WO2020138563A1

WO2020138563A1 - Band type fabric sensor and manufacturing method therefor

Info

Publication number: WO2020138563A1
Application number: PCT/KR2018/016871
Authority: WO
Inventors: 소주희; 유의상; 임대영; 김은주; 이현경; 이재경
Original assignee: 한국생산기술연구원
Priority date: 2018-12-28
Filing date: 2018-12-28
Publication date: 2020-07-02

Abstract

Disclosed are a band type fabric sensor, which is one type of body-attachable sensor, and a manufacturing method therefor. The band type fabric sensor comprises: a band type base fabric manufactured by using dielectric yarn; gauze disposed on the base fabric and made of conductive yarn or yarn in which conductive particles are dispersed; a polymeric material disposed on the base fabric and covered by the gauze; and a sensing circuit for sensing a change in resistance according to a change in volume when the volume of the polymeric material is changed as the polymeric material is wetted by liquid containing body fluid and thus acidity (pH) or temperature is changed.

Description

Band type fabric sensor and its manufacturing method

An embodiment of the present invention relates to a body-mounted sensor, and more particularly, to a band-type fabric sensor and a method of manufacturing the same.

Biosignal measurement technology through a body-mounted sensor is leading research on the development of sensors made of stretchable materials and circuits to meet human skin characteristics.

However, currently, body-mounted sensors are being developed mainly for circuit board and electronic device packaging technology, antenna and communication technology, materials and detachable technology, but there are difficulties in solving problems of elasticity, flexibility, and mass production technology.

As such, there is a great need for a body-mountable sensor that satisfies elasticity and flexibility and is easy to mass-produce.

The present invention is to solve the problems of the prior art described above, a band-type fabric sensor and a method of manufacturing the electrode material in a body fluid-sensitive polymer material by using a material in which conductive particles or conductive particles are dispersed can be arranged regularly The purpose is to provide.

Another object of the present invention is to provide a band-type fabric sensor and a method of manufacturing the same, which have flexibility and elasticity by using a disposable bandage structure widely used for wound protection, and can be easily attached and detached and easily applied to a mass production process.

Band-type fabric sensor according to an aspect of the present invention for solving the above technical problem, a base fabric in the form of a band manufactured using a dielectric constant yarn; Gauze made of a yarn disposed on the base fabric and having conductive yarns or conductive particles dispersed therein; A polymer material disposed on the base fabric and covered by the gauze; And a sensing circuit that senses a change in resistance according to the change in volume when the volume changes as the acidity (ph) or temperature changes because the polymer material is wetted by a liquid containing body fluid.

In one embodiment, the electrode material made of a material in which conductive particles or conductive particles are dispersed is uniformly arranged in a body fluid-sensitive polymer material. The regular arrangement includes, but is not limited to, regular spacing, regular grid arrangement, and the like, and may have various bends depending on the gauze weaving method or material. However, in any case, the average density or injection amount per unit area of the electrode material of the gauze may have a deviation below a certain level. That is, the average density or injection amount per unit area of the electrode material of the gauze may be significantly the same within the error range.

In one embodiment, the polymer material may include a hydrogel. The hydrogel may have an average diameter of 0.1 mm or more and 1 mm or less.

In one embodiment, the gauze may have a density in which the contact amount of adjacent conductive yarns or adjacent yarns increases according to a pressing change of the polymer material according to the change in volume. The density of the gauze is less than 1/3 of the base fabric on the basis of a densimeter and may have a number of threads of 10 or less in 1 cm in diameter.

In one embodiment, the gus may have at least a double weave structure or a multi-layer structure in which a plurality of layers overlap. The material of the gauze may be cotton, silk, rayon or a combination thereof.

In one embodiment, the length of the base fabric may be less than 20 cm and the width may be less than 5 cm.

In one embodiment, the conductive particles may include carbon black, carbon nanobubbles, metal particles, metal fibers, graphene, or a combination thereof.

A method of manufacturing a band-type fabric sensor according to another aspect of the present invention for solving the above technical problem comprises: preparing a base fabric in a band form manufactured using a dielectric constant yarn and having wiring; Attaching an electronic element to the base fabric and connecting one end of the wiring; Preparing gauze in which electrode materials made of a material in which conductive particles or conductive particles are dispersed are uniformly arranged on average; Joining an edge to the base fabric, leaving a portion of the edge of the gauze to surround the central portion of one surface of the base fabric and to be connected to the other end of the wiring; And inserting a polymer material whose volume changes as the acidity (ph) or temperature changes by being wetted by a liquid containing body fluid through the portion of the gauze and blocking the portion of the electronic device. Senses the change in resistance according to the change in volume.

In one embodiment, the bonding step may include a process of stitching with a conductive fiber and coating with a hot melt so that the other end of the wiring and the yarn in which the conductive particles or conductive particles are dispersed are electrically connected to each other.

In one embodiment, the sensing circuit may be implemented to calculate a resistance change by Young's modulus, bulk modulus, or a combination thereof.

Using the above-described band-type fabric sensor and its manufacturing method, it is possible to manufacture a sensor that responds to bodily fluids emitted from the skin with a simple configuration and material, and has an advantage of being easily introduced into a mass production process. For reference, prior art techniques for measuring a biosignal in the skin have had difficulties in device packaging, desorption, and mass production process technology development, but the present invention can solve the problems of such prior arts.

In addition, according to the present invention, it is possible to provide a band-type fabric sensor that can be widely applied to the health care and medical fields, and can be effectively utilized for measuring bio signals measurable in the skin and wound healing, continuous monitoring of the wound healing process There is an advantage.

1 is a plan view of a band-type fabric sensor according to an embodiment of the present invention.

FIG. 2 is a cross-sectional view of the banded fabric sensor of FIG. 1.

FIG. 3 is a cross-sectional view of a material in which conductive yarns or conductive particles are dispersed in the band-type fabric sensor of FIG. 1.

FIG. 4 is a partial side view of a conductive material that can be used in the band-type fabric sensor of FIG. 1.

5 is a block diagram of an electronic device that can be used in the band-type fabric sensor of FIG. 1.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings.

1 is a plan view of a band-type fabric sensor according to an embodiment of the present invention. FIG. 2 is a cross-sectional view of the banded fabric sensor of FIG. 1. FIG. 3 is a cross-sectional view of a material in which conductive yarns or conductive particles are dispersed in the band-type fabric sensor of FIG. 1. FIG. 4 is a partial side view of a conductive material that can be used in the band-type fabric sensor of FIG. 1. 5 is a block diagram of an electronic device that can be used in the band-type fabric sensor of FIG. 1.

The band-type fabric sensor according to this embodiment includes a base fabric 10, gauze 20, a polymer material 30, and an electronic device 40, as shown in FIG. 1. In the band-type fabric sensor, the gauze 20 and the electronic device 40 are connected through a wiring 50, and an adhesive component may be applied to one end of the base fabric 10.

The length L1 of the base fabric 10 may be less than 20 cm and the width W1 may be less than 5 cm. This is to limit the largest dimension in a typical band form, but a larger size base fabric 10 may be used depending on the application.

The base fabric 10 is manufactured using a dielectric constant yarn. The base fabric 10 may include a wire 50 formed using a conductive yarn or a material (thread) in which conductive particles are dispersed.

The gauze 20 may be disposed on one surface of the base fabric 10 and may be made of a material (thread) in which conductive yarns or conductive particles are dispersed. The conductive particles may include carbon black, carbon nanobubbles, metal particles, metal fibers, graphene, or a combination thereof. In this embodiment, the term'gauze' is a kind of fabric and may be referred to as a conductive fabric.

The electrode material made of a material in which conductive particles or conductive particles are dispersed is uniformly arranged in a body fluid-sensitive polymer material. The regular arrangement includes, but is not limited to, regular spacing, regular grid arrangement, and the like, and may have various bends depending on the gauze weaving method or material. However, in any case, the average density or injection amount per unit area of the electrode material of the gauze may have a deviation below a certain level. That is, the average density or injection amount per unit area of the electrode material of the gauze may be significantly the same within the error range.

In addition, the gauze 20 may be manufactured to have a density in which the contact amount of adjacent conductive yarns or adjacent yarns increases according to a pressing change of the polymer material 30 according to a change in the volume of the polymer material 30. The density of the gauze 20 is smaller than 1/3 of the base fabric 10 based on a densimeter and may have a number of threads of 10 or less in 1 cm in diameter.

In addition, the gauze 20 may be provided with a multilayer structure in which at least a double weave structure or a plurality of

layers

21, 22, and 23 are overlapped (see FIG. 2). The material of the gauze 20 may be cotton, silk, rayon, or a combination thereof.

In addition, the yarn 210 in which conductive yarns or conductive particles contained in the gauze 20 are dispersed is carbon nanotubes or graphene formed by a binder 212 on the surface of the dielectric fiber yarn 211 or carbon fiber as shown in FIG. 3. And dispersion of the fins 213. In addition, the seal 210 (hereinafter, also referred to as a conductive fiber) may further include an additive 214 dispersed with the carbon nanotubes or graphene 213 by the binder 212. The additive 214 may include graphite powder.

In addition, the conductive yarn 220 included in the gauze 20 may have a multifilament form by twisting the dielectric constant yarn 211 and the conductive fiber 210 as illustrated in FIG. 4.

Referring back to FIGS. 1 and 2, the polymer material 30 is disposed at the center of one surface of the base fabric 10 and may be covered by gauze 20. The polymer material 30 changes in volume as the acidity (ph) or temperature changes as the polymer material is wetted by a liquid containing body fluids.

The polymer material 30 may include a hydrogel. The polymer material 30 may have a spherical shape, and may have an average diameter of 0.1 mm or more and 1 mm or less.

The electronic device 40 detects a change in resistance according to a change in volume of the polymer material 30. The electronic device 40 may include a sensing circuit or may correspond to the sensing circuit. The electronic device 40 may include a power supply unit that applies a predetermined voltage to both ends of the gauze 20 through the wiring 50. The electronic device 40 may have a semiconductor chip or module structure or form. The electronic device 40 may include hardware components such as a field programmable gate array (FPGA) and an application specific integrated circuit (ASIC).

The electronic device 40 may include a power supply unit (not shown), a signal detection unit 42, a comparison unit 44, a biosignal processing unit 46, and an output unit 48 as shown in FIG. 5. The power supply unit may apply a predetermined voltage to both the conductive yarns of the gauze 20 and the terminal portions of both sides of the conductive fiber through the wiring 50. The power supply unit may include a battery, a piezoelectric generator, a thermal battery, and the like, and the piezoelectric generator and the thermal battery may be manufactured using carbon fiber.

The signal detection unit 42 is connected between the power supply unit and the gauze 20 and detects a physical quantity (resistance, etc.) according to the volume change of the polymer material 30 covered with the gauze 20. The signal detection unit 42 may include a signal amplification unit for amplifying a physical quantity according to a volume change. The input terminal of the signal detection unit 42 is an input unit of the electronic device 40 and may correspond to at least one of the input terminals of the signal amplification unit.

The comparison unit 44 compares the output signal of the signal detection unit 42 with a reference signal or a reference level.

The bio-signal processing unit 46 may detect a preset bio-signal based on the signal determined through the comparison unit 44 among the detection signals. Using such a biosignal, it is possible to perform wound treatment, continuous monitoring of the wound treatment process, and the like.

In addition, the electronic device 40 may include an output unit 48 for outputting a sensing signal sensed by the signal sensing unit 42 or a biosignal corresponding thereto. The output unit 48 may include a connector, an antenna of a communication subsystem, a display device, and the like. The communication sub-system may include a communication module for wireless communication, and the wireless communication may include short-range wireless communication, mobile communication, and the like.

The connector may be employed by selecting at least one of various existing shapes. The connector may include a universal serial bus (USB). When a connector, a communication subsystem, or the like is used, it is possible to connect a mobile terminal such as a smartphone and display a biosignal or a wound healing process on the screen through an application mounted on the mobile terminal. Of course, the bio-signals can be transmitted to a healthcare server or the like and used to monitor personal health care.

The output unit may be embodied in addition to a connector or a communication subsystem, or implemented as a display element to replace it. In this case, the output unit may be implemented to display a biosignal detected by a liquid crystal display (LED) in a predetermined number or character form Can.

The manufacturing method of the band-type fabric sensor according to the present embodiment described above may be prepared using a dielectric constant yarn and may prepare a band-shaped base fabric having wiring. Then, an electronic device can be attached to the base fabric and one end of the wiring can be connected.

Next, gauze in which electrode materials made of a material in which conductive particles or conductive particles are dispersed are uniformly arranged on average may be prepared.

Next, a part of the edge of the gauze may be left behind and the other edge of the gauze may be bonded to the base fabric, surrounding the central portion of one surface of the base fabric and connecting to the other end of the wiring.

In addition, a polymer material whose volume changes as the acidity (ph) or temperature changes due to wetness with a liquid containing body fluid in the central portion may be inserted through a portion of the gauze and block the portion.

Next, the sensing circuit of the electronic device can detect a change in resistance according to a change in volume of the polymer material. The sensing circuit may be implemented to calculate a resistance change by Young's modulus, bulk modulus, or a combination thereof.

The bonding may include a process in which the other end of the wiring and the material (thread) in which the conductive yarns or conductive particles are dispersed are electrically connected to each other and sewn with a conductive fiber and coated with a hot melt. Of course, depending on the implementation, a connection structure by lockstitch can be used.

On the other hand, in the above-described embodiment, the length in the longitudinal direction is illustrated by exemplifying a shape approximately 4 times larger than the length in the width direction, but the present invention is not limited to such a configuration, and other sizes of squares, squares, triangles, and circles , It can be implemented to have a variety of shapes, such as a half moon, star shape.

The present invention has been described with reference to the embodiment shown in the drawings, but this is only exemplary, and those skilled in the art to which the art belongs can various modifications and equivalent other embodiments from this. Will understand. Therefore, the technical protection scope of the present invention should be defined by the claims.

[Project identification number] IZ180001 / [Ministry name] Government and local governments (Gyeonggi-do) / [Research management agency] Government and local governments (Gyeonggi-do) / [Research project name] Local government consignment research sub-project: Service and R&D / [Research project Name] Development of smart textronics based on intelligent electronic fiber / [Contribution rate] 100% / [Host organization] Korea Institute of Industrial Technology / [Research period] 2017. 01. 01 ~ 2021. 12. 31

[Task identification number] JA180002 / [Ministry name] Government and local governments (Gyeonggi-do) / [Research management agency] Government and local governments (Gyeonggi-do) / [Research project name] Local government consignment research detailed project: Service and R&D / [Research project Name] Development of smart textronics based on intelligent electronic fiber / [Contribution rate] 100% / [Host organization] Korea Institute of Industrial Technology / [Research period] 2017. 01. 01 ~ 2021. 12. 31

Claims

A band-shaped base fabric manufactured using a dielectric constant yarn;

Gauze made of a yarn disposed on the base fabric and having conductive yarns or conductive particles dispersed therein;

A polymer material disposed on the base fabric and covered by the gauze; And

A band-type fabric sensor comprising a sensing circuit that senses a change in resistance according to a change in volume when the volume changes as the acidity (ph) or temperature changes as the polymer material becomes wet by a liquid containing body fluid.
The method according to claim 1,

The polymer material comprises a hydrogel, band-type fabric sensor.
The method according to claim 1,

The average diameter of the hydrogel is 0.1 mm or more, 1 mm or less, band-type fabric sensor.
The method according to claim 1,

The gauze has a density in which the contact amount of adjacent conductive yarns or adjacent yarns increases according to a change in pressure of the polymer material according to a change in the volume, a band-type fabric sensor.
The method according to claim 4,

The density of the gauze is less than 1/3 of the base fabric on a densimeter basis, and a band-type fabric sensor having a number of threads of 10 or less in 1 cm in diameter.
The method according to claim 1,

The guss has at least a double-woven structure, a multi-layered structure of two or more layers in which a plurality of layers overlap, a twill structure or a double-woven structure, a band type fabric sensor.
The method according to claim 1,

The material of the gauze is cotton, silk, rayon or a combination thereof, a band-type fabric sensor.
The method according to claim 1,

The length of the base fabric is less than 20 cm, the width is less than 5 cm, band-type fabric sensor.
The method according to claim 1,

The conductive particles include carbon black, carbon nanobubbles, metal particles, metal fibers, graphene, or a combination thereof, a band-type fabric sensor.
Preparing a base fabric in the form of a band manufactured using a dielectric constant yarn and having wiring;

Attaching an electronic element to the base fabric and connecting one end of the wiring;

Preparing gauze in which electrode materials made of a material in which conductive particles or conductive particles are dispersed are uniformly arranged on average;

Joining an edge to the base fabric, leaving a portion of the edge of the gauze to surround the central portion of one surface of the base fabric and to be connected to the other end of the wiring; And

And inserting a polymer material whose volume changes as the acidity (ph) or temperature changes by being wetted by a liquid containing body fluid through the portion of the gauze and blocking the portion,

The sensing circuit of the electronic device detects a change in resistance according to the change in volume, a method of manufacturing a band-type fabric sensor.
The method according to claim 10,

The bonding step is a method of manufacturing a band-type fabric sensor, wherein the other end of the wiring and the material in which the conductive yarn or conductive particles are dispersed are electrically connected to each other and sewn with a conductive material and coated with a hot melt.