An in-eye self-driven intraocular pressure monitoring device and its preparation method

Abstract

The present invention relates to an in-eye self-driven intraocular pressure monitoring device and a preparation method thereof, and belongs to the field of flexible sensor technology. The present invention proposes a method for preparing an in-eye self-driven intraocular pressure monitoring device by laser direct writing assisted spraying on a hemispherical deformable packaging layer and then by water transfer technology. The substrate realizes stress redistribution through a thickness division strategy, increases the thickness of the capacitor area substrate to improve the stability of the energy supply, and reduces the thickness of the strain sensor substrate to improve the sensitivity of intraocular pressure (IOP) monitoring, ultimately achieving the best system performance output. At the same time, the electrolyte of the capacitor adopts salt ions inherent in the eye such as NaCl, combined with gel electrolytes such as PVA, which has good safety when used in the eye.

Description

Technical Field

[0001] The present invention relates to an in-eye self-driven intraocular pressure monitoring device and a preparation method thereof, belonging to the technical field of flexible sensors, and specifically to an in-eye power supply capacitor, an in-eye intraocular pressure sensor and an in-eye self-driven intraocular pressure monitoring device and a preparation method thereof. Background Art

[0002] Intraocular pressure (IOP), a key physiological signal in the eye, reflects the state of aqueous humor circulation, provides a basis for the qualitative diagnosis of eye diseases, and guides individualized treatment. Glaucoma, characterized by intermittent or persistent elevations in IOP, threatens the optic nerve and visual function, but has no obvious early symptoms. IOP is the only controllable and measurable factor in glaucoma treatment. Therefore, the development of a wearable device for continuous IOP monitoring could help prevent glaucoma through early detection and avoid vision loss.

[0003] In existing technologies, intraocular pressure sensors installed in contact lenses typically rely on external power supplies via wires, making them inconvenient to wear. Integrating batteries / capacitors into contact lenses to power the sensors presents the challenge of varying the capacitor's capacitance due to changes in intraocular pressure. Furthermore, leakage of electrode materials or electrolytes from the batteries / capacitors can often cause eye damage. Summary of the Invention

[0004] The technical problem solved by the present invention is to overcome the deficiencies of the prior art and propose an in-eye self-driven intraocular pressure monitoring device and a preparation method thereof.

[0005] The technical solution of the present invention is:

[0006] An in-eye self-driven intraocular pressure monitoring device, which includes, from bottom to top, a second flexible packaging layer 42, a capacitor substrate 11, a sensor substrate 12, a capacitor functional unit 21, a sensor functional unit 22, an electrolyte 3, and a first flexible packaging layer 41;

[0007] The capacitor substrate 11 , the sensor substrate 12 , the capacitor functional unit 21 , the sensor functional unit 22 , and the electrolyte 3 are located between the second flexible packaging layer 42 and the first flexible packaging layer 41 ;

[0008] The capacitor functional unit 21 includes a positive electrode and a negative electrode;

[0009] The sensor function unit 22 is a resistance type sensor with a charging interface;

[0010] The capacitor substrate 11 and the sensor substrate 12 are bonded by solution phase and are located on the second flexible packaging layer 42;

[0011] The capacitor functional unit 21 is located on the capacitor substrate 11 , that is, the capacitor substrate 11 is used to support the capacitor functional unit 21 ;

[0012] The sensor functional unit 22 is located on the sensor substrate 12 , that is, the sensor substrate 12 is used to support the sensor functional unit 22 ;

[0013] The capacitor functional unit 21 is connected to the sensor functional unit 22 (integrally formed);

[0014] The electrolyte 3 is located on the capacitor functional unit 21; the electrolyte 3 is in a gel state;

[0015] The capacitor substrate 11 is thicker than the sensor substrate 12;

[0016] The capacitor substrate 11 has an electrode groove in it, and the capacitor substrate 11 is divided into two parts facing each other and crossing each other by the electrode groove; the groove width is 50 to 500 μm;

[0017] The capacitor functional unit 21 has an electrode groove therein, and the capacitor functional unit 21 is divided into two parts facing each other and intersecting each other by the electrode groove; the groove width is 50 to 500 μm;

[0018] The capacitor substrate 11 and the sensor substrate 12 are made of polymer film material;

[0019] The capacitor functional unit 21 and the sensor functional unit 22 are made of two-dimensional nanosheet conductive materials such as MXene and graphene;

[0020] The electrolyte 3 is in gel form and includes salt ions and polymers. The salt ions include but are not limited to Na + , K + and Zn 2+ etc., polymers include but are not limited to polyvinyl alcohol (PVA);

[0021] The materials used for the second flexible encapsulation layer 42 and the first flexible encapsulation layer 41 include, but are not limited to, polydimethylsiloxane (PDMS), waterborne polyurethane (WPU), hydrogel, and the like.

[0022] The thickness of the in-eye self-driven intraocular pressure monitoring device is 100 to 400 μm;

[0023] The thickness of the capacitor substrate 11 is 50 to 200 μm;

[0024] The sensor substrate 12 has a thickness of 10 to 80 μm and a width of 0.1 to 3 mm;

[0025] The capacitor functional unit 21 and the sensor functional unit 22 have the same thickness, both of which are 0.1 to 10 μm;

[0026] The capacitor substrate 11 has the same shape as the capacitor functional unit 21, including but not limited to a finger shape and a ring shape;

[0027] The capacitor substrate 11 and the sensor substrate 12 are made of the same material, including but not limited to polymer films such as polyethylene terephthalate (PET), polyimide (PI) and polyvinylidene fluoride (PVFD);

[0028] A method for preparing an in-eye self-driven intraocular pressure monitoring device, comprising:

[0029] S1: Spin-coating a polymer solution on a clean glass sheet a, drying to obtain a polymer film a, and then laser-etching the outlines of the capacitor substrate 11 and the sensor substrate 12 on the polymer film a;

[0030] S2: Spin-coating the polymer solution on a clean glass sheet b, drying to obtain a polymer film b, and then laser-etching the outline of the sensor substrate 12 on the polymer film b;

[0031] S3: Remove the sensor substrate 12 on the glass sheet a, place the sensor substrate 12 on the glass sheet b in the position of the sensor substrate 12 on the glass sheet a, and connect the polymer film b (i.e., the sensor substrate 12) to the capacitor substrate 11 via the polymer solution; the thickness of the polymer film b is smaller than that of the polymer film a;

[0032] S4: spraying a functional material on the sensor substrate 12 on the glass sheet a to form a sensor functional unit 22, and spraying a functional material on the capacitor substrate 11 to form a capacitor functional unit 21. After spraying, the polymer film and functional material outside the outlines of the sensor substrate 12 and the capacitor substrate 11 are removed, that is, only the sensor substrate 12 and the capacitor substrate 11 as well as the capacitor functional unit 21 and the sensor functional unit 22 are retained;

[0033] S5: Spin-coating a water-soluble film on the capacitor functional unit 21 and the sensor functional unit 22, and removing the film together with the sensor substrate 12, the capacitor substrate 11, the capacitor functional unit 21, and the sensor functional unit 22 after drying;

[0034] S6: applying a packaging material onto the hemispherical mold and drying the material to obtain a first flexible packaging layer 41;

[0035] S7: The product removed in step S5 is rinsed vertically with water above the first flexible packaging layer 41 obtained in step S6, and the sensor substrate 12 and the capacitor substrate 11 as well as the capacitor functional unit 21 and the sensor functional unit 22 are transferred to the first flexible packaging layer 41;

[0036] S8: Applying gel electrolyte 3 on the capacitor functional unit 21;

[0037] S9: A packaging material is drop-coated on the product obtained in step S7 and dried to obtain a second flexible packaging layer 42 located above the product, thereby completing the preparation of the in-eye self-driven intraocular pressure monitoring device.

[0038] In step S1, the polymer solution is spin-coated at a speed of 100-3000 rpm for 5-20 s;

[0039] In step S1, the polymer film is dried at a temperature of 30-90° C. for 10-30 minutes.

[0040] In step S1 , the laser is used to write the outline of the substrate at a speed of 1000 to 3000 mm / s, a current of 1 to 5 amps, and a number of times of 1 to 10 times.

[0041] In step S3, when spraying the functional material, the glass plate should be placed on a heating table at a temperature of 50-80°C, and the distance between the spray gun and the glass plate should be 20-40 cm.

[0042] In step S4, the water-soluble film is polyethylene oxide (PEO), polyvinyl alcohol (PVA), etc.;

[0043] In step S4, the rotation speed of the spin coating water-soluble film is 100-1000 rpm, and the time is 5-10 s;

[0044] In step S4, the water-soluble film is dried at a temperature of 30-60° C. for 10-30 minutes.

[0045] In step S5, the packaging material is dried at a temperature of 90-150° C. for 10-30 minutes.

[0046] Beneficial effects

[0047] The present invention proposes a method for preparing an in-eye, self-powered intraocular pressure monitoring device by laser direct writing-assisted spray coating on a hemispherical deformable encapsulation layer, followed by water transfer technology. The substrate achieves stress redistribution through a thickness partitioning strategy. The thickness of the capacitor region substrate is increased to improve energy supply stability, while the thickness of the strain sensor substrate is reduced to increase the sensitivity of intraocular pressure (IOP) monitoring, ultimately achieving optimal system performance output. Furthermore, the capacitor electrolyte uses salt ions inherent in the eye, such as NaCl, combined with a gel electrolyte such as PVA, ensuring excellent safety for intraocular use. BRIEF DESCRIPTION OF THE DRAWINGS

[0048] Figure 1 2 is a schematic diagram of the structure of the self-driven intraocular pressure monitoring device according to an embodiment of the present invention;

[0049] Figure 2 Schematic diagram of the manufacturing process of the in-eye self-driven intraocular pressure monitoring device according to an embodiment of the present invention;

[0050] Figure 3 a is the thickness of the P(VDF-TrFE) substrate prepared at 1500 rpm and 500 rpm in an embodiment of the present invention and the finite element simulation under a tensile stress of 50 kPa;

[0051] Figure 3 b is the stress-strain curve of the P (VDF-TrFE) substrate with a width of 200 μm prepared at rotation speeds of 1500 rpm and 500 rpm in an embodiment of the present invention;

[0052] Figure 3 c is a curve showing the change in resistance of a functional unit prepared on a P(VDF-TrFE) substrate with a width of 200 μm and prepared at rotation speeds of 1500 rpm and 500 rpm as a function of tensile stress in an embodiment of the present invention;

[0053] Figure 4 a is the CV curve of the capacitor at different scan rates in an embodiment of the present invention;

[0054] Figure 4 b is a curve showing the change of area specific capacitance and capacitance retention rate of the capacitor at different scan rates according to the embodiment of the present invention;

[0055] Figure 5 Schematic diagram of an intraocular pressure simulation test platform constructed in an embodiment of the present invention;

[0056] Figure 6 a is a dynamic step response curve of the intraocular pressure sensor in an embodiment of the present invention;

[0057] Figure 6 b is a curve of resistance change (ΔR) and pressure change of the intraocular pressure sensor in the rising and falling stages according to an embodiment of the present invention;

[0058] Figure 7 a is a three-dimensional finite element simulation of the forces on the substrate in the in-eye self-driven intraocular pressure monitoring device according to an embodiment of the present invention;

[0059] Figure 7 b is the CV curve of the capacitor under different intraocular pressures in the embodiment of the present invention at a sweep rate of 50 mV / s;

[0060] Figure 7 c is the periodic response of the capacitor-driven intraocular pressure sensor to pressures ranging from 0 to 21 mmHg in an embodiment of the present invention;

[0061] Figure 7d is the periodic response of the intraocular pressure sensor driven by a voltage of 0.5 V to a pressure of 0 to 21 mmHg in an embodiment of the present invention. DETAILED DESCRIPTION

[0062] In order to make the objectives, technical solutions and advantages of the present invention more clearly understood, the present invention is further described in detail below in combination with specific embodiments and with reference to the accompanying drawings, but this should not be construed as limiting the scope of protection of the present invention.

[0063] Example 1

[0064] like Figure 1 As shown, an in-eye self-driven intraocular pressure monitoring device includes, from bottom to top, a second flexible packaging layer 42, a capacitor substrate 11, a sensor substrate 12, a capacitor functional unit 21, a sensor functional unit 22, an electrolyte 3, and a first flexible packaging layer 41;

[0065] The capacitor substrate 11 , the sensor substrate 12 , the capacitor functional unit 21 , the sensor functional unit 22 , and the electrolyte 3 are located between the second flexible packaging layer 42 and the first flexible packaging layer 41 ;

[0066] The capacitor functional unit 21 includes a positive electrode and a negative electrode;

[0067] The sensor function unit 22 is a resistance type sensor with a charging interface;

[0068] The capacitor substrate 11 and the sensor substrate 12 are bonded together by a P(VDF-TrFE) polymer solution and are located on top of the second flexible encapsulation layer 42;

[0069] The capacitor functional unit 21 is located on the capacitor substrate 11 , that is, the capacitor substrate 11 is used to support the capacitor functional unit 21 ;

[0070] The sensor functional unit 22 is located on the sensor substrate 12 , that is, the sensor substrate 12 is used to support the sensor functional unit 22 ;

[0071] The capacitor functional unit 21 is connected to the sensor functional unit 22 (integrally formed);

[0072] The electrolyte 3 is located on the capacitor functional unit 21; the electrolyte 3 is in a gel state;

[0073] The thickness of the capacitor substrate 11 is 150 μm, and the thickness of the sensor substrate 12 is 50 μm and the width is 1 mm;

[0074] The capacitor substrate 11 has the same shape as the capacitor functional unit 21, which is a finger-shaped;

[0075] The capacitor substrate 11 has an electrode groove in it, and the capacitor substrate 11 is divided into two parts facing each other and crossing each other by the electrode groove; the groove width is 100 μm;

[0076] The capacitor functional unit 21 has an electrode groove in it, and the capacitor functional unit 21 is divided into two parts facing each other and crossing each other by the electrode groove; the groove width is 100 μm;

[0077] The capacitor substrate 11 and the sensor substrate 12 are made of P(VDF-TrFE) polymer material;

[0078] The capacitor functional unit 21 and the sensor functional unit 22 are made of MXene two-dimensional nanosheet conductive material;

[0079] The electrolyte 3 is in gel form and contains NaCl and polyvinyl alcohol (PVA);

[0080] The material used for the second flexible encapsulation layer 42 and the first flexible encapsulation layer 41 is polydimethylsiloxane (PDMS);

[0081] A method for preparing an in-eye self-driven intraocular pressure monitoring device, such as Figure 2 ,include:

[0082] S1: A P(VDF-TrFE) polymer solution was spin-coated on a clean glass slide a at 500 rpm for 10 seconds and dried at 30°C for 20 minutes to obtain a P(VDF-TrFE) polymer film a. The contours of the capacitor substrate 11 and the sensor substrate 12 were then etched on the P(VDF-TrFE) polymer film using a laser at a speed of 1000 mm / s and a current of 1 amp. The width of the sensor substrate 12 was 200 μm. The thickness of the P(VDF-TrFE) polymer film a was 193.25 μm.

[0083] In step S1, the solvent of the P(VDF-TrFE) polymer solution is dimethylformamide (DMF) with a concentration of 10%;

[0084] S2: The P(VDF-TrFE) polymer solution was spin-coated on a glass slide b at a speed of 1500 rpm for 10 seconds and dried at 30°C for 15 minutes to obtain a P(VDF-TrFE) polymer film b. The thickness of the P(VDF-TrFE) polymer film b was 37.68 μm. The outline of the sensor substrate 12 (the width of the sensor substrate 12 was 200 μm) was then laser-etched on the polymer film b.

[0085] S3: Remove the sensor substrate 12 on the glass sheet a, place the sensor substrate 12 on the glass sheet b on the position of the sensor substrate 12 on the glass sheet a, and connect the polymer film b, i.e., the sensor substrate 12, and the capacitor substrate 11 via the P(VDF-TrFE) polymer solution;

[0086] S4: Place the glass sheet a on a heating platform at a temperature of 60°C, with the spray gun at a distance of 20 cm from the glass sheet, and spray Ti3C2T on the sensor substrate 12 on the glass sheet. X MXene functional material forms the sensor functional unit 22, and Ti3C2T is sprayed on the capacitor substrate 11. X The MXene functional material forms the capacitor functional unit 21. After spraying, the polymer film and functional material outside the outline of the sensor substrate 12 and the capacitor substrate 11 are removed, that is, only the sensor substrate 12 and the capacitor substrate 11 as well as the capacitor functional unit 21 and the sensor functional unit 22 are retained;

[0087] In step S4, Ti3C2T X The concentration of MXene material was 2 mg / ml and the volume was 2 ml;

[0088] S5: Spin-coat a layer of polyethylene oxide (PEO) solution on the capacitor functional unit 21 and the sensor functional unit 22 at a speed of 300 rpm for 10 seconds, dry at 30° C. for 20 minutes, and then remove the sensor substrate 12, the capacitor substrate 11, the capacitor functional unit 21, and the sensor functional unit 22 together;

[0089] S6: drop-coating the PDMS solution on the hemispherical mold and drying it at 90° C. for 30 min to obtain a first flexible encapsulation layer 41;

[0090] S7: The product removed in step S5 is rinsed vertically with water above the first flexible packaging layer 41 obtained in step S6, and the sensor substrate 12 and the capacitor substrate 11 as well as the capacitor functional unit 21 and the sensor functional unit 22 are transferred to the first flexible packaging layer 41;

[0091] S8: Applying NaCl gel electrolyte 3 on the capacitor functional unit 21;

[0092] In step S8, the concentration of NaCl is 0.3M, and the gel is polyvinyl alcohol (PVA) with a concentration of 10%;

[0093] S9: PDMS packaging material is drop-coated on the product obtained in step S7 and dried at 90° C. for 30 minutes to obtain a second flexible packaging layer 42 located above the product, thereby completing the preparation of the in-eye self-driven intraocular pressure monitoring device.

[0094] Finite element simulation is performed on the sensor substrate 12 formed by the polymer film a in step S1 and the sensor substrate 12 formed by the polymer film b in step S2. Figure 3 The results of a show that, when the same stress is applied, the stress absorption of the sensor substrate 12 formed of the polymer film b (37.68 μm) is more prominent than that of the sensor substrate 12 formed of the polymer film a (193.25 μm).

[0095] The sensor substrate 12 formed by the polymer film a in step S1 and the sensor substrate 12 formed by the polymer film b in step S2 were subjected to a tensile test respectively, with a pause of 5 seconds for each 10KPa increase in stress. Figure 3 The stress-strain curve of b shows that under the same stress tension, the displacement change of the sensor substrate 12 formed of the polymer film b (37.68 μm) is larger than that of the sensor substrate 12 formed of the polymer film a (193.25 μm).

[0096] The Ti3C2T on the sensor substrate 12 formed by the polymer film a in step S1 and the sensor substrate 12 formed by the polymer film b in step S2 are respectively X The MXene functional material is used to form the sensor functional unit 22 for electrochemical testing. A stress of 10 kPa and a pause of 5 seconds are applied to the sensor substrate 12 and the sensor functional unit 22, and the output current of the sensor functional unit 22 is measured during the stress application process. Figure 3 The sensitivity-stress curve in c shows that the sensor functional unit 22 on the polymer film a (37.68 μm) in step S1 has a higher sensitivity than the sensor functional unit 22 on the polymer film b (193.25 μm) in step S2;

[0097] In some embodiments of the present invention, it is known that under the action of the same stress, the displacement change of a thicker substrate is smaller, which is suitable for the substrate of a capacitor, and can avoid the change of the capacitor capacity when the eyeball is deformed; the displacement change of a thinner substrate is larger, which is suitable for the substrate of an intraocular pressure sensor, and can improve the sensitivity of the functional unit.

[0098] The capacitor composed of the capacitor substrate 11 obtained in step S1, the capacitor functional unit 21 obtained in step S4, and the NaCl gel electrolyte 3 applied in step S8 is subjected to an electrochemical performance test, including:

[0099] The electrochemical workstation and the capacitor were connected by wires. The test environment temperature was room temperature. The cyclic voltammetry curves (IV curves, Figure 4a), the optimal voltage window of the capacitor is 0-1.4 V, the curve is quasi-rectangular, and no polarization phenomenon occurs in the curve as the scan rate increases.

[0100] Depend on Figure 4 a further calculated the area specific capacitance of the capacitor, by Figure 4 As shown in b, when the scan rate is 5mV / s, the area specific capacitance is 32mF / cm 2 When the scan rate increases from 5mV / s to 125mV / s, the area specific capacitance can still reach 53.6% of the area specific capacitance at 5mV / s.

[0101] The electrochemical performance test of the sensor composed of the sensor substrate 12 obtained in step S2 and the sensor functional unit 22 obtained in step S4 is performed, including:

[0102] Build an intraocular pressure testing platform ( Figure 5 ), consists of a simulated eyeball, a lifting motor, a liquid bag, a pressure gauge and a test original meter; the liquid bag is suspended on the lift and moves with the lift to control the height of the liquid bag; the liquid bag is connected to the simulated eyeball, and the pressure in the simulated eyeball is controlled by changing the height of the liquid bag; the other end of the simulated eyeball is connected to the pressure gauge to test the pressure in the simulated eyeball; the in-eye self-driven intraocular pressure monitoring device obtained in step S9 is placed on the simulated eyeball to sense the pressure changes in the simulated eyeball; the test original meter is connected to the in-eye self-driven intraocular pressure monitoring device obtained in step S9 to power the sensor composed of the sensor substrate 12 obtained in step S2 and the sensor functional unit 22 obtained in step S4, and then collects the corresponding output voltage of the device.

[0103] The sensor composed of the sensor substrate 12 obtained in step S2 and the sensor functional unit 22 obtained in step S4 is powered by the test original meter. The height of the liquid bag is changed by the elevator to control the dynamic step of the pressure in the simulated eyeball within the range of 0-50 mmHg, that is, the pressure is paused for 10 seconds every time it rises by 6.25 mmHg. Figure 6 The sensor's resistance change (a) closely matches the pressure change, demonstrating its excellent responsivity. The symmetrical distribution of the rising and falling parts further confirms the sensor's excellent deformation recovery capability.

[0104] right Figure 6 The pressure and resistance changes at each pause in a are linearly fitted. Figure 6 The fitting curve of resistance change versus pressure in b shows that there is an excellent linear relationship between the resistance change of the sensor and the pressure during the application of increasing and decreasing pressure. The sensitivity of the sensor composed of the sensor substrate 12 obtained in step S2 and the sensor functional unit 22 obtained in step S4 is 0.014 mmHg-1 , the linear regression coefficient of the rising process (R 2 ) is 0.99612, and the linear regression coefficient of the descending process (R 2 The similar sensitivity of the two processes indicates that the IOP sensor has good reproducibility and stability, showing the potential of the sensor in practical applications.

[0105] Finite element simulation and electrochemical testing were performed on the obtained in-eye self-driven intraocular pressure monitoring device, including:

[0106] The capacitor substrate 11 obtained in step S1 and the sensor substrate 12 obtained in step S2 are subjected to three-dimensional finite element simulation on the two substrates connected in step S3. The plastic region of the capacitor substrate is formed by a wide and thick P (VDF-TrFE) film, and the elastic region of the intraocular pressure sensor substrate is formed by a narrow and thin P (VDF-TrFE) film. Figure 7 Figure a shows that the elastic zone formed by the sensor substrate 12 obtained in step S2 allows for more pronounced stress concentration, enabling rapid response to various minor stresses, while the plastic zone formed by the capacitor substrate 11 obtained in step S1 does not experience further deformation under stress. Therefore, the P(VDF-TrFE) substrate width and thickness division strategy enables stable voltage drive of the capacitor in the in-eye self-driven intraocular pressure monitoring device, resulting in satisfactory sensitivity of the intraocular pressure sensor.

[0107] The capacitor composed of the capacitor substrate 11 obtained in step S1, the capacitor functional unit 21 obtained in step S4, and the NaCl gel electrolyte 3 applied in step S8 in the in-eye self-driven intraocular pressure monitoring device obtained in step S9 is tested for electrochemical performance changes with simulated intraocular pressure. Figure 7 b The current-voltage change curves (IV curves) under intraocular pressures of 0 mmHg, 10 mmHg, 20 mmHg, 30 mmHg, 40 mmHg and 50 mmHg were obtained. The curve shapes under different pressures were almost the same, indicating that it can continuously power the intraocular pressure sensor.

[0108] Furthermore, the electrochemical performance of the sensor composed of the sensor substrate 12 obtained in step S2 and the sensor functional unit 22 obtained in step S4 in the in-eye self-driven intraocular pressure monitoring device obtained in step S9 was tested. The sensor was powered by a capacitor composed of the capacitor substrate 11 obtained in step S1, the capacitor functional unit 21 obtained in step S4, and the NaCl gel electrolyte 3 applied in step S8. When the pressure in the simulated eye changed back and forth within the range of 0-21 mmHg, the sensitivity of the capacitor-driven sensor was similar to that of the 0.5 V voltage-driven sensor, as shown in FIG. Figure 7c, d. At the same time, it was confirmed that the hemispherical integrated device can be used for real-time monitoring of eye health, providing convenient services for high IOP diseases such as glaucoma.

[0109] In summary, the above are only preferred embodiments of the present invention and are not intended to limit the scope of protection of the present invention. Any modifications, equivalent replacements, 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. An in-eye self-driven intraocular pressure monitoring device, characterized by: The intraocular pressure monitoring device comprises, from bottom to top, a second flexible packaging layer (42), a capacitor substrate (11), a sensor substrate (12), a capacitor functional unit (21), a sensor functional unit (22), an electrolyte (3), and a first flexible packaging layer (41); The capacitor substrate (11), the sensor substrate (12), the capacitor functional unit (21), the sensor functional unit (22), and the electrolyte (3) are located between the second flexible packaging layer (42) and the first flexible packaging layer (41); The capacitor functional unit (21) includes a positive electrode and a negative electrode; The sensor functional unit (22) is a resistance type sensor having a charging interface; The capacitor substrate (11) and the sensor substrate (12) are bonded via a solution phase and are located on top of the second flexible packaging layer (42); The capacitor functional unit (21) is located on the capacitor substrate (11); The sensor functional unit (22) is located on the sensor substrate (12); The capacitor functional unit (21) is connected to the sensor functional unit (22); The electrolyte (3) is located on the capacitor functional unit (21), and the electrolyte (3) is in a gel state; The capacitor substrate (11) is thicker than the sensor substrate (12); An electrode groove A is provided in the capacitor substrate (11), and the capacitor substrate (11) is divided into two parts facing each other and intersecting each other by the electrode groove A; the groove A has a width of 50 to 500 μm; An electrode groove B is provided in the capacitor functional unit (21), and the capacitor functional unit (21) is divided into two parts facing each other and intersecting each other by the electrode groove B; the width of the groove B is 50 to 500 μm.

2. The in-eye self-driven intraocular pressure monitoring device according to claim 1, characterized in that: The capacitor substrate (11) and the sensor substrate (12) are made of polymer film material.

3. The in-eye self-driven intraocular pressure monitoring device according to claim 1 or 2, characterized in that: The capacitor functional unit (21) and the sensor functional unit (22) are made of MXene or graphene two-dimensional nanosheet conductive material.

4. The in-eye self-driven intraocular pressure monitoring device according to claim 1, characterized in that: The electrolyte (3) consists of salt ions and polymers. The salt ions are Na + , K + or Zn 2+ , the polymer is polyvinyl alcohol.

5. The in-eye self-driven intraocular pressure monitoring device according to claim 1, characterized in that: The materials used for the second flexible encapsulation layer (42) and the first flexible encapsulation layer (41) are polydimethylsiloxane, aqueous polyurethane or hydrogel.

6. The in-eye self-driven intraocular pressure monitoring device according to claim 1, characterized in that: The thickness of the in-eye self-driven intraocular pressure monitoring device is 100 to 400 μm; The capacitor substrate (11) has a thickness of 50 to 200 μm; The sensor substrate (12) has a thickness of 10 to 80 μm and a width of 0.1 to 3 mm; The capacitor functional unit (21) and the sensor functional unit (22) have the same thickness, both of which are 0.1 to 10 μm; The capacitor substrate (11) and the capacitor functional unit (21) have the same shape; The capacitor substrate (11) and the sensor substrate (12) are made of the same material, namely, polyethylene terephthalate, polyimide or polyvinylidene fluoride.

7. A method for preparing an in-eye self-driven intraocular pressure monitoring device, characterized in that The steps include: S1: Spin-coating a polymer solution on a glass sheet a, drying to obtain a polymer film a, and then laser-etching the outlines of the capacitor substrate (11) and the sensor substrate (12) on the polymer film a; S2: Spin-coating a polymer solution on a glass sheet b, drying to obtain a polymer film b, and then laser-etching the outline of the sensor substrate (12) on the polymer film b; S3: removing the sensor substrate (12) on the glass sheet a, placing the sensor substrate (12) on the glass sheet b at the position of the sensor substrate (12) on the glass sheet a, and then connecting the sensor substrate (12) on the glass sheet a to the capacitor substrate (11) via a polymer solution; the thickness of the polymer film b is smaller than the thickness of the polymer film a; S4: spraying a functional material on the sensor substrate (12) on the glass sheet a to form a sensor functional unit (22), and spraying a functional material on the capacitor substrate (11) to form a capacitor functional unit (21), and after spraying is completed, removing the polymer film and functional material outside the outline of the sensor substrate (12) and the capacitor substrate (11), that is, only retaining the sensor substrate (12) and the capacitor substrate (11) as well as the capacitor functional unit (21) and the sensor functional unit (22); S5: Spin-coating a water-soluble film on the capacitor functional unit (21) and the sensor functional unit (22), and removing the sensor substrate (12), the capacitor substrate (11), the capacitor functional unit (21), and the sensor functional unit (22) together after drying; S6: drop-coating the encapsulation material on the hemispherical mold and drying it to obtain a first flexible encapsulation layer (41); S7: The product removed in step S5 is vertically rinsed with water above the first flexible packaging layer (41) obtained in step S6, and the sensor substrate (12) and the capacitor substrate (11) as well as the capacitor functional unit (21) and the sensor functional unit (22) are transferred to the first flexible packaging layer (41); S8: applying a gel electrolyte (3) on the capacitor functional unit (21); S9: A packaging material is drop-coated on the product obtained in step S7 and dried to obtain a second flexible packaging layer (42) located above the product, thereby completing the preparation of the in-eye self-driven intraocular pressure monitoring device.

8. The method for preparing the in-eye self-driven intraocular pressure monitoring device according to claim 7, characterized in that: In step S1, the polymer solution is spin-coated at a speed of 100-3000 rpm for 5-20 s; In step S1, the polymer film is dried at a temperature of 30-90°C for 10-30 minutes; In step S1 , the laser is used to write the outline of the substrate at a speed of 1000 to 3000 mm / s, a current of 1 to 5 amps, and a number of times of 1 to 10 times.

9. The method for preparing the in-eye self-driven intraocular pressure monitoring device according to claim 7, characterized in that: In step S4, when spraying the functional material, the glass sheet a should be placed on a heating table at a temperature of 50-80° C., and the distance between the spray gun and the glass sheet a should be 20-40 cm.

10. The method for preparing the in-eye self-driven intraocular pressure monitoring device according to claim 7, characterized in that: In step S5, the water-soluble film is polyethylene oxide or polyvinyl alcohol; In step S5, the rotation speed of spin coating the water-soluble film is 100-1000 rpm, and the time is 5-10 s; In step S5, the water-soluble film is dried at a temperature of 30-60° C. for 10-30 minutes; In steps S6 and S9, the packaging material is dried at a temperature of 90-150° C. for 10-30 minutes.

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