An intraocular pressure measuring device

Abstract

The application discloses an intraocular pressure measuring device, and belongs to the technical field of intraocular pressure measuring equipment. The device comprises an in-vivo machine, which is implanted in the scleral stroma of an eyeball; the in-vivo machine is internally provided with a parallel resonant circuit which changes impedance spectrum with the change of intraocular pressure; an in-vivo machine is in communication connection with the in-vivo machine and is internally provided with a detection circuit which can receive the impedance spectrum reflected by the parallel resonant circuit; and an information processing module which identifies the resonant frequency of the parallel resonant circuit according to the impedance spectrum and obtains the intraocular pressure value according to the resonant frequency; the information processing module is electrically connected with the detection circuit. The application adopts the above-mentioned intraocular pressure measuring device, so that the measurement result is more accurate, 7*24-hour continuous measurement can be realized, the intraocular pressure condition can be monitored in real time, the measured intraocular pressure data can be uploaded to the cloud, and doctors can understand the illness condition of patients more clearly to provide more reasonable treatment plans for the patients.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of intraocular pressure measuring devices, in particular to an intraocular pressure measuring device. BACKGROUND

[0002] Glaucoma is an ophthalmic disease caused by damage to the optic nerve due to pathological elevation of intraocular pressure, resulting in visual impairment or even blindness. It is the second leading cause of blindness, next to cataract. The main cause of glaucoma is the obstruction of aqueous humor flow, which causes the intraocular pressure to rise, causing the optic nerve to be squeezed and damaged by the sclera, thereby causing visual impairment. Therefore, glaucoma patients should often pay attention to their intraocular pressure fluctuations, and should be treated in time if the intraocular pressure is abnormal to avoid further damage to the vision caused by the continuous increase of the intraocular pressure. There is currently no effective treatment for glaucoma, and only prevention is possible. Since the cause of glaucoma is mainly related to intraocular pressure, patients need to regularly check their intraocular pressure and seek medical treatment in time if the intraocular pressure is elevated or abnormal.

[0003] The current tonometer for measuring intraocular pressure generally has the problems of complicated measurement process and inaccurate measurement data. Patients often need to go to the hospital for registration and hospitalization for intraocular pressure measurement. Although some tonometers can be used at home, they are generally complicated to measure and inaccurate in measurement data, which delays the disease. In addition, when contacting the tonometer, patients have a fear in their minds, which further causes the inaccuracy of intraocular pressure measurement. In addition, the current tonometer cannot meet the real-time intraocular pressure measurement, which is an important defect of the current tonometer. The current tonometer can only measure the intraocular pressure at a certain time point, while the intraocular pressure of a person often fluctuates over time. The intraocular pressure is highest in the morning and lower in the afternoon. The current tonometer cannot obtain the intraocular pressure value of the patient continuously over time. SUMMARY

[0004] The purpose of the present application is to provide an intraocular pressure measuring device which can make the measurement result more accurate, can realize 7 24-hour continuous measurement, achieve real-time monitoring of the intraocular pressure condition and upload the measured intraocular pressure data to the cloud, so that the doctor can better understand the patient's condition and give the patient a more reasonable treatment plan.

[0005] To achieve the above purpose, the present application provides an intraocular pressure measuring device, comprising:

[0006] An in-vivo machine is implanted in the scleral stroma layer of the eyeball, and the in-vivo machine is internally provided with a parallel resonant circuit which changes the impedance spectrum with the change of the intraocular pressure;

[0007] The in-vivo machine is connected in communication with the in-vitro machine, and has a detection circuit capable of receiving the impedance spectrum reflected by the parallel resonant circuit, and an information processing module capable of identifying the resonant frequency of the parallel resonant circuit according to the impedance spectrum and obtaining the intraocular pressure value according to the resonant frequency;

[0008] The information processing module is electrically connected with the detection circuit.

[0009] Preferably, the parallel resonant circuit comprises:

[0010] A pressure-controlled variable capacitor capable of changing the capacitance value with the change of the intraocular pressure;

[0011] A first inductor electrically connected with the pressure-controlled variable capacitor, connected in communication with the in-vitro machine, and capable of reflecting the impedance spectrum of the parallel resonant circuit to the in-vitro machine with the change of the capacitance value;

[0012] The detection circuit comprises a second inductor electromagnetically coupled with the first inductor, for receiving the impedance spectrum of the parallel resonant circuit, and the second inductor is electrically connected with the detection circuit.

[0013] The in-vivo machine is provided with a flexible protective layer on the outermost side, and the parallel resonant circuit is arranged inside the flexible protective layer.

[0014] Preferably, the in-vivo machine is a disc-shaped flexible thin film pressure sensor with a diameter of 4 6mm and a thickness of 0.4 0.6mm.

[0015] Preferably, the first inductor comprises a gold wire coil, and the pressure-controlled variable capacitor is arranged at the center of the annular coil of the gold wire coil, and the pressure-controlled variable capacitor is composed of a circular pressure-sensitive thin film capacitor and a flexible electrode.

[0016] The flexible electrode is provided with two, respectively mounted on both sides of the pressure-sensitive thin film capacitor and connected with the gold wire coil.

[0017] Preferably, the flexible protective layer is wrapped with a flexible circuit board, the flexible circuit board has a shape of two circular shapes connected by a thin strip in the middle and is folded from the middle position of the thin strip to make the two circular shapes in a parallel state, the inner side of the center position of the two circular shapes on the flexible circuit board is provided with a solder pad, the flexible circuit board is filled with a flexible thin film capacitor medium in the middle, and the solder pad and the flexible thin film capacitor medium therebetween arranged in parallel constitute the pressure-controlled variable capacitor, and a copper foil coil is horizontally wound around the solder pad to constitute the first inductor.

[0018] Preferably, the solder pad is circular with a diameter of 2.48 2.52mm.

[0019] Preferably, the in-vitro machine further comprises a power management module, a lithium battery module and a display module; the second inductor is coaxially arranged with the first inductor of the in-vivo machine.

[0020] Preferably, the output voltage of the lithium battery module is between 3.7V 4.2V, and the input voltage of the second inductor is 5V.

[0021] Preferably, the mobile terminal is further included, which is connected with the in-vitro machine in a wireless communication mode to display the intraocular pressure information obtained by the in-vitro machine; and the in-vitro machine further comprises a Bluetooth module.

[0022] Preferably, the in-vivo machine is implanted in the stroma layer of the sclera between the superior rectus muscle and the lateral rectus muscle.

[0023] Therefore, the intraocular pressure measuring device has the following advantages:

[0024] (1) Small surgical damage: the flexible film pressure sensor has a diameter of 5mm and a thickness of 0.5mm, and is bendable. The implantation position is between the attachment positions of the superior rectus muscle and the lateral rectus muscle on the sclera. The incision on the sclera during the operation is small, and the patient does not need to be hospitalized.

[0025] (2) Accurate measurement: the sensor for measuring intraocular pressure is a flexible film sensor implanted in the stroma layer of the sclera, which directly measures the internal pressure of the eyeball. The measurement result is not affected by factors such as corneal thickness and tear film surface tension. At the same time, the measurement process of the intraocular pressure measuring device is continuous and unconscious. The user will not feel nervous or fearful during the measurement, and the measurement result is more real.

[0026] (3) No cross infection: the passive flexible film pressure sensor is implanted in the stroma layer of the sclera of the patient by surgery. After the operation, the measurement of the intraocular pressure of the patient is performed by the device placed outside the body to read the test data of the sensor wirelessly. During the measurement process, the external device does not have physical contact with the eyeball, and will not cause infection to the eyeball. The external device is only for one person, and there is no mutual infection between patients.

[0027] (4) 7 24-hour continuous measurement: the intraocular pressure measurement process is performed by the external device to read the pressure data measured by the in-vivo sensor wirelessly. The intraocular pressure measurement is completed without the patient's knowledge. Even if the patient is in a closed-eye resting state, the intraocular pressure measurement can still be performed normally.

[0028] (5) The measured intraocular pressure data can be uploaded to the cloud to realize real-time communication between doctors and patients: after the external device reads the intraocular pressure value, it is transmitted to the mobile terminal of the patient, such as a mobile phone, a tablet computer, etc. through Bluetooth. These mobile terminals can transmit the measurement data to the cloud through APP, and doctors can analyze the intraocular pressure data on the cloud to guide patients to reasonable treatment.

[0029] The technical solutions of the present application will be further described in detail below with the help of the accompanying drawings and examples. BRIEF DESCRIPTION OF DRAWINGS

[0030] Figure 1 is a schematic diagram of the structure of an embodiment of the intraocular pressure measuring device of the present application;

[0031] Figure 2 is a schematic diagram of the structure of the in-vivo machine of the intraocular pressure measuring device of the present application;

[0032] Figure 3 is a schematic diagram of the structure of the in-vivo machine 1 of the embodiment of the intraocular pressure measuring device of the present application;

[0033] Figure 4 is a schematic diagram of the structure of the in-vivo machine 1 of the embodiment of the intraocular pressure measuring device of the present application;

[0034] Figure 5 is a schematic diagram of the structure of the in-vivo machine 1 of the embodiment of the intraocular pressure measuring device of the present application;

[0035] Figure 6 is a schematic diagram of the implantation position of the flexible thin film pressure sensor of the intraocular pressure measuring device of the present application on the eyeball.

[0036] REFERENCE NUMERALS

[0037] In-vivo machine; 11, pressure control variable capacitor; 111, pressure sensitive thin film capacitor; 112, flexible thin film capacitor dielectric; 113, flexible electrode; 114, solder pad; 12, flexible protective layer; 121, flexible circuit board; 13, first inductor; 131, gold wire coil; 132, copper foil coil; 2, external machine; 3, mobile terminal. DETAILED DESCRIPTION

[0038] The technical solutions of the present application will be further described in detail below with the help of the accompanying drawings and examples.

[0039] Unless otherwise defined, technical terms or scientific terms used in the present application shall have the meanings that can be commonly understood by a person having ordinary skill in the art to which the present application belongs. The terms "first", "second", and similar terms in the present application do not denote any order, quantity, or importance, but are used to distinguish different components. The terms "include", "contain", and similar terms mean that the elements or objects before the terms encompass the elements or objects listed after the terms and their equivalents, and do not exclude other elements or objects. The terms "connect" or "connected" and similar terms are not limited to physical or mechanical connections, but can include electrical connections, whether direct or indirect. The terms "upper", "lower", "left", "right", and the like are used only to indicate relative positional relationships, and when the absolute positions of the described objects are changed, the relative positional relationships can also be changed accordingly.

[0040] The present application provides an intraocular pressure measuring device, comprising:

[0041] The in-vivo machine 1 is implanted in the scleral stroma layer of the eyeball, the in-vivo machine 1 is internally provided with a parallel resonant circuit which changes impedance spectrum with the change of intraocular pressure, and the in-vivo machine 1 is externally provided with a flexible protective layer 12, and the parallel resonant circuit is arranged inside the flexible protective layer 12.

[0042] The in-vivo machine 2 is in communication connection with the in-vivo machine 1, internally provided with a detection circuit which can receive the impedance spectrum reflected by the parallel resonant circuit, and an information processing module which can identify the resonant frequency of the parallel resonant circuit according to the impedance spectrum and obtain the intraocular pressure value according to the resonant frequency, and the information processing module is in electrical connection with the detection circuit.

[0043] Specifically, the parallel resonant circuit comprises:

[0044] The pressure control variable capacitor 11 can change the capacitance value with the change of intraocular pressure.

[0045] The first inductor 13 is in electrical connection with the pressure control variable capacitor 11, in communication connection with the in-vivo machine 2, and reflects the impedance spectrum of the parallel resonant circuit to the in-vivo machine 2 with the change of the capacitance value.

[0046] The detection circuit comprises:

[0047] The second inductor which is in electromagnetic coupling with the first inductor 13 is used to receive the impedance spectrum of the parallel resonant circuit, and the second inductor is in electrical connection with the detection circuit.

[0048] Specifically, the in-vivo machine 1 is a circular disc type flexible thin film pressure sensor with a diameter of 4-6 mm and a thickness of 0.4-0.6 mm.

[0049] Specifically, the first inductor 13 comprises a gold wire coil 131; a pressure-controlled variable capacitor 11 is arranged at the center of the annular coil of the gold wire coil 131, and the pressure-controlled variable capacitor 11 is composed of a circular pressure-sensitive thin film capacitor 111 and a flexible electrode 113.

[0050] The flexible electrode 113 is provided with two flexible electrodes 113, which are respectively arranged on the two sides of the pressure-sensitive thin film capacitor 111 and connected with the gold wire coil 131.

[0051] Specifically, the flexible protection layer 12 is wrapped with a flexible circuit board 121, the shape of the flexible circuit board 121 is two circular shapes connected by a thin strip in the middle, and the two circular shapes are folded at the middle position of the thin strip to be parallel to each other. The inner side of the center position of the two circular shapes on the flexible circuit board 121 is provided with a solder pad 114, and the flexible circuit board 121 is filled with a flexible thin film capacitor medium 112 in the middle. The solder pads 114 and the flexible thin film capacitor medium 112 therebetween arranged in parallel constitute the pressure-controlled variable capacitor 11. A copper foil coil 132 is horizontally wound around the solder pad 114, which constitutes the first inductor 13.

[0052] Specifically, the solder pad 114 is circular, and the diameter is 2.48-2.52 mm.

[0053] Specifically, the extracorporeal machine 2 further comprises a power management module, a lithium battery module and a display module. The second inductor is coaxially arranged with the first inductor 13 of the intracorporeal machine 1.

[0054] Specifically, the output voltage of the lithium battery module is between 3.7V and 4.2V, and the input voltage of the second inductor is 5V.

[0055] Specifically, the mobile terminal 3 is further included, and the mobile terminal 3 is connected with the extracorporeal machine 2 in a wireless communication mode to display the intraocular pressure information obtained by the extracorporeal machine. The extracorporeal machine 2 is further provided with a Bluetooth module, which can perform wireless data transmission with the mobile terminal 3.

[0056] Specifically, the implantation position of the intracorporeal machine 1 is arranged in the stroma layer of the sclera between the lateral rectus muscle and the superior rectus muscle.

[0057] The application will be further described below through specific embodiments. Embodiment one

[0058] As shown in the Figure 1 The application provides an intraocular pressure measuring device, which comprises:

[0059] The intracorporeal machine 1 is implanted in the stroma layer of the sclera of the eyeball, and the intracorporeal machine 1 is internally provided with a parallel resonant circuit which changes the impedance spectrum with the change of the intraocular pressure.

[0060] The external unit 2 is communicatively connected to the internal unit 1. The external unit 2 has a built-in detection circuit that can receive the impedance spectrum reflected by the parallel resonant circuit, and an information processing module that identifies the resonant frequency of the parallel resonant circuit based on the impedance spectrum and obtains the intraocular pressure value based on the resonant frequency. The information processing module is electrically connected to the detection circuit, so that the external unit 2 can obtain the intraocular pressure by detecting the resonant frequency of the internal unit 1.

[0061] Parallel resonant circuits include:

[0062] Pressure-controlled variable capacitor 11: Its capacitance value can be changed according to changes in intraocular pressure.

[0063] First inductor 13: Electrically connected to pressure-controlled variable capacitor 11 and communicatively connected to external unit 2, and reflects the impedance spectrum of parallel resonant circuit to external unit 2 as the capacitance value changes.

[0064] The detection circuit includes a second inductor electromagnetically coupled to the first inductor 13 for receiving the impedance spectrum of the parallel resonant circuit, and the second inductor is electrically connected to the detection circuit.

[0065] like Figure 2 As shown, the in-body unit 1 is a disc-shaped flexible thin-film pressure sensor with a diameter of 4mm and a thickness of 0.4mm. Due to the small size of the in-body unit 1, the pressure control variable capacitor 11 is small, resulting in a larger resonant frequency and thus a higher measured intraocular pressure value. This allows for very sensitive detection of changes in intraocular pressure. The relatively small size increases the difficulty of manufacturing, subsequent encapsulation, and surgical implantation, but it improves detection accuracy and enhances the user experience, eliminating the feeling of a foreign body. It is suitable for children and adults with more severe symptoms. A flexible protective layer 12 is located on the outermost side of the in-body unit 1, and the parallel resonant circuit is located inside the flexible protective layer 12.

[0066] The flexible protective layer 12 is an overlay made of silicone, a material that can be directly implanted into the human body in existing technologies. It has good biocompatibility, is non-irritating, non-toxic, non-allergenic to human tissues, and has very little rejection reaction from the body. It has good physicochemical properties and can maintain its original elasticity and softness during contact with body fluids and tissues. It is not degraded and is a fairly stable inert material. It can improve the stability of parallel resonant circuits without causing damage to the user.

[0067] like Figure 3As shown, the first inductor 13 is a gold wire coil 131 wound with gold wire, and the gold wire coil 131 is circular. The pressure-controlled variable capacitor 11 is arranged at the center of the annular coil of the gold wire coil 131, and the pressure-controlled variable capacitor 11 is composed of a circular pressure-sensitive thin film capacitor 111 and flexible electrodes 113. The flexible electrodes 113 are arranged in two, and are respectively mounted on both sides of the pressure-sensitive thin film capacitor 111 and connected with the gold wire coil 131.

[0068] As shown in FIG. 1, the in-vivo machine 1 is implanted in the sclera between the lateral rectus muscle and the superior rectus muscle. Figure 6 As shown, the implantation position of the in-vivo machine 1 is arranged in the stroma layer of the sclera between the lateral rectus muscle and the superior rectus muscle. Since the shape of the in-vivo machine 1 is circular and flexible, the surgical incision can be smaller than the diameter of the in-vivo machine 1 when implanted in the sclera stroma layer.

[0069] The sclera is located on the surface of the eyeball, and together with the cornea in front of the eyeball, it constitutes the outer wall of the eyeball. The sclera accounts for 5 / 6 of the area of the eyeball, and is milky white. The sclera is thickest at the part where the optic nerve passes out of the posterior pole of the eyeball, about 1.0 mm, and thins forward, with a thickness of 0.4-0.5 mm at the equatorial part and a thickness of 0.3 mm at the attachment of the rectus muscle. The sclera is wrapped by fascia and conjunctiva on the outside, and the anterior edge is connected to the limbus, and the posterior part is continuous with the optic nerve dural sheath. The sclera is divided from the outside to the inside into the surface layer, the stroma layer, and the brown-black layer. The surface layer is composed of loose connective tissue, connected with the fascia layer, and has relatively rich nerves and blood vessels; the stroma layer is composed of dense connective tissue and elastic fibers, with fiber synthesis bundles, intercrossing and irregular arrangement, and the whole is opaque, with fewer blood vessels and nerves; the brown-black layer has small connective tissue fiber bundles and significantly increased elastic fibers, and has a large number of pigment cells, making the inside of the sclera brown.

[0070] The implantation site of the surgery is the part of the sclera between the lateral rectus muscle and the superior rectus muscle, and the surgical process is as follows:

[0071] (1) Incise the conjunctiva on the outside of the sclera of the eyeball to expose the white sclera.

[0072] (2) Cut an incision in the part of the sclera between the attachment position of the lateral rectus muscle on the sclera and the attachment position of the superior rectus muscle on the sclera, and separate the stroma layer of the sclera in the vicinity of this part by a certain area.

[0073] (3) Insert the in-vivo machine into the sclera through the incision.

[0074] (4) Suture the incision of the sclera.

[0075] (5) Suture the incision of the conjunctiva.

[0076] The in-vitro machine 2 further comprises a power management module, a lithium battery module and a display module. The information processing module comprises a microprocessor, a direct digital synthesis (DDS) sweep signal generator and an impedance analyzer.

[0077] The second inductor of the in-vitro machine 2 is coaxially arranged with the first inductor 13 of the in-vivo machine 1, so that the second inductor is electromagnetically coupled with the first inductor 13 of the in-vivo machine 1, the impedance of the resonance circuit of the in-vivo machine 1 is reflected to the second inductor, so that the impedance spectrum of the second inductor, i.e. the impedance spectrum of the resonance circuit of the in-vivo machine 1, is obtained. The microprocessor has pre-set an algorithm for identifying the resonance frequency of the parallel resonance circuit according to the impedance spectrum and obtaining the intraocular pressure value according to the resonance frequency. When the impedance spectrum information detected by the second inductor is transmitted to the microprocessor, the calculation result can be directly transmitted to the display module for display after calculation. The microprocessor has pre-set a healthy eye pressure threshold value, and when the detected intraocular pressure is higher than the threshold value, the corresponding additional output reminder information is provided.

[0078] The display module

[0079] The display module is a display screen installed on the in-vitro machine 2, which can display the basic intraocular pressure information, and when the intraocular pressure is higher than the threshold value, the display module will also flicker to remind.

[0080] The microprocessor

[0081] The microprocessor is responsible for the management and control of all functional modules of the in-vitro machine 2, such as the frequency control of the direct digital synthesis (DDS) sweep signal generator, the impedance calculation of the impedance analyzer, and the reading and indication of the lithium battery module power by the power management module.

[0082] The power management module and the lithium battery module

[0083] The output voltage of the lithium battery module is between 3.7V and 4.2V, and the power management module is responsible for converting the voltage of the lithium battery module into the voltage required by each functional module of the in-vitro machine 2 to provide power for it. Among them, the microprocessor requires 2.5V and 1.8V, the direct digital synthesis (DDS) sweep signal generator requires 3.3V, and the second inductor requires 5V.

[0084] The power management module is also responsible for the charging management of the lithium battery module, providing overheat, overvoltage and overcurrent protection to ensure its reliable operation.

[0085] Direct digital synthesis (DDS) sweep signal generator

[0086] The direct digital synthesis (DDS) sweep signal generator generates a sinusoidal signal with a continuously variable frequency under the control of a microprocessor, the peak-to-peak voltage of the sinusoidal signal being 1V, and the frequency being between 100MHz and 500MHz. The sinusoidal signal is transmitted to the second inductor as an excitation signal, and is used to obtain the impedance of the in-vivo resonant circuit at different frequencies.

[0087] Impedance analyzer

[0088] The impedance analyzer respectively collects the voltage and current across the second inductor, digitizes them, and transmits them to the microprocessor. The microprocessor respectively performs FFT transformation on them to obtain the amplitude and phase values of the voltage and current, and the phase value of the voltage minus the phase value of the current, thereby obtaining the phase value of the impedance of the second inductor at different frequencies. The microprocessor analyzes the phase value to find the frequency point at which the extreme value of the change is located, i.e. at this frequency point, the phase value increases no matter whether the frequency increases or decreases, and this frequency point is the resonant frequency of the resonant circuit.

[0089] The mobile terminal 3 is also included, which is connected to the external machine 2 in a wireless communication manner, and can be a mobile phone or a tablet computer of the patient. The mobile terminal 3 can display more rich intraocular pressure information such as real-time intraocular pressure values, historical intraocular pressure data, and an intraocular pressure change curve over time. Meanwhile, a Bluetooth module is also correspondingly arranged in the external machine 2, and the results measured by the external machine 2 can be transmitted to the mobile terminal 3 in a wireless communication manner.

[0090] In addition, the intraocular pressure threshold value can also be set in the mobile terminal 3, and when the collected intraocular pressure value is greater than the threshold value, the mobile terminal 3 can issue a prompt sound or vibration to remind the user, and simultaneously highlight the intraocular pressure value at this time and the improvement measure suggestion given for the intraocular pressure value on the display screen. When the collected intraocular pressure value is less than the threshold value, the mobile terminal 3 only receives and stores the intraocular pressure information, and the corresponding intraocular pressure information can only be viewed when the user operates the mobile terminal 3.

[0091] The working principle of the intraocular pressure measuring device is that the pressure control variable capacitor 11 in the in-vivo machine 1 changes the capacitance value when subjected to pressure changes, thereby changing the resonant frequency of the flexible thin film pressure sensor. The in-vivo machine 2 is a resonant frequency detection circuit, which reads the impedance of the in-vivo machine 1 at different frequencies through electromagnetic induction, obtains the resonant frequency, and thereby obtains the size of the intraocular pressure. Specifically, the second inductor on the in-vivo machine 2 is electromagnetically coupled with the first inductor 13 of the in-vivo machine 1, the impedance of the in-vivo machine 1 is reflected to the in-vivo machine 2, so that the impedance of the second inductor of the in-vivo machine 2 changes, the in-vivo machine 2 measures the impedance of the second inductor at different frequencies, and according to the measured impedance of the in-vivo machine 2, the impedance of the in-vivo machine 1 at different frequencies can be obtained. The impedance is a complex number containing amplitude and phase, the in-vivo machine 2 measures the impedance of the in-vivo machine 1, when the in-vivo machine 1 resonates at a certain frequency, the phase of its impedance will reach a certain extreme value, according to this characteristic, the resonant frequency of the in-vivo machine 1 can be obtained. The corresponding relationship between the resonant frequency of the in-vivo machine 1 and the intraocular pressure is statistically obtained in advance, and according to the measured resonant frequency, the size of the intraocular pressure can be obtained through the preselected algorithm in the microprocessor.

[0092] The microprocessor on the in-vivo machine 2 sends the intraocular pressure value to the display module for display and simultaneously sends it to the patient's mobile terminal 3 through a Bluetooth signal, so that the patient can see the change rule of his own eye pressure with time in real time through the mobile terminal 3. Example two

[0093] The difference from example one is that the in-vivo machine 1 is a disc-shaped flexible thin film pressure sensor with a diameter of 5mm and a thickness of 0.5mm. Compared with example one, the size of the in-vivo machine 1 is relatively improved, the pressure control variable capacitor 11 is increased, the measured resonant frequency is reduced, the measured intraocular pressure value is low, and the accuracy of the in-vivo machine 1 in measuring the change of the intraocular pressure is decreased. In addition, the volume of the in-vivo machine 1 is increased, which reduces the manufacturing difficulty and surgical implantation difficulty of the in-vivo machine 1, but has higher requirements for the implantation position of the patient's ocular stroma layer, and is not suitable for children, but is more suitable for adults with not particularly serious illness, and does not cause discomfort to the user. Example three

[0094] The difference from example one is that the in-vivo machine 1 is a disc-shaped flexible thin film pressure sensor with a diameter of 6mm and a thickness of 0.6mm

[0095] Pressure sensor. The size of the in-vivo machine 1 is obviously increased, which makes the pressure-controlled variable capacitor 11 inside the in-vivo machine 1 larger, reduces the difficulty of manufacturing and surgical implantation, but also makes the measurement accuracy decrease. Due to the size, the requirements for the implantation position of the patient's ocular stroma layer are higher, and it is only suitable for adult patients with mild symptoms who meet the implantation requirements after measurement. Example four

[0096] The difference between this embodiment and example one is that the structure of the in-vivo machine 1 is different, as shown in Figure 4 and Figure 5 , in this embodiment, the flexible protective layer 12 of the in-vivo machine 1 is wrapped with a flexible circuit board 121, the thickness of the flexible circuit board 121 is 0.05mm, and the shape is two circular shapes connected by a thin strip in the middle, and the two circular shapes are folded at the middle position of the thin strip to make the two circular shapes parallel to each other. The inner side of the center position of the two circular shapes on the flexible circuit board 121 is provided with a solder pad 114.

[0097] The folded flexible circuit board 121 is filled with a flexible thin film capacitor medium 112, and the material of the flexible thin film capacitor medium 112 is hydrogel. The parallelly arranged solder pads 114 and the flexible thin film capacitor medium 112 therebetween constitute the pressure-controlled variable capacitor 11.

[0098] The solder pad 114 is circular, and the diameter is 2.48mm. The diameter of the solder pad 114 is smaller, so the pressure-controlled variable capacitor 11 is also smaller, which is more sensitive to the change of the resonant frequency, resulting in the increase of the final measured resonant frequency and the high measurement of the intraocular pressure value, which can improve the detection accuracy. At the same time, the size of the in-vivo machine 1 is also smaller, although it increases the difficulty of manufacturing, subsequent encapsulation and surgical implantation, but the wearer will not feel foreign body sensation, which is suitable for children and adult patients with more serious symptoms.

[0099] A copper foil coil 132 is wound around the solder pad 114 horizontally, and the thickness of the copper foil in the copper foil coil 132 is 0.01mm, which constitutes the first inductor 13. Among them, the material of the solder pad 114 and the copper foil coil 132 is copper material, which has good chemical stability and conductivity. Example five

[0100] The difference between this embodiment and example four is that the diameter of the solder pad 114 is 2.5mm. Due to the increase of the size of the solder pad 114, the pressure-controlled variable capacitor 11 is also increased, which reduces the sensitivity to the change of the resonant frequency, resulting in the decrease of the final measured resonant frequency and the decrease of the measurement of the intraocular pressure value, which slightly reduces the detection accuracy. At the same time, the size of the in-vivo machine 1 is increased, which reduces the difficulty of manufacturing, subsequent encapsulation and surgical implantation, but has higher requirements for the implantation position of the patient's ocular stroma layer, which is not suitable for children, but is more suitable for adult patients with not too serious symptoms, and the wearer will not feel foreign body sensation. Example six

[0101] Different from example four, the diameter of the pad 114 is 2.52mm. Due to the significant increase of the size of the pad 114, the pressure-controllable capacitor 11 also increases significantly, the sensitivity to the change of the resonant frequency decreases, the final measured resonant frequency decreases, the measured intraocular pressure value is lower, and the detection accuracy decreases.

[0102] The increase of the pad 114 also increases the size of the in-vivo machine 1, which reduces the difficulty of manufacturing, subsequent encapsulation and surgical implantation, but requires a higher implantation position of the patient's ocular stroma layer, and is only suitable for adult patients with mild symptoms who meet the implantation requirements after measurement.

[0103] Therefore, the intraocular pressure measuring device can make the measurement result more accurate, and the intraocular pressure measuring device can realize 7 24-hour continuous measurement, real-time monitoring of the intraocular pressure condition, and uploading of the measured intraocular pressure data to the cloud, so that the doctor can understand the patient's condition better to give the patient a more reasonable treatment plan.

[0104] Finally, it should be noted that: the above examples are only used to illustrate the technical solutions of the present application and not to limit them, although the present application has been described in detail with reference to the preferred embodiments, those skilled in the art should understand: it can still modify or equivalently replace the technical solutions of the present application, and these modifications or equivalent replacements cannot make the modified technical solutions deviate from the spirit and scope of the technical solutions of the present application.

Claims

1. An intraocular pressure measuring device, characterized in that... ,include: The in vivo device is implanted in the scleral stroma layer of the eyeball, and the in vivo device contains a parallel resonant circuit that changes its impedance spectrum in response to changes in intraocular pressure; An external unit, communicatively connected to the internal unit, includes a built-in detection circuit capable of receiving the impedance spectrum reflected by the parallel resonant circuit; and an information processing module that identifies the resonant frequency of the parallel resonant circuit based on the impedance spectrum and obtains the intraocular pressure value based on the resonant frequency. The information processing module is electrically connected to the detection circuit; The parallel resonant circuit includes: a pressure-controlled variable capacitor whose capacitance changes with intraocular pressure; The first inductor is electrically connected to the pressure-controlled variable capacitor and communicatively connected to the external unit. It reflects the impedance spectrum of the parallel resonant circuit to the external unit as the capacitance value changes. The detection circuit includes: a second inductor electromagnetically coupled to the first inductor, used to receive the impedance spectrum of the parallel resonant circuit; The outermost side of the internal organ is provided with a flexible protective layer, and the parallel resonant circuit is disposed inside the flexible protective layer. The implantation site of the in vivo device is located in the stromal layer of the sclera between the lateral rectus muscle and the superior rectus muscle of the eyeball.

2. The intraocular pressure measuring device according to claim 1, characterized in that: The internal component is a disc-shaped flexible thin-film pressure sensor with a diameter of 4-6 mm and a thickness of 0.4-0.6 mm.

3. The intraocular pressure measuring device according to claim 2, characterized in that: The first inductor includes a gold wire coil: the pressure-controlled variable capacitor is disposed at the center of the annular coil, and the pressure-controlled variable capacitor is composed of a circular pressure-sensitive film capacitor and a flexible electrode; Two flexible electrodes are provided, which are respectively installed on both sides of the pressure-sensitive film capacitor and connected to the gold wire coil.

4. The intraocular pressure measuring device according to claim 1, characterized in that: The flexible protective layer encloses a flexible circuit board, which is shaped like two circles connected by a thin strip in the middle and folded in half at the middle of the strip so that the two circles are parallel to each other. Pads are provided on the inner side of the center of each of the two circles on the flexible circuit board. The folded flexible circuit board is filled with a flexible thin-film capacitor dielectric. The parallel pads and the flexible thin-film capacitor dielectric between them constitute the pressure-controlled variable capacitor. Copper foil coils are horizontally wound around the pads, which constitute the first inductor.

5. The intraocular pressure measuring device according to claim 4, characterized in that... The pads are circular with a diameter of 2.48-2.52 mm.

6. The intraocular pressure measuring device according to claim 4, characterized in that... The external unit also includes a power management module, a lithium battery module, and a display module; the second inductor is coaxially arranged with the first inductor of the internal unit.

7. The intraocular pressure measuring device according to claim 6, characterized in that... The output voltage of the lithium battery module is between 3.7V and 4.2V, and the input voltage of the second inductor is 5V.

8. The intraocular pressure measuring device according to claim 1, characterized in that... It also includes a mobile terminal, which is connected to the external device via wireless communication to display the intraocular pressure information obtained by the external device; the external device is also equipped with a Bluetooth module.

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