的所有第一电极连接在一起并连接到列导电端子，而每一行的导电电极的所有第二电极连接在一起并连接到行导电端子。例如，在图6中，第一列的导电电极的所有第一电极连接在一起并连接到列导电端子223，第二列的导电电极的所有第一电极连接在一起并连接到列导电端子224，第三列的导电电极的所有第一电极连接在一起并连接到列导电端子225；第一行的导电电极的所有第二电极连接在一起并连接到行导电端子226，第二行的导电电极的所有第二电极连接在一起并连接到行导电端子227，第三行的导电电极的所有第二电极连接在一起并连接到行导电端子228。
如上提供的汗液传感系统，通过设置阵列排布的多个导电电极，可以获取多个采样点的数据，进一步提高单位面积汗液出汗量和汗液电解质浓度分析的准确性。
上述对本申请的特定实施例进行了描述。其它实施例在所附权利要求书的范围内。
在整个本说明书中使用的术语“示例性”、“示例”等意味着“用作示例、实例或例示”，并不意味着比其它实施例“优选”或“具有优势”。出于提供对所描述技术的理解的目的，具体实施方式包括具体细节。然而，可以在没有这些具体细节的情况下实施这些技术。在一些实例中，为了避免对所描述的实施例的概念造成难以理解，公知的结构和装置以框图形式示出。
以上结合附图详细描述了本申请的实施例的可选实施方式，但是，本申请的实施例并不限于上述实施方式中的具体细节，在本申请的实施例的技术构思范围内，可以对本申请的实施例的技术方案进行多种简单变型，这些简单变型均属于本申请的实施例的保护范围。
本说明书内容的上述描述被提供来使得本领域任何普通技术人员能够实现或者使用本说明书内容。对于本领域普通技术人员来说，对本说明书内容进行的各种修改是显而易见的，并且，也可以在不脱离本说明书内容的保护范围的情况下，将本文所定义的一般性原理应用于其它变型。因此，本说明书内容并不限于本文所描述的示例和设计，而是与符合本文公开的原理和新颖性特征的最广范围相一致。

Claims (10)

  1. 一种汗液传感器，其特征在于，所述汗液传感器包括：
    导汗电极层，包括绝缘层、设置于所述绝缘层内的导电电极以及第一通孔，所述第一通孔贯穿所述绝缘层和所述导电电极；
    粘合层，设置于所述绝缘层上，且具有与所述第一通孔连通的第二通孔；
    吸水扩散层，设置于所述粘合层上，且覆盖所述第二通孔。
  2. 根据权利要求1所述的汗液传感器，其特征在于，所述第一通孔的中心轴线与所述第二通孔的中心轴线重合。
  3. 根据权利要求1或2所述的汗液传感器，其特征在于，所述导电电极包括第一电极和第二电极，所述第一电极和所述第二电极位于同一平面内，并且所述第一电极的电极通孔的中心轴线、所述第二电极的电极通孔的中心轴线以及所述第一通孔的中心轴线重合。
  4. 根据权利要求1或2所述的汗液传感器，其特征在于，所述导电电极包括第一电极和第二电极，所述第一电极和所述第二电极位于不同平面内，并且所述第一电极的电极通孔的中心轴线、所述第二电极的电极通孔的中心轴线以及所述第一通孔的中心轴线重合。
  5. 根据权利要求1所述的汗液传感器，其特征在于，所述汗液传感器还包括：接触层，设置于所述绝缘层的背向所述粘合层的表面上，所述接触层中具有与所述第一通孔连通的第三通孔。
  6. 根据权利要求5所述的汗液传感器，其特征在于，所述第一通孔的中心轴线与所述第三通孔的中心轴线重合。
  7. 根据权利要求1所述的汗液传感器，其特征在于，当利用所述汗液传感器检测汗液时，根据所述导电电极记录的通过所述第一通孔的汗液的电导数值获取电导方波曲线，通过所述电导方波曲线同时获取汗液电解质总浓度和汗液总量；其中，所述电导方波曲线的幅值与所述通孔内实时的汗液电解质总浓度呈相关性，所述汗液通过所述通孔的体积和出汗速率与所述电导方波曲线中电导方波之间的时间差呈相关性。
  8. 一种汗液传感系统，其特征在于，所述汗液传感系统包括：
    导汗电极层，包括绝缘层、设置于所述绝缘层内的多个导电电极以及多个第一通孔，每个第一通孔贯穿所述绝缘层以及相应的一个所述导电电极；
    粘合层，设置于所述绝缘层上且具有多个第二通孔，所述第二通孔与所述第一通孔一一对应连通；
    吸水扩散层，设置于所述粘合层上，且覆盖所述多个第二通孔。
  9. 根据权利要求8所述的汗液传感系统，其特征在于，每个导电电极包括第一电极和第二电极，每个导电电极的第一电极和第二电极位于不同平面内，并且各个导电电极的第一电极位于同一平面内，各个导电电极的第二电极位于同一平面内，每个导电电极的第一电极的电极通孔的中心轴线、第二电极的电极通孔的中心轴线以及相应的第一通孔的中心轴线重合；
    所述多个导电电极阵列排布，同一列的导电电极的第一电极连接在一起，同一行的导电电极的第二电极连接在一起。
  10. 根据权利要求8或9所述的汗液传感系统，其特征在于，所述汗液传感系统还包括：接触层，设置于所述绝缘层的背向所述粘合层的表面上，所述接触层中具有多个第三通孔，所述第三通孔与所述第一通孔一一对应连通。
PCT/CN2021/133342 2020-12-31 2021-11-26 汗液传感器以及汗液传感系统 WO2022142910A1 (zh)

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