CN117017206A - Intraocular pressure measuring device - Google Patents

Abstract

The invention discloses an intraocular pressure measuring device, which belongs to the technical field of intraocular pressure measuring equipment. It includes: an internal machine, which is implanted in the scleral matrix layer of the eyeball. The internal machine has a built-in parallel circuit that changes the impedance spectrum as the intraocular pressure changes. A resonant circuit; an external machine, which is communicatively connected to the internal machine and has a built-in detection circuit that can receive the impedance spectrum reflected by the parallel resonant circuit; and identifies the resonant frequency of the parallel resonant circuit based on the impedance spectrum and obtains it based on the resonant frequency. An information processing module for intraocular pressure value; the information processing module is electrically connected to the detection circuit. The present invention adopts the above-mentioned intraocular pressure measuring device, which can make the measurement results more accurate, realize 7*24 hours of continuous measurement, achieve real-time monitoring of intraocular pressure conditions and upload the measured intraocular pressure data to the cloud, which is convenient for doctors. Gain a better understanding of the patient's condition in order to provide the patient with a more reasonable treatment plan.

Description

Intraocular pressure measuring device

Technical field

The present invention relates to the technical field of intraocular pressure measurement equipment, and in particular, to an intraocular pressure measurement device.

Background technique

Glaucoma is an eye disease that causes damage to the optic nerve due to a pathological increase in intraocular pressure, resulting in visual impairment or even blindness. It is the second leading cause of blindness, second only to cataracts. The main cause of glaucoma is that the aqueous humor circulation channel is blocked, causing intraocular pressure to increase, causing the optic nerve to be squeezed by the cribriform plate and damaged, resulting in visual impairment. Therefore, glaucoma patients should always pay attention to the fluctuations of their intraocular pressure, and should promptly treat any abnormalities in intraocular pressure to avoid further damage to their vision caused by continued increase in intraocular pressure. There is currently no effective treatment for glaucoma, and prevention is the main approach. Since the cause of glaucoma is mainly related to intraocular pressure, patients need to frequently check their intraocular pressure and seek medical advice promptly if they find increased or abnormal intraocular pressure.

Current tonometers commonly used to measure intraocular pressure have troublesome measurement processes and inaccurate measurement data. Patients often need to go to the hospital to register and be hospitalized for intraocular pressure measurement. Although some tonometers can be used at home, the measurement process is generally complicated and the measurement data is inaccurate, which delays the condition. In addition, patients are afraid of contacting the tonometry, which further causes inaccuracy in intraocular pressure measurement. In addition, the inability to measure intraocular pressure in real time is also an important drawback of current tonometers. The current tonometer can only measure the intraocular pressure at a certain point in time, and human intraocular pressure often fluctuates with time. The intraocular pressure is the highest in the morning and becomes lower in the afternoon. At present, the tonometer cannot obtain the patient's continuous time intraocular pressure value.

Contents of the invention

The purpose of the present invention is to provide an intraocular pressure measuring device that can make the measurement results more accurate, can achieve 7*24 hours of continuous measurement, achieve real-time monitoring of intraocular pressure conditions and upload the measured intraocular pressure data to the cloud, which is convenient Doctors have a better understanding of the patient's condition and can give the patient a more reasonable treatment plan.

In order to achieve the above object, the present invention provides an intraocular pressure measuring device, including:

The internal machine is implanted in the scleral matrix layer of the eyeball. The internal machine has a built-in parallel resonant circuit that changes the impedance spectrum as the intraocular pressure changes;

The external machine is communicatively connected to the internal machine and has a built-in detection circuit that can receive the impedance spectrum reflected by the parallel resonant circuit; and identify the resonant frequency of the parallel resonant circuit based on the impedance spectrum and obtain the intraocular pressure based on the resonant frequency. Value information processing module;

The information processing module is electrically connected to the detection circuit.

Preferably, the parallel resonant circuit includes:

Pressure-controlled variable capacitor changes capacitance as intraocular pressure changes;

The first inductor is electrically connected to the pressure control variable capacitor, communicatively connected to the external machine, and reflects the impedance spectrum of the parallel resonant circuit to the external machine as the capacitance changes;

The detection circuit includes: a second inductor electromagnetically coupled to the first inductor for receiving the impedance spectrum of the parallel resonant circuit, and the second inductor is electrically connected to the detection circuit;

A flexible protective layer is provided on the outermost side of the internal body, and the parallel resonant circuit is provided inside the flexible protective layer.

Preferably, the internal body is a disc-type flexible film pressure sensor with a diameter of 4-6mm and a thickness of 0.4-0.6mm.

Preferably, the first inductor includes a gold wire coil; the pressure control variable capacitor is provided at the center of the annular ring of the gold wire coil, and the pressure control variable capacitor is composed of a circular pressure-sensitive film capacitor and a Flexible electrode composition;

There are two flexible electrodes, which are installed on both sides of the pressure-sensitive film capacitor and connected to the gold wire coil.

Preferably, a flexible circuit board is wrapped inside the flexible protective layer, and the shape of the flexible circuit board is two circles connected by a thin strip in the middle, and the two circles are folded in half from the middle position of the thin strip so that the two circles are parallel to each other; Welding pads are provided on the inner sides of the two circular center positions on the flexible circuit board; the middle of the folded flexible circuit board is filled with a flexible film capacitive medium, and the welding pads arranged in parallel and the flexible parts between them are The film capacitive medium constitutes the pressure control variable capacitor; a copper foil coil is wound horizontally around the pad to constitute the first inductor.

Preferably, the soldering pad is circular and has a diameter of 2.48-2.52mm.

Preferably, the in vitro machine further 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 in vivo machine.

Preferably, 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.

Preferably, it also includes a mobile terminal, the mobile terminal is connected to the in vitro machine through wireless communication, and is used to display the intraocular pressure information obtained by the in vitro machine; a Bluetooth module is also provided in the in vitro machine.

Preferably, the implantation position of the internal machine is set in the stromal layer of the sclera between the lateral rectus muscle and the superior rectus muscle of the eyeball.

Therefore, the beneficial effects of using an intraocular pressure measuring device in the present invention are as follows:

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

(2) Accurate measurement: The sensor for measuring intraocular pressure is a flexible film sensor implanted between the scleral stroma layers, which directly measures the pressure inside the eyeball. The measurement results will not be affected by corneal thickness and tear film surface tension such as traditional tonometers. influence of other factors. At the same time, the intraocular pressure measuring device measures the patient's intraocular pressure continuously and unconsciously. The user will not feel nervous or fearful during the measurement, and the measurement results are more realistic.

(3) No cross-infection: The passive flexible film pressure sensor is surgically implanted into the patient's scleral matrix at one time. After surgery, the patient's intraocular pressure is measured by a device placed outside the body that wirelessly reads the sensor. test data. During the measurement process, there is no physical contact between the external device and the eyeball, and it will not cause infection to the eyeball. There is only one extracorporeal device per person, and there will be no mutual infection between patients.

(4) 7*24-hour continuous measurement can be achieved: The process of intraocular pressure measurement is to read the pressure data measured by the internal sensor through an external device wirelessly. The intraocular pressure measurement is completed without the patient's knowledge. Even if the patient is resting with his eyes closed, intraocular pressure measurement can still be performed normally.

(5) The measured intraocular pressure data can be uploaded to the cloud to enable real-time communication between doctors and patients: after the intraocular pressure value is read by the external device, it is transmitted to the patient's mobile terminal, such as a mobile phone, tablet, etc., via Bluetooth. . These mobile terminals can transmit measurement data to the cloud through the APP, and doctors can analyze the intraocular pressure data in the cloud to guide patients to carry out reasonable treatment.

The technical solution of the present invention will be further described in detail below through the accompanying drawings and examples.

Description of the drawings

Figure 1 is a schematic structural diagram of an embodiment of an intraocular pressure measuring device according to the present invention;

Figure 2 is a schematic structural diagram of the internal machine in an intraocular pressure measuring device of the present invention;

Figure 3 is a schematic structural diagram of the internal body 1 of an embodiment of an intraocular pressure measuring device of the present invention;

Figure 4 is a schematic three-dimensional structural diagram of the internal body 2 of an embodiment of an intraocular pressure measuring device of the present invention;

Figure 5 is a schematic front view structural diagram of the internal body 2 of an embodiment of an intraocular pressure measuring device of the present invention;

Figure 6 is a schematic diagram of the implantation position of the flexible film pressure sensor of the intraocular pressure measuring device of the present invention on the eyeball.

Reference signs

1. In vivo machine; 11. Pressure control variable capacitor; 111. Pressure-sensitive film capacitor; 112. Flexible film capacitor medium; 113. Flexible electrode; 114. Welding pad; 12. Flexible protective layer; 121. Flexible circuit board; 13 , the first inductor; 131, gold wire coil; 132, copper foil coil; 2, in vitro machine; 3, mobile terminal.

Detailed ways

The technical solution of the present invention will be further described below through the drawings and examples.

Unless otherwise defined, technical terms or scientific terms used in the present invention shall have the usual meaning understood by a person with ordinary skill in the field to which the present invention belongs. "First", "second" and similar words used in the present invention do not indicate any order, quantity or importance, but are only used to distinguish different components. Words such as "include" or "comprising" mean that the elements or things appearing before the word include the elements or things listed after the word and their equivalents, without excluding other elements or things. Words such as "connected" or "connected" are not limited to physical or mechanical connections, but may include electrical connections, whether direct or indirect. "Up", "down", "left", "right", etc. are only used to express relative positional relationships. When the absolute position of the described object changes, the relative positional relationship may also change accordingly.

The invention provides an intraocular pressure measuring device, which includes:

The internal machine 1 is implanted in the scleral matrix layer of the eyeball. The internal machine 1 has a built-in parallel resonant circuit that changes the impedance spectrum as the intraocular pressure changes. The outermost side of the internal machine 1 is provided with a flexible protective layer 12, and the parallel resonant circuit is provided on the flexible protective layer. Level 12 interior.

The external machine 2 is communicatively connected to the internal machine 1 and has a built-in detection circuit that can receive the impedance spectrum reflected by the parallel resonant circuit, and information processing 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. module, the information processing module is electrically connected to the detection circuit.

Specifically, the parallel resonant circuit includes:

The pressure-controlled variable capacitor 11 can change its capacitance as the intraocular pressure changes.

The first inductor 13 is electrically connected to the pressure control variable capacitor 11, is communicatively connected to the external machine 2, and reflects the impedance spectrum of the parallel resonant circuit to the external machine 2 as the capacitance changes.

The detection circuit includes:

The second inductor electromagnetically coupled to the first inductor 13 is used to receive the impedance spectrum of the parallel resonant circuit, and the second inductor is electrically connected to the detection circuit.

Specifically, the body 1 is a disk-type flexible film pressure sensor with a diameter of 4-6mm and a thickness of 0.4-0.6mm.

Specifically, the first inductor 13 includes a gold wire coil 131; a pressure control variable capacitor 11 is provided at the center of the annular ring of the gold wire coil 131. The pressure control variable capacitor 11 is composed of a circular pressure-sensitive film capacitor 111 and a flexible electrode. 113 composition.

There are two flexible electrodes 113 , which are respectively installed on both sides of the pressure-sensitive film capacitor 111 and connected to the gold wire coil 131 .

Specifically, a flexible circuit board 121 is wrapped inside the flexible protective layer 12. The shape of the flexible circuit board 121 is two circles connected by a thin strip in the middle, and the two circles are folded in half from the middle position of the thin strip so that the two circles are parallel to each other. The flexible circuit board 121 is provided with welding pads 114 on the inner sides of the two circular center positions. The folded flexible circuit board 121 is filled with a flexible film capacitor medium 112 in the middle. The parallel welding pads 114 and the flexible film capacitors between them are The medium 112 forms the pressure controlled variable capacitor 11 . A copper foil coil 132 is wound horizontally around the bonding pad 114 to form the first inductor 13 .

Specifically, the bonding pad 114 is circular and has a diameter of 2.48-2.52 mm.

Specifically, the external machine 2 also includes 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 internal body 1 .

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.

Specifically, it also includes a mobile terminal 3. The mobile terminal 3 is connected to the extracorporeal machine 2 using wireless communication to display the intraocular pressure information obtained by the extracorporeal machine. The external machine 2 is also equipped with a Bluetooth module, which can conduct wireless data transmission with the mobile terminal 3 .

Specifically, the implantation position of the internal machine 1 is set in the stromal layer of the sclera between the lateral rectus muscle and the superior rectus muscle of the eyeball.

The present invention will be further elaborated below through specific embodiments.

Embodiment 1

As shown in Figure 1, the present invention provides an intraocular pressure measuring device, including:

The internal machine 1 is implanted in the scleral matrix layer of the eyeball. The internal machine 1 has a built-in parallel resonant circuit that changes the impedance spectrum as the intraocular pressure changes.

The external machine 2 is communicatively connected to the internal machine 1. The external machine 2 has a built-in detection circuit that can receive the impedance spectrum reflected by the parallel resonant circuit, and identify the resonant frequency of the parallel resonant circuit based on the impedance spectrum and obtain the intraocular pressure value based on the resonant frequency. The information processing module is electrically connected to the detection circuit, so that the external machine 2 detects the resonant frequency of the internal machine 1 to obtain the intraocular pressure.

Parallel resonant circuits include:

Pressure control variable capacitor 11: The capacitance can be changed as the intraocular pressure changes.

The first inductor 13: is electrically connected to the pressure control variable capacitor 11 and is communicatively connected to the external machine 2, and reflects the impedance spectrum of the parallel resonant circuit to the external machine 2 as the capacitance changes.

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.

As shown in Figure 2, the internal body 1 is a disc-type flexible film pressure sensor with a diameter of 4mm and a thickness of 0.4mm. Since the size of the internal machine 1 is small, the pressure control variable capacitor 11 is small, and the measured resonant frequency is large, making the measured intraocular pressure value higher, and the change of the intraocular pressure value can be identified very sensitively. Due to the relatively small size, it increases the difficulty of manufacturing, subsequent encapsulation and surgical implantation, but it can improve detection accuracy and improve the wearer's experience without making the wearer feel a foreign body sensation. It is suitable for children and symptoms More serious adults. A flexible protective layer 12 is provided on the outermost side of the extracorporeal machine 1 , and a parallel resonant circuit is provided inside the flexible protective layer 12 .

The flexible protective layer 12 is made of rubber, which is made of silicone material that can be directly used for implantation in the human body in the prior art. It has good biocompatibility, is non-irritating to human tissue, non-toxic, has no allergic reaction, and has no harmful effects on the body. It has very few rejection reactions and has good physical and chemical properties. It can maintain its original elasticity and softness during contact with body fluids and tissues and will not be degraded. It is a fairly stable inert substance that can improve the performance of parallel resonant circuits. Stability without causing damage to the user.

As shown in FIG. 3 , the first inductor 13 is a gold wire coil 131 made of gold wire, and the gold wire coil 131 is circular. A pressure control variable capacitor 11 is provided at the center of the annular ring of the gold wire coil 131. The pressure control variable capacitor 11 is composed of a circular pressure-sensitive film capacitor 111 and a flexible electrode 113. There are two flexible electrodes 113 installed on both sides of the pressure-sensitive film capacitor 111 and connected to the gold wire coil 131 .

As shown in Figure 6, the implantation position of the internal machine 1 is set in the stromal layer of the sclera between the lateral rectus muscle and the superior rectus muscle of the eyeball. Since the internal machine 1 is round in shape and is a flexible film, the implantation position is When reaching the stromal layer of the sclera of the eyeball, the surgical incision can be smaller than the diameter of the machine 1 in the body.

The sclera is located on the surface of the eyeball, and together with the cornea in front of the eyeball, forms the outer wall of the eyeball. The sclera occupies 5/6 of the eyeball area and is milky white. The sclera is thickest at the posterior pole of the eyeball where the optic nerve penetrates, about 1.0mm, and becomes thinner toward the front. The thickness at the equatorial part is 0.4-0.5mm, and the thickness at the attachment of the rectus muscle is 0.3mm. The outside of the sclera is wrapped by fascia and conjunctiva, its anterior edge is connected to the limbus, and its posterior edge is continued with the dural sheath of the optic nerve. The sclera is divided into surface layer, stromal layer, and brown-black layer from outside to inside. The surface layer is composed of loose connective tissue, connected to the fascial layer, and has abundant nerves and blood vessels. The stromal layer is composed of dense connective tissue and elastic fibers, and the fibers are synthetic. The bundles cross each other, are not arranged neatly, are opaque overall, and have fewer blood vessels and nerves; the brown-black layer connective tissue fiber bundles are small, elastic fibers are significantly increased, and there are a large number of pigment cells, making the inside of the sclera brown.

The surgical implant site is the scleral part between the lateral rectus muscle and the superior rectus muscle. The surgical process is as follows:

(1) Cut the conjunctiva outside the sclera of the eyeball to expose the white sclera.

(2) Make an incision in 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 stromal layer of the sclera near this part by a certain area.

(3) Insert the internal machine into the sclera through the incision.

(4) Suture the scleral incision.

(5) Suture the conjunctival incision.

The external machine 2 also includes a power management module, a lithium battery module and a display module. The information processing module includes a microprocessor, a direct digital synthesis (Direct Digital Synthesis, DDS) sweep signal generator and an impedance analyzer.

The second inductor of the external machine 2 is coaxially arranged with the first inductor 13 of the internal machine 1, which facilitates electromagnetic coupling between the second inductor and the first inductor 13 of the resonant circuit of the internal machine 1. The impedance is reflected to the second inductor, thereby obtaining the impedance spectrum of the second inductor, that is, the impedance spectrum of the resonant circuit of the body 1 inside the body. The microprocessor has been preset with an algorithm 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. When the impedance spectrum information detected by the second inductor is transmitted to the microprocessor, After calculation, the calculation settlement can be directly transmitted to the display module for display, and a healthy intraocular pressure threshold is preset in the microprocessor. When the detected intraocular pressure is higher than the threshold, a corresponding additional reminder message is output.

display module

The display module is a display screen installed on the external machine 2, which can display basic intraocular pressure information, and when the intraocular pressure is higher than the threshold, the display module will also flash a reminder accordingly.

microprocessor

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 power management module's control of the lithium battery module's power. Reading and Instruction.

Power management module and lithium battery module

The output voltage of the lithium battery module is between 3.7V and 4.2V. 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 external machine 2 and providing electric energy for it. Among them, the voltage required by the microprocessor is 2.5V and 1.8V, the voltage required by the Direct Digital Synthesis (DDS) sweep signal generator is 3.3V, and the voltage required by the second inductor is 5V.

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

Direct Digital Synthesis (DDS) sweep signal generator

Direct Digital Synthesis (DDS) frequency sweep signal generator, under the control of a microprocessor, generates a sine wave signal with a continuously variable frequency and a certain voltage. The peak-to-peak voltage of the sine wave is 1V, and the frequency is between 100MHz-500MHz. between. The sine wave is used as an excitation signal and is transmitted to the second inductor to obtain the impedance of the resonant circuit in the body at different frequencies.

Impedance Analyzer

The impedance analyzer collects the voltage and current at both ends of the second inductor, digitizes them, and transmits them to the microprocessor. The microprocessor performs FFT transformation on them respectively to obtain the amplitude value and phase value of the voltage and current. The phase value of the voltage minus the phase value of the current is obtained to obtain the phase value of the impedance of the second inductor at different frequencies. The microprocessor analyzes the phase value and finds the frequency point of the extreme value of its change. That is, at this frequency point, whether the frequency increases or decreases, the phase value becomes larger. This frequency point is the resonant frequency of the resonant circuit.

It also includes a mobile terminal 3, which is connected to the external machine 2 by wireless communication. The mobile terminal 3 can be the patient's mobile phone or tablet computer. The mobile terminal 3 can display real-time intraocular pressure values, historical intraocular pressure data and time-dependent intraocular pressure data. Richer intraocular pressure information such as the intraocular pressure change curve. At the same time, the external machine 2 is also equipped with a Bluetooth module, which can send the results measured by the external machine 2 to the mobile terminal 3 through wireless communication.

In addition, the intraocular pressure threshold can also be set in the mobile terminal 3. When the collected intraocular pressure value is greater than the threshold, the mobile terminal 3 can issue a prompt sound or vibrate to remind the user, and at the same time highlight the current eye pressure on the display screen. The intraocular pressure value and the suggestions for improvement measures given for the intraocular pressure value. When the collected intraocular pressure value is less than the threshold, 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 .

The working principle of an intraocular pressure measuring device of the present invention is as follows: the pressure control variable capacitor 11 in the internal machine 1 changes in capacity as the pressure changes, thereby causing the resonant frequency of the flexible film pressure sensor to change. The external machine 2 is a resonant frequency detection circuit that reads the impedance of the internal machine 1 at different frequencies through the principle of electromagnetic induction to obtain its resonant frequency and thereby obtain the intraocular pressure. Specifically: the second inductor on the external machine 2 and the first inductor 13 of the internal machine 1 undergo electromagnetic coupling, and the impedance of the internal machine 1 is reflected to the external machine 2, causing the impedance of the second inductor of the external machine 2 to occur. Change, the external machine 2 measures the impedance of its second inductor at different frequencies, and based on the measured impedance of the external machine 2, the impedance of the internal machine 1 at different frequencies can be obtained. Impedance is a complex number including amplitude and phase. The external machine 2 measures the impedance of the internal machine 1. When the internal machine 1 resonates at a certain frequency, the phase of its impedance will reach a certain extreme value. According to this characteristic, the internal machine 1 can be obtained The resonant frequency of machine 1. The corresponding relationship between the resonant frequency of the internal machine 1 and the intraocular pressure is calculated in advance. According to the measured resonant frequency, the intraocular pressure can be obtained through a pre-selected algorithm in the microprocessor.

The microprocessor on the extracorporeal 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. The patient can see the changes in his intraocular pressure over time through the mobile terminal 3 in real time. .

Embodiment 2

The difference from the first embodiment is that the internal body 1 is a disc-type flexible film pressure sensor with a diameter of 5 mm and a thickness of 0.5 mm. Since the size of the internal body 1 has been increased compared to the first embodiment, the pressure control variable capacitor 11 has been enlarged compared to the first embodiment, which reduces the measured resonant frequency, resulting in a low measured intraocular pressure value. The accuracy of measuring intraocular pressure changes with the in vivo machine 1 has decreased. In addition, the increased volume of the intracorporeal machine 1 will reduce the difficulty of manufacturing and surgical implantation of the intracorporeal machine 1. However, there are higher requirements for the implantation position of the patient's eye matrix layer, which is not very suitable for children. Instead, it is more suitable for adults whose condition is not particularly serious and will not cause discomfort to the user.

Embodiment 3

The difference from the first embodiment is that the internal body 1 is a disc-type flexible film pressure sensor with a diameter of 6 mm and a thickness of 0.6 mm. The size of the internal body 1 is significantly increased, which makes the pressure control variable capacitor 11 inside the internal body 1 larger, which reduces the difficulty of manufacturing and surgical implantation, but also reduces the measurement accuracy. Due to size regulations, the requirements for the implantation position of the patient's ocular matrix layer are higher, and it is only applicable to adult patients with mild symptoms who meet the implantation requirements after measurement.

Embodiment 4

The difference from Embodiment 1 lies in the structure of the internal body 1. As shown in Figures 4 and 5, in this embodiment, the flexible protective layer 12 of the internal body 1 is wrapped with a flexible circuit board 121, and the flexible circuit 122 has a thickness of 0.05 mm, its shape is two circles connected by a thin strip in the middle and folded in half from the middle of the middle strip so that the two circles are parallel to each other. Welding pads 114 are provided on the inner sides of the two circular center positions on the flexible circuit board 121 .

The folded flexible circuit board 121 is filled with a flexible film capacitive medium 112 in the middle, and the flexible film capacitive medium 112 is made of hydrogel. The parallel-arranged pads 114 and the flexible film capacitive medium 112 therebetween constitute the pressure control variable capacitor 11 .

The pad 114 is circular and has a diameter of 2.48mm. The diameter of the pad 114 is smaller, which makes the pressure control variable capacitor 11 smaller and more sensitive to changes in the resonant frequency, resulting in an increase in the final measured resonant frequency and a higher measured intraocular pressure value, which can improve detection accuracy. At the same time, the size of the internal body 1 is also smaller. Although it increases the difficulty of manufacturing, subsequent encapsulation and surgical implantation, the wearer will not feel a foreign body sensation and is suitable for children and adults with severe symptoms.

A copper foil coil 132 is horizontally wound around the bonding pad 114 . The thickness of the copper foil in the copper foil coil 132 is 0.01 mm, forming the first inductor 13 . Among them, the bonding pad 114 and the copper foil coil 132 are both made of copper material, which has good chemical stability and electrical conductivity.

Embodiment 5

The difference from Embodiment 4 is that the diameter of the pad 114 is 2.5 mm. As the size of the pad 114 increases, the pressure control variable capacitor 11 also increases, and its sensitivity to changes in the resonant frequency decreases, resulting in a decrease in the final measured resonant frequency, a decrease in the measured intraocular pressure value, and a slight decrease in detection accuracy. At the same time, the size of the internal machine 1 is increased, which reduces the difficulty of manufacturing, subsequent encapsulation and surgical implantation. However, there are higher requirements for the implantation position of the patient's eye matrix layer, which is not very suitable for children. It is more suitable for adults whose condition is not particularly serious, and will not cause the wearer to feel a foreign body sensation.

Embodiment 6

The difference from Embodiment 4 is that the diameter of the pad 114 is 2.52 mm. Since the size of the pad 114 is significantly increased, the pressure control variable capacitor 11 is also significantly increased, and the sensitivity to changes in the resonant frequency is reduced, resulting in a decrease in the final measured resonant frequency and a lower measured intraocular pressure value. , reducing the detection accuracy.

The increase in the pad 114 also increases the size of the body machine 1, which reduces the difficulty of manufacturing, subsequent encapsulation, and surgical implantation. However, the requirements for the implantation position of the patient's eye matrix layer are higher, and it is only applicable to Mildly symptomatic adult patients who meet implant requirements after measurement.

Therefore, the present invention adopts the above-mentioned intraocular pressure measuring device, which can make the measurement results more accurate, realize 7*24 hours of continuous measurement, achieve real-time monitoring of intraocular pressure conditions and upload the measured intraocular pressure data to the cloud, which is convenient Doctors have a better understanding of the patient's condition and can give the patient a more reasonable treatment plan.

Finally, it should be noted that the above embodiments are only used to illustrate the technical solution of the present invention rather than to limit it. Although the present invention has been described in detail with reference to the preferred embodiments, those of ordinary skill in the art should understand that: The technical solution of the present invention may be modified or equivalently substituted, but these modifications or equivalent substitutions cannot cause the modified technical solution to depart from the spirit and scope of the technical solution of the present invention.

Claims (10)

1. An intraocular pressure measurement device, comprising:

the internal body is implanted in the scleral matrix layer of the eyeball, and a parallel resonance circuit which changes the impedance spectrum along with the change of the intraocular pressure is arranged in the internal body;

the external machine is in communication connection with the internal machine and is internally provided with a detection circuit capable of receiving impedance spectrum reflected by the parallel resonant circuit; the information processing module is used for identifying the resonance frequency of the parallel resonance circuit according to the impedance spectrum and acquiring an intraocular pressure value according to the resonance frequency;

the information processing module is electrically connected with the detection circuit.

2. An intraocular pressure measurement device according to claim 1, wherein: the parallel resonant circuit includes:

a pressure-controlled variable capacitor that changes capacitance as the intraocular pressure changes;

the first inductor is electrically connected with the pressure control variable capacitor, is in communication connection with the external machine and reflects the impedance spectrum of the parallel resonant circuit to the external machine along with the change of the capacitance value;

the detection circuit includes: a second inductor electromagnetically coupled to the first inductor for receiving an impedance spectrum of the parallel resonant circuit;

the outermost side of the internal machine is provided with a flexible protection layer, and the parallel resonant circuit is arranged in the flexible protection layer.

3. An intraocular pressure measurement device according to claim 2, wherein: the internal machine is a disc type flexible film pressure sensor with the diameter of 4-6mm and the thickness of 0.4-0.6 mm.

4. An intraocular pressure measurement device according to claim 3, wherein: the first inductor comprises a gold wire coil; the pressure control variable capacitor is arranged at the central position of the annular ring of the gold wire coil and consists of a circular pressure-sensitive film capacitor and a flexible electrode;

the flexible electrodes are arranged at two sides of the pressure-sensitive film capacitor and are connected with the gold wire loops.

5. An intraocular pressure measurement device according to claim 2, wherein: the flexible protection layer is internally wrapped with a flexible circuit board, and the flexible circuit board is in a shape of two circles connected by a thin strip in the middle and folded in half from the middle of the thin strip to enable the two circles to be in a state of being parallel to each other; pads are arranged on the inner sides of the two circular center positions on the flexible circuit board; the flexible circuit board is filled with flexible thin film capacitance media in the middle of the folded flexible circuit board, and the pads arranged in parallel and the flexible thin film capacitance media between the pads form the pressure control variable capacitor; copper foil coils are horizontally wound around the bonding pads to form the first inductor.

6. An intraocular pressure measurement device according to claim 5, wherein: the bonding pad is round and has a diameter of 2.48-2.52mm.

7. An intraocular pressure measurement device according to claim 2, wherein: the external machine also comprises a power management module, a lithium battery module and a display module; the second inductor is coaxially disposed with the first inductor of the in-vivo machine.

8. An intraocular pressure measurement device according to claim 7, wherein: 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.

9. An intraocular pressure measurement device according to claim 1, wherein: the system also comprises a mobile terminal, wherein the mobile terminal is connected with the external machine in a wireless communication mode and is used for displaying intraocular pressure information obtained by the external machine; and a Bluetooth module is also arranged in the external machine.

10. An intraocular pressure measurement device according to claim 1, wherein: the implantation site of the in vivo machine is disposed in the stroma layer of the sclera between the extraocular rectus muscle and the superior rectus muscle.