Intraocular pressure measuring device

Abstract

The invention relates to the technical field of medical instruments, in particular to an intraocular pressure measuring device which comprises an intraocular pressure sensor, a shooting module and a shooting element. Wherein the intraocular pressure sensor is provided with a Fabry-Perot microcavity; the shooting module comprises a shell, a light path assembly arranged in the shell and a light source arranged outside the shell; a shooting hole is formed in the shell; light emitted by the light source is transmitted to the Fabry-Perot microcavity after passing through the light path assembly, and an interference pattern is generated; the shooting element comprises a lens; the shooting hole is suitable for being matched with the lens so as to acquire the interference pattern through the shooting element. According to the invention, by introducing the shooting module matched with the existing shooting element, the detection of the intraocular pressure can be completed by means of the existing shooting element; in the detection process, the positions of the shooting module and the shooting element can be flexibly adjusted according to the position of the Fabry-Perot microcavity in the intraocular pressure sensor, so that the incident beam meets the requirement of vertical incidence, and the difficulty of angle adjustment in the intraocular pressure detection process is greatly reduced.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and particularly to an intraocular pressure measuring device. Background Art

[0002] Glaucoma is one of the three major causes of blindness in the human eye and is extremely harmful. High intraocular pressure is considered an important risk factor for the onset of glaucoma. Therefore, intraocular pressure is an important indicator for determining the treatment goals of glaucoma, as well as evaluating the treatment effect and prognosis in clinical practice.

[0003] Currently, the main method for detecting intraocular pressure is to detect the instantaneous intraocular pressure of patients through instruments. The detection instruments mainly include applanation tonometers, air puff tonometers, etc. Among them, the applanation tonometer has a complex measurement process, with disadvantages such as the need for surface anesthesia before measurement, instillation of fluorescein sodium on the cornea during measurement, and the measured value being affected by the central corneal thickness. Compared with the applanation tonometer, the air puff tonometer simplifies the process of measuring intraocular pressure and does not require surface anesthesia and fluorescein sodium. However, the air puff tonometer also has many problems, such as the impact air flow causing discomfort in the patient's eyes, the instrument being expensive and not portable.

[0004] In addition, there are currently many studies on micro-implantable intraocular pressure sensors based on different principles. The common features of these studies are: 1. The sensor is separated from the detection device, and the sensing method is non-contact; 2. The area and volume of the sensor are very small, ranging from hundreds of micrometers to a few millimeters; 3. The sensor is in contact with the eye structure, attached to the eyeball or implanted inside the eyeball.

[0005] These implantable intraocular pressure sensors can be mainly classified into three types according to the sensing principle: electrical sensing, microfluidic sensing, and optical sensing. Chen et al. designed an intraocular pressure sensor based on a contact lens as a carrier, which is sensitive to pressure based on the capacitance value. The frequency of the LC oscillator formed by the capacitor and inductor also changes with the change of [pressure], and the reading device is a large network analyzer. Agaoglu et al. used a microfluidic chip to achieve intraocular pressure detection. An artificial lens integrated with the microfluidic chip was implanted into the eyeball using cataract surgery technology. As the intraocular pressure fluctuates, the position of the liquid-gas interface of the artificial lens generates displacement, and monitoring the position of this interface can obtain the intraocular pressure value. Electrical sensing is limited by the circuit structure and materials, and it is difficult to achieve a size of sub-millimeter level. Moreover, the reading device is large in volume and expensive. Microfluidic sensing is limited by the strict requirements for airtightness and the indirect sensing principle of photographing and reading, which makes miniaturization encounter a bottleneck. The volume of optical sensors is generally smaller than that of electrical sensors and microfluidic sensors. Therefore, it has become the main research direction of implantable sensors.

[0006] Existing optical - sensing - based micro - pressure sensors usually rely on desktop - type microscopes to capture optical interference patterns. During the detection process, only xyz - axis adjustments can be made, and three - dimensional angle adjustments are not possible, which cannot meet the high dependence on the incident light angle in optical interference pattern capture, thus limiting their applications. Summary of the Invention

[0007] To solve the problem that three - dimensional angle adjustment cannot be performed during the detection of intraocular pressure by existing optical - sensing - based pressure sensors, the present invention provides an intraocular pressure measurement device. By adopting a shooting module that can be compatible with existing shooting elements, during the detection process, the incident light angle is adjusted by adjusting the angle of the shooting element to meet the requirements of optical interference pattern capture, thus solving the problem that three - dimensional angle adjustment cannot be performed during the detection of intraocular pressure by existing optical - sensing - based pressure sensors.

[0008] The technical solution adopted by the present invention to solve its technical problems is as follows: An intraocular pressure measurement device includes an intraocular pressure sensor, a shooting module, and a shooting element; wherein, A Fabry - Perot microcavity is provided on the intraocular pressure sensor; The shooting module includes a housing, an optical path component disposed inside the housing, and a light source disposed outside the housing; A shooting hole is provided on the housing; The light emitted by the light source is transmitted to the Fabry - Perot microcavity through the optical path component and generates an interference pattern; The shooting element includes a lens; The shooting hole is adapted to cooperate with the lens to obtain the interference pattern through the shooting element.

[0009] Optionally, the optical path component includes a beam - splitting cube and a plano - convex lens sequentially disposed in the shooting hole.

[0010] Optionally, the optical path component further includes a narrow - band filter disposed between the light source and the beam - splitting cube.

[0011] Optionally, the shooting element is a mobile phone; a CMOS image sensor is provided in the mobile phone.

[0012] Optionally, the shooting module further includes a fixture; one end of the fixture is connected to the shooting element, and the other end is connected to the housing.

[0013] Optionally, the intraocular pressure sensor includes a sensor body and a bracket connected to the sensor body.

[0014] Optionally, the bracket is a plate - like structure.

[0015] Optionally, the bracket includes a mounting end and a fixed end connected to the mounting end.

[0016] Optionally, the fixed end is an arc-shaped structure.

[0017] Optionally, the fixed end includes a wide section, a tapered section, and a narrow section connected in sequence; the widths of the wide section, the tapered section, and the narrow section decrease in sequence.

[0018] Optionally, a drainage groove is provided on the bracket.

[0019] Optionally, the drainage groove includes a first groove-shaped structure longitudinally distributed along the bracket.

[0020] Optionally, the drainage groove further includes a second groove-shaped structure obliquely distributed on the wide section; the second groove-shaped structure is communicated with the first groove-shaped structure.

[0021] The beneficial effects of the present invention are as follows: The intraocular pressure measuring device provided by the present invention can complete the detection of intraocular pressure by introducing a shooting module adapted to the existing shooting element, and by means of the existing shooting element; moreover, during the detection process, the positions of the shooting module and the shooting element can be flexibly adjusted according to the position of the Fabry-Perot microcavity in the intraocular pressure sensor, so that the incident light beam meets the requirement of perpendicular incidence, thereby greatly reducing the difficulty of angle adjustment during the intraocular pressure detection process, making it more portable, efficient and easy to use. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] The present invention will be further described below with reference to the drawings and embodiments.

[0023] Figure 1 is a schematic structural diagram of the intraocular pressure measuring device in the present invention; Figure 2 is an exploded view of the intraocular pressure sensor in the present invention; Figure 3 is an exploded view of the shooting module in the present invention; Figure 4 is a schematic structural diagram of the optical path component in the present invention; Figure 5 is a schematic diagram of the influence of the shooting angle on the integrity of the optical interference pattern in the present invention.

[0024] In the figure: 1 - intraocular pressure sensor; 11 - sensor body; 12 - bracket; 121 - mounting end; 122 - fixed end; 1221 - wide section; 1222 - tapered section; 1223 - narrow section; 1224 - anti-slip structure; 123 - drainage groove; 1231 - first groove structure; 1232 - second groove structure; 2 - photographing module; 21 - housing; 211 - photographing hole; 22 - optical path component; 221 - beam splitter cube; 222 - plano-convex lens; 223 - narrowband filter; 23 - light source; 24 - fixture; 241 - C-shaped element; 2411 - mounting groove; 2412 - through hole; 242 - threaded connector; 3 - photographing element; 31 - lens. Detailed implementation manners

[0025] The present invention will now be described in further detail. The embodiments described below are exemplary and are intended to explain the present invention, and should not be construed as limiting the present invention. All other embodiments obtained by those of ordinary skill in the art based on the embodiments of the present invention without creative efforts fall within the scope of protection of the present invention.

[0026] In order to make the above objects, features, and advantages of the present invention more apparent and understandable, the specific embodiments of the present invention will be described in detail below with reference to the accompanying drawings.

[0027] In order to solve the problem that the three-dimensional angle adjustment cannot be performed during the detection of intraocular pressure by a pressure sensor based on optical sensing in the prior art, the present invention provides an intraocular pressure measuring device. Refer to Figure 1 As shown, the intraocular pressure measuring device includes an intraocular pressure sensor 1, a photographing module 2, and a photographing element 3; it should be noted that, in the present invention Figure 1 In order to clearly show the structure of the intraocular pressure measuring device, the size of the intraocular pressure sensor is artificially enlarged; among them, the intraocular pressure sensor 1 is a MEMS sensor. Refer to Figure 2 As shown, a Fabry-Perot microcavity is provided on the intraocular pressure sensor 1. Refer to Figure 3 As shown, the photographing module 2 includes a housing 21, preferably the housing 21 is made of polylactic acid (PLA) material and prepared by an extrusion 3D printing process; an optical path component 22 provided inside the housing 21, and a light source 23 provided outside the housing 21; a photographing hole 211 is provided on the housing 21; the light emitted by the light source 23 is transmitted to the Fabry-Perot microcavity through the optical path component 22 and generates an interference pattern; the photographing element 3 includes a lens 31; the photographing hole 211 is adapted to cooperate with the lens 31 to obtain the interference pattern through the photographing element 3.

[0028] The present invention preferably uses the light source 23 as a white light source.

[0029] During operation, the light emitted by the light source 23 passes through the optical path component 22 and then perpendicularly enters the Fabry-Perot microcavity of the intraocular pressure sensor 1, that is, the F-P resonant cavity. It enters the cavity of the Fabry-Perot microcavity, is reflected by multiple surfaces and interferes to obtain an interference pattern. The obtained interference pattern passes through the optical path component 22 and is then transmitted to the lens 31 of the imaging element 3. By taking a photo with the imaging element 3, the interference pattern can be captured in real time, and thus the real-time intraocular pressure can be obtained based on the interference pattern captured in real time.

[0030] Specifically, for the method of obtaining the intraocular pressure based on the interference pattern, corresponding existing technologies can be selected.

[0031] For example, during use, the intraocular pressure sensor 1 is implanted into the anterior chamber of the eye. The outer surface of the Fabry-Perot microcavity is in contact with the intraocular fluid to sense the change in intraocular pressure. When the intraocular pressure increases, the Fabry-Perot microcavity deforms, resulting in a change in the optical path of the reflected light, and the generated interference pattern changes. The interference fringes bend. By accurately identifying, segmenting, and extracting the area containing the interference fringes in the interference pattern, the skeleton of the fringes is extracted after binarization, and the order of each fringe is marked. Then, the central deflection of the film of the Fabry-Perot microcavity after being pressed is calculated. The central deflection of the film of the Fabry-Perot microcavity corresponds one-to-one with the pressure value of the film of the Fabry-Perot microcavity calibrated by the calibration device, realizing the conversion of the photo containing the interference fringe image captured into a pressure value, and thus the intraocular pressure can be obtained based on the change in the interference pattern.

[0032] Among them, for the method of obtaining the intraocular pressure based on the change in the interference pattern, corresponding existing technologies can also be selected. For example, the intraocular pressure is obtained by performing image processing and pressure calculation on the interference pattern captured by the imaging element 1.

[0033] The intraocular pressure measuring device provided by the present invention completes the detection of the intraocular pressure by introducing the imaging module 2 adapted to the existing imaging element 3 and with the help of the existing imaging element 3. Moreover, during the detection process, the positions of the imaging module 2 and the imaging element 3 can be flexibly adjusted according to the position of the Fabry-Perot microcavity in the intraocular pressure sensor 1, so that the incident light beam meets the requirement of perpendicular incidence, thereby greatly reducing the difficulty of angle adjustment during the intraocular pressure detection process and making it more portable, efficient, and easy to use.

[0034] To achieve the measurement of the intraocular pressure, refer to Figure 4As shown, the preferred optical path component 22 of the present invention includes a beam splitter cube 221 and a plano-convex lens 222 sequentially arranged in the shooting hole 211. The working wavelength range of the beam splitter cube 221 is 450–650 nm. When light is incident at an angle of 45°, the incident light can be split into two beams of light with a ratio of approximately 50% transmission (T) and 50% reflection (R), and the tolerance is ±5% (T / R = 50% : 50% ±5%). After the light emitted by the light source 23 is reflected by the beam splitter cube 221 to adjust the optical path direction, it passes through the plano-convex lens 222 and converges to the target plane for generating an optical interference pattern, that is, the position of the Fabry-Perot microcavity; the reflected light of the interference pattern passes through the plano-convex lens 222 and the beam splitter cube 221 again, and then reaches the lens 31 of the shooting element 3 to realize the acquisition and imaging of the interference pattern; preferably, the designed wavelength of the plano-convex lens 222 is 350-700 nm, and the focal length is 20 mm.

[0035] Furthermore, the preferred optical path component 22 of the present invention further includes a narrow-band filter 223 arranged between the light source 23 and the beam splitter cube 221. The narrow-band filter 223 is a 633 nm narrow-band filter, so that the light emitted by the light source 23 can obtain monochromatic light with a central wavelength of 633 nm and a bandwidth of ±10 nm after being filtered by the narrow-band filter 223.

[0036] The shooting element 3 in the present invention can be any existing digital camera, video camera, smart phone, etc. including a CMOS image sensor; to further reduce the shooting difficulty, the shooting element 3 is preferably a mobile phone; a CMOS image sensor is arranged in the mobile phone to realize the acquisition and imaging of the interference pattern.

[0037] When the existing pressure sensors based on optical sensing measure intraocular pressure, the incident light needs to satisfy equal inclination interference; for equal inclination interference, the main requirement is that when the two interfering light beams are reflected or refracted, the incident angle and the reflection angle (or refraction angle) are equal. In other words, the incident light beam needs to satisfy the requirement of perpendicular incidence to ensure the complete formation of interference fringes. When the micro pressure sensor is implanted into the pressure detection environment, due to its too small size, it is impossible to ensure whether it is horizontal. When using a desktop microscope, the microscope generally can only maintain a vertically downward angle. Then, if you want to obtain a complete optical interference pattern, you can only adjust the spatial angle position of the object to be measured by feeling, which is extremely difficult, especially when the object to be measured is an object whose spatial angle position cannot be adjusted, such as an intraocular pressure sensor implanted in the eye. Based on this, the present invention proposes an external shooting module 2 that can be adapted to any smart phone. Compared with adjusting the uncertain spatial angle position of the object to be measured, it is obviously much easier to adjust the angle of the handheld phone. Further, we can judge which angle to tilt the phone according to the image captured by the phone camera in real time. The optical interference pattern captured by the phone camera in real time is a square area. When the incident light angle is not perpendicular to the interference plane, the square area is incomplete, showing a state of being bright in part and dark in part. See Figure 5 As shown, we can imagine the square interference area as a sealed "square box" filled with water, and the bright part as a "bubble" in the sealed space. Then, when the "bubble" is in which direction of the square area, the "square box" should be tilted in that direction until the "bubble" moves to the center of the square area. The mobile phone is the "square box". When the "bubble" moves to the center of the square area, it means that the incident light angle is perpendicular to the interference plane, and at this time, a complete optical interference pattern is captured.

[0038] To facilitate connection with the mobile phone, the shooting module 2 of the present invention preferably further includes a fixture 24; one end of the fixture 24 is connected to the shooting element 3, that is, the mobile phone, and the other end is connected to the housing 21.

[0039] The fixture 24 of the present invention is preferably made of polylactic acid (PLA) material and prepared by an extrusion 3D printing process; and further preferably, the fixture 24 is a C-shaped clip-like structure, including a C-shaped element 241 and a threaded connector 242; the C-shaped element 241 is connected to the housing 21; the C-shaped element 241 is connected to the shooting element 3 through the threaded connector 242; during use, the mobile phone is placed in the C-shaped element 241, and by tightening the threaded connector 242, the connection with the mobile phone is realized; the present invention preferably sets the opening and closing range of the C-shaped element 241 to be 8-20 mm, and this range can adapt to the thickness of most smart phones on the market.

[0040] Furthermore, in the present invention, it is preferred that the housing 21 and the fixture 24 are connected by a snap - fit method. Specifically, preferably, on the C - shaped element 241 of the fixture 24, there is an installation groove 2411 adapted to the housing 21, and there are concave points in the installation groove 2411. There are convex points on the outer side of the housing 21 adapted to the concave points. Through the mutual cooperation of the convex points and the concave points, the two parts can be assembled or disassembled conveniently.

[0041] Moreover, a through - hole 2412 adapted to the shooting hole 211 is provided in the installation groove 2411 to avoid the influence of the C - shaped element 241 on light transmission.

[0042] In summary, the present invention provides an external shooting module 2 compatible with any smart phone. The housing 21 of the external shooting module 2 is made of an environmentally friendly polylactic acid (PLA) material and is prepared by an accurately controlled extrusion - type 3D printing process, ensuring the consistency of structural strength and quality. The shooting module 2 integrates an optimized customized optical path design and high - performance optical elements, and combines real - time image capture to achieve stable shooting of high - quality images. Compared with the initial desktop microscope - type image capture method, this module not only ensures image clarity and optical imaging quality, but also significantly reduces the complexity of user operation and the influence of jitter during the shooting process, making the device more portable, the operation more efficient, and at the same time improving the experience and applicability.

[0043] The intraocular pressure sensor 1 in the present invention can be any existing intraocular pressure sensor provided with a Fabry - Perot micro - cavity; since the intraocular pressure monitoring device provided by the present invention detects the intraocular pressure based on optical sensing, as described above, during the detection process, the incident light needs to satisfy equal - inclination interference, and equal - inclination interference requires that the incident light beam satisfies the requirement of perpendicular incidence; therefore, to ensure the clarity of the detection image, it is required that the position of the intraocular pressure sensor 1 remains fixed and does not move during the detection process; to avoid the movement of the intraocular pressure sensor 1 during the detection process, the present invention preferably includes a sensor body 11 and a bracket 12 connected to the sensor body 11 for fixing the intraocular pressure sensor body 11 through the bracket 12, reducing the detection difficulty and improving the clarity of the detection image.

[0044] Existing brackets for fixing intraocular implants are mostly cylindrical structures; since in the intraocular pressure measuring device provided by the present invention, if the position of the intraocular pressure sensor body 11 moves slightly during the detection process, it will cause the incident light beam not to be perpendicularly incident, and the shooting angle of the shooting element 3 needs to be readjusted. Therefore, to ensure the stability of the position of the intraocular pressure sensor body 11 during the detection process, the present invention preferably has the bracket 12 as a plate - like structure to increase the contact area between the bracket 12 and the inside of the eye and avoid the movement of the intraocular pressure sensor body 11.

[0045] Specifically, the stent 12 of the present invention preferably includes an installation end 121 and a fixed end 122 connected to the installation end 121. The installation end 121 is used to be connected to the intraocular pressure sensor body 11. In the present invention, the intraocular pressure sensor body 11 and the installation end 121 can be connected by means such as high-temperature bonding and bonding with compatible materials. The size of the installation end 121 is determined according to the size of the intraocular pressure sensor body 11.

[0046] Since the eyeball has a certain curvature, to improve the fitting degree of the stent 12 to the eyeball, while improving the stability of the intraocular pressure sensor body 11 and the comfort of the patient, the fixed end 122 of the present invention is preferably an arc-shaped structure, and the curvature of the arc-shaped structure is determined according to the curvature of the eyeball.

[0047] To improve the comfort while ensuring the stability of the intraocular pressure sensor body 11, the fixed end 122 of the present invention preferably includes a wide section 1221, a tapered section 1222, and a narrow section 1223 connected in sequence. The widths of the wide section 1221, the tapered section 1222, and the narrow section 1223 decrease in sequence.

[0048] It should be noted that in the stent 12 of the present invention, in the length direction of the distribution direction of the wide section 1221, the tapered section 1222, and the narrow section 1223, on the plane of the plate-shaped structure of the stent 12, the direction perpendicular to this length direction is the width direction.

[0049] Specifically, the wide section 1221 of the present invention is preferably a plate-shaped structure with a rectangular cross-section to ensure the contact area between the stent 12 and the eyeball. The width of the tapered section 1222 preferably decreases in sequence. The width of the end connected to the wide section 1221 is the same as the width of the wide section 1221, and the width of the end connected to the narrow section 1223 is the same as the width of the narrow section 1223.

[0050] To balance comfort and the stability of the position of the intraocular pressure sensor body 11, the present invention preferably sets the length ratio of the wide section 1221, the tapered section 1222, and the narrow section 1223 to (1.4 - 1.7):(1.1 - 1.4):(0.7 - 1).

[0051] To further improve the stability of the intraocular pressure sensor body 11 after implantation, the present invention preferably provides an anti-slip structure 1224 on the outer side of the narrow section 1223, and specifically preferably the anti-slip structure 1224 is a convex structure extending outward along the narrow section 1223.

[0052] To balance the stability of the position of the intraocular pressure sensor body 11 and comfort, the present invention further preferably sets the number of convex structures to at least two groups. Each group includes two convexes of the same size symmetrically arranged on both sides of the narrow section 1223. Moreover, the size of the convexes gradually decreases in the direction away from the tapered section 1222.

[0053] The present invention further preferably provides a drainage groove 123 on the bracket 12, so that the intraocular pressure measuring device provided by the present invention not only has the function of measuring intraocular pressure, but also has a certain drainage effect.

[0054] Existing intraocular pressure sensors usually only have the function of detecting intraocular pressure and cannot achieve drainage; when the intraocular pressure is high, a corresponding drainage device needs to be introduced to achieve the therapeutic effect; based on this, the present invention preferably provides a drainage groove 123 on the bracket 12, so as to diffuse the aqueous humor to the surrounding tissues of the eye through the drainage groove 123, enabling the intraocular pressure sensor to have both the functions of detecting intraocular pressure and drainage, so that intraocular pressure detection and drainage can be achieved by one implantation without increasing the number of implantations, surgical trauma, or patient pain.

[0055] The drainage groove 123 includes a groove-shaped structure longitudinally distributed along the bracket 12 and sequentially penetrating through the mounting end 121 and the fixing end 122, denoted as the first groove-shaped structure 1231; to further improve the drainage effect, the drainage groove 123 further includes a second groove-shaped structure 1232 obliquely distributed on the wide section 1221, and the second groove-shaped structure 1232 is communicated with the first groove-shaped structure 1231.

[0056] The intraocular pressure sensor provided by the present invention can be implanted into the eye by injection, significantly reducing surgical trauma; the intraocular pressure sensor provided by the present invention through a breakthrough design can be implanted into the eye by minimally invasive injection, and the system can achieve all-weather continuous monitoring of intraocular pressure without electronic components and electromagnetic energy supply, and the intraocular pressure measurement accuracy reaches ±1 mmHg.

[0057] For the intraocular pressure sensor provided by the present invention, based on the change in the interference fringe spacing of the sensor caused by the change in intraocular pressure, the function relationship between the deflection of the Fabry-Perot microcavity in the central area of the sensor and intraocular pressure can be established. Through the advanced M-net neural network training and sparse attention Transformer image restoration algorithm integrated in the mobile phone APP, the interference fringe area of the sensor can be automatically focused, identified, and cropped, and real-time intraocular pressure demodulation can be performed, enabling patients to self-measure intraocular pressure at home with a mobile phone, independent of the signal transmission of electromagnetic energy supply, and effectively avoiding signal loss caused by external factors.

[0058] The intraocular pressure sensor provided by the present invention has stronger compatibility and universality, can be compatible and used with any existing ophthalmic implant device, and helps to further explore the feasibility of the clinical new technology of integrated glaucoma monitoring and treatment.

[0059] Inspired by the above-described ideal embodiments of the present invention, through the above description, relevant staff can completely make various changes and modifications without departing from the technical idea of this invention. The technical scope of this invention is not limited to the content in the specification, and its technical scope must be determined according to the scope of the claims.

Claims

1. An intraocular pressure measuring device, characterized in that, It includes an intraocular pressure sensor (1), a shooting module (2) and a shooting element (3); wherein, A Fabry-Perot microcavity is provided on the intraocular pressure sensor (1); The shooting module (2) includes a housing (21), an optical path component (22) disposed inside the housing (21), and a light source (23) disposed outside the housing (21); A shooting hole (211) is provided on the housing (21); The light emitted by the light source (23) is transmitted to the Fabry-Perot microcavity through the optical path component (22) and an interference pattern is generated; The shooting element (3) includes a lens (31); The shooting hole (211) is adapted to cooperate with the lens (31) to obtain the interference pattern through the shooting element (3).

2. The intraocular pressure measuring device according to claim 1, characterized in that, The optical path component (22) includes a beam splitter cube (221) and a plano-convex lens (222) sequentially disposed in the shooting hole (211).

3. The intraocular pressure measuring device according to claim 2, wherein The optical path component (22) further includes a narrowband filter (223) disposed between the light source (23) and the beam splitter cube (221).

4. The intraocular pressure measuring device according to claim 1, wherein The shooting element (3) is a mobile phone; a CMOS image sensor is provided in the mobile phone.

5. The intraocular pressure measuring device according to claim 1, characterized in that, The shooting module (2) further includes a fixture (24); one end of the fixture (24) is connected to the shooting element (3), and the other end is connected to the housing (21).

6. The intraocular pressure measuring device according to any one of claims 1-5, characterized in that, The intraocular pressure sensor (1) includes a sensor body (11) and a bracket (12) connected to the sensor body (11).

7. The intraocular pressure measuring device according to claim 6, characterized in that, The bracket (12) is a plate-like structure.

8. The intraocular pressure measuring device according to claim 7, wherein, The bracket (12) includes a mounting end (121) and a fixed end (122) connected to the mounting end (121).

9. The intraocular pressure measuring device according to claim 8, characterized in that, The fixed end (122) is an arc-shaped structure.

10. The intraocular pressure measuring device according to claim 8, wherein, The fixed end (122) includes a wide section (1221), a tapered section (1222) and a narrow section (1223) connected in sequence; the widths of the wide section (1221), the tapered section (1222) and the narrow section (1223) decrease in sequence.

11. The intraocular pressure measuring device according to claim 10, characterized in that, A drainage groove (123) is provided on the bracket (12).

12. The intraocular pressure measuring device according to claim 11, wherein, The drainage groove (123) includes a first groove-like structure (1231) longitudinally distributed along the bracket (12).

13. The intraocular pressure measuring device according to claim 12, characterized in that, The drainage groove (123) further includes a second groove-like structure (1232) obliquely distributed on the wide section (1221); the second groove-like structure (1232) is communicated with the first groove-like structure (1231).

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