CN117017206A - Intraocular pressure measuring device - Google Patents
Intraocular pressure measuring device Download PDFInfo
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- CN117017206A CN117017206A CN202311029058.4A CN202311029058A CN117017206A CN 117017206 A CN117017206 A CN 117017206A CN 202311029058 A CN202311029058 A CN 202311029058A CN 117017206 A CN117017206 A CN 117017206A
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/16—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for measuring intraocular pressure, e.g. tonometers
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/0016—Operational features thereof
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- Ophthalmology & Optometry (AREA)
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- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
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- Molecular Biology (AREA)
- Surgery (AREA)
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- Eye Examination Apparatus (AREA)
Abstract
The invention discloses an intraocular pressure measuring device, which belongs to the technical field of intraocular pressure measuring equipment and comprises: 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. The intraocular pressure measuring device can enable the measuring result to be more accurate, can realize continuous measurement for 7 x 24 hours, can monitor intraocular pressure conditions in real time, and can upload measured intraocular pressure data to the cloud end, so that doctors can know the illness state of patients more conveniently, and a more reasonable treatment scheme is provided for the patients.
Description
Technical Field
The invention relates to the technical field of intraocular pressure measuring equipment, in particular to an intraocular pressure measuring device.
Background
Glaucoma is an ophthalmic disease in which vision is impaired and even blindness is caused by pathological elevation of intraocular pressure, and is the second leading cause of blindness, and is second only to cataract. The main cause of glaucoma is that the channel of aqueous humor circulation is blocked to cause the rise of intraocular pressure, so that the optic nerve is damaged by the extrusion of the sieve plate, thereby causing vision impairment. Therefore, glaucoma patients should pay attention to fluctuation of their ocular tension, and abnormal ocular tension should be treated in time to avoid further vision injury caused by continuous increase of ocular tension. Glaucoma is not currently treated effectively, but only by prevention. Since the cause of glaucoma is mainly related to intraocular pressure, patients need to constantly detect their own intraocular pressure, and to make a timely visit when they find an increase in intraocular pressure or abnormality occurs.
The prior tonometer has the common problems of troublesome measuring process and inaccurate measuring data in intraocular pressure measurement. Patients often need to go to a hospital for registration and hospitalization for intraocular pressure measurement, and although some tonometers can be used in families, the common existence of complicated measurement processes and inaccurate measurement data delay the illness state. In addition, with contact tonometers, the patient has a fear of being in mind, which is more likely to cause inaccuracy in intraocular pressure measurements. In addition, the inability to meet real-time intraocular pressure measurements is also an important drawback of current tonometers. Current tonometers can only measure intraocular pressure at a certain point in time, whereas human intraocular pressure fluctuates frequently over time, with the pressure in the morning being highest and the pressure in the afternoon being lower. Current tonometers cannot obtain a patient's continuous time of tonometers.
Disclosure of Invention
The invention aims to provide an intraocular pressure measuring device, which can enable a measuring result to be more accurate, can realize continuous measurement for 7 x 24 hours, can monitor intraocular pressure conditions in real time, and can upload measured intraocular pressure data to a cloud end, so that doctors can know the illness state of patients more conveniently, and a more reasonable treatment scheme is given to the patients.
To achieve the above object, the present invention provides 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.
Preferably, 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 second inductor being electrically connected to the detection 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.
Preferably, the in-vivo machine is a disc type flexible film pressure sensor with the diameter of 4-6mm and the thickness of 0.4-0.6 mm.
Preferably, 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.
Preferably, the flexible protective layer is internally wrapped with a flexible circuit board, the shape of the flexible circuit board is two circles connected by a thin strip in the middle and folded in half from the middle of the thin strip so that the two circles are 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.
Preferably, the bonding pad is circular and has a diameter of 2.48-2.52mm.
Preferably, the external machine further 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.
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, the system further 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.
Preferably, 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.
Therefore, the invention adopts the intraocular pressure measuring device with the following beneficial effects:
(1) The surgical damage is small: the flexible film pressure sensor is a bendable flexible film with the diameter of 5mm and the thickness of 0.5mm, the implantation position is positioned between the attachment positions of the superior rectus muscle and the external rectus muscle on the sclera, the incision on the sclera is smaller in the operation process, and the patient does not need hospitalization.
(2) The measurement is accurate: the sensor for measuring the intraocular pressure is a flexible film sensor implanted between scleral stroma layers, directly measures the pressure intensity in the eyeball, and the measurement result is not influenced by factors such as the cornea thickness, the tear film surface tension and the like of the traditional tonometer. Meanwhile, the intraocular pressure measuring device is used for measuring the intraocular pressure of a patient in a continuous and unconscious manner, so that the user does not generate tension and fear during measurement, and the measuring result is more real.
(3) No cross infection: the passive flexible film pressure sensor is implanted between scleral stroma layers of a patient at one time in a surgical mode, and the measurement of intraocular pressure of the patient after the surgery is carried out by using equipment placed outside the body to read the test data of the sensor in a wireless mode. In the measurement process, the external equipment is not in physical contact with the eyeball, so that the eyeball is not infected. The external device is used for one person, and the mutual infection among patients can not occur.
(4) Continuous measurement can be achieved for 7 x 24 hours: the intraocular pressure measurement is carried out in a state that the patient is unaware by wirelessly reading pressure data measured by an in-vivo sensor from an in-vitro device. Even if the patient is in a state of eye closure rest, the measurement of intraocular pressure can still be performed normally.
(5) The measured intraocular pressure data can be uploaded to the cloud end, so that real-time communication and communication between doctors and patients are realized: after the intraocular pressure value is read by the external equipment, the intraocular pressure value is transmitted to a mobile terminal of a patient in a Bluetooth mode, such as a mobile phone, a tablet personal computer and the like. These mobile terminals accessible APP transmits measurement data to high in the clouds, and doctor accessible carries out analysis to high in the clouds intraocular pressure data, instructs the patient to carry out reasonable treatment.
The technical scheme of the invention is further described in detail through the drawings and the embodiments.
Drawings
FIG. 1 is a schematic view showing the constitution of an embodiment of an intraocular pressure measuring device of the present invention;
FIG. 2 is a schematic diagram of the structure of an in-vivo machine in an intraocular pressure measurement device of the present invention;
fig. 3 is a schematic view showing the structure of an in-vivo machine 1 according to an embodiment of the intraocular pressure measurement device of the present invention;
fig. 4 is a schematic perspective view of the in-vivo machine 2 according to an embodiment of the intraocular pressure measurement device of the present invention;
fig. 5 is a schematic diagram showing the structure of the in-vivo machine 2 in front view of an embodiment of an intraocular pressure measurement device of the present invention;
fig. 6 is a schematic view showing the implantation position of a flexible film pressure sensor of an intraocular pressure measuring device of the present invention on an eyeball.
Reference numerals
1. An in-vivo machine; 11. a pressure control variable capacitor; 111. a pressure sensitive thin film capacitor; 112. a flexible thin film capacitive medium; 113. a flexible electrode; 114. a bonding pad; 12. a flexible protective layer; 121. a flexible circuit board; 13. a first inductor; 131. a gold wire coil; 132. copper foil coils; 2. an external machine; 3. a mobile terminal.
Detailed Description
The technical scheme of the invention is further described below through the attached drawings and the embodiments.
Unless defined otherwise, technical or scientific terms used herein should be given the ordinary meaning as understood by one of ordinary skill in the art to which this invention belongs. The terms "first," "second," and the like, as used herein, do not denote any order, quantity, or importance, but rather are used to distinguish one element from another. The word "comprising" or "comprises", and the like, means that elements or items preceding the word are included in the element or item listed after the word and equivalents thereof, but does not exclude other elements or items. The terms "connected" or "connected," and the like, are not limited to physical or mechanical connections, but may include electrical connections, whether direct or indirect. "upper", "lower", "left", "right", etc. are used merely to indicate relative positional relationships, which may also be changed when the absolute position of the object to be described is changed.
The present invention provides an intraocular pressure measurement device comprising:
the internal body machine 1 is implanted in the scleral matrix layer of the eyeball, a parallel resonance circuit which changes the impedance spectrum along with the change of the intraocular pressure is arranged in the internal body machine 1, a flexible protective layer 12 is arranged at the outermost side of the internal body machine 1, and the parallel resonance circuit is arranged in the flexible protective layer 12.
The external machine 2 is in communication connection with the internal machine 1, and is internally provided with a detection circuit capable of receiving an impedance spectrum reflected by the parallel resonance circuit and an information processing module which recognizes the resonance frequency of the parallel resonance circuit according to the impedance spectrum and acquires an intraocular pressure value according to the resonance frequency, wherein the information processing module is electrically connected with the detection circuit.
Specifically, the parallel resonant circuit includes:
the pressure control variable capacitor 11 can change its capacitance with changes in intraocular pressure.
The first inductor 13 is electrically connected to the pressure-controlled 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:
a second inductor electromagnetically coupled to the first inductor 13 for receiving an impedance spectrum of the parallel resonant circuit, the second inductor being electrically connected to the detection circuit.
Specifically, the internal machine 1 is a disc type flexible film pressure sensor with the diameter of 4-6mm and the thickness of 0.4-0.6 mm.
Specifically, the first inductor 13 includes a gold wire loop 131; a pressure control variable capacitor 11 is provided at the center of the annular ring of the gold wire coil 131, and the pressure control variable capacitor 11 is composed of a circular pressure sensitive film capacitor 111 and a flexible electrode 113.
The flexible electrode 113 is provided with two electrodes respectively mounted on both sides of the pressure sensitive thin film capacitor 111 and connected with the gold wire loop 131.
Specifically, the flexible protection layer 12 is internally wrapped with a flexible circuit board 121, and the flexible circuit board 121 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 so that the two circles are in a state of being parallel to each other. The inner sides of the two circular center positions on the flexible circuit board 121 are respectively provided with a bonding pad 114, the middle of the folded flexible circuit board 121 is filled with a flexible thin film capacitance medium 112, and the bonding pads 114 which are arranged in parallel and the flexible thin film capacitance medium 112 between the bonding pads form the pressure control variable capacitor 11. A copper foil coil 132 is wound horizontally around the pad 114 to constitute the first inductor 13.
Specifically, the bonding pad 114 is circular in shape and has a diameter of 2.48-2.52mm.
Specifically, the external machine 2 further comprises a power management module, a lithium battery module and a display module. The second inductor is arranged coaxially with the first inductor 13 of the in-vivo machine 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, the device also comprises a mobile terminal 3, wherein the mobile terminal 3 is connected with the external machine 2 in a wireless communication mode and is used for displaying the intraocular pressure information obtained by the external machine. The external machine 2 is also internally provided with a Bluetooth module which can carry out wireless data transmission with the mobile terminal 3.
Specifically, the implantation site of the in vivo machine 1 is set in the stroma layer of the sclera between the extraocular rectus muscle and the superior rectus muscle.
The invention will be further illustrated by the following specific embodiments.
Example 1
As shown in fig. 1, the present invention provides an intraocular pressure measurement device comprising:
the in-vivo device 1 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 in-vivo device 1.
The external machine 2 is in communication connection with the internal machine 1, a detection circuit capable of receiving impedance spectrum reflected by the parallel resonant circuit and an information processing module which recognizes the resonant frequency of the parallel resonant circuit according to the impedance spectrum and acquires the intraocular pressure value according to the resonant frequency are arranged in the external machine 2, and the information processing module is electrically connected with the detection circuit, so that the external machine 2 can acquire the intraocular pressure by detecting the resonant frequency of the internal machine 1.
The parallel resonant circuit includes:
pressure control variable capacitor 11: the capacitance may change as the intraocular pressure changes.
The first inductor 13: is electrically connected with the pressure control variable capacitor 11, is in communication connection with the external machine 2, and reflects the impedance spectrum of the parallel resonant circuit to the external machine 2 along with the change of the capacitance value.
The detection circuit comprises 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 fig. 2, the in-vivo machine 1 is a disc-type flexible film pressure sensor having a diameter of 4mm and a thickness of 0.4 mm. Because the size of the in-vivo machine 1 is small, the pressure control variable capacitor 11 is small, the measured resonance frequency is large, the measured intraocular pressure value is high, and the change of the intraocular pressure value can be recognized very sensitively. Because the size is relatively smaller, the difficulty of manufacturing, subsequent encapsulation and surgical implantation is increased, but the detection precision can be improved, the use experience of a wearer can be improved, the wearer can not feel foreign body sensation, and the device is suitable for children and adults with serious symptoms. The outermost side of the external machine 1 is provided with a flexible protective layer 12, and a parallel resonant circuit is arranged inside the flexible protective layer 12.
The flexible protective layer 12 is encapsulated, is made of silica gel material which can be directly implanted into human body in the prior art, has good biocompatibility, no irritation, no toxicity, no anaphylactic reaction and little rejection reaction to human body tissues, has good physical and chemical properties, can keep the original elasticity and softness in the process of contacting body fluid and tissues, is not degraded, is a quite stable inert substance, and can improve the stability of the parallel resonant circuit without damaging a user.
As shown in fig. 3, the first inductor 13 is a gold wire coil 131 wound by gold wire, and the gold wire coil 131 has a circular shape. A pressure control variable capacitor 11 is provided at the center of the annular ring of the gold wire coil 131, and the pressure control variable capacitor 11 is composed of a circular pressure sensitive film capacitor 111 and a flexible electrode 113. The flexible electrode 113 is provided with two electrodes respectively mounted on both sides of the pressure sensitive thin film capacitor 111 and connected with the gold wire loop 131.
As shown in fig. 6, the implantation site of the in-vivo machine 1 is disposed in the stroma layer of the sclera between the extraocular rectus muscle and the superior rectus muscle, and since the in-vivo machine 1 is circular in shape and is a flexible film, the surgical incision can be smaller than the diameter of the in-vivo machine 1 when implanted between the stroma layers of the sclera of the eyeball.
The sclera (sclera) is located on the surface of the eyeball and forms the outer wall of the eyeball together with the cornea in front of the eyeball. The sclera occupies 5/6 of the eyeball area and is milky white. The sclera is the thickest at the posterior pole of the eyeball, from which the optic nerve passes, and is about 1.0mm, thinner as it goes forward, and has a thickness of 0.4-0.5mm at the equatorial region and 0.3mm at the rectus attachment. The sclera is surrounded by fascia and conjunctiva, with the limbus connected to the limbus and the posterior is continued with the optic nerve dura mater sheath. The sclera is divided into a surface layer, a matrix layer and a brown-black layer from outside to inside, wherein the surface layer is composed of loose connective tissue, is connected with a fascia layer, and has rich nerves and blood vessels; the matrix layer is composed of compact connective tissue and elastic fiber, the fiber is combined into a bundle, the bundles are mutually crossed, the arrangement is irregular, the whole is opaque, and blood vessels and nerves are fewer; the connective tissue fiber bundle of the brown-black layer is tiny, the elastic fiber is obviously increased, and a large number of pigment cells exist, so that the inside of the sclera is brown.
The site of surgical implantation is the scleral portion between the external rectus muscle and the superior rectus muscle, the procedure being as follows:
(1) The conjunctiva outside the sclera of the eyeball is incised to expose the white sclera.
(2) An incision is made at the scleral site between the attachment site of the external rectus muscle to the sclera and the attachment site of the superior rectus muscle to the sclera, and the stromal layers of the sclera are separated by an area adjacent to this site.
(3) The intrabody machine is inserted into the sclera through the incision.
(4) Suture the scleral incision.
(5) Suturing the conjunctival incision.
The external machine 2 also comprises a power management module, a lithium battery module and a display module, wherein the information processing module comprises a microprocessor, a direct digital synthesis (Direct Digital Synthesis, DDS) sweep frequency signal generator and an impedance analyzer.
The second inductor of the external body unit 2 is coaxially arranged with the first inductor 13 of the internal body unit 1, so that electromagnetic coupling between the second inductor and the first inductor 13 of the resonant circuit of the internal body unit 1 is facilitated, and the impedance of the resonant circuit of the internal body unit 1 is reflected to the second inductor, thereby obtaining the impedance spectrum of the second inductor, namely the impedance spectrum of the resonant circuit of the internal body unit 1. The microprocessor is preset with an algorithm for identifying the resonant frequency of the parallel resonant circuit according to the impedance spectrum and acquiring the intraocular pressure value according to the resonant frequency, when the impedance spectrum information detected by the second inductor is transmitted to the microprocessor, the calculated settlement can be directly transmitted to the display module for display through calculation, the microprocessor is preset with a healthy intraocular pressure threshold value, and when the detected intraocular pressure is higher than the threshold value, corresponding additional reminding information is output.
Display module
The display module is a display screen arranged on the external machine 2, can display basic intraocular pressure information, and can correspondingly carry out flashing reminding when the intraocular pressure is higher than a threshold value.
Microprocessor
The microprocessor is responsible for the management and control of all functional modules of the external machine 2, such as the frequency control of a direct digital synthesis (Direct Digital Synthesis, DDS) sweep frequency signal generator, the impedance calculation of an impedance analyzer, and the reading and indication of the electric quantity of the lithium battery module by the power management module.
Power management module and lithium battery module
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 external machine 2 and providing electric energy for the functional module. The voltage required by the microprocessor is 2.5V and 1.8V, the voltage required by the direct digital synthesis (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 provides overheat, overvoltage and overcurrent protection for the lithium battery module, so that reliable work of the lithium battery module is guaranteed.
Direct digital synthesis (Direct Digital Synthesis, DDS) sweep frequency signal generator
The direct digital synthesis (Direct Digital Synthesis, DDS) sweep frequency signal generator generates sine wave signals with a certain voltage and a frequency which is continuously variable under the control of the microprocessor, the peak-to-peak voltage of the sine wave is 1V, and the frequency is between 100MHz and 500 MHz. The sine wave is used as an excitation signal and transmitted to a second inductor for acquiring the impedance of the resonance circuit of the internal body machine at different frequencies.
Impedance analyzer
The impedance analyzer collects the voltage and the current at two ends of the second inductor respectively, digitizes them and transmits them to the microprocessor. The microprocessor performs FFT conversion to obtain amplitude values and phase values of the voltage and the current, and subtracts the phase value of the current from the phase value of the voltage to obtain the phase value of the impedance of the second inductor at different frequencies. The microprocessor analyzes the phase value to find the frequency point of the extreme value of the change, namely, the phase value becomes larger no matter the frequency is increased or decreased at the frequency point, and the frequency point is the resonance frequency of the resonance circuit.
The mobile terminal 3 is connected with the external machine 2 in a wireless communication mode, the mobile terminal 3 can be a mobile phone or a tablet computer of a patient, and the mobile terminal 3 can display real-time intraocular pressure values, historical intraocular pressure data, change curves of intraocular pressure with time and other richer intraocular pressure information. Meanwhile, a Bluetooth module is correspondingly arranged in the external machine 2, and the result measured by the external machine 2 can be sent to the mobile terminal 3 in a wireless communication mode.
In addition, an intraocular pressure threshold value can be set in the mobile terminal 3 by itself, when the acquired intraocular pressure value is larger than the threshold value, the mobile terminal 3 can send out a prompt tone or shake to remind a user, and meanwhile, the intraocular pressure value at the moment and the improvement measure suggestion given for the intraocular pressure value are highlighted on a display screen. When the collected intraocular pressure value is smaller than the threshold value, the mobile terminal 3 only receives and stores the intraocular pressure information, and the corresponding intraocular pressure information can be viewed only when the user operates the mobile terminal 3.
The invention relates to an intraocular pressure measuring device, which comprises the following working principles: the pressure control variable capacitor 11 in the internal body unit 1 changes in response to the pressure change, and thus the resonance frequency of the flexible thin film pressure sensor changes. The external machine 2 is a resonant frequency detection circuit, and the impedance of the internal machine 1 under different frequencies is read through the principle of electromagnetic induction to obtain the resonant frequency, so as to obtain the intraocular pressure. The method comprises the following steps: the second inductor on the external machine 2 is electromagnetically coupled with the first inductor 13 of the internal machine 1, and the impedance of the internal machine 1 is reflected to the external machine 2, so that the impedance of the second inductor of the external machine 2 is changed, the external machine 2 measures the impedance of the second inductor under different frequencies, and the impedance of the internal machine 1 under different frequencies can be obtained according to the measured impedance of the external machine 2. The impedance is a complex number including an amplitude and a phase, and the external machine 2 measures the impedance of the internal machine 1, and when the internal machine 1 resonates at a certain frequency, the phase of the impedance reaches a certain extremum, and according to this feature, the resonance frequency of the internal machine 1 can be obtained. The corresponding relation between the resonance frequency of the in-vivo machine 1 and the intraocular pressure is counted in advance, and the magnitude of the intraocular pressure can be obtained through a pre-selected and set algorithm in the microprocessor according to the measured resonance frequency.
The microprocessor on the external machine 2 sends the intraocular pressure value to the display module for display and simultaneously sends the intraocular pressure value to the mobile terminal 3 of the patient through a Bluetooth signal, and the patient can see the change rule of the intraocular pressure of the patient along with time in real time through the mobile terminal 3.
Example two
The difference from the first embodiment is that the in-vivo machine 1 is a disc-type flexible film pressure sensor with a diameter of 5mm and a thickness of 0.5 mm. Since the size of the in-vivo machine 1 is increased as compared with the first embodiment, the pressure-controlled variable capacitor 11 is increased as compared with the first embodiment, so that the measured resonance frequency is lowered, resulting in a lower measured intraocular pressure value, and thus, the accuracy of measuring changes in intraocular pressure by the in-vivo machine 1 is lowered. In addition, the volume of the internal body machine 1 is increased, the manufacturing difficulty and the operation implantation difficulty of the internal body machine 1 can be reduced, but the implantation position of the eye matrix layer of the patient is required to be higher, and the internal body machine is not suitable for children, but is more suitable for adults with less serious illness, and the wearing discomfort of the user can not be caused.
Example III
The difference from the first embodiment is that the in-vivo machine 1 is a disc-type flexible film pressure sensor with a diameter of 6mm and a thickness of 0.6 mm. The size of the internal body machine 1 is obviously improved, so that the pressure control variable capacitor 11 in the internal body machine 1 is larger, the difficulty of manufacturing and operation implantation is reduced, and the measurement accuracy is also reduced. Due to size exchange, the requirement for the implantation position of the ocular matrix layer of the patient is higher, and the method is only suitable for the adult patient with mild symptoms which meet the implantation requirement after measurement.
Example IV
The difference from the first embodiment is that the structure of the in-vivo machine 1 is different, as shown in fig. 4 and 5, in this embodiment, a flexible circuit board 121 is wrapped in a flexible protection layer 12 of the in-vivo machine 1, the flexible circuit 122 has a thickness of 0.05mm, and the shape is two circles connected by a thin strip in the middle and folded in half from the middle position of the middle thin strip so that the two circles are parallel to each other. Pads 114 are provided on the flexible circuit board 121 on the inner sides of two circular center positions.
The middle of the folded flexible circuit board 121 is filled with a flexible thin film capacitor medium 112, and the flexible thin film capacitor medium 112 is made of hydrogel. The pads 114 arranged in parallel and the flexible thin film capacitance medium 112 therebetween constitute the pressure control variable capacitor 11.
The pads 114 are circular with a diameter of 2.48mm. The diameter of the bonding pad 114 is smaller, so that the pressure control variable capacitor 11 is smaller, and is sensitive to the change of the resonant frequency, so that the resonant frequency to be finally measured is increased, the measured intraocular pressure value is higher, and the detection accuracy can be improved. At the same time, the size of the internal body machine 1 is smaller, and although the difficulty of manufacturing, subsequent encapsulation and surgical implantation is increased, the internal body machine does not feel foreign body sensation to a wearer, and is suitable for children and adults with serious symptoms.
A copper foil coil 132 is horizontally wound around the pad 114, and the thickness of the copper foil in the copper foil coil 132 is 0.01mm, constituting the first inductor 13. The pad 114 and the copper foil coil 132 are both made of copper material, and have good chemical stability and conductivity.
Example five
The difference from the fourth embodiment is that the diameter of the pad 114 is 2.5mm. As the size of the pad 114 increases, the pressure control variable capacitor 11 also increases, the sensitivity to the change in the resonance frequency decreases, the resonance frequency to be finally measured decreases, the measured intraocular pressure value decreases, and the detection accuracy slightly decreases. Meanwhile, the size of the internal machine 1 is increased, the difficulty of manufacturing, subsequent encapsulation and surgical implantation is reduced, but the implantation position of the eye matrix layer of a patient is higher in requirement, and the internal machine is not suitable for children, but is more suitable for adults with less serious illness, and the wearer cannot feel foreign body sensation.
Example six
The difference from the fourth embodiment is that the diameter of the pad 114 is 2.52mm. Since the size of the pad 114 is significantly increased, the pressure-controlled variable capacitor 11 is also significantly increased, and sensitivity to variation in resonance frequency is reduced, resulting in a consequent reduction in the resonance frequency to be finally measured, a lower intraocular pressure value to be measured, and a reduction in detection accuracy.
The increase in pad 114 increases the size of the in vivo machine 1 and reduces the difficulty of manufacturing, subsequent encapsulation and surgical implantation, but requires a higher implantation site for the ocular matrix layer of the patient, which is only suitable for an adult patient with mild symptoms that meet the implantation requirements after measurement.
Therefore, the intraocular pressure measuring device can enable the measuring result to be more accurate, can realize continuous measurement for 7 x 24 hours, can monitor the intraocular pressure condition in real time, and can upload measured intraocular pressure data to the cloud end, so that doctors can know the illness state of patients more conveniently, and a more reasonable treatment scheme can be given to the patients.
Finally, it should be noted that: the above embodiments are only for illustrating the technical solution of the present invention and not for limiting it, and although the present invention has been described in detail with reference to the preferred embodiments, it will be understood by those skilled in the art that: the technical scheme of the invention can be modified or replaced by the same, and the modified technical scheme cannot deviate from the spirit and scope of the technical scheme of the 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.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311029058.4A CN117017206A (en) | 2023-08-16 | 2023-08-16 | Intraocular pressure measuring device |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311029058.4A CN117017206A (en) | 2023-08-16 | 2023-08-16 | Intraocular pressure measuring device |
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| CN117017206A true CN117017206A (en) | 2023-11-10 |
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| CN202311029058.4A Pending CN117017206A (en) | 2023-08-16 | 2023-08-16 | Intraocular pressure measuring device |
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| CN (1) | CN117017206A (en) |
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Effective date of registration: 20241008 Address after: 211, Block E, Building 2, Zhongguancun Dongsheng International Science Park, No.1 Yongtaizhuang North Road, Haidian District, Beijing 100192 Applicant after: Wang Lejin Country or region after: China Address before: 102200 room 426, 4 / F, 101, 2-12 / F, No. 6, yard 1, No. 8, shengshengyuan Road, Changping District, Beijing (Changping Demonstration Park) Applicant before: Chaomu Technology (Beijing) Co.,Ltd. Country or region before: China |