Preparation method of myoelectricity and myosound bimodal stretchable device

Abstract

The embodiment of the invention provides a preparation method of a myoelectricity and myosound bimodal stretchable device. The method comprises the following steps: S1, preparing a flexible stretchable myoelectricity sensor by taking silica gel as a substrate and gold as a stretching conductive material by adopting a thermal evaporation technology; and S2, based on the manufactured stretchable thin film myoelectricity sensor, integrating a microphone and a multi-channel myoelectricity electrode of the flexible stretchable myoelectricity sensor through local hardening and liquid metal connection so as to complete preparation of the myoelectricity and myosound bimodal stretchable device. According to the scheme, the electromyographic electrode is soft and stretchable, can follow up the skin in a conformal mode and can stably carry out electrophysiological signal monitoring, and the related device is soft and stretchable as a whole, can follow up the skin in a conformal mode and can stably carry out in-situ synchronous monitoring of electromyographic and muscle sound bimodal signals.

Description

Technical Field

[0001] Embodiments of the present invention relate to the technical field of sensitive electronic components, and particularly to a preparation method of an electromyogram and myoacoustic bimodal stretchable device. Background Art

[0002] In some diseases in the medical field, such as muscle atrophy and stroke, not only the failure of the nerve electrical signal conduction pathway is involved, but also the failure of the muscle activity response is involved. Therefore, when treating these diseases, it is necessary to monitor the muscle activity of the human body.

[0003] On the one hand, surface electromyogram signals (EMG) represent the superposition of electrical signals from multiple motor units in the body transmitted to the body surface. Monitoring surface electromyogram signals helps to better understand muscle activity and nerve control monitoring, and is of great significance in the fields of clinical diagnosis, rehabilitation evaluation, and intelligent prosthetic control. On the other hand, myoacoustic signals (AMG) originate from muscle vibrations generated by the friction of muscle fibers when the nerve controls muscle contraction or relaxation. Monitoring myoacoustic signals can deeply understand muscle activation patterns, force output, and fatigue levels, and can be used as a means to evaluate muscle function. However, the monitoring of a single mode of electromyogram signals or myoacoustic signals cannot accurately judge the overall health status of nerves and muscles. Only when the two modes are monitored simultaneously in the target area can the overall state of neuromuscles be comprehensively reflected. Their combined monitoring can help detect lesions early and significantly improve the diagnostic accuracy.

[0004] At present, although sensors for epidermal electromyogram and muscle sound monitoring have been prepared, neuromuscular activity physiological information monitoring devices can only monitor a single physiological information in real time at the same site. Existing electromyogram electrodes and myoacoustic sensors cannot meet the in-situ synchronous acquisition of bimodal signals. Even by integrating a single-channel electromyogram electrode and a single-channel microphone to achieve synchronous acquisition of electromyogram and myoacoustic signals, the overall sensor is rigid, and when detecting some movements with large skin deformation, it will slip and detach from the skin, resulting in problems such as signal artifacts that are difficult to remove. With the innovative research and development in flexible stretchable conductive materials and microstructures, rigid electronic components can also be made flexible and stretchable as a whole through technologies such as local hardening. To a large extent, the flexible integration of multimodal physiological parameters has been achieved, including the measurement of parameters such as body temperature, heart rate, electrocardiogram, and humidity. Currently, single-mode monitoring of EMG or AMG has been achieved. However, in the form of flexible stretchable, there is no relevant research on bimodal sensors integrating multi-channel EMG and AMG.

[0005] In summary, the prior art has the following disadvantages:

[0006] (1) Commercial patch electrodes are not stretchable. When monitoring the myoelectric signals of large-deformation movements, they are prone to slipping and even detaching from the skin, resulting in unstable or even lost signals.

[0007] (2) Rigid sensors are difficult to match with the human skin, causing motion artifacts and affecting the signal quality.

[0008] (3) The information acquisition modality of flexible sensing is single, and it cannot perform in-situ multi-channel synchronous data acquisition for the dual modalities of myoelectric and myoacoustic signals. Summary of the Invention

[0009] In view of this, embodiments of the present invention provide a preparation method for a myoelectric and myoacoustic dual-modal stretchable device to at least partially solve the above problems.

[0010] According to the first aspect of the embodiments of the present invention, there is provided a preparation method for a myoelectric and myoacoustic dual-modal stretchable device, including: S1. Using silicone as the substrate, gold is used as the stretchable conductive material by thermal evaporation technology to prepare a flexible stretchable myoelectric sensor; S2. Based on the manufactured stretchable thin-film myoelectric sensor, a microphone and multi-channel myoelectric electrodes of the flexible stretchable myoelectric sensor are integrated through local hardening and liquid metal connection to complete the preparation of the myoelectric and myoacoustic dual-modal stretchable device.

[0011] In one implementation, step S1 specifically includes: S101. Mixing components A and B of Ecoflex-0020 liquid silicone in a ratio of 1:1 and performing vacuum degassing to obtain a mixture of Ecoflex-0020 liquid silicone; S102. Spin-coating the mixture on an acrylic plate and allowing it to stand until cured to form a silicone substrate; S103. Placing a PET sheet with an electrode pattern on the silicone substrate; S104. Covering a layer of gold on the film of the silicone substrate with the PET sheet placed thereon by thermal evaporation technology to generate multi-channel myoelectric electrodes; S105. Coating a layer of pressure-sensitive adhesive on the multi-channel myoelectric electrodes to ensure safe adhesion to the skin, thereby completing the preparation of the flexible stretchable myoelectric sensor.

[0012] In another implementation, step S1 further includes: Spin-coating a layer of Ecoflex material on the multi-channel myoelectric electrodes to insulate and protect the electrodes while ensuring that the contact parts of the multi-channel myoelectric electrodes are exposed.

[0013] In another implementation, step S2 specifically includes: S201, punching holes in the back of the multi-channel EMG electrode to allow myoacoustic signals to pass through; S202, placing a PET sheet on the back film of the silicone substrate and uniformly processing liquid metal to form a conductive wire; S203, fixing the ICS-40300 microphone at a specified position on the flexible and stretchable EMG sensor through Dow Corning 734 to complete the preparation of the EMG-myogram dual-modal stretchable device.

[0014] In another implementation, step S2 further includes: spin-coating a layer of Ecoflex material on the surface of the EMG-myogram dual-modal stretchable device to insulate and protect the liquid metal wire.

[0015] In another implementation, the thickness of the silicone substrate is 200 μm.

[0016] Compared with the prior art, the beneficial effects of the solution of the present invention are as follows:

[0017] (1) Compared with commercial patch electrodes, the EMG electrodes involved in the solution of the present invention are soft and stretchable, can conform to the skin and follow its movement, and can stably monitor electrophysiological signals.

[0018] (2) Compared with existing dual-modal sensors, the device involved in the solution of the present invention is soft and stretchable as a whole, can conform to the skin and follow its movement, and can stably perform in-situ synchronous monitoring of EMG and myoacoustic dual-modal signals. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] In order to more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the following will briefly introduce the drawings required for use in the description of the embodiments or the prior art. Obviously, the drawings in the following description are only some embodiments recorded in the embodiments of the present invention. For those of ordinary skill in the art, other drawings can also be obtained based on these drawings.

[0020] Figure 1 It is a flowchart of the steps of the preparation method of the EMG-myogram dual-modal stretchable device according to an embodiment of the present invention.

[0021] Figure 2 It is a specific operation flowchart of the preparation method of the EMG-myogram dual-modal stretchable device according to another embodiment of the present invention.

[0022] Figure 3 It is a specific operation flowchart of the preparation method of the EMG-myogram dual-modal stretchable device according to another embodiment of the present invention.

[0023] Figure 4 It is a distribution diagram of hard dual-modal EMG-myogram monitoring points of the preparation method of the EMG-myogram dual-modal stretchable device according to another embodiment of the present invention.

[0024] Figure 5a Images of the existing non-stretchable bimodal sensors (i, ii) attached to the neck before and after exercise and the present invention (iii, iv).

[0025] Figure 5b Amplitude and time-frequency diagrams of the existing non-stretchable bimodal sensors and the monitored electromyogram and myoacoustic signals (electromyogram channel 11 and myoacoustic channel 4) on the left side of the neck.

[0026] Figure 5c Amplitude and time-frequency diagrams of the electromyogram and myoacoustic signals (electromyogram channel 11 and myoacoustic channel 4) on the left side of the neck monitored by the present invention.

[0027] Figure 5d Amplitude distribution diagrams of the electromyogram and myoacoustic signals on both the left and right sides of the neck during a left turn of the present invention.

[0028] Figure 5e RMS values of the electromyogram and myoacoustic signals of the monitoring channels during a right turn and a left turn within the circled positions of the present invention (left side: electromyogram channels 9, 10, 13, 14 and myoacoustic channel 3; right side: electromyogram channels 1, 2, 5, 6 and myoacoustic channel 1). Detailed implementation manners

[0029] For a clearer understanding of the technical features, objectives and effects of the embodiments of the present invention, the specific implementation manners of the embodiments of the present invention will now be described with reference to the accompanying drawings.

[0030] In this document, "exemplarily" means "serving as an instance, example or illustration", and any illustration or implementation manner described as "schematic" in this document should not be interpreted as a more preferred or more advantageous technical solution.

[0031] To simplify the drawings, only the parts related to the present invention are schematically shown in each figure, and they do not represent the actual structure of the product. Additionally, to simplify the drawings for easier understanding, in some figures, components with the same structure or function are only schematically shown for one or more of them, or only one or more of them are labeled.

[0032] To enable those skilled in the art to better understand the technical solutions in the embodiments of the present invention, the technical solutions in the embodiments of the present invention will be clearly and completely described below in conjunction with the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all of the embodiments. All other embodiments obtained by those of ordinary skill in the art based on the embodiments in the present invention should fall within the scope of protection of the embodiments of the present invention.

[0033] The following further illustrates the specific implementation of the embodiments of the present invention in conjunction with the accompanying drawings of the embodiments of the present invention.

[0034] See Figure 1 FIG. Figure 1 is a step flow chart of a preparation method of an electromyogram and myoacoustic dual - mode stretchable device according to an embodiment of the present invention, which mainly includes:

[0035] Step S1: Using silicone as the substrate, gold is used as the stretchable conductive material by thermal evaporation technology to prepare a flexible stretchable electromyogram sensor;

[0036] Step S2: Based on the manufactured stretchable thin - film electromyogram sensor, the microphone and the multi - channel electromyogram electrodes of the flexible stretchable electromyogram sensor are integrated together through local hardening and liquid metal connection to complete the preparation of the electromyogram and myoacoustic dual - mode stretchable device.

[0037] Compared with the prior art, the beneficial effects of the solution of the present invention are:

[0038] (1) Compared with commercial patch electrodes, the electromyogram electrodes involved in the solution of the present invention are soft and stretchable, can conform to the skin and follow its movement, and can stably monitor electrophysiological signals.

[0039] (2) Compared with existing dual - mode sensors, the device involved in the solution of the present invention is soft and stretchable as a whole, can conform to the skin and follow its movement, and can stably perform in - situ synchronous monitoring of electromyogram and myoacoustic dual - mode signals.

[0040] In one implementation, see Figure 2 , step S1 specifically includes:

[0041] Step S101: Mix the A and B components of Ecoflex - 0020 liquid silicone in a ratio of 1:1 and perform vacuum degassing to obtain a mixture of Ecoflex - 0020 liquid silicone;

[0042] Step S102: Spin - coat the mixture on an acrylic plate and let it stand until cured to form a silicone substrate;

[0043] Step S103: Place the PET sheet with electrode patterns on the silicone substrate;

[0044] Step S104: Cover a layer of gold on the film of the silicone substrate on which the PET sheet is placed through thermal evaporation technology to generate multi - channel electromyogram electrodes;

[0045] Step S105: Coat a layer of pressure - sensitive adhesive on the multi - channel electromyogram electrodes to ensure safe adhesion to the skin, and thus complete the preparation of the flexible stretchable electromyogram sensor.

[0046] In another implementation, step S1 further includes: Spin - coat a layer of Ecoflex material on the multi - channel electromyogram electrodes to insulate and protect the electrodes, while ensuring that the contact parts of the multi - channel electromyogram electrodes are exposed.

[0047] In another implementation, referring to Figure 3 , step S2 specifically includes:

[0048] Step S201: Punch holes in the back of the multi-channel electromyogram electrode to allow myoacoustic signals to pass through;

[0049] Step S202: Place the PET sheet on the back film of the silicone substrate and uniformly process the liquid metal to form a conductive wire;

[0050] It should be understood that the introduction of liquid metal realizes a flexible and stretchable wire with low resistance.

[0051] Step S203: Fix the ICS-40300 microphone at the designated position of the flexible and stretchable electromyogram sensor through Dow Corning 734 to complete the preparation of the electromyogram and myoacoustic dual-modal stretchable device.

[0052] It should be understood that through the introduction of Dow Corning 734, the combination of a low-modulus flexible and stretchable electrode and a microphone realizes the preparation of an electromyogram and myoacoustic dual-modal sensor, achieving the combination of a rigid sensor and a flexible sensor and achieving the purpose of improving comfort.

[0053] In another implementation, step S2 further includes: spin-coating a layer of Ecoflex material on the surface of the electromyogram and myoacoustic dual-modal stretchable device to insulate and protect the liquid metal wire.

[0054] In another implementation, the thickness of the silicone substrate is 200 μm.

[0055] The following verification is carried out on the solution of the present invention through experiments:

[0056] Considering the high stretchability of the device involved in the present invention, it is very suitable for dynamic dual-modal monitoring of human skin that bears large strains. The neck usually undergoes large deformations during daily movements, which is difficult for non-stretchable electrodes to operate. In this regard, the dual-modal signals during neck movement monitored by a non-stretchable dual-modal sensor and the electromyogram and myoacoustic dual-modal stretchable device involved in the present invention are studied. The results are respectively as Figure 5a , Figure 5b , Figure 5c , Figure 5d , Figure 5e shown. A commercially available 64-channel polyimide electrode purchased is selected as the non-stretchable substrate, and 4 myoacoustic acquisition microphones are integrated. The specific channel distribution is as Figure 4 shown.

[0057] Sixteen channels are selected to verify the function during movement. At Figure 5aDuring large movements such as neck rotation, due to the non-stretchability of existing devices, the sensor separates from the skin, causing severe pain to the subject. In contrast, the stretchable bimodal sensor involved in the solution of the present invention can be appropriately deformed as the skin deforms, not only ensuring the comfort of wearing, but also capable of simultaneously collecting electromyography (EMG) signals and muscle sound signals during the entire movement process.

[0058] The recorded EMG signals and muscle sound signals are respectively as Figure 5b and Figure 5c shown, and the amplitude and corresponding frequency of the bimodal signals (EMG channel 11 and muscle sound channel 4) obtained during the right turn over time are displayed and analyzed. For non-stretchable PI-based sensors, it is difficult to eliminate motion artifacts. The solution of the present invention has the characteristics of being conformal and adaptive to the skin, showing different waveforms and time-frequency characteristics in their respective frequency bands. This result proves that the solution of the present invention has good signal acquisition performance in the face of skin deformation.

[0059] The solution of the present invention can reliably collect 16-channel EMG signals and 4-channel muscle sound signals during large deformations that occur during neck movement. By synchronously collecting data, subsequent data analysis can be carried out to understand the activation of muscles. The amplitude distribution of a complete neck rotation movement is as Figure 5d shown, and the EMG and muscle sound signals show a matching muscle activation state. When the neck turns to the left, the muscles on the left side of the neck relax, while the muscles on the right side are activated.

[0060] To further analyze the relationship between EMG and muscle sound signals, signals at symmetric positions are selected for research, as shown in the inset in Figure 5e . When the neck turns to the right, the muscles on the left side are activated, while the muscles on the right side relax, resulting in higher root mean square (RMS) values of the EMG and muscle sound signals on the left side than on the right side. Vice versa. There is a strong correlation between EMG and muscle sound signals, and these signals can effectively reflect the active state of muscles.

[0061] In summary, through experiments and use, the solution of the present invention has obtained stable bimodal monitoring results of EMG and muscle sound.

[0062] The solution involved in the present invention realizes the stability, soft stretchability, and functional integration of bimodality of the device, in-situ synchronous acquisition of multi-channel bimodal signals, and can be used for the monitoring of EMG and muscle sound bimodal signals on any skin surface.

[0063] It should be noted that according to the needs of implementation, each component / step described in the embodiments of the present invention can be split into more components / steps, or two or more components / steps or partial operations of components / steps can be combined into new components / steps to achieve the purpose of the embodiments of the present invention.

[0064] It should be understood that although this specification is described according to various embodiments, not every embodiment only contains an independent technical solution. This narrative way of the specification is only for clarity. Those skilled in the art should regard the specification as a whole, and the technical solutions in each embodiment can also be appropriately combined to form other embodiments that can be understood by those skilled in the art.

[0065] The above embodiments are only used to illustrate the embodiments of the present invention, rather than to limit the embodiments of the present invention. Those of ordinary skill in the relevant technical field can also make various changes and modifications without departing from the spirit and scope of the embodiments of the present invention. Therefore, all equivalent technical solutions also belong to the scope of the embodiments of the present invention, and the patent protection scope of the embodiments of the present invention should be defined by the claims.

Claims

1. A preparation method of an electromyogram and myoacoustic dual-modal stretchable device, characterized in that, Including: S1. Using silicone as the substrate, gold is used as the stretchable conductive material by thermal evaporation technology to prepare a flexible and stretchable electromyography sensor; S2. Based on the manufactured stretchable thin-film electromyography sensor, the microphone and the multi-channel electromyography electrodes of the flexible and stretchable electromyography sensor are integrated through local hardening and liquid metal connection to complete the preparation of the electromyography and myoacoustic dual-modal stretchable device.

2. The method according to claim 1, characterized in that, Step S1 specifically includes: S101. Mix the A and B components of Ecoflex-0020 liquid silicone in a ratio of 1:1 and perform vacuum degassing to obtain a mixture of Ecoflex-0020 liquid silicone; S102. Spin-coat the mixture on an acrylic plate and let it stand until cured to form a silicone substrate; S103. Place a PET sheet with an electrode pattern on the silicone substrate; S104. Cover a layer of gold onto the film of the silicone substrate on which the PET sheet is placed through thermal evaporation technology to generate multi-channel electromyography electrodes; S105. Coat a layer of pressure-sensitive adhesive on the multi-channel electromyography electrodes to ensure safe adhesion to the skin, thereby completing the preparation of the flexible and stretchable electromyography sensor.

3. The method according to claim 2, characterized in that, Step S1 also includes: Spin-coat a layer of Ecoflex material on the multi-channel electromyography electrodes to insulate and protect the electrodes, while ensuring that the contact parts of the multi-channel electromyography electrodes are exposed.

4. The method according to claim 1, characterized in that, Step S2 specifically includes: S201. Drill holes in the back of the multi-channel electromyography electrodes to allow myoacoustic signals to pass through; S202. Place a PET sheet on the back film of the silicone substrate and uniformly process liquid metal to form a conductive wire; S203. Fix the ICS-40300 microphone at the designated position of the flexible and stretchable electromyography sensor through Dow Corning 734 to complete the preparation of the electromyography and myoacoustic dual-modal stretchable device.

5. The method according to claim 4, characterized in that, Step S2 also includes: Spin-coat a layer of Ecoflex material on the surface of the electromyography and myoacoustic dual-modal stretchable device to insulate and protect the liquid metal wire.

6. The method according to any one of claims 1-5, characterized in that, The thickness of the silicone substrate is 200 μm.

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