CN116999076A - Wearable myoelectricity sensing device - Google Patents
Wearable myoelectricity sensing device Download PDFInfo
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- CN116999076A CN116999076A CN202210463211.3A CN202210463211A CN116999076A CN 116999076 A CN116999076 A CN 116999076A CN 202210463211 A CN202210463211 A CN 202210463211A CN 116999076 A CN116999076 A CN 116999076A
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- fabric carrier
- wearable
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- 239000004744 fabric Substances 0.000 claims abstract description 142
- 238000004873 anchoring Methods 0.000 claims abstract description 13
- 230000003183 myoelectrical effect Effects 0.000 claims description 50
- 230000005540 biological transmission Effects 0.000 claims description 7
- 210000003205 muscle Anatomy 0.000 abstract description 12
- 230000033001 locomotion Effects 0.000 abstract description 8
- 238000000034 method Methods 0.000 abstract description 8
- 230000008569 process Effects 0.000 abstract description 7
- 230000009471 action Effects 0.000 abstract description 4
- 230000009286 beneficial effect Effects 0.000 abstract description 2
- 238000010586 diagram Methods 0.000 description 12
- 230000003068 static effect Effects 0.000 description 5
- 238000005516 engineering process Methods 0.000 description 4
- 230000003993 interaction Effects 0.000 description 4
- 239000004433 Thermoplastic polyurethane Substances 0.000 description 3
- 238000005259 measurement Methods 0.000 description 3
- 230000000452 restraining effect Effects 0.000 description 3
- 229920002803 thermoplastic polyurethane Polymers 0.000 description 3
- 230000015572 biosynthetic process Effects 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 230000004118 muscle contraction Effects 0.000 description 2
- 230000000149 penetrating effect Effects 0.000 description 2
- 238000012545 processing Methods 0.000 description 2
- 239000004753 textile Substances 0.000 description 2
- 239000000853 adhesive Substances 0.000 description 1
- 230000003042 antagnostic effect Effects 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 229920001971 elastomer Polymers 0.000 description 1
- 239000011521 glass Substances 0.000 description 1
- 238000009940 knitting Methods 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000002232 neuromuscular Effects 0.000 description 1
- 230000008520 organization Effects 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 238000007655 standard test method Methods 0.000 description 1
- 210000004243 sweat Anatomy 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
- 238000012549 training Methods 0.000 description 1
- 239000002759 woven fabric Substances 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/389—Electromyography [EMG]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/251—Means for maintaining electrode contact with the body
- A61B5/256—Wearable electrodes, e.g. having straps or bands
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/263—Bioelectric electrodes therefor characterised by the electrode materials
- A61B5/27—Conductive fabrics or textiles
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/271—Arrangements of electrodes with cords, cables or leads, e.g. single leads or patient cord assemblies
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/296—Bioelectric electrodes therefor specially adapted for particular uses for electromyography [EMG]
Landscapes
- Life Sciences & Earth Sciences (AREA)
- Health & Medical Sciences (AREA)
- Medical Informatics (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Physics & Mathematics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
Abstract
A wearable myoelectricity sensing device comprises a fabric carrier, a fabric electrode and an insulating film. The fabric carrier includes an anchoring structure disposed on a first surface of the fabric carrier and a mesh extending through the fabric carrier. The fabric electrode is disposed on the first surface of the fabric carrier. The insulating film is arranged on the first surface of the fabric carrier and encapsulates the periphery of the fabric electrode, wherein the area of the fabric carrier which is not covered by the insulating film has a first elastic stretching rate, the area of the fabric carrier which is covered by the insulating film has a second elastic stretching rate, and the first elastic stretching rate is larger than the second elastic stretching rate. The wearable myoelectricity sensing device enables the electrodes to be stably kept on the correct muscle groups and not to move in the process of muscle movement, and is beneficial to measuring myoelectricity signals so as to improve the accuracy of action analysis.
Description
Technical Field
The present disclosure relates to a wearable myoelectric sensing device.
Background
In recent years, man-machine interaction has been rapidly developed in the field of exercise rehabilitation as a means of combining various virtual reality technologies, motion sensing technologies, biofeedback technologies, and the like. The method for realizing human-computer interaction by utilizing the electromyographic signal feedback control not only can increase the participation interest of a user through interaction on a human-computer interaction interface in rehabilitation training, but also can track and evaluate the neuromuscular condition of the user by extracting useful information from complex bioelectric signals, thereby improving the rehabilitation efficiency.
The existing myoelectricity sensing device is mostly attached to a user by wearing the electrode. However, when the exercise is actually performed, the electrodes are often displaced due to slipping or stretching deformation of the cloth caused by sweat or muscle contraction, so that the measured myoelectric signals are distorted and cannot be used.
Disclosure of Invention
According to an embodiment of the present invention, there is provided a wearable myoelectric sensing device including a fabric carrier, a fabric electrode, and an insulating film. The fabric carrier includes an anchoring structure disposed on a first surface of the fabric carrier and a mesh extending through the fabric carrier. The fabric electrode is disposed on the first surface of the fabric carrier. The insulating film is arranged on the first surface of the fabric carrier and encapsulates the periphery of the fabric electrode, wherein the area of the fabric carrier which is not covered by the insulating film has a first elastic stretching rate, the area of the fabric carrier which is covered by the insulating film has a second elastic stretching rate, and the first elastic stretching rate is larger than the second elastic stretching rate.
In some embodiments, the first elastic modulus is 130% to 160%.
In some embodiments, the second elastic modulus is 110% to 120%.
In some embodiments, the mesh is distributed between the anchor structures.
In some embodiments, the fabric carrier comprises a first portion and a second portion, the distribution density of the cells in the first portion being greater than the distribution density of the cells in the second portion.
In some embodiments, the anchoring structure is a non-slip yarn woven into the fabric carrier.
In some embodiments, the wearable myoelectric sensing device further comprises a binding band connected to the fabric carrier.
In some embodiments, the wearable myoelectric sensing device further comprises a conductive member disposed on the fabric carrier and coupled to the fabric electrode.
In some embodiments, the wearable myoelectricity sensing device further comprises a wireless transmission module coupled with the conductive member.
In some embodiments, the wearable myoelectric sensing device further comprises a fabric flat cable connecting the fabric electrode and the conductive member, wherein the insulating film covers the fabric flat cable.
The wearable myoelectricity sensing device provided by the invention can solve the problem that the electrode is displaced due to slipping or stretching deformation of cloth in the movement process, so that the electrode can be stably kept on a correct muscle group and cannot move in the movement process of muscles, and the measurement of myoelectricity signals is facilitated, thereby improving the accuracy of action analysis.
Drawings
For a better understanding of the present invention with the objects, features, advantages and embodiments, reference should be made to the accompanying drawings in which:
FIG. 1 is a schematic diagram of a wearable myoelectricity sensing device according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of a wearable myoelectric sensing device according to an embodiment of the present invention when stretched;
FIG. 3A is a graph of electromyographic signals measured while exercising using an embodiment of a wearable electromyographic device of the invention;
FIG. 3B is a graph of electromyographic signals measured while exercising using another wearable myoelectric sensing device;
fig. 4A and fig. 4B are a front view and a wearing schematic diagram, respectively, of another embodiment of the wearable myoelectric sensing device of the present invention;
FIG. 5 is a front view of yet another embodiment of the wearable myoelectric sensing device of the present invention;
FIGS. 6A and 6B are a weave diagram and a loop diagram, respectively, of an embodiment of a fabric carrier in a wearable myoelectric sensing device according to the invention;
fig. 7A and 7B are tissue diagrams of another embodiment of a fabric carrier in a wearable myoelectric sensing device according to the present invention.
[ symbolic description ]
100,200,300 wearable myoelectricity sensing device
110,210,310,400,500 textile support
112,212,312 first surface
120,220,320 anchoring structure
130,230,330,420,550 mesh openings
140,240,340: textile electrode
150,250,350 insulating film
242 first differential electrode pair
244 second differential electrode pair
246 reference electrode
260 conductive member
270 fabric flat cable
280 wireless transmission module
290 binding belt
410 yarn
510 elastic yarn
520 anti-slip yarn
530 float-knitting yarn
540 connecting yarn
P1, P2 target characteristics
N1 noise
U1:basic unit
Detailed Description
The spirit of the present invention will be clearly described in the following drawings and detailed description, and any person having ordinary skill in the art, having knowledge of the preferred embodiments of the present invention, can make changes and modifications by the technology taught by the present invention, without departing from the spirit and scope of the present invention.
The wearable myoelectricity sensing device provided by the invention can solve the problem that the electrode is displaced due to slipping or stretching deformation of cloth in the movement process, so that the electrode can be configured at a correct position, and the accuracy of action analysis is improved.
Referring to fig. 1, a schematic diagram of an embodiment of a wearable myoelectric sensing device according to the present invention is shown. The wearable myoelectric sensing device 100 comprises a fabric carrier 110, a fabric electrode 140, and an insulating film 150, wherein the fabric carrier 110 comprises a plurality of anchor structures 120 disposed on a first surface 112 of the fabric carrier 110, and a plurality of mesh holes 130 penetrating the fabric carrier 110. The fabric electrode 140 is disposed on the first surface 112 of the fabric carrier 110. In detail, the wearable myoelectric sensing device 100 faces the skin of the user with the first surface 112 of the fabric carrier 110, so that the fabric electrode 140 measures the myoelectric signal. The insulating film 150 is disposed on the first surface 112 of the fabric carrier 110 and encapsulates the periphery of the fabric electrode 140. The region of the fabric carrier 110 not covered with the insulating film 150 has a first elastic stretch rate, the region of the fabric carrier 110 covered with the insulating film 150 has a second elastic stretch rate, and the first elastic stretch rate is greater than the second elastic stretch rate.
Referring to fig. 1 and fig. 2, fig. 2 is a schematic diagram of a wearable myoelectric sensing device according to an embodiment of the invention when stretched. When the wearable myoelectric sensing device 100 is worn for exercise, the user may experience a phenomenon of muscle contraction/elongation during muscle exertion, and the fabric carrier 110 is deformed accordingly, as shown in fig. 2. At this time, the anchor structure 120 disposed on the first surface 112 of the fabric carrier 110 may grip the skin of the user to maintain its relative position with the skin, thereby making the wearable myoelectric sensing device 100 less prone to loosening. In other words, even if the skin of the user is deformed by the stretching of the muscles, the anchor structure 120 is held at a specific position with respect to the skin and the fabric carrier 110 is deformed by an equal amount in the direction in which the skin stretches.
In some embodiments, anchor structure 120 is a structure having a high coefficient of static friction. For example, the fabric carrier 110 provided with the anchoring structures 120 was tested with a glass sheet inclined 20 degrees, a cloth sample 10cm×10cm, an upper weight of 155g, and a maximum static friction coefficient of the anchoring structures 120 measured between 0.45 and 0.50. If the maximum coefficient of static friction of the anchoring structure 120 is less than 0.45, the anchoring structure 120 may lose the effect of grasping the skin of the user, whereas if the maximum coefficient of static friction of the anchoring structure 120 is more than 0.50, discomfort may be caused to the user. In some embodiments, anchor structure 120 may be a non-slip yarn woven into fabric carrier 110.
When the anchoring structure 120 grabs the skin of the user to deform the fabric carrier 110 in the direction in which the skin stretches, the mesh 130 provided on the wearable myoelectric sensing device 100 will be stretched, so that the fabric carrier 110 is stretched smoothly.
In some embodiments, the mesh 130 may be distributed between the anchor structures 120 such that when the fabric carrier 110 is stretched and the anchor structures 120 remain in the same position on the skin, the mesh 130 may be forced apart to correspondingly deform the fabric carrier 110. In some embodiments, the mesh 130 may comprise 10% -15% of the area of the fabric carrier 110, if the mesh 130 comprises less than 10% of the area of the fabric carrier 110, it may prevent the fabric carrier 110 from being stretched, and if the mesh 130 comprises more than 15% of the area of the fabric carrier 110, it may not allow the wearable myoelectric sensing device 100 to adequately conform to the skin surface of the user. The aforementioned area ratio of the mesh 130 to the fabric carrier 110 is measured when the wearable myoelectric sensing device 100 is not stretched by an external force.
Since the elastic stretch ratio of the region of the fabric carrier 110 not covered with the insulating film 150 is greater than that of the region of the fabric carrier 110 covered with the insulating film 150, the peripheral edge of the fabric electrode 140 is limited to a poor elastic stretch ratio to generate less deformation. Therefore, when the fabric carrier 110 deforms, the deformation of the fabric electrode 140 and the periphery thereof is less obvious, so that the fabric electrode 140 can be held at the same position on the skin of the user, thereby reducing the sensing error of the wearable myoelectric sensing device 100.
In some embodiments, the fabric carrier 110 has a native elastic stretch (i.e., first elastic stretch) of 130% to 160%, and the fabric carrier 110 has an elastic stretch (i.e., second elastic stretch) of 110% to 120% after the insulating film 150 is applied. The elastic elongation is measured by the ASTM D5035-09 standard test method, and the elastic elongation of the fabric carrier 110 attached to the insulating film 150 refers to the elastic elongation of the whole after the insulating film 150 is thermally pressed on the fabric carrier 110. In some embodiments, the material of the insulating film 150 may be thermoplastic polyurethane (Thermoplastic Polyurethane, TPU).
Referring to fig. 3A and 3B, fig. 3A is a graph of myoelectric signals measured when moving using an embodiment of the wearable myoelectric sensing device of the present invention, and fig. 3B is a graph of myoelectric signals measured when moving using another wearable myoelectric sensing device of the present invention, which is the same model as the wearable myoelectric sensing device of the present invention, but is not configured with an anchor structure, mesh and insulating film.
After the two wearable myoelectric sensing devices with the same model are worn at the same position on the subject, the subject jumps in place once every ten seconds for three times, and the measured myoelectric signal diagrams are shown in fig. 3A and 3B. As can be seen from fig. 3A, the wearable myoelectricity sensing device provided by the present invention can measure a very clear and obvious target feature P1. On the contrary, as can be seen from fig. 3B, the signal measured by the other wearable myoelectricity sensing device is added with a plurality of noise N1 in addition to the target feature P2 during jump, and the intensity of the noise N1 is enough to influence the accuracy of the myoelectricity signal measurement.
Therefore, the wearable myoelectricity sensing device can ensure that the fabric electrode is stably held and contacted with the skin of a user at the same position in the movement process of the user by the anchoring structure, the mesh and the partial covering insulating film at the periphery of the fabric electrode, thereby greatly improving the accuracy of the measured myoelectricity signals.
Referring to fig. 4A and 4B, a front view and a wearing schematic diagram of another embodiment of the wearable myoelectric sensing device of the present invention are shown. The wearable myoelectric sensing device 200 comprises a fabric carrier 210, a fabric electrode 240, and an insulating film 250, wherein the fabric carrier 210 comprises a plurality of anchor structures 220 disposed on a first surface 212 of the fabric carrier 210, and a plurality of mesh holes 230 extending through the fabric carrier 210. The fabric electrode 240 is disposed on the first surface 212 of the fabric carrier 210, the insulating film 250 is disposed on the first surface 212 of the fabric carrier 210 and encapsulates the periphery of the fabric electrode 240, and the first elastic stretch ratio of the area of the fabric carrier 210 not covered with the insulating film 250 is greater than the second elastic stretch ratio of the area of the fabric carrier 210 covered with the insulating film 250.
In some embodiments, the number of fabric electrodes 240 is a plurality. For example, the fabric electrode 240 includes a first differential electrode pair 242, a second differential electrode pair 244 and a reference electrode 246, wherein the first differential electrode pair 242 and the second differential electrode pair 244 are respectively disposed to correspond to the antagonistic muscle pairs, and the reference electrode 246 is disposed to correspond to the position with less muscle activity, such as the side of the limb. The electrodes in the first differential electrode pair 242 and the second differential electrode pair 244 are elongated and arranged in parallel. The axes of the first differential electrode pair 242 and the second differential electrode pair 244 are substantially perpendicular to the direction of the muscle, so as to facilitate the sensing of the electromyographic signals.
In some embodiments, the wearable myoelectricity sensing device 200 further includes a plurality of conductive members 260, a plurality of fabric wires 270 and a wireless transmission module 280, wherein the plurality of fabric wires 270 are used to connect the fabric electrodes 240 to the corresponding conductive members 260, and the wireless transmission module 280 is coupled to the conductive members 260. Thus, the signals measured by the fabric electrode 240 can be transmitted to the wireless transmission module 280 via the fabric wire 270 and the conductive member 260, and the wireless transmission module 280 can transmit the signals to other processing units for processing.
In some embodiments, the fabric row 270 is sewn to the first surface 212 of the fabric carrier 210, or the fabric row 270 may be woven into the fabric carrier 210. The insulating film 250 covers the fabric wires 270 to encapsulate the fabric wires 270 between the fabric carrier 210 and the insulating film 250.
In some embodiments, the wearable myoelectric sensing device 200 may further comprise a tethering strap 290, and the tethering strap 290 may encircle the limb of the user and secure the wearable myoelectric sensing device 200 to the user after the wearable myoelectric sensing device 200 is fitted around the limb of the user. In some embodiments, the restraining strip 290 is a self-adhesive restraining strip having elasticity, for example, a velcro disposed on the restraining strip 290.
Referring to fig. 5, a front view of a further embodiment of the wearable myoelectric sensing device of the present invention is shown. The wearable myoelectricity sensing device 300 comprises a fabric carrier 310, a fabric electrode 340 and an insulating film 350, wherein the fabric carrier 310 comprises a plurality of anchor structures 320 disposed on a first surface 312 of the fabric carrier 310, and a plurality of mesh holes 330 penetrating the fabric carrier 310. The fabric electrode 340 is disposed on the first surface 312 of the fabric carrier 310, the insulating film 350 is disposed on the first surface 312 of the fabric carrier 310 and encapsulates the periphery of the fabric electrode 340, and the first elastic stretch ratio of the area of the fabric carrier 310 not covered with the insulating film 350 is greater than the second elastic stretch ratio of the area of the fabric carrier 310 covered with the insulating film 350.
In some embodiments, the distribution density of the mesh openings 330 on the fabric carrier 310 may be adjusted depending on the location of the arrangement. For example, if the deformation of the wearable myoelectric sensing device 300 is observed to be more pronounced in a particular portion 302 than in other portions 304, the design of the fabric carrier 310 may be adjusted so that the portion 302 has more mesh openings 330. In other words. That is, the distribution density of the mesh holes 330 of the portion 302 is greater than that of the mesh holes 330 of the other portion 304, so that the shape of the wearable myoelectric sensing device 300 is changed to be smooth. In some embodiments, portion 302 is the portion corresponding to the greater amount of muscle.
Referring to fig. 6A and 6B, a weave diagram and a loop diagram of an embodiment of a fabric carrier in a wearable myoelectric sensing device according to the invention are shown. In some embodiments, fabric carrier 400 may be a flat-woven fabric structure formed from yarns 410, including non-slip yarns and elastic yarns, which are looped through a front row of needles and a back row of needles. The loops may be removed at locations where the mesh 420 is intended to be formed, where the mesh 420 may be formed. For example, if it is desired to form mesh 420 at the 4 th and 5 th needle positions, the loops originally intended at the 4 th needle position may be transferred to the 3 rd needle, the loops originally intended at the 5 th needle position may be transferred to the 6 th needle, and the 4 th and 5 th needle positions may be left empty to form mesh 420.
Referring to fig. 7A and 7B, there is shown an organization chart of another embodiment of a fabric carrier in a wearable myoelectric sensing device according to the present invention. In other embodiments, the fabric carrier 500 is a warp knitted fabric structure, wherein the base unit U1 comprises two pairs of elastic yarns 510 as warp yarns, and the anti-slip yarns 520 are wrapped around the surface of the elastic yarns 510, wherein the elastic yarns 510 have a stretchability greater than that of the anti-slip yarns 520, and the static friction coefficient of the anti-slip yarns 520 is greater than that of the elastic yarns 510. In some embodiments, the wire diameter of the elastic yarn 510 is also larger than the wire diameter of the anti-slip yarn 520, and the elastic yarn 510 may be, for example, rubber yarn.
Float yarn 530 is wrapped around non-slip yarn 520 and float yarn 530 is wrapped around only non-slip yarn 520 on the outer surface of fabric carrier 500. In other words, the non-slip yarns 520 located on the inner surface of the fabric carrier 500 are not configured with the float yarns 530 so that the fabric carrier 500 still contacts the wearer's skin with the non-slip yarns 520. The yarn diameter of float 530 may be less than the yarn diameter of anti-slip yarn 520, and the loop formation density of float 530 may be greater than the loop formation density of anti-slip yarn 520. In this manner, the portions of the float yarns 530 exposed on the outer surface of the fabric carrier 500 may be used directly as bonding locations for the tie down strap 290 as in fig. 4A.
In these embodiments, two adjacent base units U1 may be connected by a tie yarn 540. Specifically, as shown in fig. 7A, the bonding yarn 540 may connect the anti-slip yarns 520 in two adjacent base units U1, while as shown in fig. 7B, the bonding yarn 540 is not disposed at the position of the mesh 550 to connect two adjacent base units U1, so that the mesh 550 may be formed on the fabric carrier 500.
The wearable myoelectricity sensing device provided by the invention can solve the problem that the electrode is displaced due to slipping or stretching deformation of cloth in the movement process, so that the electrode can be stably fixed on a correct muscle group and cannot move or slide in the movement process of muscles, thereby being beneficial to improving the measurement stability of myoelectricity signals and further improving the accuracy of action analysis.
Although the present invention has been described with reference to the above embodiments, it should be understood that the invention is not limited thereto, but may be modified and altered in various ways without departing from the spirit and scope of the present invention.
Claims (10)
1. A wearable myoelectric sensing device, comprising:
a fabric carrier comprising an anchoring structure disposed at a first surface of the fabric carrier, and a mesh passing through the fabric carrier;
a fabric electrode disposed on the first surface of the fabric carrier; and
an insulating film disposed on the first surface of the fabric carrier and encapsulating a periphery of the fabric electrode, wherein a region of the fabric carrier not covered with the insulating film has a first elastic stretch, a region of the fabric carrier covered with the insulating film has a second elastic stretch, and the first elastic stretch is greater than the second elastic stretch.
2. The wearable myoelectric sensing device of claim 1, wherein the first elastic stretch is 130% to 160%.
3. The wearable myoelectric sensing device of claim 1, wherein the second elastic stretch is 110% to 120%.
4. The wearable myoelectric sensing device of claim 1, wherein the mesh is distributed between the anchor structures.
5. The wearable myoelectric sensing device of claim 1, wherein the fabric carrier comprises a first portion and a second portion, the distribution density of the mesh in the first portion being greater than the distribution density of the mesh in the second portion.
6. The wearable myoelectric sensing device of claim 1, wherein the anchoring structure is a non-slip yarn woven into the fabric carrier.
7. The wearable myoelectric sensing device of claim 1, further comprising a tie-down strap connected to the fabric carrier.
8. The wearable myoelectric sensing device of claim 1, further comprising a conductive member disposed on the fabric carrier and coupled to the fabric electrode.
9. The wearable myoelectric sensing device of claim 8, further comprising a wireless transmission module coupled to the conductive member.
10. The wearable myoelectric sensing device of claim 8, further comprising a fabric wire harness connecting the fabric electrode and the conductive member, wherein the insulating film covers the fabric wire harness.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202210463211.3A CN116999076A (en) | 2022-04-28 | 2022-04-28 | Wearable myoelectricity sensing device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202210463211.3A CN116999076A (en) | 2022-04-28 | 2022-04-28 | Wearable myoelectricity sensing device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN116999076A true CN116999076A (en) | 2023-11-07 |
Family
ID=88562273
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202210463211.3A Pending CN116999076A (en) | 2022-04-28 | 2022-04-28 | Wearable myoelectricity sensing device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN116999076A (en) |
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2022
- 2022-04-28 CN CN202210463211.3A patent/CN116999076A/en active Pending
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