High-performance ionic piezoelectric hydrogel system based on molecular network reconstruction and micro-nano structure cooperative regulation and establishment method thereof

Abstract

The invention discloses a high-performance ionic piezoelectric hydrogel system based on molecular network reconstruction and micro-nano structure coordinated regulation and an establishment method thereof, and the establishment method comprises the following steps: S1, mixing acrylamide, polyacrylamide, sodium gluconate and polyvinyl alcohol to prepare a pre-polymerized solution, and adding HCl into the pre-polymerized solution to obtain a mixed solution system; and S2, carrying out gradient cross-linking and ultraviolet curing on the mixed solution system to obtain the high-performance ionic piezoelectric hydrogel system based on molecular network reconstruction and micro-nano structure coordinated regulation. The sensitivity is improved by 66%, and the problem that a traditional material is insufficient in response to weak biological signals (such as pulse micro-vibration) is solved.

Description

Technical Field

[0001] The present invention belongs to the technical field of high-performance ionic piezoelectric hydrogel systems, and in particular relates to a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructures and a method for establishing the system. Background Art

[0002] At present, the main problems faced by high-performance ionic piezoelectric hydrogels in preparation and application include: (1) it is difficult to coordinately optimize the mechanical strength and electrical properties of the material, resulting in insufficient long-term stability and sensitivity of flexible devices; (2) the ion migration rate and piezoelectric response efficiency are limited by the heterogeneity of the network structure, which limits the accuracy of dynamic signal detection and response speed; (3) the environmental stability is poor, and it is easily affected by external factors such as humidity and temperature, resulting in performance degradation; (4) the large-scale preparation process is immature, with large batch differences and high costs. These problems are mainly due to the difficulty in regulating the dynamic balance of the ion-polymer network inside the hydrogel, the poor compatibility of the piezoelectric phase (such as PVDF, piezoelectric ceramics) with the hydrophilic matrix leading to phase separation, the lack of precise design of the spatial distribution and interfacial interaction of functional components (ionic conductors, piezoelectric fillers), and the insufficient controllability of the microstructure by traditional cross-linking methods, which limits the directional optimization of material properties and adaptability to actual scenarios. Summary of the Invention

[0003] In view of this, the present invention aims to propose a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure and its establishment method, so as to solve at least one technical problem in the background technology.

[0004] To achieve the above object, the technical solution of the present invention is achieved as follows: A method for establishing a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructures comprises the following steps: S1: adding hydrochloric acid to the polyvinyl alcohol solution, stirring evenly, and then adding acrylamide, polyacrylamide, and sodium gluconate to obtain a mixed solution system; S2: The mixed liquid system is prepared by gradient cross-linking and UV curing to obtain a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure.

[0005] Furthermore, in step S1, the molar ratio of acrylamide, polyacrylamide, sodium gluconate, polyvinyl alcohol, and hydrochloric acid is 13-17: 1.5-2.5: 2.5-3.5: 3.5-6: 0.5-1.5.

[0006] Preferably, the molar ratio of acrylamide, polyacrylamide, sodium gluconate, polyvinyl alcohol and hydrochloric acid is 15:2:3:4:1.

[0007] Furthermore, N,N'-methylenebisacrylamide is added to the gradient cross-linking in step S2, and the amount of N,N'-methylenebisacrylamide added is 0.01-0.05 wt%.

[0008] Furthermore, the wavelength of the UV curing in step S2 is 360-370 nm.

[0009] Furthermore, in step S2, the photo adhesive 2959 is added to the UV curing, the stirring time is 2-3 hours, and the UV lamp irradiation time is 4-7 minutes.

[0010] The above-mentioned method for establishing a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure is a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure.

[0011] A motion sensor uses the above-mentioned high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructures integrated with flexible electrodes. It dynamically captures limb movements through piezoelectric signals, has a response time of 8.5 ms, a recovery time of 68 ms, and can identify 0.1° joint angle changes.

[0012] The above-mentioned high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure is applied to motion monitoring, trauma detection, and self-powered systems.

[0013] Furthermore, trauma detection can classify wound types through differences in impedance change rates, with an accuracy rate of >95%.

[0014] Furthermore, the self-powered system outputs a power density of 90μW / cm² at a loading speed of 0.35 m / s.

[0015] Compared with the existing technology, the high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure and the method for establishing the system described in the present invention have the following advantages: This application demonstrates a breakthrough in sensitivity. By synergistically regulating ion mobility using sodium gluconate / HCl, the piezoelectric response current increases from 75 μA in the baseline group to 200 μA (a 167% increase), achieving a detection limit of 50 mg (equivalent to the pressure of a mosquito). Compared to the previously reported MXene-based hydrogel (120 μA, Adv. Mater. 2023), this sensitivity is increased by 66%, addressing the issue of traditional materials' inadequate response to weak biological signals, such as pulse microvibrations.

[0016] This application demonstrates precise biomechanical adaptation, with a dual PVA / PAM network that allows for an adjustable Young's modulus of 0.5-2 MPa, achieving mechanical compatibility with human skin (0.1-2 MPa) and muscle (0.1-0.5 MPa). In simulated joint bending experiments, the device achieved a stress transfer efficiency of 92% (compared to 65% for conventional PDMS-based materials), eliminating the signal distortion and discomfort associated with rigid materials.

[0017] This application demonstrates a breakthrough in long-term durability. The dynamically cross-linked network achieves a resistance fluctuation of less than 5% after 1,000 stretch cycles, and performance degradation of less than 10% in environments with a pH range of 3-11 and a humidity of 30-90%. Compared to single-network hydrogels (which break after 500 cycles), this extends the material's lifespan by more than three times, overcoming the technical bottleneck of flexible devices prone to failure in complex environments.

[0018] 4. This application also includes expansion of multi-scenario applications: motion monitoring: real-time capture of limb movement (response time 8.5 ms, recovery time 68 ms), capable of identifying 0.1° joint angle changes; trauma detection: wound type classification is achieved through impedance change rate differences (scratch ΔR = 200% vs. abrasion ΔR = 140%), with an accuracy rate > 95%; the self-powered system outputs a power density of 90 μW / cm² at a loading speed of 0.35 m / s, which can continuously power low-power sensors. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] The accompanying drawings, which constitute part of the present invention, are provided to provide a further understanding of the present invention. The exemplary embodiments of the present invention and their descriptions are provided to explain the present invention and do not constitute an undue limitation of the present invention. In the accompanying drawings: Figure 1 TG and DSC curves measured by the thermogravimetric analyzer (TG, model TGA 550) described in the embodiment of the present invention; Figure 2 This is a tensile performance curve tested by the universal material testing system (model E3000) described in an embodiment of the present invention; Figure 3 This is a compression performance curve tested by the universal material testing system (model E3000) according to an embodiment of the present invention; Figure 4 A piezoelectric stability diagram according to an embodiment of the present invention; Figure 5 This is a diagram of deformation response signals corresponding to different strains according to an embodiment of the present invention; Figure 6 The application of the hydrogel according to the embodiment of the present invention for piezoelectric monitoring of different motion parts; Figure 7 Schematic diagram of the detection mechanism according to an embodiment of the present invention; Figure 8 The effect of PVA content on the tensile properties of hydrogels described in the embodiments of the present invention; Figure 9 The influence of the compressive properties of the hydrogel described in the embodiment of the present invention; Figure 10 This is a SEM image of a cross section of the hydrogel described in an embodiment of the present invention; Figure 11 This is a SEM image of the surface of the hydrogel described in the embodiment of the present invention; Figure 12 FT-IR characterization of the ionic piezoelectric hydrogel described in the embodiment of the present invention; Figure 13 Comparison of actual detection signals for different degrees of damage (scratches, abrasions, and wounds) described in the embodiments of the present invention; Figure 14 Schematic diagram of detecting different degrees of damage (abrasions, wounds, and scratches from left to right) according to an embodiment of the present invention. DETAILED DESCRIPTION

[0020] It should be noted that, in the absence of conflict, the embodiments of the present invention and the features in the embodiments may be combined with each other.

[0021] The present invention will be described in detail below with reference to the accompanying drawings and in conjunction with embodiments.

[0022] Example 1 Material composition and preparation method: Preparation of PVA\PAM hydrogel 1g, 2g, or 3g of PVA was added to 100ml of deionized water and magnetically stirred at 95°C for 3 hours to obtain a homogeneous PVA solution. A 100:1 ratio of hydrochloric acid was then added to the PVA solution, stirred thoroughly, and then 5g of AAM, 0.7g of PAM, and 3.2g of sodium gluconate were added. The mixture was magnetically stirred for 3 hours. Subsequently, 0.05g of MBAA and 0.08g of photoadhesive 2959 were added and stirred for 2-3 hours. After the solution cooled, it was poured into a suitable mold and cured by UV irradiation for 4-7 minutes to obtain a double-network hydrogel. The resulting hydrogel was then stored in a refrigerator at -15°C. Finally, the final tactile-mimicking hydrogel was obtained through three cycles of freezing (8 hours of freezing and 4 hours of thawing).

[0023] The hydrogel was damaged into 5 cm long scratches and 2 cm 2 The gap area is 4cm 2 The researchers created gaps in the hydrogel surface to simulate scratches, small wounds, and large wounds. Two copper tapes were attached to the top and bottom of the hydrogel to serve as electrodes. The electrodes were then sealed with medical PU tape.

[0024] The matrix construction of this application: acrylamide (AAM) and polyacrylamide (PAM) are used as a double network skeleton, and a three-dimensional cross-linked network is formed by ultraviolet light-induced free radical polymerization.

[0025] Ion mobility regulation of this application: introduction of sodium gluconate (C6H 11 NaO7) as an anion source, through the difference in mobility between its macromolecular organic anions and Na⁺ (Δμ=2.3×10⁻ 4 cm² / Vs) to achieve charge separation; hydrochloric acid (HCl) is also incorporated to adjust the porosity and optimize the ion transport channel (pore size range 20-50 nm).

[0026] The dynamic cross-linking enhancement of this application: polyvinyl alcohol (PVA) is introduced to construct a double network structure, and physical cross-linking points are formed through freeze-thaw cycles to form a gradient modulus (0.5-2 MPa) and self-healing ability.

[0027] Preparation process: A two-step method is adopted: ① Add 0.1-2 mL HCl to the prepolymer solution to regulate the acid-base environment; ② The network structure is directional constructed through gradient cross-linking (MBAA concentration 0.01-0.05 wt%) and UV curing (365 nm, 4-7 min). Motion sensor module: Integrates hydrogel with flexible electrodes (copper tape / PU packaging) to dynamically capture limb movements through piezoelectric signals (response time 8.5 ms).

[0028] Trauma simulation detection: A gradient modulus area is constructed through mechanical damage (scratches / notches), and the impedance change rate (ΔR / R0=150%-300%) is used to identify the trauma type.

[0029] The ion polarization coordinated regulation mechanism of this application: a composite doping strategy of sodium gluconate and hydrochloric acid is adopted to 11 NaO7 - ) and H + The mobility difference (up to 3.2 times) induces space charge separation, which increases the piezoelectric current by 167% (200μA).

[0030] This application's dual-network dynamic cross-linking technology: Through the PVA / PAM interpenetrating network and freeze-thaw cycle process, it achieves precise modulus control (0.5-2 MPa to adapt to human tissue) and at the same time imparts self-healing ability (resistance fluctuation <5% after 1000 cycles).

[0031] The gradient response structure design of this application is to construct a pore size gradient (50 nm in the surface layer → 20 nm in the core layer) and a cross-linking density gradient inside the material to achieve decoupled detection of multimodal mechanical stimuli (compression / shear).

[0032] Compared with the disclosed CN114456488A (ion gel piezoelectric device) and WO2022183864A1 (double network hydrogel), this application achieves breakthroughs in the following dimensions through innovative ion polarization regulation and gradient structure design: Piezoelectric coefficient improvement: d 33 The value reaches 35 pC / N (traditional PVDF is only 20-25 pC / N); environmental stability: it still maintains 85% conductivity at a low temperature of -20°C (the comparative material drops to 50%); manufacturing compatibility: using UV curing process, the production cycle is shortened to 10 minutes (traditional thermal curing takes 2 hours).

[0033] This technology provides high-performance material solutions for flexible electronics, smart medical and other fields, and has clear industrialization prospects.

[0034] The piezoelectric stability of the hydrogel was also tested. Figure 4 As shown in the graph, the current values fluctuate periodically from 0 to 400 s, remaining within a certain range for most of the time. The higher current peak is around 250 µA, while the lower portion remains stable around 50 µA, indicating that the hydrogel is continuously generating current output.

[0035] By changing the strain degree (from 10% to 60%), it can be observed that the peak value of the resistance change rate of the hydrogel increases significantly, but all have good peak shape and repeatability ( Figure 5 The peak value of the resistance change rate is small at 10% strain, while the peak value is significantly higher at 60% strain, indicating that the resistance change rate of the hydrogel is positively correlated with the degree of strain. This enables the hydrogel to detect different degrees of deformation through resistance changes, indicating that when used as a sensor, the hydrogel can exhibit good detection performance across a wide range of strains.

[0036] like Figure 6 As shown in Figure a, the hydrogel can be used as a generator to charge the capacitor, which continuously provides electrical energy for a certain period of time, reflecting the power generation capacity of the hydrogel generator and the sustainability of the power output. Therefore, we made a flexible wearable device based on hydrogel ( Figure 6 b). The device consists of a wristband (Bwristband), tinfoil (Tinfoil), and a middle layer of hydrogel generator (Hydrogel generator).

[0037] like Figure 6 c and 6f, the hydrogel-based sensor device is attached to the wrist joint and elbow joint respectively, and the movement process such as bending and stretching can be accurately and quickly detected through electrical signals. Figure 6Figure d shows the voltage rising over time, demonstrating that during the cyclical motion of shooting a basketball, the hydrogel generator can effectively convert the mechanical energy generated by human motion into electrical energy to charge the capacitor, demonstrating the device's power generation capabilities in dynamic motion scenarios. Furthermore, these fluctuations correspond to arm bending movements, indicating that the hydrogel generator can respond to the bending or extension of human joints by generating periodic voltage changes, further demonstrating its effectiveness in motion detection and energy harvesting from different body parts.

[0038] like Figure 7 As shown, different skin stimuli are reflected differently in the above detection mechanism: Stimulus type: When subjected to different types of stimuli, such as pressure, vibration, and touch, the movement and distribution of ions within the material change differently, generating different electrical signal characteristics. This allows for differentiation between different types of stimuli. For example, pressure stimulation may cause ions within the material to move more concentratedly in a certain direction, while vibration stimulation may cause ions to move back and forth, generating an electrical signal of a specific frequency.

[0039] Stimulus intensity: Different levels of stimulation (such as light touch versus firm pressure) cause different deformations in the material, leading to varying degrees of changes in ion transport and electrical signals. Generally speaking, greater stimulation leads to more pronounced changes in ion transport and higher electrical signal strength, which the biomimetic tactile sensor can use to determine the strength of the stimulus.

[0040] Skin type differences: Different skin types (such as dry, oily, and sensitive) respond to different stimuli to varying degrees. In biomimetic tactile sensing, the composition and structure of the material can be adjusted to simulate the sensitivity of different skin types, making the sensor more tailored to the actual needs of different application scenarios. For example, a sensor that simulates sensitive skin may produce a faster and stronger electrical signal response to weak stimuli.

[0041] (4) First, macro compression tests were conducted on hydrogels with 1% to 3% PVA added. When the compression strain was about 90%, the compressive stress of the hydrogel after adding PVA reached more than 1.5 MPa. Compared with the compression test of hydrogel (see Figure 10 ), even with the addition of the optimal ratio of AAM, the compressive stress of the hydrogel cannot be greater than 1MPa (also 90% compressive strain). This comparison result shows that the addition of PVA enhances the pressure-bearing capacity of the piezoelectric hydrogel, enabling it to adapt to the traumatic deformation of bionic skin, such as Figure 9 shown.

[0042] like Figure 8As shown in the figure, macroscopic tensile tests were then conducted on hydrogels with 1% to 3% PVA added. The addition of 2% PVA resulted in a hydrogel with the best tensile elongation at break (~1100%), and the stress was not significantly affected (20 to 30 kPa). 11 The microstructure composition, thermal stability and mechanical properties of NaO7\HCl\PVA ionic piezoelectric hydrogel were characterized.

[0043] Firstly, the cross-section and surface microstructure of the ionic piezoelectric hydrogel were characterized by SEM. Figure 11 shown. Figure 10 This is the internal characterization of the damaged hydrogel particles, showing a complex network structure; the surface of the hydrogel presents an irregular wrinkled morphology. Figure 11 , its non-uniform corrugated structure originates from the three-dimensional features formed by drying shrinkage during the preparation process. The wrinkled structure significantly increases the specific surface area of the material, providing more transmission channels and active sites for ion adsorption and migration. This property is crucial to enhancing the ion piezoelectric effect - the improvement in ion migration efficiency directly promotes the generation of electrical signals. The surface morphology also reflects the internal loose interpenetrating three-dimensional network structure. This porous architecture can not only accommodate a large number of ions and solvent molecules, but its dynamic cross-linking properties also allow the material to produce sufficient steric hindrance effects when deformed. When external force acts, the dynamic reconstruction of the polymer network and the directional migration of ions form a synergistic effect, thereby effectively improving the piezoelectric response performance.

[0044] This article discusses PAM\C6H 11 NaO7\HCl (control group) and PAM\C6H 11 The NaO7\HCl\PVA ionic piezoelectric hydrogel was characterized by Fourier transform infrared spectroscopy (FT-IR). Figure 12 As shown; The blank control group (Blank) was detected at a wave number of 1662 cm −1 There is an absorption peak at 1649 cm, which can be attributed to the characteristic peak of the amide group (C=O stretching vibration and other amide-related vibrations) in the PAM hydrogel. After adding PVA, the peak position shifted to 1649 cm −1. The significant shift in peak position indicates that the addition of PVA changes the chemical environment of the amide group. This may be because PVA molecules, as a polyhydroxy polymer, can interact with PAM polymer chains, such as hydrogen bonding, which changes the electron cloud distribution and chemical bond force constant of the amide group, thereby affecting its vibration frequency, reflecting that PVA has an effect on the network structure of the hydrogel polymer. In addition, the PVA molecular chain can interact with the original hydroxyl or amino groups in the hydrogel, changing the strength and distribution of hydrogen bonds, thereby causing changes in the vibration frequency, which is reflected in the 3450 cm −1 and 3442 cm −1 The change of wavenumber before and after further proves that PVA participates in the intermolecular interaction of hydrogel. From the change of infrared spectrum, we can see that PVA and PAM\C6H 11 The NaO7\HCl hydrogel exhibited significant interactions. This interaction affected the hydrogel's microstructure, altering the regularity of the polymer network and the intermolecular forces. In terms of performance, structural changes can influence the transport pathways and migration efficiency of ions within the hydrogel. For example, the interaction between PVA and the polymer chains may adjust the size and shape of ion transport channels, affecting the ion migration rate and, in turn, the hydrogel's ionic piezoelectric properties. These favorable microstructural changes can improve the hydrogel's mechanical properties, such as enhancing its toughness and strength, making it more suitable for tactile sensing applications that simulate post-traumatic skin.

[0045] Actual bionic simulated piezoelectric tests were conducted on skin injuries of different degrees. The results are as follows: Figure 13 As shown. From the overall current response characteristics, the current peaks of the curves corresponding to the three types of damage are significantly higher than those of the control group, and there are differences in the current peaks of different types of damage. The experimental group with the scratched surface (red curve) showed the current pulse with the largest relative amplitude (~ 200µA), followed by the blue curve corresponding to the trauma (~ 140µA), and the black curve corresponding to the abrasion was slightly lower. This shows that the biomimetic gel can be sensitively detected when subjected to damage of different types and intensities, especially scratch-type damage. This highlights the PAM\C6H 11 NaO7\HCl\PVA hydrogel, as a biomimetic ionic piezoelectric hydrogel, has significant potential for tactile sensing of post-traumatic skin. By detecting the intensity of the piezoelectric current generated by the hydrogel, it is possible to distinguish whether the skin is injured and the type of injury, providing a potential method for real-time monitoring of skin injuries. This specific response to different injury types makes this hydrogel promising for applications in healthcare, such as the development of wearable skin health monitoring devices that can monitor skin injuries in real time, provide timely feedback to medical staff or patients, and assist in wound diagnosis and treatment.

[0046] Based on the above 11 The various properties and structural characterizations of NaO7\HCl\PVA ion piezoelectric hydrogels indicate their potential for application in monitoring the presence or absence of skin trauma and the presence of different wound surfaces. Therefore, this paper conducted experiments to test the hydrogel for different degrees of damage (from left to right, trauma, abrasion, and scratch). The schematic diagram of the experiment for detecting different degrees of skin damage is shown in the figure. Figure 14 As shown, the wound site (far left) is marked by a blue oval, the abrasion site (center) is marked by a red oval, and the scratch site (far right) is marked by a black oval, connected by a black dotted line. The electrical signal generated by the hydrogel when stimulated at the corresponding injury site can be expressed in the form of current pulses, showing the electrical signal output of the hydrogel under the corresponding injury type.

[0047] The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principles of the present invention should be included in the scope of protection of the present invention.

Claims

1. A method for establishing a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure, characterized by: The steps include: S1: adding hydrochloric acid to the polyvinyl alcohol solution, stirring evenly, and then adding acrylamide, polyacrylamide, and sodium gluconate to obtain a mixed solution system; S2: The mixed liquid system is prepared by gradient cross-linking and UV curing to obtain a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure.

2. The method for establishing a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure according to claim 1, characterized in that: In step S1, the molar ratio of acrylamide, polyacrylamide, sodium gluconate, polyvinyl alcohol, and hydrochloric acid is 13-17: 1.5-2.5: 2.5-3.5: 3.5-6: 0.5-1.

5.

3. The method for establishing a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure according to claim 1, characterized in that: In step S2, N,N'-methylenebisacrylamide is added to the gradient cross-linking, and the amount of N,N'-methylenebisacrylamide added is 0.01-0.05 wt%.

4. The method for establishing a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure according to claim 1, characterized in that: The wavelength of the UV curing in step S2 is 360-370 nm.

5. The method for establishing a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure according to claim 1, characterized in that: In step S2, the photo adhesive 2959 is added to the UV curing, the stirring time is 2-3 hours, and the UV lamp irradiation time is 4-7 minutes.

6. A method for establishing a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure as described in any one of claims 1-5, wherein the method comprises establishing a high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure.

7. A motion sensor, comprising the high-performance ionic piezoelectric hydrogel system based on molecular network reconstruction and micro-nanostructure coordinated regulation according to claim 6 integrated with flexible electrodes, and dynamically capturing limb motion through piezoelectric signals, characterized in that: The response time is 8.5 ms, the recovery time is 68 ms, and it can recognize 0.1° joint angle changes.

8. The high-performance ionic piezoelectric hydrogel system based on the coordinated regulation of molecular network reconstruction and micro-nanostructure as described in claim 6 is applied to motion monitoring, trauma detection, and self-powered systems.

9. The use according to claim 8, characterized in that: Trauma detection classifies wound types through differences in impedance change rates, with an accuracy rate of >95%.

10. The use according to claim 8, characterized in that: The self-powered system outputs a power density of 90μW / cm² at a loading speed of 0.35 m / s.

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