An intraocular pressure measuring device

Abstract

The application relates to the technical field of medical devices, 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; the shell is provided with a shooting hole; the 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 adapted to cooperate with the lens so as to acquire the interference pattern through the shooting element. The shooting module adapted to the existing shooting element is introduced, and the detection of the intraocular pressure can be completed by means of the existing shooting element; 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 vertical incidence, thereby greatly reducing the difficulty of angle adjustment during the intraocular pressure detection process.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to an intraocular pressure measuring device. Background Technology

[0002] Glaucoma is one of the three leading causes of blindness and poses a significant threat to human health. High intraocular pressure is considered a major risk factor for glaucoma; therefore, intraocular pressure is an important indicator in clinical practice for determining glaucoma treatment goals and assessing treatment effectiveness and prognosis.

[0003] Currently, the main method for measuring intraocular pressure (IOP) is through instruments that measure the patient's IOP in real time. These instruments primarily include applanation tonometers and aero-jet tonometers. Applanation tonometers, however, are complex and have drawbacks such as requiring topical anesthesia before measurement, needing to instill fluorescein sodium into the cornea during measurement, and the measurement being affected by the central corneal thickness. Aero-jet tonometers, compared to applanation tonometers, simplify the measurement process and do not require topical anesthesia or fluorescein sodium. However, aero-jet tonometers also have several drawbacks, including the impact of the airflow causing eye discomfort, high cost, and inconvenience.

[0004] In addition, there are many studies on miniature implantable intraocular pressure sensors based on different principles. These studies share the following characteristics: 1. The sensor is separate from the detection device, and the sensing method is non-contact; 2. The sensor area and volume are tiny, ranging from hundreds of micrometers to a few millimeters; 3. The sensor is in contact with the eye structure, either attached to the eyeball or implanted inside the eyeball.

[0005] These implantable intraocular pressure (IOP) sensors, classified according to their sensing principles, mainly fall into three categories: electro-sensing, microfluidic sensing, and optical sensing. Chen et al. designed an IOP sensor based on capacitance sensitivity to pressure, using a contact lens as a carrier. The frequency of an LC oscillator formed by capacitance and inductance changes with pressure, and the reading device is a large network analyzer. Agaoglu et al. used a microfluidic chip to achieve IOP detection. An artificial lens integrating the microfluidic chip was implanted into the eyeball using cataract surgery. As IOP fluctuates, the liquid-gas interface of the artificial lens shifts, and the IOP value is obtained by monitoring this interface position. Electro-sensing is limited by circuit structure and materials, making it difficult to achieve sub-millimeter sizes, and the reading devices are large and expensive. Microfluidic sensing faces bottlenecks in miniaturization due to stringent requirements for airtightness and the indirect sensing principle of image reading. Optical sensors, on the other hand, are generally smaller than electro-sensors and microfluidic sensors, thus becoming a major research direction for implantable sensors.

[0006] Existing optically based miniature pressure sensors typically rely on desktop microscopes to capture optical interference patterns. During the detection process, only three-axis adjustments (x, y, z) can be made, and three-dimensional angle adjustments are not possible. This fails to meet the high dependence of optical interference pattern capture on the incident angle of light, thus limiting its application. Summary of the Invention

[0007] To address the problem that existing optical pressure sensors cannot perform three-dimensional angle adjustments during intraocular pressure (IOP) detection, this invention provides an IOP measuring device. This device employs an imaging module compatible with existing imaging elements. During the detection process, the angle of the imaging element is adjusted to ensure that the incident angle of light meets the requirements for capturing optical interference patterns, thus solving the problem of the inability to perform three-dimensional angle adjustments during IOP detection using existing optical pressure sensors.

[0008] The technical solution adopted by this invention to solve its technical problem is:

[0009] An intraocular pressure measurement device includes an intraocular pressure sensor, an imaging module, and an imaging element; wherein,

[0010] The intraocular pressure sensor is provided with a Fabry-Perot microcavity;

[0011] The imaging module includes a housing, an optical path assembly disposed inside the housing, and a light source disposed outside the housing;

[0012] The housing is provided with a camera hole;

[0013] The light emitted by the light source is transmitted to the Fabry-Perot microcavity after passing through the optical path assembly, and an interference pattern is generated.

[0014] The imaging element includes a lens;

[0015] The imaging aperture is adapted to cooperate with the lens to acquire the interference pattern through the imaging element.

[0016] Optionally, the optical path assembly includes a beam-splitting cube and a plano-convex lens sequentially disposed in the imaging aperture.

[0017] Optionally, the optical path assembly further includes a narrowband filter disposed between the light source and the beam splitter cube.

[0018] Optionally, the imaging element is a mobile phone; the mobile phone is equipped with a CMOS image sensor.

[0019] Optionally, the shooting module further includes a clamp; one end of the clamp is connected to the shooting element, and the other end is connected to the housing.

[0020] Optionally, the intraocular pressure sensor includes a sensor body and a bracket connected to the sensor body.

[0021] Optionally, the support is a plate-like structure.

[0022] Optionally, the bracket includes a mounting end and a fixing end connected to the mounting end.

[0023] Optionally, the fixed end has an arc-shaped structure.

[0024] Optionally, the fixed end includes a wide segment, a gradient segment, and a narrow segment connected in sequence; the widths of the wide segment, the gradient segment, and the narrow segment decrease sequentially.

[0025] Optionally, the bracket is provided with a drainage groove.

[0026] Optionally, the drainage channel includes a first groove-shaped structure distributed longitudinally along the support.

[0027] Optionally, the drainage channel further includes a second channel-shaped structure obliquely distributed on the wide section; the second channel-shaped structure is connected to the first channel-shaped structure.

[0028] The beneficial effects of this invention are:

[0029] The intraocular pressure measurement device provided by this invention introduces an imaging module adapted to existing imaging elements, enabling the detection of intraocular pressure using existing imaging elements. Furthermore, during the detection process, the positions of the imaging module and imaging elements can be flexibly adjusted according to the position of the Fabry-Perot microcavity in the intraocular pressure sensor, ensuring that the incident light beam meets the requirement of perpendicular incidence. This significantly reduces the difficulty of angle adjustment during intraocular pressure detection, making it more portable, efficient, and easy to use. Attached Figure Description

[0030] The present invention will be further described below with reference to the accompanying drawings and embodiments.

[0031] Figure 1 This is a simplified structural diagram of the intraocular pressure measuring device in this invention;

[0032] Figure 2 This is an exploded view of the intraocular pressure sensor in this invention;

[0033] Figure 3 This is an exploded view of the imaging module in this invention;

[0034] Figure 4 This is a schematic diagram of the optical path component in this invention;

[0035] Figure 5 This is a schematic diagram illustrating the effect of the shooting angle on the integrity of the optical interference pattern in this invention.

[0036] In the diagram: 1-Intraocular pressure sensor; 11-Sensor body; 12-Bracket; 121-Mounting end; 122-Fixed end; 1221-Wide section; 1222-Gradual section; 1223-Narrow section; 1224-Anti-slip structure; 123-Drainage groove; 1231-First groove structure; 1232-Second groove structure; 2-Imaging module; 21-Housing; 211-Imaging hole; 22-Optical path assembly; 221-Beam splitter cube; 222-Planar-convex lens; 223-Narrow band filter; 23-Light source; 24-Clamp; 241-C-shaped element; 2411-Mounting groove; 2412-Through hole; 242-Threaded connector; 3-Imaging element; 31-Lens. Detailed Implementation

[0037] The present invention will now be described in further detail. The embodiments described below are exemplary and intended to explain the present invention, and should not be construed as limiting the present invention. All other embodiments obtained by those skilled in the art based on the embodiments of the present invention without inventive effort are within the scope of protection of the present invention.

[0038] To make the above-mentioned objects, features and advantages of the present invention more apparent and understandable, specific embodiments of the present invention will be described in detail below with reference to the accompanying drawings.

[0039] To address the limitation of existing optical pressure sensors in detecting intraocular pressure in terms of their inability to perform three-dimensional angle adjustments, this invention provides an intraocular pressure measurement device. (See attached image.) Figure 1 As shown, the intraocular pressure measurement device includes an intraocular pressure sensor 1, an imaging module 2, and an imaging element 3; it should be noted that the present invention... Figure 1 To clearly illustrate the structure of the intraocular pressure measurement device, the size of the intraocular pressure sensor has been artificially enlarged; among them, intraocular pressure sensor 1 is a MEMS sensor, see [link / reference]. Figure 2 As shown, the intraocular pressure sensor 1 is equipped with a Fabry-Perot microcavity; see [link / reference] Figure 3 As shown, the imaging module 2 includes a housing 21, preferably made of polylactic acid (PLA) material and fabricated by extrusion 3D printing; an optical path assembly 22 disposed inside the housing 21, and a light source 23 disposed outside the housing 21; an imaging hole 211 is provided on the housing 21; the light emitted by the light source 23 is transmitted to the Fabry-Perot microcavity after passing through the optical path assembly 22, and generates an interference pattern; the imaging element 3 includes a lens 31; the imaging hole 211 is adapted to cooperate with the lens 31 to obtain the interference pattern through the imaging element 3.

[0040] The preferred light source 23 of this invention is a white light source.

[0041] During operation, the light emitted by the light source 23 passes through the optical path assembly 22 and is incident perpendicularly on the Fabry-Perot microcavity (FP resonant cavity) of the intraocular pressure sensor 1. Upon entering the cavity of the Fabry-Perot microcavity, the light is reflected by multiple surfaces and interferes to obtain an interference pattern. The obtained interference pattern is then transmitted through the optical path assembly 22 to the lens 31 of the imaging element 3. The interference pattern can be captured in real time by taking a picture through the imaging element 3, and the real-time intraocular pressure can be obtained based on the real-time captured interference pattern.

[0042] Specifically, existing technologies can be used to obtain intraocular pressure based on interference patterns.

[0043] For example, during use, the intraocular pressure sensor 1 is implanted in the anterior chamber of the eye. The outer surface of the Fabry-Perot microcavity comes into contact with the intraocular fluid and senses changes in intraocular pressure. When the intraocular pressure increases, the Fabry-Perot microcavity deforms, causing a change in the optical path of the reflected light, which in turn changes the interference pattern and causes the interference fringes to bend. By accurately identifying, segmenting, and extracting the interference fringe regions contained in the interference pattern, and then binarizing them to extract the skeleton of the fringes and identifying the order of each fringe, the central deflection of the Fabry-Perot microcavity membrane after being compressed can be calculated. The central deflection of the Fabry-Perot microcavity membrane corresponds one-to-one with the pressure value of the Fabry-Perot microcavity membrane calibrated by the calibration device. This allows the captured image containing interference fringes to be converted into a pressure value, and thus the intraocular pressure can be obtained based on the changes in the interference pattern.

[0044] The method of obtaining intraocular pressure based on changes in interference patterns can also use existing technologies, such as obtaining intraocular pressure by performing image processing and pressure calculation on the interference pattern captured by the imaging element 1.

[0045] The intraocular pressure measurement device provided by the present invention introduces an imaging module 2 that is compatible with the existing imaging element 3, so that the intraocular pressure can be detected by means of the existing imaging element 3. Furthermore, 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 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.

[0046] To measure intraocular pressure, see [link to relevant documentation]. Figure 4As shown, the preferred optical path assembly 22 of the present invention includes a beam splitter cube 221 and a plano-convex lens 222 sequentially disposed in the imaging aperture 211. The beam splitter cube 221 operates in the wavelength range of 450–650 nm. When light is incident at an incident angle of 45°, it can split the incident light into two beams with a ratio of approximately 50% transmission (T) and 50% reflection (R), with a tolerance of ±5% (T / R = 50% : 50% ±5%). This allows the light emitted by the light source 23 to be reflected by the beam splitter cube 221 to adjust the optical path direction, and then converged by the plano-convex lens 222 to the target plane used to generate the optical interference pattern, i.e., the position of the Fabry-Perot microcavity. The reflected light of the interference pattern is then transmitted to the lens 31 of the imaging element 3 after passing through the plano-convex lens 222 and the beam splitter cube 221, thereby realizing the acquisition and imaging of the interference pattern. Preferably, the design wavelength of the plano-convex lens 222 is 350-700 nm, and the focal length is 20 mm.

[0047] Furthermore, the preferred optical path component 22 of the present invention further includes a narrowband filter 223 disposed between the light source 23 and the beam splitter cube 221, wherein the narrowband filter 223 is a 633nm narrowband filter, so that the light emitted by the light source 23 is filtered by the narrowband filter 223 to obtain monochromatic light with a center wavelength of 633 nm and a bandwidth of ±10 nm.

[0048] The imaging element 3 in this invention can be any existing digital camera, camcorder, or smartphone, including a CMOS image sensor; to further reduce the difficulty of shooting, the imaging element 3 is preferably a mobile phone; the mobile phone is equipped with a CMOS image sensor to realize the acquisition and imaging of interference patterns.

[0049] Existing optical pressure sensors require equal-inclination interference from the incident light beams when measuring intraocular pressure. For equal-inclination interference, the main requirement is that the angles of incidence and reflection (or refraction) are equal when the two interfering beams are reflected or refracted. In other words, the incident beams must be perpendicular to the surface to ensure complete interference fringes. When a miniature pressure sensor is implanted in a pressure detection environment, its small size makes it impossible to guarantee its horizontal orientation. When using a desktop microscope, the microscope can generally only maintain a vertically downward angle. Therefore, to obtain a complete optical interference pattern, one must rely on intuition to adjust the spatial angle of the object being measured, which is extremely difficult, especially when the object being measured is one whose spatial angle cannot be adjusted, such as an intraocular pressure sensor implanted in the eye. Based on this, this invention proposes an external camera module 2 adaptable to any smartphone. Compared to adjusting the uncertain spatial angle of the object being measured, adjusting the angle of the handheld phone is obviously much easier. Furthermore, we can determine the appropriate angle to tilt the phone based on the real-time image captured by the phone's camera. The optical interference pattern captured in real-time by a mobile phone camera is a square region. When the angle of incidence of light is not perpendicular to the interference plane, the square region is incomplete, appearing as a mixture of bright and dark areas. See also Figure 5 As shown, we can imagine the square interference region as a sealed "box" filled with water, and the bright part as a "bubble" inside the sealed space. The "box" should tilt in the direction the "bubble" is positioned within the square region, until the "bubble" moves to the center of the square region. The mobile phone is the "box." When the "bubble" moves to the center of the square region, the angle of incidence of the light is perpendicular to the interference plane, at which point the complete optical interference pattern is captured.

[0050] To facilitate connection with a mobile phone, the shooting module 2 of the present invention preferably also includes a clamp 24; one end of the clamp 24 is connected to the shooting element 3, i.e., the mobile phone, and the other end is connected to the housing 21.

[0051] The clamp 24 of this invention is preferably made of polylactic acid (PLA) material and is prepared by extrusion 3D printing process; and more preferably, the clamp 24 is a C-shaped clamp 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 the connection with the mobile phone is achieved by tightening the threaded connector 242; the opening and closing range of the C-shaped element 241 is preferably 8-20mm, which can be adapted to the thickness of most smartphones on the market.

[0052] Furthermore, the present invention preferably connects the housing 21 and the clamp 24 by means of a snap-fit. Specifically, the C-shaped element 241 of the clamp 24 preferably has a mounting groove 2411 that is adapted to the housing 21, and the mounting groove 2411 has a concave point. The outer side of the housing 21 has a protrusion that is adapted to the concave point. The two parts can be easily assembled or disassembled by the cooperation of the protrusion and the concave point.

[0053] Furthermore, the mounting slot 2411 is provided with a through hole 2412 that matches the shooting hole 211, so as to avoid the C-shaped element 241 affecting the light transmission.

[0054] In summary, this invention provides an external camera module 2 compatible with any smartphone. The housing 21 of this external camera module 2 is made of environmentally friendly polylactic acid (PLA) material and is manufactured through a precisely controlled extrusion 3D printing process, ensuring consistent structural strength and quality. The camera module 2 integrates an optimized customized optical path design and high-performance optical components, combined with real-time image capture, to achieve stable capture of high-quality images. Compared to the first-generation desktop microscope-style image capture method, this module not only guarantees image clarity and optical imaging quality but also significantly reduces the complexity of user operation and the impact of camera shake during shooting, making the device more portable, more efficient in operation, and improving both user experience and applicability.

[0055] The intraocular pressure sensor 1 in this invention can be any existing intraocular pressure sensor with a Fabry-Perot microcavity. Since the intraocular pressure monitoring device provided by this invention is based on optical sensing to detect intraocular pressure, as mentioned above, during the detection process, the incident light needs to satisfy equal inclination interference, and equal inclination interference requires the incident beam to meet the requirement of perpendicular incidence. Therefore, in order to ensure the clarity of the detection image, the position of the intraocular pressure sensor 1 must remain fixed and not move during the detection process. To avoid the intraocular pressure sensor 1 moving during the detection process, this invention preferably includes a sensor body 11 and a bracket 12 connected to the sensor body 11, so as to fix the intraocular pressure sensor body 11 through the bracket 12, reduce the detection difficulty, and improve the clarity of the detection image.

[0056] Existing stents used to fix intraocular implants are mostly cylindrical structures. However, in the intraocular pressure measurement device provided by this invention, if the position of the intraocular pressure sensor body 11 moves slightly during the detection process, the incident light beam will not be able to be incident perpendicularly, and the shooting angle of the imaging element 3 needs to be readjusted. Therefore, in order to ensure the stability of the position of the intraocular pressure sensor body 11 during the detection process, this invention preferably uses a plate-shaped structure for the stent 12 to increase the contact area between the stent 12 and the inside of the eye, and to prevent the intraocular pressure sensor body 11 from moving.

[0057] Specifically, the preferred bracket 12 of the present invention includes an installation end 121 and a fixing end 122 connected to the installation end 121; wherein the installation end 121 is used to connect to the intraocular pressure sensor body 11, and the intraocular pressure sensor body 11 and the installation end 121 in the present invention can be connected by high temperature bonding, adhesive bonding of compatible materials, etc.; the size of the installation end 121 is determined according to the size of the intraocular pressure sensor body 11.

[0058] Since the eyeball has a certain curvature, in order to improve the fit between the bracket 12 and the eyeball, improve the stability of the intraocular pressure sensor body 11, and improve the patient's comfort, the present invention preferably has an arc-shaped structure for the fixed end 122, the curvature of which is determined according to the curvature of the eyeball.

[0059] To ensure the stability of the intraocular pressure sensor body 11 while improving comfort, the fixed end 122 of the present invention preferably includes a wide segment 1221, a gradient segment 1222, and a narrow segment 1223 connected in sequence; wherein the widths of the wide segment 1221, the gradient segment 1222, and the narrow segment 1223 decrease sequentially.

[0060] It should be noted that, in the bracket 12 of the present invention, the length direction in which the wide segment 1221, the gradient segment 1222 and the narrow segment 1223 are distributed is the width direction on the plane of the plate-like structure of the bracket 12, which is perpendicular to the length direction.

[0061] Specifically, the present invention preferably has a rectangular plate structure for the wide section 1221 to ensure the contact area between the support 12 and the eyeball; preferably, the width of the gradient section 1222 decreases sequentially, 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.

[0062] To balance comfort and the stability of the position of the intraocular pressure sensor body 11, the present invention preferably has a length ratio of (1.4~1.7):(1.1~1.4):(0.7~1) for the wide segment 1221, the gradient segment 1222 and the narrow segment 1223.

[0063] 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 segment 1223, and specifically preferably the anti-slip structure 1224 is a protruding structure extending outward along the narrow segment 1223.

[0064] To balance the stability and comfort of the position of the intraocular pressure sensor body 11, the present invention further preferably has at least two sets of protrusion structures, each set including two protrusions of the same size, symmetrically arranged on both sides of the narrow section 1223; and the size of the protrusions gradually decreases in the direction away from the gradient section 1222.

[0065] In a further preferred embodiment of the present invention, the support 12 is provided with a drainage groove 123 so that the intraocular pressure measuring device provided by the present invention has an intraocular pressure measuring function and also has a certain drainage function.

[0066] Existing intraocular pressure sensors typically only have the function of detecting intraocular pressure and cannot achieve drainage. When the intraocular pressure is high, it is necessary to introduce a corresponding drainage device to achieve the therapeutic effect. Based on this, the present invention preferably provides a drainage groove 123 on the stent 12 so that the aqueous humor can be diffused to the periocular tissue through the drainage groove 123. This allows the intraocular pressure sensor to have both intraocular pressure detection and drainage functions, so that intraocular pressure detection and drainage can be achieved with a single implantation without increasing the number of implantations, increasing surgical damage, or increasing patient pain.

[0067] The drainage channel 123 includes a groove-shaped structure distributed longitudinally along the support 12 and passing through the mounting end 121 and the fixing end 122 in sequence, referred to as the first groove-shaped structure 1231; to further improve the drainage effect, the drainage channel 123 also includes a second groove-shaped structure 1232 obliquely distributed on the wide section 1221, and the second groove-shaped structure 1232 is connected to the first groove-shaped structure 1231.

[0068] The intraocular pressure sensor provided by this invention can be implanted into the eye via injection, significantly reducing surgical trauma. Through its groundbreaking design, this invention provides an intraocular pressure sensor that can be implanted into the eye via minimally invasive injection. The system can achieve continuous 24 / 7 monitoring of intraocular pressure without the need for electronic components or electromagnetic energy supply, and the intraocular pressure measurement accuracy reaches ±1 mmHg.

[0069] The intraocular pressure sensor provided by this invention establishes a functional relationship between the Fabry-Perot microcavity deflection in the sensor's central region and intraocular pressure based on the change in the spacing of the sensor's interference fringes caused by changes in intraocular pressure. By integrating advanced M-net neural network training and sparse attention Transformer image restoration algorithm into a mobile APP, it automatically focuses, identifies, and crops the sensor's interference fringes region and performs real-time intraocular pressure demodulation, enabling patients to self-test their intraocular pressure at home using their mobile phones. The signal transmission does not rely on electromagnetic energy supply and effectively avoids signal loss caused by external factors.

[0070] The intraocular pressure sensor provided by this invention has stronger compatibility and universality, and can be used in conjunction with any existing ophthalmic implantable device, which helps to further explore the feasibility of new clinical technologies that integrate glaucoma monitoring and diagnosis.

[0071] Based on the above-described preferred embodiments of the present invention, and through the foregoing description, those skilled in the art can make various changes and modifications without departing from the inventive concept. The technical scope of this invention is not limited to the contents of the specification, but 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), an imaging module (2), and an imaging element (3); among which, The intraocular pressure sensor (1) is provided with a Fabry-Perot microcavity; 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). The housing (21) is provided with a shooting hole (211); The light emitted by the light source (23) is transmitted to the Fabry-Perot microcavity after passing through the optical path component (22), and an interference pattern is generated; The imaging element (3) includes a lens (31); The imaging aperture (211) is adapted to cooperate with the lens (31) to obtain the interference pattern through the imaging element (3); The optical path assembly (22) includes a beam splitter cube (221) and a plano-convex lens (222) sequentially disposed in the imaging aperture (211). The optical path assembly (22) also includes a narrowband filter (223) disposed between the light source (23) and the beam splitter (221). The intraocular pressure sensor (1) includes a sensor body (11) and a bracket (12) connected to the sensor body (11). The bracket (12) includes a mounting end (121) and a fixing end (122) connected to the mounting end (121). The fixed end (122) includes a wide segment (1221), a gradient segment (1222), and a narrow segment (1223) connected in sequence; the widths of the wide segment (1221), the gradient segment (1222), and the narrow segment (1223) decrease sequentially. The bracket (12) is provided with a drainage groove (123); The drainage channel (123) includes a first groove structure (1231) distributed longitudinally along the support (12); The drainage channel (123) further includes a second channel structure (1232) obliquely distributed on the wide section (1221); the second channel structure (1232) is connected to the first channel structure (1231).

2. The intraocular pressure measuring device as described in claim 1, characterized in that, The shooting element (3) is a mobile phone; the mobile phone is equipped with a CMOS image sensor.

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

4. The intraocular pressure measuring device as described in claim 1, characterized in that, The support (12) is a plate-shaped structure.

5. The intraocular pressure measuring device as described in claim 1, characterized in that, The fixed end (122) has an arc-shaped structure.

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