CN109374713B - Sweat monitors sensor-based system, patch and preparation method thereof - Google Patents

Sweat monitors sensor-based system, patch and preparation method thereof Download PDF

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Publication number
CN109374713B
CN109374713B CN201811508757.6A CN201811508757A CN109374713B CN 109374713 B CN109374713 B CN 109374713B CN 201811508757 A CN201811508757 A CN 201811508757A CN 109374713 B CN109374713 B CN 109374713B
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sensing chip
manufacturing
sweat
chip
sensing
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CN109374713A (en
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黄显
杨晴
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Tianjin University
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Tianjin University
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    • 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
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/403—Cells and electrode assemblies
    • G01N27/414—Ion-sensitive or chemical field-effect transistors, i.e. ISFETS or CHEMFETS
    • G01N27/4148—Integrated circuits therefor, e.g. fabricated by CMOS processing
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
    • G01K13/00—Thermometers specially adapted for specific purposes
    • G01K13/20—Clinical contact thermometers for use with humans or animals
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
    • G01K7/00—Measuring temperature based on the use of electric or magnetic elements directly sensitive to heat ; Power supply therefor, e.g. using thermoelectric elements
    • G01K7/16—Measuring temperature based on the use of electric or magnetic elements directly sensitive to heat ; Power supply therefor, e.g. using thermoelectric elements using resistive elements
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    • G01N27/04—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating impedance by investigating resistance
    • G01N27/12—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating impedance by investigating resistance of a solid body in dependence upon absorption of a fluid; of a solid body in dependence upon reaction with a fluid, for detecting components in the fluid
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    • 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
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    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/302—Electrodes, e.g. test electrodes; Half-cells pH sensitive, e.g. quinhydron, antimony or hydrogen electrodes
    • G—PHYSICS
    • G01—MEASURING; TESTING
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    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/308—Electrodes, e.g. test electrodes; Half-cells at least partially made of carbon
    • G—PHYSICS
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    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
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    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
    • G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
    • G01N27/3272—Test elements therefor, i.e. disposable laminated substrates with electrodes, reagent and channels
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
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    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
    • G01N27/3275—Sensing specific biomolecules, e.g. nucleic acid strands, based on an electrode surface reaction
    • G01N27/3277—Sensing specific biomolecules, e.g. nucleic acid strands, based on an electrode surface reaction being a redox reaction, e.g. detection by cyclic voltammetry
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    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
    • G01N27/3275—Sensing specific biomolecules, e.g. nucleic acid strands, based on an electrode surface reaction
    • G01N27/3278—Sensing specific biomolecules, e.g. nucleic acid strands, based on an electrode surface reaction involving nanosized elements, e.g. nanogaps or nanoparticles
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    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
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    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/403—Cells and electrode assemblies
    • G01N27/414—Ion-sensitive or chemical field-effect transistors, i.e. ISFETS or CHEMFETS
    • G01N27/4146—Ion-sensitive or chemical field-effect transistors, i.e. ISFETS or CHEMFETS involving nanosized elements, e.g. nanotubes, nanowires

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Abstract

The present invention provides a kind of sweat monitoring sensor-based systems, patch and preparation method thereof, wherein the described method includes: preparing flexible extending substrate；Make hydrophilic aperture silica-gel sponge；Make multiple sensing chips；Each sensing chip is transferred in flexible extending substrate, hydrophilic aperture silica-gel sponge is set at the top of each sensing chip.The configuration of the present invention is simple, preparation is convenient, is conducive to meet monitoring requirements.

Description

Sweat monitoring and sensing system, patch and preparation method thereof
Technical Field
The invention relates to the technical field of monitoring, in particular to a sweat monitoring and sensing system, a patch and a preparation method thereof.
Background
Along with the rapid development of science and technology and the improvement of standard of living, the demand to physiological monitoring is also more and more, and the requirement also increases thereupon, then current monitoring product and method, often the operation is complicated, and the cost is higher, and the practicality is not enough, and monitoring efficiency is not high to and can't dress obtain physiological parameter index from the molecular aspect on the human body in real time and not have the ground, the user demand of satisfying that can not be fine.
Disclosure of Invention
Technical problem to be solved
In view of the above technical problems, it is an object of the present invention to provide a sweat monitoring and sensing system, a patch and a method for manufacturing the same, so as to solve at least one of the above problems.
(II) technical scheme
According to one aspect of the present invention, there is provided a method of making a sweat monitoring sensing patch, comprising:
preparing a flexible, extensible substrate;
manufacturing a hydrophilic open-cell silica gel sponge;
manufacturing a plurality of sensing chips;
and transferring each sensing chip to the flexible extensible substrate, and arranging the hydrophilic open-pore silica gel sponge on the top of each sensing chip.
In some embodiments, the making a hydrophilic open-cell silicone sponge comprises:
manufacturing an open-cell sponge matrix by adding platinum catalytic silica gel;
and carrying out surface modification on the open-cell sponge matrix by utilizing a super-hydrophilic coating to obtain the hydrophilic open-cell silica gel sponge.
In some embodiments, a plurality of the sensor chips comprises: the sensor comprises a sodium ion sensing chip, a potassium ion sensing chip, a calcium ion sensing chip, a chloride ion sensing chip, a glucose sensing chip and a lactic acid sensing chip; manufacturing the sensing chip, including:
manufacturing a basic electrode, a magnetic type output interface and a horseshoe-shaped line connecting the basic electrode and the magnetic type output interface;
and modifying the working electrode in the basic electrode to obtain the sensing chip.
In some embodiments, a plurality of the sensor chips comprises: a sweat pH value sensing chip and a perspiration amount sensing chip; manufacturing the sensing chip, including: manufacturing a basic electrode, a magnetic type output interface and a horseshoe-shaped line connecting the basic electrode and the magnetic type output interface to obtain the sensing chip; or
The plurality of sensor chips include: a skin temperature sensing chip; manufacturing the sensing chip, including: the magnetic type output interface and the horseshoe-shaped line connected with the magnetic type output interface are manufactured to obtain the sensing chip.
In some embodiments, the base electrode comprises a reference electrode, and the making of the base electrode, the magnetic-type output interface, and the horseshoe-shaped line connecting the base electrode and the magnetic-type output interface comprises:
spin-coating a lower insulating layer on a copper foil, and connecting the lower insulating layer with a metal layer substrate;
sputtering a titanium layer on the copper foil, and sputtering a gold layer on the titanium layer;
electroplating the reference electrode on the gold layer;
manufacturing the basic electrode, the magnetic type output interface and the horseshoe-shaped line except the reference electrode by utilizing photoetching technology and a plurality of etching solutions;
manufacturing an upper insulating layer on the horseshoe-shaped line;
and stripping the base electrode, the magnetic suction type output interface, the horseshoe-shaped line, the lower insulating layer and the upper insulating layer from the metal layer substrate.
In some embodiments, if the sensing chip is the sodium ion sensing chip, the potassium ion sensing chip, the calcium ion sensing chip, or the chloride ion sensing chip, the modifying the working electrode in the base electrode to obtain the sensing chip includes:
manufacturing a conductive organic polymer electron transfer layer on the working electrode;
configuring an ion-selective membrane with an ion-selective carrier, a membrane matrix, a plasticizer, and an ion exchanger;
disposing the ion-selective membrane onto the conductive organic polymer electron transfer layer.
In some embodiments, if the sensing chip is the glucose sensing chip or the lactate sensing chip, the modifying the working electrode in the base electrode to obtain the sensing chip includes:
manufacturing an electron transfer layer on the working electrode;
dripping an oxidase solution on the electron transfer layer, standing and airing to form an oxidase layer;
and manufacturing an active substance protection layer on the oxidase layer.
In some embodiments, the reference electrodes of the sodium ion sensing chip, the potassium ion sensing chip, the calcium ion sensing chip and the chloride ion sensing chip are connected to the same magnetic type output interface, and the reference electrodes of the glucose sensing chip and the lactate sensing chip are connected to the same magnetic type output interface.
In accordance with another aspect of the present invention, there is provided a sweat monitoring sensing patch comprising:
a flexible, extensible substrate;
a plurality of sensor chips located on the flexible malleable substrate; and
a hydrophilic open-cell silicone sponge on top of each of the sensor chips.
According to yet another aspect of the present invention, there is provided a sweat monitoring sensing system comprising: the terminal, the flexible signal processing and transmitting circuit and the sweat monitoring and sensing patch are arranged on the base; wherein,
the sweat monitoring and sensing patch is connected with the flexible signal processing and transmitting circuit and is used for sending the signals monitored by the sweat monitoring and sensing patch to the flexible signal processing and transmitting circuit;
the flexible signal processing and transmitting circuit is connected with the terminal and is used for receiving the signal sent by the sweat monitoring and sensing patch, converting the signal into sweat component information and sending the sweat component information to the terminal;
and the terminal is used for receiving and analyzing the sweat component information sent by the flexible signal processing and transmitting circuit.
(III) advantageous effects
According to the technical scheme, the sweat monitoring and sensing system, the patch and the preparation method thereof have the following beneficial effects:
(1) the sweat monitoring sensing patch of the present invention includes a flexible, malleable substrate; a plurality of sensor chips located on the flexible malleable substrate; and every hydrophilic trompil silica gel sponge at sensor chip's top, simple structure, preparation is convenient, is favorable to satisfying the monitoring demand.
(2) The invention can solve the technical problem that the requirement of wearable human body on real-time non-invasive acquisition of physiological parameter indexes from a molecular level cannot be met in the prior art, and achieves the technical effect of meeting the requirement of wearable human body on real-time non-invasive acquisition of physiological parameter indexes from a molecular level.
(3) According to the invention, the horseshoe-shaped line is used for connecting the basic electrode and the magnetic type output interface, sharp angles are removed, the pressure concentration effect is avoided, the pressure resistance is improved, the occurrence of short circuit of the connecting line caused by various mechanical factors is reduced, the bending in various directions can be realized, and the extensibility and the practicability are increased;
(4) in the invention, the reference electrodes of the sodium ion sensing chip, the potassium ion sensing chip, the calcium ion sensing chip and the chloride ion sensing chip are connected with the same magnetic-type output interface, and the reference electrodes of the glucose sensing chip and the lactic acid sensing chip are connected with the same magnetic-type output interface, so that the volume of the sweat monitoring and sensing patch can be reduced, the sweat monitoring and sensing patch is easier to wear and move, meanwhile, the manufacturing material is saved, and the cost for manufacturing the sweat monitoring and sensing patch is reduced;
(5) in the invention, the sweat monitoring sensing patch is connected with the flexible signal processing and transmitting circuit through the magnetic type output interface, and the magnetic type output interface can be used for quickly and conveniently realizing connection or disconnection operation, thereby saving the operation time and improving the use efficiency;
(6) the hydrophilic open-cell silica gel sponge prepared by the invention collects sweat by utilizing the capillary action and removes grease, so that a metal electrode is prevented from directly contacting the skin of a human body, and the sweat monitoring efficiency can be improved;
(7) in the invention, each sensing chip is a high-channel integrated chip, and each sensing chip is transferred to the flexible extensible substrate, so that the sweat monitoring sensing patch can simultaneously monitor various physiological parameter indexes of a human body in real time, and the monitoring efficiency and the practicability are improved;
(8) in the invention, each sensing chip is manufactured by using materials such as copper, titanium, gold, silver, polyimide and the like by utilizing a CMOS (complementary metal oxide semiconductor) process, so that the sensing chip has the characteristics of high precision, low power consumption, high speed, high integration level and the like.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, and it is obvious that the drawings in the following description are some embodiments of the present invention, and other drawings can be obtained by those skilled in the art without creative efforts.
Fig. 1 is a flow chart of a method for manufacturing a sweat monitoring sensor patch according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of a process for manufacturing a base electrode, a magnetic-type output interface, and a horseshoe-shaped line according to an embodiment of the present invention;
FIG. 3 is a schematic diagram of a process for modifying working electrodes of a sodium ion sensing chip, a potassium ion sensing chip, a calcium ion sensing chip, and a chloride ion sensing chip according to an embodiment of the present invention;
fig. 4 is a schematic structural diagram of connection between reference electrodes of a sodium ion sensing chip, a potassium ion sensing chip, a calcium ion sensing chip, and a chloride ion sensing chip provided in an embodiment of the present invention and the same magnetic-type output interface;
FIG. 5 is a schematic diagram of a process for modifying working electrodes of a glucose sensor chip and a lactate sensor chip according to an embodiment of the present invention;
fig. 6 is a schematic structural diagram of connection between reference electrodes of a glucose sensing chip and a lactate sensing chip provided in an embodiment of the present invention and the same magnetic-type output interface;
fig. 7 is a schematic layout view of a sweat monitoring sensor patch according to an embodiment of the present invention;
fig. 8 is a cross-sectional view of a sweat monitoring sensing patch provided in accordance with an embodiment of the present invention.
Detailed Description
To make the objects, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings, and it is apparent that the described embodiments are some, but not all embodiments of the present invention. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
The sweat monitoring and sensing system, the patch and the preparation method thereof provided by the embodiment of the invention can solve the technical problem that the requirement of wearable human body on real-time non-invasive acquisition of physiological parameter indexes from a molecular level cannot be met in the prior art, and achieve the technical effect of meeting the requirement of wearable human body on real-time non-invasive acquisition of physiological parameter indexes from a molecular level.
To facilitate understanding of this embodiment, a method for manufacturing a sweat monitoring sensor patch disclosed in this embodiment of the present invention will be described in detail, and as shown in fig. 1, the method may include the following steps.
Step S101, a flexible, malleable substrate is prepared.
The flexible extensible substrate can be in a flexible extensible epidermis film structure, and can be made of ultra-thin high polymer materials with ultra-high elasticity and ultra-high extensibility, can deform and extend along with the skin of a human body, and does not hinder the movement of the skin of the human body. The flexible extensible substrate may be adsorbed to the human skin surface by natural intermolecular affinity.
Specifically, the flexible extensible substrate may be 5% spandex 95% polyester four-side stretch polyester fabric.
And S102, manufacturing the hydrophilic open-cell silica gel sponge.
Further, step S102 may include the steps of:
and (3) manufacturing the open-pore sponge matrix by adding platinum catalytic silica gel.
Specifically, a silica gel foaming process is used, and the addition of the platinum catalytic silica gel is performed in a proportion of 1: 1, and foaming in a container with air holes to avoid flatulence. The gas phase was air, the liquid phase was deionized water, and the droplets were 2 μ L. Hydrophilicity can be tested at this time using a contact angle meter. The contact angle may be 130 degrees, in a hydrophobic state.
And carrying out surface modification on the open-cell sponge matrix by utilizing a super-hydrophilic coating to obtain the hydrophilic open-cell silica gel sponge.
Illustratively, the open-pore sponge matrix can also be subjected to surface modification by using methods such as plasma surface modification and grafting surface modification. For example, in the grafting surface modification method, plasma etching may be performed on an open-cell sponge substrate, then the etched open-cell sponge substrate is soaked under the action of a catalyst, finally, the open-cell sponge substrate is dried in an oven at 80 ℃, and the soaking and drying steps are repeated for 5 times to obtain the hydrophilic open-cell silica gel sponge.
Wherein, in the use, hydrophilic trompil silica gel sponge and human skin contact, hydrophilic trompil silica gel sponge have the sweat and collect the filtration function, can utilize capillary action to collect the sweat, get rid of the grease simultaneously to carry the sweat to sensor chip, avoid the metal electrode direct contact human epidermis in the sensor chip.
Step S103, a plurality of sensor chips are manufactured.
Wherein the plurality of sensor chips may include: the device comprises a sodium ion sensing chip, a potassium ion sensing chip, a calcium ion sensing chip, a chloride ion sensing chip, a glucose sensing chip, a lactic acid sensing chip, a sweat pH value sensing chip, a perspiration amount sensing chip and a skin temperature sensing chip.
If the sensing chip is a sodium ion sensing chip, a potassium ion sensing chip, a calcium ion sensing chip or a chloride ion sensing chip, manufacturing the sensing chip, including:
the magnetic type magnetic sensor comprises a basic electrode, a magnetic type output interface and a horseshoe-shaped line, wherein the horseshoe-shaped line is connected with the basic electrode and the magnetic type output interface.
Further, as shown in fig. 3, the base electrode includes: a working electrode 7 and a reference electrode 6. The working electrode can be a gold electrode, inert metal gold is selected as the working electrode, the gold has the characteristics of excellent conductivity, stable chemical property, incapability of influencing the electrochemical reaction to be researched by the reaction generated on the surface of the gold, and the like, and meanwhile, high-purity gold is easy to obtain and the processing technology is simpler. The reference electrode may be an Ag/AgCl electrode. The Ag/AgCl potential is close to ideal, no polarization, constant potential and little influence by external force, can provide a stable contrast potential, and the solid phase of the Ag/AgCl can not be dissolved in electrolyte, thus having good reproducibility.
Wherein, preparation basic electrode, magnetism are inhaled formula output interface 4 and are connected basic electrode with magnetism inhale formula output interface 4's horseshoe shape line 5, can include following step:
as shown in fig. 2, a lower insulating layer is spin-coated on a copper foil, and the lower insulating layer is connected to the metal layer substrate 1.
Illustratively, the metal layer substrate includes a glass sheet and polydimethylsiloxane disposed over the glass sheet. The lower insulating layer may be polyimide.
Specifically, PDMS (polydimethylsiloxane) was spin-coated on a glass plate at 500 rpm for 45 seconds, and PI (Polyimide) of 8% sigma company was spin-coated on a copper foil having a thickness of 3 μm at 2000 rpm for 45 seconds, wherein the diluted PI was diluted with NMP (N-Methyl pyrrolidone). The PI was adsorbed with PDMS by van der waals force, with copper foil on top.
And sputtering a titanium layer on the copper foil, and sputtering a gold layer on the titanium layer.
Specifically, a titanium layer having a thickness of 5nm may be sputtered using a magnetron sputter of a kyropoulos crystal, and then a gold layer having a thickness of 25nm may be sputtered on the titanium layer. Wherein the titanium layer may act as an adhesion layer.
And electroplating the reference electrode on the gold layer.
Specifically, after exposure and development, the reference electrode is exposed on the gold layer by using a photoetching technology, and silver electroplating is performed. The process of electroplating silver may be: soaking in silver pre-plating solution for 1 minute, observing and fully washing with deionized water to ensure that each part of the reference electrode can be plated with silver. Then, taking the sputtered gold layer as a cathode, taking a pure silver sheet with the same size as the glass sheet as an anode, and soaking the pure silver sheet in the silver electroplating solution for 4 minutes, wherein the reaction principle is shown as a formula 1.1 and a formula 1.2.
And (3) anode reaction: ag-e-→Ag+ (1.1)
And (3) cathode reaction: ag++e-→Ag (1.2)
And manufacturing the basic electrode, the magnetic suction type output interface and the horseshoe-shaped line except the reference electrode by utilizing photoetching technology and a plurality of etching solutions.
Specifically, the reference electrode and the working electrode are partially covered by photoresist, gold etching solution, titanium etching solution and copper etching solution are sequentially used, and metal is patterned by wet etching to form the working electrode, the magnetic type output interface and the horseshoe-shaped line. Forming a metal layer 2 as shown in fig. 2, wherein the metal layer 2 is a lower insulating layer PI, a copper foil, a titanium layer and a gold layer in sequence from bottom to top.
And manufacturing an upper insulating layer on the horseshoe-shaped line.
Specifically, as shown in fig. 2, PI is spin-coated again as the upper insulating layer 3 on the gold layer after patterning. And (3) protecting the basic electrode and the magnetic suction type output interface by using a photoetching process and dry etching to form a hollow structure by using an oxygen plasma etching technology. The U-shaped line sequentially comprises a copper foil, a titanium layer and a gold layer from bottom to top. The copper foil is positioned above the lower insulating layer PI, and the upper insulating layer 3 is positioned above the gold layer.
And stripping the base electrode, the magnetic suction type output interface, the horseshoe-shaped line, the lower insulating layer and the upper insulating layer from the metal layer substrate.
And modifying the working electrode in the basic electrode to obtain the sensing chip.
The modifying the working electrode in the base electrode to obtain the sensing chip may include:
as shown in fig. 3 and 4, a conductive organic polymer electron transfer layer 11 is fabricated on the working electrode 7.
Illustratively, the conductive organic polymer electron transport layer 11 may be a conductive polymer poly 3, 4-ethylenedioxythiophene/polystyrene sulfonate (PEDOT: PSS). PEDOT: PSS is a high molecular polymer aqueous solution, the conductivity is very high, and aqueous solutions with different conductivities can be obtained according to different formulas. PEDOT: PSS is composed of PEDOT and PSS. PEDOT is a polymer of EDOT (3, 4-ethylenedioxythiophene monomer) and PSS is polystyrene sulfonate. Together, these two substances greatly improve the solubility of PEDOT.
Specifically, PEDOT: PSS is dripped on the working electrode, and the working electrode is kept stand and dried.
Configuring the ion-selective membrane 12 with an ion-selective carrier, a membrane matrix, a plasticizer, and an ion exchanger; the ion selective membrane 12 is disposed on the conductive organic polymer electron transfer layer 11.
The prepared conductive organic polymer electron transfer layer can improve the monitoring sensitivity and increase the current and voltage response.
(1) If the sensing chip is a sodium ion sensing chip, the sensing chip specifically may be:
the ion selective membrane of the sodium ion sensing chip is a sodium ion selective membrane, so the ion exchanger of the sodium ion sensing chip is a cation exchanger. The preparation proportion is as follows: each 100mg of cation selective membrane contained 2mg of ion selective carrier, 33mg of membrane matrix, 64.5mg of plasticizer, and 0.5mg of cation exchanger.
Preferably, the ion-selective carrier is ETH 2120. The membrane matrix is polyvinyl chloride. The plasticizer is diisooctyl sebacate, which is used to increase the flexibility of the ion-selective membrane. The cation exchanger is sodium tetrakis [3, 5-bis (trifluoromethyl) phenyl ] borate.
When the sodium ion sensing chip is contacted with a solution containing sodium ions, the sodium ion selective film only allows the sodium ions to enter the sodium ion sensing chip from a film water interface, and charges caused by the process are unevenly distributed on the film water interface to generate an interphase potential. The electrode potential between the working and reference electrodes reflects the activity of ions in the solution containing sodium ions.
(2) If the sensing chip is a potassium ion sensing chip, the specific method may be as follows:
the ion selective film of the potassium ion sensing chip is a potassium ion selective film, so the ion exchanger of the potassium ion sensing chip is a cation exchanger. The preparation proportion is as follows: each 100mg of cation selective membrane contained 2mg of ion selective carrier, 33mg of membrane matrix, 64.5mg of plasticizer, and 0.5mg of cation exchanger.
Preferably, the ion-selective carrier is valinomycin. The membrane matrix is polyvinyl chloride. The plasticizer is diisooctyl sebacate, which is used to increase the flexibility of the ion-selective membrane. The cation exchanger is sodium tetrakis [3, 5-bis (trifluoromethyl) phenyl ] borate.
When the potassium ion sensing chip is contacted with a solution containing potassium ions, the potassium ion selective film only allows potassium ions to enter the potassium ion sensing chip from a film water interface, and charges caused by the process are unevenly distributed on the film water interface to generate an interphase potential. The electrode potential between the working and reference electrodes reflects the activity of the ions in the solution containing potassium ions.
(3) If the sensing chip is a calcium ion sensing chip, the sensing chip specifically may be:
the ion selective membrane of the calcium ion sensing chip is a calcium ion selective membrane, so the ion exchanger of the calcium ion sensing chip is a cation exchanger. The preparation proportion is as follows: each 100mg of cation selective membrane contained 2mg of ion selective carrier, 33mg of membrane matrix, 64.5mg of plasticizer, and 0.5mg of cation exchanger.
Preferably, the ion-selective carrier is a 23187. The membrane matrix is polyvinyl chloride. The plasticizer is diisooctyl sebacate, which is used to increase the flexibility of the ion-selective membrane. The cation exchanger is sodium tetrakis [3, 5-bis (trifluoromethyl) phenyl ] borate.
When the calcium ion sensing chip is contacted with a solution containing calcium ions, the calcium ion selective film only allows the calcium ions to enter the calcium ion sensing chip from the water interface of the film, and the electric charges caused by the process are unevenly distributed on the water interface of the film to generate an interphase potential. The electrode potential between the working and reference electrodes reflects the activity of the ions in the solution containing calcium ions.
(4) If the sensing chip is a chloride ion sensing chip, the specific sensing chip may be:
the ion selective membrane of the chloride ion sensing chip is a chloride ion selective membrane, so the ion exchanger of the chloride ion sensing chip is an anion exchanger. The preparation proportion is as follows: each 100mg of anion selective membrane contained 2mg of ion selective carrier, 33mg of membrane matrix, 64.5mg of plasticizer, and 0.5mg of anion exchanger.
Preferably, the ion selective carrier is tetraphenyl porphine manganese chloride. The membrane matrix is polyvinyl chloride. The plasticizer is diisooctyl sebacate, which is used to increase the flexibility of the ion-selective membrane. The anion exchanger is tetradodecyl ammonium tetrakis (4-chlorophenyl) borate.
When the chloride ion sensing chip is contacted with a solution containing chloride ions, the chloride ion selective film only allows the chloride ions to enter the interior of the chloride ion sensing chip from the water interface of the film, and the electric charges caused by the process are unevenly distributed on the water interface of the film to generate an interphase potential. The electrode potential between the working and reference electrodes reflects the activity of the ions in the solution containing chloride ions.
Wherein, the cation exchanger contains a large number of anion groups, which can eliminate anion interference. The anion exchanger contains a large number of cationic groups, which can eliminate cationic interference.
It should be noted that, as shown in fig. 4, the reference electrodes 6 of the sodium ion sensing chip, the potassium ion sensing chip, the calcium ion sensing chip and the chloride ion sensing chip may be connected to the same magnetic-type output interface 30.
Preferably, can make simultaneously sodium ion sensing chip potassium ion sensing chip calcium ion sensing chip with chloride ion sensing chip at first makes four sensing chip's whole basic electrode and whole magnetism and inhale formula output interface, then makes the horseshoe line of connecting basic electrode and magnetism and inhale formula output interface, modifies every sensing chip's working electrode at last.
(II) if the sensing chip is a glucose sensing chip or a lactate sensing chip, manufacturing the sensing chip, including:
the magnetic type magnetic sensor comprises a basic electrode, a magnetic type output interface and a horseshoe-shaped line, wherein the horseshoe-shaped line is connected with the basic electrode and the magnetic type output interface.
Further, as shown in fig. 6, the base electrode includes: working electrode 9, reference electrode 10 and counter electrode 8. The reference electrode can be an Ag/AgCl electrode, and the working electrode and the counter electrode can be gold electrodes. The counter electrode should have a large surface area so that externally applied polarization acts mainly on the working electrode, thereby preventing damage to the electrode.
The specific processes of manufacturing the base electrode, the magnetic-type output interface and the horseshoe-shaped line connecting the base electrode and the magnetic-type output interface are mentioned above, and are not described herein again.
And modifying the working electrode in the basic electrode to obtain the sensing chip.
The modifying the working electrode in the base electrode to obtain the sensing chip may include:
as shown in fig. 5 and 6, an electron transfer layer 13 is formed on the working electrode 9.
Wherein, a chronopotentiometric method can be adopted to electroplate the nano-porous gold on the working electrode, specifically, the duty ratio of the applied voltage between the working electrode and the counter electrode is 3: 7, and the current density is 1.99mA/cm2The deposition time was 200 s. Then, prussian blue is electroplated on the nano-porous gold, specifically, the formula of the electroplating solution is 2.5mM potassium ferricyanide, 2.5mM ferric chloride, 100mM potassium chloride and 100mM hydrochloric acid, and the electronic transfer layer is formed by circulating for 2 circles by using cyclic voltammetry, using a scanning speed of 0.01V/s and a scanning range of 0V-0.3V. Or, a 1: 1 mixed solution of graphene and carbon nanotubes can be used as an electron transfer layer, the mixed solution is dripped on a working electrode, and the working electrode is kept stand and dried.
The nano porous gold can increase the specific surface area of the working electrode and improve the sensitivity of the sensing chip. Prussian blue can catalyze the decomposition of hydrogen peroxide and reduce the bias voltage.
Dripping an oxidase solution on the electron transfer layer 13, standing and airing to form an oxidase layer 14; an active material protective layer 15 is formed on the oxidase layer 14.
The manufactured electron transfer layer can improve the monitoring sensitivity and increase the current and voltage response.
(1) If the sensing chip is a glucose sensing chip, the specific sensing chip may be:
and dripping an oxidase solution on the electron transfer layer, standing and airing to form an oxidase layer.
Wherein the oxidase solution is 60mg/ml glucose oxidase, and the solvent is PBS (phosphate buffer saline). Preferably, in the standing and airing process, the preservation temperature can be set to be 4 ℃.
And manufacturing an active substance protection layer on the oxidase layer.
Specifically, chitosan can be dissolved in 2% acetic acid, magnetic stirring is carried out for 1 hour, cation exchanger is added, and the mixture is placed still and dried after being dripped. Alternatively, a film-forming substance such as perfluorosulfonic acid (Nafion) may be used as the active material protective layer. The active substance protective layer can exclude interference of ascorbic acid on glucose.
(2) If the sensing chip is a lactate sensing chip, it may specifically be:
and dripping an oxidase solution on the electron transfer layer, standing and airing to form an oxidase layer.
Wherein, the oxidase solution can be a 40mg/ml lactate oxidase solution, and the solvent is PBS. Preferably, in the standing and airing process, the preservation temperature can be set to be 4 ℃.
And manufacturing an active substance protection layer on the oxidase layer.
Specifically, chitosan can be dissolved in 2% acetic acid, magnetic stirring is carried out for 1 hour, cation exchanger is added, and the mixture is placed still and dried after being dripped. Alternatively, a film-forming substance such as perfluorosulfonic acid (Nafion) may be used as the active material protective layer. The active substance protective layer can eliminate interference of ascorbic acid on lactic acid.
The glucose sensing chip and the lactic acid sensing chip have the following principles: the enzyme catalyzes the reactant to generate oxidation-reduction reaction and generate electron transfer with the working electrode, the potentiostat provides a bias voltage between the working electrode and the reference electrode, and the current between the working electrode and the counter electrode increases along with the increase of the concentration of the detection object.
It should be noted that, as shown in fig. 6, the reference electrodes 10 of the glucose sensing chip and the lactate sensing chip are connected to the same magnetic-attraction output interface 29.
Preferably, the glucose sensing chip and the lactate sensing chip can be manufactured simultaneously, the integral basic electrodes of the two sensing chips and all the magnetic type output interfaces are manufactured firstly, then horseshoe-shaped lines for connecting the basic electrodes and the magnetic type output interfaces are manufactured, and finally the working electrode of each sensing chip is modified.
(III) if the sensing chip is a sweat pH value sensing chip, manufacturing the sensing chip, including:
the sensor chip comprises a basic electrode, a magnetic type output interface, a U-shaped line and a magnetic type output interface, wherein the U-shaped line is used for manufacturing the basic electrode, the magnetic type output interface and connecting the basic electrode and the magnetic type output interface to obtain the sensor chip. Wherein the base electrode includes: a reference electrode and a working electrode. The working electrode may employ a hydrogen ion sensitive polymer such as polyaniline. The reference electrode may be an Ag/AgCl electrode. The sweat PH voltage signal changes with changes in sweat PH.
Specifically, a lower insulating layer is spin-coated on a copper foil, and the lower insulating layer is connected with a metal layer substrate. And sputtering a titanium layer on the copper foil, and sputtering a gold layer on the titanium layer. And electroplating the reference electrode on the gold layer. And manufacturing a working electrode, the magnetic type output interface and the horseshoe-shaped line by utilizing a photoetching technology and various etching liquids. And manufacturing an upper insulating layer on the horseshoe-shaped line. And stripping the base electrode, the magnetic suction type output interface, the horseshoe-shaped line, the lower insulating layer and the upper insulating layer from the metal layer substrate.
(IV) if the sensing chip is a perspiration amount sensing chip, making the sensing chip, including:
the sensor chip comprises a basic electrode, a magnetic type output interface, a U-shaped line and a magnetic type output interface, wherein the U-shaped line is used for manufacturing the basic electrode, the magnetic type output interface and connecting the basic electrode and the magnetic type output interface to obtain the sensor chip. Wherein the base electrode includes: a reference electrode and a working electrode.
The perspiration sensor chip may be a resistive sensor chip or a capacitive sensor chip. The resistance-type sensing chip converts the humidity change into resistance value change, and materials sensitive to humidity are used as electrodes, such as ceramics, polymers and the like; the capacitance sensing chip converts the humidity change into the capacitance change, the dielectric coefficient of the dielectric is changed in a function way along with the humidity change, and a proper dielectric material needs to be selected as an electrode, such as polymers such as ceramics, polyamide and the like.
Specifically, a lower insulating layer is coated on a copper foil in a spin mode, and the lower insulating layer is connected with a metal layer substrate; sputtering a titanium layer on the copper foil, and sputtering a gold layer on the titanium layer; electroplating the reference electrode on the gold layer; manufacturing the basic electrode, the magnetic type output interface and the horseshoe-shaped line except the reference electrode by utilizing photoetching technology and a plurality of etching solutions; manufacturing an upper insulating layer on the horseshoe-shaped line; and stripping the base electrode, the magnetic suction type output interface, the horseshoe-shaped line, the lower insulating layer and the upper insulating layer from the metal layer substrate.
(V) if the sensing chip is the epidermis temperature sensing chip, make the said sensing chip, including: the magnetic type output interface and the horseshoe-shaped line connected with the magnetic type output interface are manufactured to obtain the sensing chip. The line width of the epidermis temperature sensing chip part can be 20 microns, and the resistance value of the electric wire of the epidermis temperature sensing chip part changes along with the change of the epidermis temperature of a human body.
Specifically, a lower insulating layer is spin-coated on a copper foil, and the lower insulating layer is connected with a metal layer substrate. And sputtering a titanium layer on the copper foil, and sputtering a gold layer on the titanium layer. And manufacturing the magnetic type output interface and the horseshoe-shaped line by utilizing a photoetching technology and various etching liquids. And stripping the base electrode, the magnetic suction type output interface, the horseshoe-shaped line, the lower insulating layer and the upper insulating layer from the metal layer substrate.
It should be noted that, in the process of using the skin temperature sensing chip, the flexible thin film battery in the flexible signal processing and transmitting circuit is required to supply power, and after the skin temperature of a person changes, the resistance value of the skin temperature sensing chip also changes, so that the skin temperature sensing chip can output a skin temperature voltage signal in real time.
Step S104, transferring each sensing chip to the flexible extensible substrate, and arranging the hydrophilic open-pore silica gel sponge on the top of each sensing chip.
As shown in fig. 7, before each of the sensor chips is transferred onto the flexible and extensible substrate 16, silica is evaporated on the lower insulating layer of each of the sensor chips by using an electron beam, and then each of the sensor chips is bonded onto the flexible and extensible substrate containing a thin PDMS layer, which is treated by ultraviolet ozone. The flexible, malleable substrate may carry the electrochemical and bioelectrical reactions that take place between the sensing chip and sweat.
Fig. 8 is a cross-sectional view of a sweat monitoring sensor patch according to an embodiment of the present invention, in which a PDMS thin layer 26 is disposed on a flexible and extensible substrate 16, the PDMS thin layer 26 is connected to a sensor chip 27 through silicon dioxide, and a hydrophilic open-cell silicone sponge 28 is disposed on the sensor chip 27.
In the embodiment of the invention, after the sweat monitoring and sensing patch is worn on a human body, the hydrophilic open-cell silica gel sponge on each sensing chip absorbs sweat and conveys the sweat to the sensing chip, and the sodium ion sensing chip 18 outputs a sodium ion content voltage signal in real time after contacting the sweat; after the potassium ion sensing chip 17 contacts sweat, a potassium ion content voltage signal is output in real time; after the calcium ion sensing chip 20 is contacted with sweat, a calcium ion content voltage signal is output in real time; after the chloride ion sensing chip 19 is contacted with sweat, a chloride ion content voltage signal is output in real time; after the glucose sensing chip 23 is contacted with sweat, a glucose content current signal is output in real time; after the lactic acid sensing chip 24 is contacted with sweat, a lactic acid content current signal is output in real time; after the sweat pH value sensing chip 22 is contacted with sweat, outputting a sweat pH value voltage signal in real time; after the perspiration quantity sensing chip 21 is contacted with the perspiration, a perspiration quantity voltage signal is output in real time; after the skin temperature sensing chip 25 contacts sweat, a skin temperature voltage signal is output in real time.
In the embodiment of the present invention, the external dimension of each sensor chip may be: 18mm 10mm 5 μm, the overall package size of the sweat monitoring and sensing patch may be: 100mm 50mm 5mm, like this, the overall dimension of sensing chip and sweat monitoring sensing paster is all smaller for sweat monitoring sensing paster has good ductility.
In the embodiment of the invention, each sensing chip is manufactured by using a CMOS processing method, and various sensing chips are transferred to the flexible extensible substrate to obtain the sweat monitoring sensing patch which has small volume, good extensibility and high sensitivity and can be worn on the epidermis of a human body without burden.
In yet another embodiment of the present invention, a sweat monitoring sensing patch of the present invention is described in detail, comprising: the sensor comprises a flexible extensible substrate and a plurality of sensor chips arranged on the flexible extensible substrate, wherein the top of each sensor chip is provided with a hydrophilic open-pore silica gel sponge. The sweat monitoring and sensing patch can be prepared by adopting the preparation method.
The flexible extensible substrate is in contact with the human epidermis and is used for fixing the plurality of sensing chips between the human epidermis and the flexible extensible substrate.
Hydrophilic trompil silica gel sponge be located human epidermis with between the sensing chip, hydrophilic trompil silica gel sponge and human epidermis contact for absorb the sweat of human epidermis, and carry the sweat extremely sensing chip.
The sensing chip is used for outputting a voltage signal or a current signal after contacting sweat.
The hydrophilic open-cell silica gel sponge on each sensing chip absorbs sweat and conveys the sweat to the sensing chip, and the sodium ion sensing chip 18 outputs a sodium ion content voltage signal in real time after contacting the sweat; after the potassium ion sensing chip 17 contacts sweat, a potassium ion content voltage signal is output in real time; after the calcium ion sensing chip 20 is contacted with sweat, a calcium ion content voltage signal is output in real time; after the chloride ion sensing chip 19 is contacted with sweat, a chloride ion content voltage signal is output in real time; after the glucose sensing chip 23 is contacted with sweat, a glucose content current signal is output in real time; after the lactic acid sensing chip 24 is contacted with sweat, a lactic acid content current signal is output in real time; after the sweat pH value sensing chip 22 is contacted with sweat, outputting a sweat pH value voltage signal in real time; after the perspiration quantity sensing chip 21 is contacted with the perspiration, a perspiration quantity voltage signal is output in real time; after the skin temperature sensing chip 25 contacts sweat, a skin temperature voltage signal is output in real time.
In yet another embodiment of the present invention, a sweat monitoring and sensing system as disclosed in embodiments of the present invention is described in detail, comprising: terminal, flexible signal processing transmission circuit and sweat monitoring sensing patch as described in the above embodiments.
The sweat monitoring and sensing patch is connected with the flexible signal processing and transmitting circuit and used for sending the acquired voltage signal and current signal to the flexible signal processing and transmitting circuit.
Wherein the voltage signal may include: sodium ion content voltage signal, potassium ion content voltage signal, calcium ion content voltage signal, chloride ion content voltage signal, sweat PH value voltage signal, perspiration volume voltage signal and epidermis temperature voltage signal. The current signal may include: a glucose content current signal and a lactate content current signal.
The flexible signal processing and transmitting circuit is connected with the terminal and used for receiving the voltage signal and the current signal sent by the sweat monitoring and sensing patch, converting the voltage signal and the current signal into sweat component information and sending the sweat component information to the terminal.
The flexible signal processing and transmitting circuit can wirelessly transmit sweat component information to the terminal through Bluetooth. The flexible signal processing transmission circuit may include: flexible malleable substrates and flexible thin film batteries. The flexible thin film battery can be used for supplying power to the skin temperature sensing chip. The flexible signal processing and transmitting circuit can be connected with each sensing chip through the magnetic type output interface.
Specifically, the processing procedure of the glucose content current signal and the lactate content current signal may be: a two-channel 2: 1 multiplexer or two LMP91000 chips (realized by using a constant potential rectifier and a transimpedance amplifier consisting of an operational amplifier) is used for receiving a glucose content current signal and a lactic acid content current signal, and is controlled by a CC 2541. The CC2541 is a single chip microcomputer integrated with a Bluetooth receiving and sending device, the CC2541 is also used for controlling the ADC to convert a glucose content current signal and a lactic acid content current signal into glucose content information and lactic acid content information respectively, and the CC2541 controls the Bluetooth to transmit the glucose content information and the lactic acid content information to the terminal.
Specifically, to the processing procedure of sodium ion content voltage signal, potassium ion content voltage signal, calcium ion content voltage signal, chloride ion content voltage signal and sweat PH voltage signal, can be: the method comprises the steps of respectively receiving a sodium ion content voltage signal, a potassium ion content voltage signal, a calcium ion content voltage signal, a chloride ion content voltage signal and a sweat pH value voltage signal by utilizing a 5-to-1 multiplexer, amplifying the voltage signals by using an operational amplifier, controlling the ADC by the CC2541 to respectively convert the amplified sodium ion content voltage signal, the amplified potassium ion content voltage signal, the amplified calcium ion content voltage signal, the amplified chloride ion content voltage signal and the amplified sweat pH value voltage signal into sodium ion content information, potassium ion content information, calcium ion content information, chloride ion content information and sweat pH value information, and finally controlling the Bluetooth by the CC2541 to transmit the sodium ion content information, the potassium ion content information, the calcium ion content information, the chloride ion content information and the sweat pH value information to a terminal.
Specifically, the processing procedure of the perspiration discharge voltage signal and the skin temperature voltage signal may be: utilize huygens bridge to measure sweat discharge voltage signal and epidermis temperature voltage signal respectively, CC2541 control ADC converts sweat discharge voltage signal and epidermis temperature voltage signal after measuring into sweat discharge information and epidermis temperature information respectively, then CC2541 control bluetooth with sweat discharge information and epidermis temperature information transmission for the terminal. Preferably, a time interval for receiving the perspiration amount voltage signal may be set, the perspiration rate information may be determined using the perspiration amount information and the time interval, and the CC2541 controls the bluetooth to transmit the perspiration rate information to the terminal.
Wherein the sweat composition information may include: sodium ion content information, potassium ion content information, calcium ion content information, chloride ion content information, sweat pH value information, glucose content information, lactic acid content information, perspiration amount information, and epidermis temperature information. Preferably, the sweat composition information may include: sodium ion content information, potassium ion content information, calcium ion content information, chloride ion content information, sweat pH value information, glucose content information, lactic acid content information, perspiration amount information, epidermis temperature information, and perspiration rate information.
The terminal is used for receiving the sweat component information sent by the flexible signal processing and transmitting circuit, inputting the sweat component information into a model (such as a disease model), and generating analysis data corresponding to the sweat component information.
Illustratively, the terminal may be a desktop computer, a notebook computer, a mobile phone or a tablet computer. Analyzing the data may include: sports, training recommendations, etc.
According to the technical scheme, the sweat monitoring and sensing system, the patch and the preparation method thereof have the following beneficial effects:
(1) in the invention, the preparation method of the sweat monitoring and sensing patch comprises the following steps: preparing a flexible, extensible substrate; manufacturing a hydrophilic open-cell silica gel sponge; manufacturing a plurality of sensing chips; with every sensor chip rendition to flexible extending basement, set up hydrophilic trompil silica gel sponge at every sensor chip's top, during the use, flexible extending basement adsorbs on human skin surface, with a plurality of sensor chip clamp between human skin surface and the flexible extending basement, hydrophilic trompil silica gel sponge and human epidermis contact, absorb human epidermis sweat, carry sweat for sensor chip, sensor chip output physiological parameter index, therefore, can alleviate the technical problem that can't satisfy the demand that wearable was got physiological parameter index from the molecule aspect on the human body in real time and woundlessly, the technological effect that can satisfy the demand that wearable was got physiological parameter index from the molecule aspect on the human body in real time and woundlessly has been reached.
(2) According to the invention, the horseshoe-shaped line is used for connecting the basic electrode and the magnetic type output interface, sharp angles are removed, the pressure concentration effect is avoided, the pressure resistance is improved, the occurrence of short circuit of the connecting line caused by various mechanical factors is reduced, the bending in various directions can be realized, and the extensibility and the practicability are increased;
(3) in the invention, the reference electrodes of the sodium ion sensing chip, the potassium ion sensing chip, the calcium ion sensing chip and the chloride ion sensing chip are connected with the same magnetic-type output interface, and the reference electrodes of the glucose sensing chip and the lactic acid sensing chip are connected with the same magnetic-type output interface, so that the volume of the sweat monitoring and sensing patch can be reduced, the sweat monitoring and sensing patch is easier to wear and move, meanwhile, the manufacturing material is saved, and the cost for manufacturing the sweat monitoring and sensing patch is reduced;
(4) in the invention, the sweat monitoring sensing patch is connected with the flexible signal processing and transmitting circuit through the magnetic type output interface, and the magnetic type output interface can be used for quickly and conveniently realizing connection or disconnection operation, thereby saving the operation time and improving the use efficiency;
(5) the hydrophilic open-cell silica gel sponge prepared by the invention collects sweat by utilizing the capillary action and removes grease, so that a metal electrode is prevented from directly contacting the skin of a human body, and the sweat monitoring efficiency can be improved;
(6) in the invention, each sensing chip is a high-channel integrated chip, and each sensing chip is transferred to the flexible extensible substrate, so that the sweat monitoring sensing patch can simultaneously monitor various physiological parameter indexes of a human body in real time, and the monitoring efficiency and the practicability are improved;
(7) in the invention, each sensing chip is manufactured by using materials such as copper, titanium, gold, silver, polyimide and the like by utilizing a CMOS (complementary metal oxide semiconductor) process, so that the sensing chip has the characteristics of high precision, low power consumption, high speed, high integration level and the like.
The above-mentioned embodiments are intended to illustrate the objects, technical solutions and advantages of the present invention in further detail, and it should be understood that the above-mentioned embodiments are only exemplary embodiments of the present invention, and are not intended to limit the present invention, and any modifications, equivalents, improvements and the like made within the spirit and principle of the present invention should be included in the protection scope of the present invention.

Claims (10)

1. A method for preparing a sweat monitoring sensing patch is characterized by comprising the following steps:
preparing a flexible, extensible substrate;
manufacturing a hydrophilic open-cell silica gel sponge;
manufacturing a plurality of sensing chips;
and transferring each sensing chip to the flexible extensible substrate, and arranging the hydrophilic open-pore silica gel sponge on the top of each sensing chip.
2. The method of manufacturing a sweat monitoring sensor patch according to claim 1, wherein the making of a hydrophilic open-cell silicone sponge comprises:
manufacturing an open-cell sponge matrix by adding platinum catalytic silica gel;
and carrying out surface modification on the open-cell sponge matrix by utilizing a super-hydrophilic coating to obtain the hydrophilic open-cell silica gel sponge.
3. A method of manufacturing a sweat monitoring sensor patch as claimed in claim 1, wherein the plurality of sensor chips include: the sensor comprises a sodium ion sensing chip, a potassium ion sensing chip, a calcium ion sensing chip, a chloride ion sensing chip, a glucose sensing chip and a lactic acid sensing chip; manufacturing the sensing chip, including:
manufacturing a basic electrode, a magnetic type output interface and a horseshoe-shaped line connecting the basic electrode and the magnetic type output interface;
and modifying the working electrode in the basic electrode to obtain the sensing chip.
4. The method of manufacturing a sweat monitoring sensing patch of claim 1 wherein,
the plurality of sensor chips include: a sweat pH value sensing chip and a perspiration amount sensing chip; manufacturing the sensing chip, including: manufacturing a basic electrode, a magnetic type output interface and a horseshoe-shaped line connecting the basic electrode and the magnetic type output interface to obtain the sensing chip; or
The plurality of sensor chips include: a skin temperature sensing chip; manufacturing the sensing chip, including: the magnetic type output interface and the horseshoe-shaped line connected with the magnetic type output interface are manufactured to obtain the sensing chip.
5. The method of manufacturing a sweat monitoring sensor patch of claim 3, wherein the base electrode includes a reference electrode, and the manufacturing of the base electrode, the magnetic-type output interface, and the horseshoe-shaped wire connecting the base electrode and the magnetic-type output interface includes:
spin-coating a lower insulating layer on a copper foil, and connecting the lower insulating layer with a metal layer substrate;
sputtering a titanium layer on the copper foil, and sputtering a gold layer on the titanium layer;
electroplating the reference electrode on the gold layer;
manufacturing the basic electrode, the magnetic type output interface and the horseshoe-shaped line except the reference electrode by utilizing photoetching technology and a plurality of etching solutions;
manufacturing an upper insulating layer on the horseshoe-shaped line;
and stripping the base electrode, the magnetic suction type output interface, the horseshoe-shaped line, the lower insulating layer and the upper insulating layer from the metal layer substrate.
6. The method of manufacturing a sweat monitoring sensor patch according to claim 3, wherein if the sensor chip is the sodium ion sensor chip, the potassium ion sensor chip, the calcium ion sensor chip or the chloride ion sensor chip, the modification of the working electrode in the base electrode to obtain the sensor chip comprises:
manufacturing a conductive organic polymer electron transfer layer on the working electrode;
configuring an ion-selective membrane with an ion-selective carrier, a membrane matrix, a plasticizer, and an ion exchanger;
disposing the ion-selective membrane onto the conductive organic polymer electron transfer layer.
7. The method of manufacturing a sweat monitoring sensor patch according to claim 3, wherein if the sensor chip is the glucose sensor chip or the lactate sensor chip, the modifying the working electrode of the base electrode to obtain the sensor chip comprises:
manufacturing an electron transfer layer on the working electrode;
dripping an oxidase solution on the electron transfer layer, standing and airing to form an oxidase layer;
and manufacturing an active substance protection layer on the oxidase layer.
8. The method of manufacturing a sweat monitoring sensor patch according to claim 5, wherein the reference electrodes of the sodium ion sensor chip, the potassium ion sensor chip, the calcium ion sensor chip, and the chloride ion sensor chip are connected to a same magnetic-type output interface, and the reference electrodes of the glucose sensor chip and the lactate sensor chip are connected to a same magnetic-type output interface.
9. A sweat monitoring sensing patch, comprising:
a flexible, extensible substrate;
a plurality of sensor chips located on the flexible malleable substrate; and
a hydrophilic open-cell silicone sponge on top of each of the sensor chips.
10. A sweat monitoring sensing system, comprising: a terminal, a flexible signal processing transmission circuit, and the sweat monitoring sensor patch of claim 9; wherein,
the sweat monitoring and sensing patch is connected with the flexible signal processing and transmitting circuit and is used for sending the signals monitored by the sweat monitoring and sensing patch to the flexible signal processing and transmitting circuit;
the flexible signal processing and transmitting circuit is connected with the terminal and is used for receiving the signal sent by the sweat monitoring and sensing patch, converting the signal into sweat component information and sending the sweat component information to the terminal;
and the terminal is used for receiving and analyzing the sweat component information sent by the flexible signal processing and transmitting circuit.
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