An ionic gel flexible sensor for motion and health monitoring

Abstract

The utility model relates to the related flexible sensor technical field of human body movement and health monitoring, the utility model discloses a kind of ion gel flexible sensor for movement and health monitoring, including flexible sensing module;The flexible sensing module includes the flexible encapsulation layer, flexible electrode and ion gel sensing unit sequentially arranged from top to bottom;One surface of the ion gel sensing unit is exposed outside the flexible encapsulation layer, constitutes skin bonding interface, signal lead wire, with the flexible electrode electric connection, the sensor is with polydimethylsiloxane or ecological flexible rubber as flexible encapsulation layer, match flexible electrode and the ion gel sensing unit of specific component, consider super tensile property and stable sensing, repeatedly stretched signal does not drift;High adhesion interface is equipped with isolation protective layer, solve the problem of poor durability of strong adhesion material;Layered assembly is easy to prepare, high reliability, and flexible assembly is attached to skin, biocompatibility is good, can accurately long-term physiological signal acquisition.

Description

Technical Field

[0001] This utility model relates to the field of flexible sensor technology related to human movement and health monitoring, specifically an ion gel flexible sensor for movement and health monitoring. Background Technology

[0002] With the rapid development of wearable devices, the demand for flexible sensors for human motion and health monitoring is increasing. An ideal flexible sensor should possess good flexibility, stretchability, biocompatibility, and a stable, comfortable, and conformal interface with human skin, enabling accurate and long-term acquisition of various physiological signals, such as joint movement, muscle activity, heart rate, and pulse waves. Existing flexible sensors struggle to balance ultra-stretchability, high adhesion, and stable sensing performance, exhibiting inherent drawbacks such as poor durability of strongly adhesive materials, significant electrical signal drift after repeated stretching, and complex fabrication and insufficient reliability due to inter-performance constraints. Therefore, we propose an iongel flexible sensor for motion and health monitoring to address these issues. Utility Model Content

[0003] To address the shortcomings of existing technologies, this invention provides an ion gel flexible sensor for sports and health monitoring. It solves the problems of existing flexible sensors, which struggle to balance super-stretchability, high adhesion, and stable sensing performance. Furthermore, existing sensors suffer from poor durability of strongly adhesive materials, significant electrical signal drift after repeated stretching, and complex fabrication and insufficient reliability due to mutual constraints among various properties. This invention resolves these issues that affect the accuracy of the sensor and its ability to collect physiological signals over long periods.

[0004] To achieve the above objectives, this utility model is implemented through the following technical solution: an ion gel flexible sensor for sports and health monitoring, comprising a flexible sensing module;

[0005] The flexible sensing module includes a flexible encapsulation layer, a flexible electrode, and an ion gel sensing unit arranged sequentially from top to bottom.

[0006] One surface of the ion gel sensing unit is exposed outside the flexible encapsulation layer, forming a skin adhesion interface;

[0007] The signal lead is electrically connected to the flexible electrode.

[0008] Preferably, the skin-adhesion interface of the ionogel sensing unit is provided with an isolation protective layer for protecting the skin-adhesion interface.

[0009] Preferably, the ion gel sensing unit is composed of a first monomer, a second monomer, a photoinitiator, and an ionic liquid.

[0010] Preferably, the first monomer is acrylamide, the second monomer is methoxyethyl acrylate, the ionic liquid is lithium bis(trifluoromethanesulfonyl)imide, and the photoinitiator is hydroxy-methylacetone.

[0011] Preferably, the flexible encapsulation layer can be made of polydimethylsiloxane or eco-friendly flexible rubber.

[0012] Preferably, the ion gel sensing unit is configured as a resistive sensing unit, which adheres to the skin through the skin adhesion interface and senses the stretching and contraction deformation of the skin surface.

[0013] Beneficial effects

[0014] This invention provides an ion gel flexible sensor for motion and health monitoring. Compared with the prior art, it has the following advantages:

[0015] This ion gel flexible sensor for sports and health monitoring features a flexible encapsulation layer made of polydimethylsiloxane or eco-friendly flexible rubber. The flexible electrodes and ion gel sensing unit work synergistically, balancing ultra-stretchability with stable sensing performance. The ion gel sensing unit, composed of acrylamide, methoxyethyl acrylate, hydroxymethyl acetone, and lithium bis(trifluoromethanesulfonyl)imide, serves as a resistive sensing unit, exhibiting no significant drift in electrical signals after repeated stretching. The skin-adhesive interface of the ion gel sensing unit possesses high adhesion, further enhanced by a protective isolation layer, addressing the poor durability of highly adhesive materials. The overall design employs a layered assembly structure of flexible encapsulation layer, flexible electrodes, and ion gel sensing unit, with complementary and unrestricted performance among components. This simplifies the manufacturing process and improves reliability. Furthermore, the flexible components exhibit high skin adhesion and good biocompatibility, forming a stable and comfortable conformal interface, enabling accurate and long-term acquisition of physiological signals. Attached Figure Description

[0016] Figure 1 This is an exploded view of the overall structure of this utility model;

[0017] Figure 2 This is a schematic diagram of the uniaxial stress-strain curve of the ion gel sensing unit provided in Embodiments 1 to 5 of this utility model;

[0018] Figure 3 This is a schematic diagram of the uniaxial stress-strain curve of the ion gel sensing unit provided in Embodiments 1 and 6 to 8 of this utility model;

[0019] Figure 4 This is a schematic diagram of the adhesion performance of the ion gel sensing unit in Embodiment 3 of this utility model;

[0020] Figure 5This is a schematic diagram of the 20-cycle stretching curve of the ion gel sensing unit provided in Embodiment 3 of this utility model;

[0021] Figure 6 This is a schematic diagram of the relative resistance change of the ion gel sensor provided in Embodiment 3 of this utility model under 50% strain after 1000 cycles of stretching.

[0022] In the figure: 1. Flexible sensing module; 101. Flexible encapsulation layer; 102. Flexible electrode; 103. Ion gel sensing unit; 104. Isolation and protection layer. Detailed Implementation

[0023] The technical solutions of the present utility model will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present utility model, and not all embodiments. Based on the embodiments of the present utility model, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the protection scope of the present utility model.

[0024] like Figure 1 As shown:

[0025] An ion gel flexible sensor for motion and health monitoring, comprising a flexible sensing module 1;

[0026] The flexible sensing module 1 includes a flexible encapsulation layer 101, a flexible electrode 102, and an ion gel sensing unit 103 arranged sequentially from top to bottom. The ion gel sensing unit 103 is composed of a first monomer, a second monomer, a photoinitiator, and an ionic liquid. The first monomer is acrylamide, the second monomer is 2-methoxyethyl acrylate, the ionic liquid is lithium bis(trifluoromethanesulfonylimide), and the photoinitiator is 2-hydroxy-2-methylphenylacetone.

[0027] One surface of the ion gel sensing unit 103 is exposed outside the flexible encapsulation layer 101, forming a skin adhesion interface;

[0028] The signal lead is electrically connected to the flexible electrode 102;

[0029] An isolation protective layer 104 is provided on the skin adhesion interface of the ion gel sensing unit 103 to protect the skin adhesion interface;

[0030] The flexible encapsulation layer 101 can be made of polydimethylsiloxane or eco-friendly flexible rubber;

[0031] The ion gel sensing unit 103 is configured as a resistive sensing unit, which adheres to the skin through a skin-adhesive interface and senses the stretching and contraction deformation of the skin surface.

[0032] In this implementation scheme: the ion gel flexible sensor for sports and health monitoring uses a flexible encapsulation layer 101 made of polydimethylsiloxane or eco-friendly flexible rubber as the outermost structure of the sensor, laying the foundation for overall flexibility and providing protection for internal components.

[0033] Below the flexible encapsulation layer 101, the flexible electrode 102 is fixed in a preset position to ensure that the electrode surface is flat, so as to prepare for subsequent electrical signal conduction, while ensuring the adhesion between the electrode and the encapsulation layer to avoid affecting signal transmission due to interlayer separation.

[0034] The ion gel sensing unit 103 was prepared by mixing acrylamide (first monomer), 2-methoxyethyl acrylate (second monomer), 2-hydroxy-2-methylphenylacetone (photoinitiator), and lithium bis(trifluoromethanesulfonyl)imide (ionic liquid). The molar ratio of acrylamide to 2-methoxyethyl acrylate was 1:9, the molar concentration of lithium bis(trifluoromethanesulfonyl)imide was 1.5M, and 2-hydroxy-2-methylphenylacetone accounted for 1 wt% of the total mass of the mixture. The mixture was irradiated with ultraviolet light at room temperature for 5 min to initiate the monomer polymerization reaction, thus obtaining the ion gel sensing unit 103.

[0035] The prepared ion gel sensing unit 103 is assembled below the flexible electrode 102, ensuring that one of its surfaces is exposed outside the flexible encapsulation layer 101, and this exposed surface constitutes the skin adhesion interface.

[0036] An isolation protective layer 104 is covered on the skin adhesion interface of the ion gel sensing unit 103 to protect the skin adhesion interface from dust, pollution and physical damage, so as to avoid damage to the interface performance when not in use.

[0037] The signal lead is stably electrically connected to the flexible electrode 102 to ensure good contact between the lead and the electrode and to avoid excessive contact resistance, thus creating a path for subsequent electrical signal output.

[0038] Before use, remove the protective layer 104 on the skin bonding interface of the ion gel sensing unit 103 to expose the interface and make it suitable for skin bonding. Then, attach the skin bonding interface of the ion gel sensing unit 103 to the target monitoring part of the human body, such as joints, wrists, muscles, etc. Utilize the adhesive properties of the ion gel to achieve stable bonding and ensure that the sensor is closely conformal to the skin.

[0039] When the human body exercises or engages in physiological activities, the skin surface undergoes stretching or contraction deformation. This deformation is transmitted to the ion gel sensing unit 103 through the skin adhesion interface. Since the ion gel sensing unit 103 is configured as a resistive sensing unit, its internal ion transmission channel changes with the deformation, causing the unit's own resistance value to change regularly, thus realizing the conversion of deformation and resistance signals. The flexible electrode 102 captures the resistance change signal of the ion gel sensing unit 103 in real time and converts it into a transmittable electrical signal. The electrical signal is transmitted to an external data acquisition device through the signal lead connected to the flexible electrode 102, completing one signal acquisition cycle.

[0040] The flexible encapsulation layer 101 continuously protects the internal flexible electrode 102 and ion gel sensing unit 103, preventing external environmental corrosion of the internal components. At the same time, the stability of the ion gel material ensures that the correspondence between resistance and deformation remains consistent during repeated stretching and long-term use, reducing electrical signal drift. The overall flexible structure of the sensor can flexibly deform with real-time human movement, always maintaining conformal fit with the skin, ensuring continuous sensing of skin stretching and contraction deformation, and realizing continuous and stable physiological signal acquisition.

[0041] In this solution, the flexible encapsulation layer 101, made of polydimethylsiloxane or eco-friendly flexible rubber, works synergistically with the flexible electrode 102 and the ion gel sensing unit 103, balancing ultra-stretchability and stable sensing performance. The ion gel sensing unit 103, composed of acrylamide, 2-methoxyethyl acrylate, 2-hydroxy-2-methylphenylacetone, and lithium bis(trifluoromethanesulfonylimide), serves as a resistive sensing unit, exhibiting no significant drift in electrical signals after repeated stretching. The skin-adhesive interface of the ion gel sensing unit 103 possesses high adhesion, which, combined with the protective isolation layer 104, solves the problem of poor durability of highly adhesive materials. The overall structure employs a layered assembly structure of the flexible encapsulation layer 101, flexible electrode 102, and ion gel sensing unit 103, with complementary and unrestricted performance of each component, a simple manufacturing process, and improved reliability. Furthermore, each flexible component exhibits high skin adhesion and good biocompatibility, forming a stable and comfortable conformal interface, enabling accurate and long-term acquisition of physiological signals.

[0042] like Figures 2-6 As shown:

[0043] It should be noted that:

[0044] Example 1:

[0045] Acrylamide, 2-methoxyethyl acrylate, photoinitiator and ionic liquid were mixed evenly to obtain a mixture.

[0046] Acrylamide and 2-methoxyethyl acrylate are the polymerization monomers, 2-hydroxy-2-methylphenylacetone is the photoinitiator, and lithium bis(trifluoromethanesulfonyl)imide is the ionic liquid.

[0047] The molar ratio of acrylamide to 2-methoxyethyl acrylate was 1:9, the molar concentration of lithium bis(trifluoromethanesulfonylimide) was 1.5M, and 2-hydroxy-2-methylphenylacetone accounted for 1 wt% of the total mass of the mixture. The mixture was irradiated with ultraviolet light at room temperature for 5 min to initiate the monomer polymerization reaction and obtain the ion gel sensing unit 103.

[0048] Example 2:

[0049] Acrylamide, 2-methoxyethyl acrylate, photoinitiator and ionic liquid were mixed evenly to obtain a mixture.

[0050] Acrylamide and 2-methoxyethyl acrylate are the polymerization monomers, 2-hydroxy-2-methylphenylacetone is the photoinitiator, and lithium bis(trifluoromethanesulfonyl)imide is the ionic liquid.

[0051] The molar ratio of acrylamide to 2-methoxyethyl acrylate was 2:8, the molar concentration of lithium bis(trifluoromethanesulfonylimide) was 1.5M, and 2-hydroxy-2-methylphenylacetone accounted for 1 wt% of the total mass of the mixture. The mixture was irradiated with ultraviolet light at room temperature for 5 min to initiate the monomer polymerization reaction, thus obtaining the ion gel sensing unit 103.

[0052] Example 3:

[0053] Acrylamide, 2-methoxyethyl acrylate, photoinitiator and ionic liquid were mixed evenly to obtain a mixture.

[0054] Acrylamide and 2-methoxyethyl acrylate are the polymerization monomers, 2-hydroxy-2-methylphenylacetone is the photoinitiator, and lithium bis(trifluoromethanesulfonyl)imide is the ionic liquid.

[0055] The molar ratio of acrylamide to 2-methoxyethyl acrylate was 3:7, the molar concentration of lithium bis(trifluoromethanesulfonylimide) was 1.5M, and 2-hydroxy-2-methylphenylacetone accounted for 1 wt% of the total mass of the mixture. The mixture was irradiated with ultraviolet light at room temperature for 5 min to initiate the monomer polymerization reaction, thus obtaining the ion gel sensing unit 103.

[0056] Example 4:

[0057] Acrylamide, 2-methoxyethyl acrylate, photoinitiator and ionic liquid were mixed evenly to obtain a mixture.

[0058] Acrylamide and 2-methoxyethyl acrylate are the polymerization monomers, 2-hydroxy-2-methylphenylacetone is the photoinitiator, and lithium bis(trifluoromethanesulfonyl)imide is the ionic liquid.

[0059] The molar ratio of acrylamide to 2-methoxyethyl acrylate was 4:6, the molar concentration of lithium bis(trifluoromethanesulfonylimide) was 1.5M, and 2-hydroxy-2-methylphenylacetone accounted for 1 wt% of the total mass of the mixture. The mixture was irradiated with ultraviolet light at room temperature for 5 min to initiate the monomer polymerization reaction, thus obtaining the ion gel sensing unit 103.

[0060] Example 5:

[0061] Acrylamide, 2-methoxyethyl acrylate, photoinitiator and ionic liquid were mixed evenly to obtain a mixture.

[0062] Acrylamide and 2-methoxyethyl acrylate are the polymerization monomers, 2-hydroxy-2-methylphenylacetone is the photoinitiator, and lithium bis(trifluoromethanesulfonyl)imide is the ionic liquid.

[0063] The molar ratio of acrylamide to 2-methoxyethyl acrylate was 5:5, the molar concentration of lithium bis(trifluoromethanesulfonylimide) was 1.5M, and 2-hydroxy-2-methylphenylacetone accounted for 1 wt% of the total mass of the mixture. The mixture was irradiated with ultraviolet light at room temperature for 5 min to initiate the monomer polymerization reaction, thus obtaining the ion gel sensing unit 103.

[0064] Example 6;

[0065] Acrylamide, 2-methoxyethyl acrylate, photoinitiator and ionic liquid were mixed evenly to obtain a mixture.

[0066] Acrylamide and 2-methoxyethyl acrylate are the polymerization monomers, 2-hydroxy-2-methylphenylacetone is the photoinitiator, and lithium bis(trifluoromethanesulfonyl)imide is the ionic liquid.

[0067] The molar ratio of acrylamide to 2-methoxyethyl acrylate was 1:9, the molar concentration of lithium bis(trifluoromethanesulfonylimide) was 0.5M, and 2-hydroxy-2-methylphenylacetone accounted for 1 wt% of the total mass of the mixture. The mixture was irradiated with ultraviolet light at room temperature for 5 min to initiate the monomer polymerization reaction, thus obtaining the ion gel sensing unit 103.

[0068] Example 7;

[0069] Acrylamide, 2-methoxyethyl acrylate, photoinitiator and ionic liquid were mixed evenly to obtain a mixture.

[0070] Acrylamide and 2-methoxyethyl acrylate are the polymerization monomers, 2-hydroxy-2-methylphenylacetone is the photoinitiator, and lithium bis(trifluoromethanesulfonyl)imide is the ionic liquid.

[0071] The molar ratio of acrylamide to 2-methoxyethyl acrylate was 1:9, the molar concentration of lithium bis(trifluoromethanesulfonylimide) was 1M, and 2-hydroxy-2-methylphenylacetone accounted for 1 wt% of the total mass of the mixture. The mixture was irradiated with ultraviolet light at room temperature for 5 min to initiate the monomer polymerization reaction, thus obtaining the ion gel sensing unit 103.

[0072] Example 8;

[0073] Acrylamide, 2-methoxyethyl acrylate, photoinitiator and ionic liquid were mixed evenly to obtain a mixture.

[0074] Acrylamide and 2-methoxyethyl acrylate are the polymerization monomers, 2-hydroxy-2-methylphenylacetone is the photoinitiator, and lithium bis(trifluoromethanesulfonyl)imide is the ionic liquid.

[0075] The molar ratio of acrylamide to 2-methoxyethyl acrylate is 1:9, the molar concentration of lithium bis(trifluoromethanesulfonylimide) is 2M, and 2-hydroxy-2-methylphenylacetone accounts for 1 wt% of the total mass of the mixture. The mixture is irradiated with ultraviolet light at room temperature for 5 min to initiate the monomer polymerization reaction, thus obtaining the ion gel sensing unit 103, which can be flexibly selected according to actual application requirements.

[0076] Finally, it should be noted that the above description is merely a preferred embodiment of this utility model and is not intended to limit the utility model. Although the utility model has been described in detail with reference to the foregoing embodiments, those skilled in the art can still modify the technical solutions described in the foregoing embodiments or make equivalent substitutions for some of the technical features. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this utility model should be included within the protection scope of this utility model.

Claims

1. An ionogel flexible sensor for motion and health monitoring, characterized in that: Includes a flexible sensing module (1); The flexible sensing module (1) includes a flexible encapsulation layer (101), a flexible electrode (102), and an ion gel sensing unit (103) arranged sequentially from top to bottom; One surface of the ion gel sensing unit (103) is exposed outside the flexible encapsulation layer (101), forming a skin adhesion interface; The signal lead is electrically connected to the flexible electrode (102).

2. The ionogel flexible sensor for motion and health monitoring according to claim 1, characterized in that: The ion gel sensing unit (103) has an isolation protective layer (104) on its skin adhesion interface for protecting the skin adhesion interface.

3. The ionogel flexible sensor for motion and health monitoring according to claim 2, characterized in that: The ion gel sensing unit (103) is composed of a first monomer, a second monomer, a photoinitiator, and an ionic liquid.

4. The ionogel flexible sensor for motion and health monitoring according to claim 3, characterized in that: The first monomer is acrylamide, the second monomer is 2-methoxyethyl acrylate, the ionic liquid is lithium bis(trifluoromethanesulfonyl)imide, and the photoinitiator is 2-hydroxy-2-methylphenylacetone.

5. The ionogel flexible sensor for motion and health monitoring according to claim 1, characterized in that: The flexible encapsulation layer (101) can be made of polydimethylsiloxane or eco-friendly flexible rubber.

6. The ionogel flexible sensor for motion and health monitoring according to claim 1, characterized in that: The ion gel sensing unit (103) is configured as a resistive sensing unit, which is bonded to the skin through the skin adhesion interface and senses the stretching and contraction deformation of the skin surface.

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