CN109717864B - Fabric electrode and intelligent electrocardio-coat - Google Patents
Fabric electrode and intelligent electrocardio-coat Download PDFInfo
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- CN109717864B CN109717864B CN201910155491.XA CN201910155491A CN109717864B CN 109717864 B CN109717864 B CN 109717864B CN 201910155491 A CN201910155491 A CN 201910155491A CN 109717864 B CN109717864 B CN 109717864B
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Abstract
The invention provides a method for manufacturing conductive cloth, which comprises the steps of firstly, hot-pressing a textile fabric at a thermal deformation temperature to flatten fibers, and bonding the fibers at a crossed lap joint part, so that the protruding part of the flattened fabric is in a plane; and then plating a conductive layer on the surface of the flattened fabric. The surface of the conductive cloth manufactured by the manufacturing method is a planar conductive layer, and when the conductive cloth is applied to a fabric electrode, the effective area of the conductive cloth in contact with the skin is greatly increased under the same pressure, so that the signal acquisition capability is improved. Meanwhile, fibers at the crossed and overlapped part of the conductive cloth are bonded together, so that the conductive fibers of the conductive cloth cannot be dislocated, and noise cannot be introduced; and the porosity of the conductive cloth is greatly reduced, which is beneficial to moderate sweat building, and further improves the signal acquisition capability on the surface of dry skin. The invention also provides a fabric electrode and an intelligent electrocardio-coat.
Description
Technical Field
The invention relates to the technical field of medical instruments, in particular to a fabric electrode and an intelligent electrocardio coat.
Background
The fabric electrode on the existing intelligent electrocardio-coat is composed of conductive cloth and foam; the traditional conductive cloth is woven by silver-plated fibers and then is woven into the conductive cloth, and the fibers can move in a staggered manner. Because the conductive cloth is of a three-dimensional weaving structure, when the conductive cloth is contacted with the skin, only some raised point-shaped areas of the weaving structure are contacted with the skin, other areas are not actually contacted with the skin, and the signal acquisition capability is low, so that the acquired electrocardiosignals are weak, even no signals exist.
Meanwhile, the fabric electrode can be attached to the skin only by the binding force of the electrocardio-coat, and when the human body moves or the pressure changes, the conductive fibers can be dislocated, so that noise is easily introduced due to the fluctuation of resistance and capacitance. In order to avoid the problems, the prior art mainly increases the tightening degree of the electrocardio-clothes, so that the fabric electrode of the electrocardio-clothes is tightly pressed against the surface of the skin, which causes discomfort to the human body and causes local thrombus risk in severe cases.
Disclosure of Invention
In view of the above, the present invention provides a method for manufacturing a conductive fabric to improve signal acquisition capability.
Another object of the present invention is to provide a fabric electrode and an intelligent electrocardio-coat, so as to improve the signal acquisition capability.
In order to achieve the purpose, the invention provides the following technical scheme:
a method for manufacturing conductive cloth comprises the following steps:
hot pressing the woven fabric at a heat distortion temperature to flatten the fibers and bonding the fibers at the cross lap joint, so that the protruding part of the flattened fabric is in a plane;
and plating a conductive layer on the surface of the flattened fabric.
According to the technical scheme, the manufacturing method of the conductive cloth provided by the invention comprises the steps of firstly, carrying out hot pressing on a woven fabric at a thermal deformation temperature to flatten fibers, and bonding the fibers at a crossed lap joint part, so that the protruding part of the flattened fabric is in a plane; and then plating a conductive layer on the surface of the flattened fabric.
The surface of the conductive cloth manufactured by the manufacturing method is a planar conductive layer, and when the conductive cloth is applied to a fabric electrode, the effective area of the conductive cloth in contact with the skin is greatly increased under the same pressure, so that the signal acquisition capability is improved.
Meanwhile, fibers at the crossed and overlapped part of the conductive cloth are bonded together, so that the conductive fibers of the conductive cloth cannot be dislocated, and noise cannot be introduced; and the porosity of the conductive cloth is greatly reduced, which is beneficial to moderate sweat building, and further improves the signal acquisition capability on the surface of dry skin.
In addition, the area of the plane conducting layer of the conducting cloth manufactured by the invention is constant, and cannot be changed along with the contact distance between the conducting cloth and the skin, so that the influence of the binding pressure change (such as the pressure change during the movement and the respiration of a human body) of the electrocardio-coat on the signal acquired by the conducting cloth is small, and the acquired electrocardio-signal is prevented from generating larger noise and clutter.
The invention also provides a fabric electrode which comprises conductive cloth and a non-conductive elastic pressing layer arranged on the non-collection surface of the conductive cloth, wherein the conductive cloth comprises fabric with plane protruding parts and a conductive layer plated on the surface of the fabric.
Preferably, the fabric electrode further comprises a non-conductive fabric surrounding the conductive fabric and the non-conductive elastic laminate, and the non-conductive fabric is fixed to the fabric tape.
Preferably, the fabric electrode further comprises a flexible support structure surrounding the non-conductive cloth.
Preferably, in the fabric electrode, the flexible support structure is a flexible support ring, and the flexible support ring includes:
flexible silicone rubber;
and one end of the flexible framework is fixedly connected with the flexible silicon rubber, and the other end of the flexible framework penetrates through the non-conductive cloth and is used for being fixed on the fabric belt.
Preferably, in the above fabric electrode, the flexible skeleton includes:
an annular plate;
the hollow rectangular bulges are uniformly arranged on one surface of the annular plate and are integrally formed with the flexible silicon rubber in an injection molding mode;
the columnar protrusions are evenly arranged on the other surface of the annular plate, and the non-conductive cloth is provided with mounting holes for the columnar protrusions to penetrate through.
Preferably, in the fabric electrode, one end of the flexible silicon rubber, which is close to the collection surface of the conductive cloth, is provided with a plurality of pressure-bearing protrusions.
Preferably, in the fabric electrode, one side of the conductive cloth is provided with a conductive insertion sheet for transmitting a collected signal, the conductive insertion sheet is parallel to the collection surface of the conductive cloth, and the outer side of the conductive insertion sheet is provided with an insulating protection layer.
Preferably, in the fabric electrode, the non-conductive elastic laminate is an elastic sponge.
According to the technical scheme, the fabric electrode comprises conductive cloth and a non-conductive elastic pressing layer arranged on the non-collecting surface of the conductive cloth, wherein the conductive cloth comprises fabric with plane protruding parts and a conductive layer plated on the surface of the fabric.
The surface of the conductive cloth of the fabric electrode is the planar conductive layer, so that the contact effective area of the conductive cloth and the skin is greatly increased under the same pressure, and the signal acquisition capacity is improved.
Meanwhile, fibers at the crossed and overlapped part of the conductive cloth are bonded together, so that the conductive fibers of the conductive cloth cannot be dislocated, and noise cannot be introduced; and the porosity of the conductive cloth is greatly reduced, which is beneficial to moderate sweat building, and further improves the signal acquisition capability on the surface of dry skin.
In addition, because the area of the plane conducting layer of the conducting cloth is constant and cannot be changed along with the contact distance between the conducting cloth and the skin, the influence of the binding pressure change (such as the pressure change during the movement and the breathing of a human body) of the electrocardio-coat on the signal collected by the conducting cloth is small, and the collected electrocardio-signal is prevented from generating larger noise and clutter.
The invention also provides the intelligent electrocardio-coat, which comprises a fabric belt and fabric electrodes arranged on the fabric belt, wherein the fabric electrodes are any one of the fabric electrodes, and the fabric electrodes have the effects, so that the intelligent electrocardio-coat with the fabric electrodes has the same effects, and the details are not repeated herein.
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 introduced below, and it is obvious that the drawings in the following description are some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to these drawings without creative efforts.
Fig. 1 is a perspective view of a conductive fabric according to an embodiment of the present invention;
fig. 2 is a side view of a conductive cloth provided in an embodiment of the present invention;
FIG. 3 is a schematic front view of a fabric electrode mounted on a fabric strip in accordance with an embodiment of the present invention;
FIG. 4 is a schematic view of the back side of a fabric electrode provided in an embodiment of the present invention when mounted on a fabric strip;
FIG. 5 is a cross-sectional view of a fabric electrode provided in accordance with an embodiment of the present invention as installed in a fabric strip;
FIG. 6 is a partially enlarged structural view of FIG. 5;
FIG. 7 is an exploded view of a fabric electrode provided in accordance with an embodiment of the present invention as installed in a fabric strip;
fig. 8 is a schematic diagram of a back structure of a non-conductive fabric provided in an embodiment of the present invention;
FIG. 9 is a schematic structural diagram of the front side of a flexible silicone rubber provided by an embodiment of the present invention;
fig. 10 is a schematic structural view of the back side of a flexible silicone rubber provided by an embodiment of the present invention;
FIG. 11 is a schematic front view of a ductile metallic skeleton according to an embodiment of the present invention;
FIG. 12 is a schematic diagram of a back side structure of a ductile metallic skeleton according to an embodiment of the present invention;
fig. 13 is a schematic structural view of a heat-sealing screw cap according to an embodiment of the present invention.
Detailed Description
The embodiment of the invention provides a manufacturing method of conductive cloth, which improves the signal acquisition capability.
In order to make the objects, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious 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 manufacturing method of the conductive cloth provided by the embodiment of the invention comprises the steps of hot-pressing a textile fabric at a thermal deformation temperature to flatten fibers, and bonding the fibers at a crossed lap joint part, so that the protruding part of the flattened fabric is in a plane; and then plating a conductive layer on the surface of the flattened fabric.
The plated conductive layer may be silver plated, or plated with another conductive coating.
As shown in fig. 1-2, the surface of the conductive cloth 1 manufactured by the manufacturing method is a planar conductive layer, and when the conductive cloth 1 is applied to a fabric electrode, the effective area of the conductive cloth 1 contacting with the skin is greatly increased under the same pressure, so that the signal acquisition capability is improved.
Meanwhile, fibers at the crossed and overlapped part of the conductive cloth 1 are bonded together, so that the conductive fibers of the conductive cloth 1 cannot be dislocated, and noise cannot be introduced; and the porosity of the conductive cloth 1 is greatly reduced, which is beneficial to moderate sweat building, and further improves the signal acquisition capability on the surface of dry skin.
In addition, because the area of the plane conducting layer of the conducting cloth 1 manufactured by the invention is constant and can not change along with the contact distance between the conducting cloth 1 and the skin, the influence of the binding pressure change (such as the pressure change during the movement and the breathing of a human body) of the electrocardio-coat on the signal acquired by the conducting cloth 1 is small, and the acquired electrocardio-signal is prevented from generating larger noise and clutter.
Referring to fig. 1-13, the embodiment of the present invention further provides a fabric electrode, which includes a conductive fabric 1 and a non-conductive elastic pressing layer disposed on a non-collecting surface (a surface far from the skin, often called a back surface) of the conductive fabric 1, where the conductive fabric 1 includes a fabric having a planar protruding portion and a conductive layer plated on a surface of the fabric.
The non-conductive elastic pressure layer is preferably an elastic sponge 6 for providing necessary elasticity, but may be an elastic rubber or the like for providing elastic pressure to the conductive cloth 1 to press the conductive cloth 1 against the skin.
The surface of the conductive cloth 1 of the fabric electrode is a planar conductive layer, so that the effective area of the conductive cloth 1 contacted with the skin is greatly increased under the same pressure, and the signal acquisition capability is improved.
Meanwhile, fibers at the crossed and overlapped part of the conductive cloth 1 are bonded together, so that the conductive fibers of the conductive cloth 1 cannot be dislocated, and noise cannot be introduced; and the porosity of the conductive cloth 1 is greatly reduced, which is beneficial to moderate sweat building, and further improves the signal acquisition capability on the surface of dry skin.
In addition, because the area of the plane conducting layer of the conducting cloth 1 is constant and cannot be changed along with the contact distance between the conducting cloth 1 and the skin, the influence of the binding pressure change (such as the pressure change during the movement and the breathing of a human body) of the electrocardio-coat on the signal collected by the conducting cloth 1 is small, and the collected electrocardio-signal is prevented from generating larger noise and clutter.
In order to optimize the above technical solution, the fabric electrode further comprises a non-conductive cloth 2 surrounding the conductive cloth 1 and the non-conductive elastic laminate, the non-conductive cloth 2 being used to be fixed on the fabric tape 4, as shown in fig. 7 to 8. Specifically, the conductive cloth 1 and the non-conductive cloth 2 are fixed together by hot melt adhesive.
According to the invention, the non-conductive cloth 2 is added around the conductive cloth 1, so that the deformation area caused by the change of the binding pressure of the electrocardio-coat is positioned in the non-conductive cloth 2 area of the outer ring, and the conductive cloth 1 area of the middle part is not influenced by the binding pressure, thereby ensuring that the shape of the conductive area of the electrode and the contact area of the conductive area and the skin are unchanged, and avoiding the introduction of signal noise.
Preferably, the non-conductive cloth 2 has elasticity, and when the non-conductive cloth 2 is under pressure, the non-conductive cloth 2 deforms elastically, so that the bonding force generated on the conductive cloth 1 is small, and the constancy of the area of the conductive cloth 1 is further improved.
It will be appreciated that the non-conductive cloth 2 may also be non-elastic. The non-conductive cloth 2 may have other structures, such as a non-conductive elastic cylinder.
Further, the fabric electrode also comprises a flexible support structure surrounding the non-conductive cloth 2, as shown in fig. 3. According to the invention, a circle of flexible supporting structure is added on the periphery of the non-conductive cloth 2, so that when the binding pressure of the electrocardio-garment changes, the pressure borne by the conductive cloth 1 in the flexible supporting structure is almost unchanged (only the pressure provided by the elastic sponge 6 at the back is borne) through pressure bearing, thus the contact pressure and the contact area of the conductive cloth 1 of the fabric electrode and the skin are constant, the signal sensitivity is further enhanced, and the introduction of noise is reduced.
Meanwhile, the flexible supporting structure has the functions of anti-slip and edge supporting, the stability of the fabric electrode is improved, and the acquisition accuracy of electrode signals is further ensured.
In a preferred embodiment, the flexible supporting structure is a flexible supporting ring, the flexible supporting ring comprises a flexible silicon rubber 3 and a flexible skeleton 7, one end of the flexible skeleton 7 is fixedly connected with the flexible silicon rubber 3, and the other end of the flexible skeleton 7 penetrates through the non-conductive cloth 2 and is used for being fixed on the fabric belt 4.
The flexible silicon rubber 3 is used for bearing the tightening pressure of the fabric belt 4 of the electrocardio-suit, plays a role in supporting, enables the pressure of the conductive area inside the fabric belt 4 to be relatively constant, and avoids the influence of the fluctuation of the tightening pressure of the fabric belt 4 on the contact area and the contact distance between the conductive cloth 1 and the skin.
The flexible framework 7 is used for fixing the flexible silicon rubber 3 and the non-conductive cloth 2 on the fabric belt 4, so that the flexible silicon rubber and the non-conductive cloth are prevented from falling off in use or washing, and meanwhile, the flexible framework also plays a role in fixing the fabric electrode.
In the embodiment, the fabric electrode is supported by the flexible support ring, so that the structure is simpler and the support strength is better. Of course, the flexible supporting structure can also be formed by splicing a plurality of supporting plates.
As shown in fig. 6, 11-12, the ductile metallic skeleton 7 comprises an annular plate 71; a plurality of hollow rectangular protrusions 73 uniformly arranged on one surface of the annular plate 71, the hollow rectangular protrusions 73 and the flexible silicone rubber 3 being molded integrally by injection; a plurality of stud protrusions 72 uniformly provided on the other face of the annular plate 71, and the non-conductive cloth 2 is provided with mounting holes 21 through which the stud protrusions 72 pass.
The toughness skeleton 7 of this embodiment moulds plastics integrated into one piece through protruding 73 of cavity rectangle and flexible silicon rubber 3, has improved toughness skeleton 7 and flexible silicon rubber 3's joint strength, and of course, the protruding 73 of cavity rectangle can also be replaced by cylindrical protrusion etc. toughness skeleton 7 and flexible silicon rubber 3 also can adopt the joint to fix.
Meanwhile, the columnar protrusions 72 of the flexible framework 7 penetrate through the mounting holes 21 of the non-conductive cloth 2 and are fixed on the fabric belt 4 through the heat-seal nuts 5, as shown in fig. 4 and 7, the structure is simple, the assembly and disassembly are convenient, and the fabric electrode can be reused and washed by water. Of course, the flexible framework 7 and the non-conductive cloth 2 can also be fixed together by means of adhesion. The invention can also fix the flexible framework 7 on the non-conductive cloth 2, and fix the non-conductive cloth 2 on the fabric belt 4 by means of snap fasteners, thread gluing and the like.
In order to bear pressure and improve the anti-skid property, one end of the flexible silicon rubber 3 close to the collection surface of the conductive cloth 1 is provided with a plurality of pressure-bearing bulges 31. As shown in fig. 9 to 10, the pressure-bearing protrusions 31 are rectangular protrusions and are uniformly distributed along the circumferential direction of the non-conductive cloth 2, and when the pressure-bearing protrusions 31 are applied, the pressure-bearing protrusions 31 abut against the skin, so that good anti-skid property is ensured. Of course, the skin-contacting surface of the flexible silicone rubber 3 may also be a unitary flat surface.
Preferably, one side of the conductive cloth 1 is provided with a conductive insertion sheet 11 for transmitting the collected signal, the conductive insertion sheet 11 is parallel to the collection surface of the conductive cloth 1, and the outer side of the conductive insertion sheet 11 is provided with an insulating protection layer 8. The insulating protective layer 8 can prevent the electric leakage or water leakage of the conducting wire area of the conductive cloth 1, and improve the working reliability.
According to the invention, the conductive insertion sheet 11 is in the lateral direction, the conductive insertion sheet 11 is parallel to the collection surface of the conductive cloth 1, so that uneven pressure of the conductive cloth 1 on the skin caused by the conductive insertion sheet 11 can be avoided, and the collection accuracy of electrode signals is further improved.
The embodiment of the invention further provides an intelligent electrocardio-coat, which comprises a fabric belt 4 and a fabric electrode arranged on the fabric belt 4, wherein the fabric electrode is the fabric electrode provided by any one of the embodiments, so that the signal acquisition capability is improved.
The fabric tape 4 is used for carrying the fabric electrode and is tightened on the body of the user.
The embodiments in the present description are described in a progressive manner, each embodiment focuses on differences from other embodiments, and the same and similar parts among the embodiments are referred to each other.
The previous description of the disclosed embodiments is provided to enable any person skilled in the art to make or use the present invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other embodiments without departing from the spirit or scope of the invention. Thus, the present invention is not intended to be limited to the embodiments shown herein but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.
Claims (7)
1. A fabric electrode comprising:
the conductive fabric comprises a fabric with a plane protruding part and a conductive layer plated on the surface of the fabric;
the non-conductive cloth is wrapped around the conductive cloth and the non-conductive elastic pressing layer and is used for being fixed on the fabric belt;
a flexible support structure surrounding the non-conductive cloth.
2. The fabric electrode of claim 1, the flexible support structure being a flexible support ring comprising:
flexible silicone rubber;
and one end of the flexible framework is fixedly connected with the flexible silicon rubber, and the other end of the flexible framework penetrates through the non-conductive cloth and is used for being fixed on the fabric belt.
3. The fabric electrode of claim 2, the malleable skeleton comprising:
an annular plate;
the hollow rectangular bulges are uniformly arranged on one surface of the annular plate and are integrally formed with the flexible silicon rubber in an injection molding mode;
the columnar protrusions are evenly arranged on the other surface of the annular plate, and the non-conductive cloth is provided with mounting holes for the columnar protrusions to penetrate through.
4. The fabric electrode according to claim 2, wherein one end of the flexible silicon rubber close to the collection surface of the conductive cloth is provided with a plurality of pressure-bearing protrusions.
5. The fabric electrode according to claim 1, wherein one side of the conductive cloth is provided with a conductive insert sheet for transmitting a collected signal, the conductive insert sheet is parallel to the collection surface of the conductive cloth, and the outer side of the conductive insert sheet is provided with an insulating protection layer.
6. The fabric electrode of any of claims 1-5, said non-conductive elastic laminate being an elastic sponge.
7. An intelligent electrocardio-coat comprising a fabric strip and a fabric electrode arranged on the fabric strip, wherein the fabric electrode is the fabric electrode as claimed in any one of claims 1 to 6.
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| CN201910155491.XA CN109717864B (en) | 2019-03-01 | 2019-03-01 | Fabric electrode and intelligent electrocardio-coat |
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| CN201910155491.XA CN109717864B (en) | 2019-03-01 | 2019-03-01 | Fabric electrode and intelligent electrocardio-coat |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN110464331A (en) * | 2019-09-03 | 2019-11-19 | 上海定九康科技股份有限公司 | A kind of electrode slice and the close-fitting object wearing device with electrode slice |
| CN111657930A (en) * | 2020-05-21 | 2020-09-15 | 无锡驰枫信息技术有限公司 | Fabric electrode and intelligent electrocardio-coat |
| WO2022134081A1 (en) * | 2020-12-25 | 2022-06-30 | 深圳市韶音科技有限公司 | Device and method for collecting and processing electromyographic signal |
| CN113380941B (en) * | 2021-06-07 | 2022-07-26 | 北京航空航天大学 | Out-of-plane thermoelectric device with stretchable porous structure |
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| CN101153462B (en) * | 2006-09-28 | 2011-04-13 | 福懋兴业股份有限公司 | Method for manufacturing elastic conductive cloth |
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