A continuous intraocular pressure detection device and a method for measuring the same

Abstract

The present invention discloses a continuous intraocular pressure detection device and a measurement method thereof; the device comprises a glasses body, an invisible intraocular pressure sensor and a signal processing module. The invisible intraocular pressure sensor comprises a sensor body. An optical correction area, a pressure deformation cavity, a sensing channel and a first inductance coil are arranged in sequence from the center to the edge in the sensor body. Liquid medium is stored in the pressure deformation cavity. The sensing channel is connected to the pressure deformation cavity. The impedance value of the sensing channel changes with the change in the volume of the liquid medium entering the sensing channel. The first inductance coil is connected to the sensing channel to form a closed loop. The present invention implants a sensing channel in a flexible corneal contact lens, and uses intraocular pressure changes to adjust the volume of the liquid medium in the sensing channel, thereby adjusting the impedance value of the sensing channel to realize intraocular pressure monitoring. It has the characteristics of being non-invasive and wearable, and can realize dynamic and continuous monitoring of intraocular pressure.

Description

Technical Field

[0001] The present invention belongs to the technical field of intraocular pressure detection for non-diagnostic purposes, and specifically relates to a continuous intraocular pressure detection device and a measurement method thereof, which consists of two parts: a contact lens intraocular pressure sensor and a signal processing module. The principle of the intraocular pressure sensor is that the pressure deformation cavity is deformed by the intraocular pressure, and the internal liquid is squeezed into the sensing channel to cause the impedance value (capacitance or resistance) to change, and then the signal is transmitted to the outside through the coil. The glasses frame part collects the signal through the coil on the lens, and processes the signal in the microprocessor part and converts it into intraocular pressure. The present invention has the characteristics of non-invasive and wearable, and can continuously monitor intraocular pressure for 24 hours. Background Art

[0002] Intraocular pressure plays a very important role in eye health. Normal intraocular pressure can not only maintain the stability of the eyeball, but also maintain good optical quality and ensure normal metabolic processes in the eye. Under pathological conditions, excessive or low intraocular pressure can damage eye health. For example, pathological increase in intraocular pressure is the main risk factor for glaucoma. Increased intraocular pressure causes optic nerve damage through two mechanisms: mechanical compression and optic nerve ischemia. Therefore, intraocular pressure monitoring is of great significance.

[0003] The current intraocular pressure measurement mainly relies on intraocular pressure detection equipment in hospitals. Although it can directly obtain accurate values ​​of intraocular pressure, it requires special personnel to measure it. It is not only large in size and poor in portability, but also cannot achieve 24-hour continuous dynamic monitoring of intraocular pressure. For invasive intraocular pressure sensors, although they are highly accurate and can detect continuously, implanting them in the eyes will cause certain trauma to patients. Summary of the invention

[0004] The object of the present invention is to provide a continuous intraocular pressure detection device and a measurement method thereof.

[0005] A continuous intraocular pressure detection device includes a pair of glasses, an invisible intraocular pressure sensor and a signal processing module. The invisible intraocular pressure sensor includes a sensor body. The sensor body is provided with an optical correction area, a pressure deformation cavity, a sensing channel and a first inductance coil arranged in sequence from the center to the edge. A liquid medium is stored in the pressure deformation cavity. The sensing channel is connected to the pressure deformation cavity. The impedance value of the sensing channel changes with the change of the volume of the liquid medium entering the sensing channel. The first inductance coil is connected to the sensing channel to form a closed loop.

[0006] The signal processing module includes a second inductor located on the lens of the glasses body, a voltage-dividing resistor, an AC power supply and a data acquisition processing module located on the frame of the glasses body. The AC power supply, the voltage-dividing resistor and the second inductor are connected in series to form a closed loop. During operation, the second inductor is aligned with the first inductor to generate electromagnetic coupling. The data acquisition processing module detects the voltage value at both ends of the voltage-dividing resistor.

[0007] Preferably, the sensor body adopts a flexible corneal contact lens.

[0008] Preferably, the optical correction area is a transparent optical window.

[0009] Preferably, electrode strips are provided on opposite sides of the sensing channel.

[0010] Preferably, the material of the first inductor coil is graphene or liquid metal.

[0011] Preferably, the pressure deformation chamber comprises a plurality of concentrically arranged annular chambers; the sensing channel is in an arc shape. The center of the sensing channel coincides with the center of each annular chamber. Each annular chamber is connected to one end of the sensing channel through a radial flow channel.

[0012] Preferably, the inner diameter of the innermost circular cavity is less than or equal to 11.5 mm, and the outer diameter of the outermost circular cavity is greater than or equal to 12 mm.

[0013] Preferably, the difference between the inner and outer radii of the pressure deformation cavity is 450-680 μm. The difference between the inner and outer radii of a single annular cavity is 120 μm. The thickness of the pressure deformation cavity is 90-250 μm. The distance between two adjacent annular cavities is less than or equal to 100 μm.

[0014] Preferably, the liquid medium stored in the pressure deformation chamber is water.

[0015] Preferably, the data acquisition and processing module includes a voltage monitoring module, a signal processing module, a controller, a battery management module and a communication module. The voltage monitoring module is used to monitor the voltage across the voltage divider resistor and transmit the monitored voltage signal to the signal processing module; the signal processing module is used to process the voltage signal; the voltage signal processing process is: amplifying, filtering, and analog-to-digital conversion of the voltage signal in sequence; the digital signal output by the signal processing module is transmitted to the controller. The controller calculates the impedance value of the sensing channel based on the equivalent voltage across the monitored voltage divider, and then obtains the user's intraocular pressure.

[0016] The measurement method of the continuous intraocular pressure detection device has the following specific process: the invisible intraocular pressure sensor is worn in the user's eyes; the user's intraocular pressure changes the length of the liquid section in the sensing channel, so that the capacitance value of the sensing channel changes accordingly, and the equivalent impedance of the second inductor in the closed loop changes accordingly; the data acquisition and processing module detects the voltage amplitude U1 of the voltage divider resistor, and calculates the user's intraocular pressure value IOP based on the obtained voltage amplitude U1 as the sum of the preset intraocular pressure reference value IOP_initial (related to the relevant parameters of the invisible intraocular pressure sensor and the liquid level length) and the intraocular pressure change ΔIOP after wearing, that is, IOP = IOP_initial + ΔIOP. The intraocular pressure change ΔIOP is obtained by the following formula:

[0017]

[0018] Where U0 is the output voltage amplitude of the AC power supply; ω is the output frequency of the AC power supply; It is the initial phase of the AC power supply; is the initial phase of the voltage across the voltage divider resistor; R is the resistance value of the voltage divider resistor; Z1 is the impedance of the second inductor (7); ω is the frequency of the AC power supply; L2 is the inductance value of the second inductor (5); K is the coupling coefficient; M is the mutual inductance coefficient; L1 is the inductance value of the second inductor (7); L2 is the inductance value of the first inductor (5); C0 is the initial capacitance value of the sensing channel; E is the Young's modulus of polydimethylsiloxane, wd is the width of the annular cavity; H0 is the thickness of the pressure deformation cavity, K0 is the coefficient regarding the length change of the liquid in the sensing channel, and K1 is the coefficient regarding the capacitance change.

[0019] The beneficial effects of the present invention are:

[0020] 1. The present invention implants a sensing channel in a flexible corneal contact lens, and utilizes intraocular pressure changes to adjust the volume of the liquid medium in the sensing channel, thereby adjusting the impedance value of the sensing channel to achieve intraocular pressure monitoring. It has the characteristics of being non-invasive and wearable, and can achieve dynamic and continuous monitoring of intraocular pressure.

[0021] 2. The present invention realizes wireless detection of the capacitance value of the sensing channel in the flexible corneal contact lens by means of electromagnetic coupling, and has the characteristics of strong anti-interference ability and high precision.

[0022] 3. The structural design of the present invention is simple and lightweight, will not cause any burden to the wearer, can realize real-time monitoring of intraocular pressure for 24 hours, and does not need to be implanted in the eye, thereby improving the safety of intraocular pressure monitoring for patients. BRIEF DESCRIPTION OF THE DRAWINGS

[0023] Figure 1 This is a structural design diagram of the invisible intraocular pressure sensor of the present invention;

[0024] Figure 2 It is a structural design diagram of the signal processing module in the present invention;

[0025] Figure 3 is a cross-sectional schematic diagram of the invisible intraocular pressure sensor of the present invention;

[0026] Figure 4 is a schematic diagram of a signal processing module in the present invention;

[0027] Figure 5 This is a diagram showing the process of deformation of the pressure deformation cavity caused by changes in intraocular pressure in the present invention;

[0028] Figure 6 It is a schematic diagram of the change of the length of the liquid section in the sensing channel of the present invention;

[0029] Figure 7 The figure is an equivalent circuit diagram between the closed loop formed by the AC power supply, the voltage-dividing resistor and the second inductor and the invisible intraocular pressure sensor in the present invention. DETAILED DESCRIPTION

[0030] The present invention will be further described below in conjunction with the accompanying drawings.

[0031] like Figure 1 and 2 As shown, a continuous intraocular pressure detection device includes a glasses body, an invisible intraocular pressure sensor 1 and a signal processing module 2. The invisible intraocular pressure sensor 1 includes a sensor body. The sensor body adopts a flexible corneal contact lens for corneal adhesion, and the material is hydrogel or silicone hydrogel. An optical correction area 6 is arranged in the sensor body, as well as a pressure deformation cavity 3 surrounding the outside of the optical correction area 6, a sensing channel 4 surrounding the outside of the pressure deformation cavity 3, and a first inductance coil 5 surrounding the outside of the sensing channel 4. The optical correction area 6 is arranged at the center of the sensor body and is aligned with the pupil when in use.

[0032] The optical correction area 6 is a transparent optical window, which not only does not block the line of sight, but also plays a role in vision correction, so that the user can observe the external environment normally through vision.

[0033] like Figure 3 and 5 As shown, the pressure deformation chamber 3 can be deformed under pressure, and a liquid medium is stored inside to sense changes in intraocular pressure. The mechanism of action of the pressure deformation chamber 3 is that the increase in intraocular pressure causes the cornea to deform, which reduces the pressure volume of the pressure deformation chamber 3 and pushes the liquid inside the pressure deformation chamber 3 to flow to the sensing channel 4.

[0034] The sensing channel 4 is a device that converts intraocular pressure signals into electrical signals. It is essentially a variable capacitor or variable resistor. Its working mechanism is that when liquid enters the sensing channel, it causes a change in impedance value (capacitance or resistance). The material can be graphene or ordinary metal. In some embodiments, the sensing channel 4 is provided with two electrode strips located on opposite sides of the sensing channel 4; a liquid passage is formed between the two electrode strips, thereby forming a hollow variable capacitor structure; the capacitance value between the two electrode strips changes with the increase or decrease of the liquid medium in the liquid passage. The outer surface of the electrode strip is wrapped with insulating material to protect the electrode sheet and isolate the interference of air and other substances and improve the anti-interference ability.

[0035] The first inductor 5 is used to wirelessly transmit the signal measured by the sensing channel 4 to the outside. The material of the first inductor 5 is graphene, liquid metal or non-liquid common metal.

[0036] The signal processing module 2 is integrated into the main body of the glasses, including a second inductor 7 located on the lens of the main body of the glasses, and a voltage-dividing resistor R1, an AC power supply 8 and a data acquisition and processing module 9 located on the frame of the main body of the glasses. The AC power supply 8, the voltage-dividing resistor R1 and the second inductor 7 are connected in series to form a closed loop; during operation, the second inductor 7 is aligned with the first inductor 5 so that the first inductor 5 and the second inductor 7 are electromagnetically coupled. When the capacitance of the sensing channel 4 changes, the equivalent impedance of the second inductor 7 changes accordingly, and then the voltage on the voltage-dividing resistor R1 changes accordingly, so that the capacitance value of the sensing channel 4 can be obtained by detecting the change in the equivalent voltage U1 of the voltage-dividing resistor R1, and then the intraocular pressure value can be obtained. At the same time, the AC power supply 8 supplies power to the data acquisition and processing module 9 through a voltage stabilizing circuit to maintain the normal operation of the circuit.

[0037] The data acquisition and processing module 9 can realize signal acquisition and signal processing, and it also has a wireless transmission module inside, which can transmit the processed intraocular pressure value to a smart phone or computer through technologies such as Bluetooth, NFC or RFID.

[0038] In some embodiments, a signal amplification module is provided between the second inductor 7 and the data acquisition and processing module 9 so that the data acquisition and processing module 9 can receive slight intraocular pressure changes.

[0039] In some embodiments, the pressure deformation chamber 3 includes three concentrically arranged annular chambers; the sensing channel 4 is in an arc shape. The center of the sensing channel 4 coincides with the center of each annular chamber. Each annular chamber is connected to one end of the sensing channel 4 through a radial flow channel. The purpose of setting multiple annular chambers is that when the width of a single cavity is small, the detection effect is better; at the same time, in order to increase the volume of the pressure deformation chamber 3, multiple independent annular chambers are set.

[0040] The diameter of a normal cornea is mostly between 11.5mm and 12mm; therefore, the circular area 11.5mm to 12mm away from the center of the pupil is the junction of the cornea and the sclera. When the intraocular pressure increases, the degree of deformation is large. Therefore, the inner diameter of the innermost circular cavity is set to be less than or equal to 11.5mm, and the outer diameter of the outermost circular cavity is set to be greater than or equal to 12mm, thereby increasing the deformation of the pressure deformation cavity 3 with the change of intraocular pressure and improving the detection accuracy.

[0041] The total width of the pressure deformation cavity 3 is set between 450 and 680 μm, preferably 500 μm, and the width of a single annular cavity is preferably 120 μm; the thickness of the pressure deformation cavity 3 is between 90 and 250 μm, preferably 100 μm. The distance between two adjacent annular cavities does not exceed 100 μm, preferably 70 μm.

[0042] In this embodiment, the diameter of the invisible intraocular pressure sensor 1 is 13.5-14.5 mm, preferably 14 mm; the base curve is the radius of curvature of the contact lens, and its size is between 8 and 8.6 mm, and the preferred base curve size is 8.4 mm; the sensor thickness is less than or equal to 300 μm, preferably 300 μm.

[0043] In some embodiments, the liquid medium stored in the pressure deformation chamber 3 is a liquid harmless to the human body, and can be water or glycerin, preferably water.

[0044] In this embodiment, the inner radius r1 and the outer radius r2 of the sensing channel 4 are both less than 150 μm and less than the thickness of the pressure deformation chamber 3 . Preferably, the inner radius r1 is 80 μm and the outer radius r2 is 100 μm.

[0045] In this embodiment, the radius r3 of the inductor coil is greater than 12 mm, preferably 12.5 mm.

[0046] In this embodiment, the material of the sensor body is polydimethylsiloxane (PDMS); the pressure deformation chamber 3 is located inside the polydimethylsiloxane. PDMS (polydimethylsiloxane) has the following advantages as a strain material: 1. Flexibility and stretchability: PDMS has good flexibility and stretchability, can adapt to structures of various shapes and sizes, and can be applied to various strain measurement scenarios. 2. Biocompatibility: PDMS has good biocompatibility and can contact with biological tissues and cells without causing obvious toxicity or irritation, which makes it have a wide range of application potential in biomedical strain measurement and biosensors.

[0047] In some embodiments, the electrodes on the sensing channel 4 (variable capacitor or variable resistor) are made of graphene material. Graphene has high conductivity, so graphene as a cylindrical hollow capacitor or cylindrical hollow resistor material can effectively conduct current and reduce resistance loss.

[0048] In some embodiments, the first inductor 5 uses graphene or liquid metal. Among them, liquid metal as an inductor material has the following advantages: 1. High conductivity: Liquid metal usually has a very high conductivity, so it can effectively conduct current and reduce resistance loss. 2. High magnetic permeability: Liquid metal usually has a high magnetic permeability, which means that it can effectively generate and store magnetic fields, making the inductor have a higher inductive capacity. 3. Low resistance loss: Due to the good conductivity of liquid metal, the inductor made of the inductor can have a lower resistance loss, improving the efficiency of energy transmission.

[0049] like Figure 4 As shown, the data acquisition and processing module in this embodiment includes a voltage monitoring module, a signal processing module, a controller, a battery management module and a communication module. The voltage monitoring module is mainly used to monitor the voltage across the resistor and transmit the monitored voltage signal to the signal processing module; the signal processing module is mainly used to process the voltage signal, specifically to first amplify the voltage signal (a differential amplifier can be used to eliminate distortion), then filter it through a filter (noise can be eliminated and signal distortion can be reduced), and finally convert the processed analog signal into a digital signal and transmit it to the controller. The controller calculates the intraocular pressure according to the corresponding algorithm. The communication module uses wireless transmission technology, such as Bluetooth, NFC, RFID, etc., to wirelessly transmit the intraocular pressure data to the host computer (such as a smart phone or PC). The battery management module is mainly used to maintain the normal operation of the controller and the communication module.

[0050] In some embodiments, the size of the second inductor 7 is consistent with the size of the first inductor 5 .

[0051] In this embodiment, the process of converting the intraocular pressure change into an electrical signal is as follows:

[0052] A change in intraocular pressure ΔIOP will cause a change in the thickness of the pressure deformation cavity ΔH (see Figure 5 ),Right now Where H0 is the original thickness of the pressure deformation cavity, and E is the Young's modulus of polydimethylsiloxane.

[0053] The change in the thickness of the pressure deformation chamber will cause the volume of the liquid in the pressure deformation chamber to change, and the change amount is ΔV2=L0·ΔS, where Δs=wd·ΔH is the change in the cross-sectional area of ​​the pressure deformation chamber, L0=2πr0 is the length of the pressure deformation chamber, and r0 is the radius of the pressure deformation chamber.

[0054] The change in the volume of the liquid in the pressure deformation chamber ΔV2 is equal to the change in the volume of the liquid in the sensing channel 4 ΔV1. The liquid flowing into the sensing channel will increase the length of the liquid in the sensing channel by ΔD1 (see Figure 6 ),Right now make ΔD1=K0ΔS, where r1 and r2 are the inner radius and outer radius of the sensing channel, and K0 is the coefficient regarding the length change of the liquid in the sensing channel.

[0055] Liquid is the medium of the sensing channel. The change of its length in the sensing channel causes the change of the capacitance value of the sensing channel. The final capacitance value is C0 is the initial capacitance value of the sensing channel, which is related to the shape of the sensing channel and the length of the liquid in the channel and is calculated as follows: Where r1 and r2 are the inner and outer radii of the sensing channel, D0 is the length of the sensing channel, D10 is the preset length of the liquid in the sensing channel, ε0 is the dielectric constant of the air in the sensing channel, ε1 is the dielectric constant of the liquid, and That is, K1 is the capacitance variation coefficient.

[0056] The change in capacitance value will cause the loop including the inductor 5 ( Figure 7 The change in the equivalent resistance in the circuit on the left) is actually Where ω is the frequency of the AC power supply, L2 is the inductance of the inductor coil 5, K is the coupling coefficient, which is related to the coil structure, relative position and surrounding magnetic medium, and M is the mutual inductance coefficient, which is an inherent parameter of the coil.

[0057] From the equivalent circuit (see Figure 7 ), U1 is actually the voltage divider of the AC power supply, that is, Wherein Z1=jωL1 is the impedance of the inductor 7, L1 is the inductance of the inductor 7, U0 is the AC power supply voltage; U1 is the voltage across the resistor R; ω is the AC power supply frequency, and R is the resistor connected to the loop of the inductor 7.

[0058] According to U1, the actual capacitance value C of the sensing channel can be calculated, and thus the capacitance value C of the sensing channel 4 can be obtained. The expression is as follows:

[0059]

[0060] According to the above formula, the relationship between the detected electrical signal and the change in intraocular pressure is further derived, as shown in formula (1):

[0061]

[0062] Among them, U0 is the output voltage amplitude of the AC power supply; U1 is the measured voltage amplitude across the voltage divider resistor R1; ω is the AC power frequency; It is the initial phase of the AC power supply; is the initial phase of the voltage across the voltage-dividing resistor R1; R is the resistance value of the voltage-dividing resistor R1; Z1 is the impedance of the inductor 7; ω is the frequency of the AC power supply; L2 is the inductance of the second inductor 5; K is the coupling coefficient, which is related to the coil structure, relative position and surrounding magnetic medium; M is the mutual inductance coefficient, which is an inherent parameter of the coil; L1 is the inductance value of the second inductor 7; L2 is the inductance value of the first inductor 5, C0 is the initial capacitance value of the sensing channel; E is the Young's modulus of polydimethylsiloxane, wd is the width of the annular cavity; H0 is the thickness of the pressure deformation cavity, K0 is the coefficient of length change of the liquid in the sensing channel, and K1 is the capacitance change coefficient.

[0063] In this embodiment, after determining the relevant morphological parameters and material of the contact lens sensor, the preset pressure value IOP_initial of the contact lens sensor can be measured, and the actual specific intraocular pressure value IOP is the sum of the preset pressure value IOP_initial and the pressure change ΔIOP. The initial intraocular pressure of the patient is the sum of ΔIOP calculated by the first change in the liquid level length in the sensing channel after wearing and the preset pressure value IOP_initial.

[0064] In this embodiment, the intraocular pressure sensor achieves the detection accuracy of 0.1 mmHg of the commonly used commercial tonometer, the coupling coefficient K of the designed sensor is 0.5, the initial capacitance is 58 uF, the power supply voltage is 5 mV, the frequency is 1000 Hz, the initial phase is 0, the resistance R is 10 Ω, the inductance value is 1 mH, the Young's modulus of PDMS is 12 mmHg, and the mutual inductance coefficient M is 0.5 mH. The dielectric constant of air is 8.854 nF / mm, and the dielectric constant of water is 78.54 nF / mm.

Claims

1. A continuous intraocular pressure detection device, comprising a glasses body; characterized in that: It also comprises an invisible intraocular pressure sensor (1) and a signal processing module (2); the invisible intraocular pressure sensor (1) comprises a sensor body; the sensor body is provided with an optical correction area (6), a pressure deformation cavity (3), a sensing channel (4) and a first inductance coil (5) arranged in sequence from the center to the edge; a liquid medium is stored in the pressure deformation cavity (3); the sensing channel (4) is connected to the pressure deformation cavity (3); the impedance value of the sensing channel (4) changes as the volume of the liquid medium entering the sensing channel (4) changes; the first inductance coil (5) and the sensing channel (4) are connected to form a closed loop; The signal processing module (2) comprises a second inductor (7) located on the lens of the eyeglass body, and a voltage-dividing resistor, an AC power supply (8) and a data acquisition processing module (9) located on the frame of the eyeglass body; the AC power supply (8), the voltage-dividing resistor and the second inductor (7) are connected in series to form a closed loop; during operation, the second inductor (7) is aligned with the first inductor (5) to generate electromagnetic coupling; and the data acquisition processing module (9) detects the voltage value at both ends of the voltage-dividing resistor.

2. A continuous intraocular pressure detection device according to claim 1, characterized in that: The sensor body adopts a flexible corneal contact lens.

3. A continuous intraocular pressure detection device according to claim 1, characterized in that: Electrode strips are provided on opposite sides of the sensing channel (4).

4. A continuous intraocular pressure detection device according to claim 1, characterized in that: The material of the first inductor coil (5) is graphene or liquid metal.

5. A continuous intraocular pressure detection device according to claim 1, characterized in that: The pressure deformation chamber (3) comprises a plurality of concentrically arranged annular chambers; the sensing channel (4) is in an arc shape; the center of the sensing channel (4) coincides with the center of each annular chamber; each annular chamber is connected to one end of the sensing channel (4) via a radial flow channel.

6. A continuous intraocular pressure detection device according to claim 5, characterized in that: The inner diameter of the innermost circular cavity is less than or equal to 11.5 mm, and the outer diameter of the outermost circular cavity is greater than or equal to 12 mm.

7. A continuous intraocular pressure detection device according to claim 5, characterized in that: The difference between the inner and outer radii of the pressure deformation cavity (3) is 450-680 μm; the difference between the inner and outer radii of a single annular cavity is 120 μm; the thickness of the pressure deformation cavity (3) is 90-250 μm; and the distance between two adjacent annular cavities is less than or equal to 100 μm.

8. A continuous intraocular pressure detection device according to claim 1, characterized in that: The liquid medium stored in the pressure deformation chamber (3) is glycerol.

9. A continuous intraocular pressure detection device according to claim 1, characterized in that: The data acquisition and processing module includes a voltage monitoring module, a signal processing module, a controller, a battery management module and a communication module; the voltage monitoring module is used to monitor the voltage across the voltage divider resistor and transmit the monitored voltage signal to the signal processing module; the signal processing module is used to process the voltage signal; the process of voltage signal processing is: amplifying, filtering, and analog-to-digital conversion of the voltage signal in sequence; the digital signal output by the signal processing module is transmitted to the controller; the controller calculates the impedance value of the sensing channel according to the equivalent voltage across the monitored voltage divider, and then obtains the user's intraocular pressure.

10. The detection method of the continuous intraocular pressure detection device according to claim 5, characterized in that: The specific process is as follows: the invisible intraocular pressure sensor (1) is worn into the user's eye; the user's intraocular pressure changes the length of the liquid section in the sensing channel, so that the capacitance value of the sensing channel changes accordingly, and the equivalent impedance of the second inductor (7) in the closed loop changes accordingly; the data acquisition and processing module detects the voltage amplitude U1 of the voltage divider resistor, and calculates the user's intraocular pressure value IOP according to the obtained voltage amplitude U1 as follows: IOP=IOP_initial+ΔIOP ; Among them, IOP_initial is the baseline value of intraocular pressure; U0 is the output voltage amplitude of the AC power supply; ω is the output frequency of the AC power supply; It is the initial phase of the AC power supply; is the initial phase of the voltage across the voltage divider resistor; R is the resistance value of the voltage divider resistor; Z1 is the impedance of the second inductor (7); ω is the frequency of the AC power supply; L2 is the inductance value of the second inductor (5); K is the coupling coefficient; M is the mutual inductance coefficient; L1 is the inductance value of the second inductor (7); L2 is the inductance value of the first inductor (5); C0 is the initial capacitance value of the sensing channel; E is the Young's modulus of polydimethylsiloxane, wd is the width of the annular cavity; h is the thickness of the pressure deformation cavity, K0 is the coefficient of the length change of the liquid in the sensing channel, K1 is the coefficient of the capacitance change; ΔIOP is the change in intraocular pressure after insertion; U1 is the voltage amplitude of the voltage divider resistor detected by the data acquisition processing module; j is the imaginary number symbol.

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