Non-invasive intraocular pressure monitoring device

Abstract

The invention discloses a non-invasive intraocular pressure monitoring device, and relates to the technical field of ophthalmology. The multifunctional probe is fixed to the inner side of the lens body and located at the position, right facing the cornea of a user, of the lens body when the lens is worn, and an OCT unit, a sound wave excitation and sensing unit and an environment temperature sensing unit are integrated in the multifunctional probe; the dynamic deformation process of the cornea under sound wave excitation is captured in a high-precision mode through the OCT technology, acoustic feedback signals of the cornea are analyzed synchronously through the sound wave sensor, the biomechanical state of the cornea is jointly represented from the two dimensions of optical mechanics and acoustic impedance, measurement errors caused by individual cornea characteristic differences are remarkably reduced, and the measurement accuracy is improved. An environment temperature sensor is introduced for real-time compensation, the influence of environment temperature changes on cornea tissue elasticity and sound wave propagation speed is effectively eliminated, a monitoring module is integrated in the intelligent glasses, cornea curvature changes are continuously monitored through a multifunctional sensing probe, and continuous intraocular pressure monitoring in a daily scene is achieved.

Description

Technical Field

[0001] This invention relates to the field of ophthalmic technology, specifically to a non-invasive intraocular pressure monitoring device. Background Technology

[0002] Glaucoma is a disease characterized by optic nerve atrophy and visual field defects, and it is one of the three major causes of blindness in humans. Pathological intraocular pressure (IOP) elevation and abnormal IOP fluctuations are its main risk factors. Normal IOP ranges from approximately 10-21 mmHg, but individual tolerance to IOP varies, so pathological IOP elevation varies from person to person clinically. IOP fluctuates within a certain range over 24 hours; in normal individuals, the diurnal fluctuation should not exceed 8 mmHg, otherwise it is considered pathological. In glaucoma patients, the diurnal fluctuation of IOP can be 2-3 times greater than normal, and its manifestations are more subtle. Therefore, IOP is a key physiological parameter for diagnosing and monitoring glaucoma and other ophthalmic diseases. Currently, the widely used non-contact tonometer (jet-type) in clinical practice mainly works by spraying a rapid pulse of air into the cornea, causing deformation, and using an optical system to detect the deformation state to calculate the IOP value.

[0003] However, this traditional technology has several significant drawbacks:

[0004] 1. Patient discomfort and poor cooperation: The airflow impact during measurement can easily cause patients to feel tense, anxious and blink reflex, resulting in decreased cooperation and affecting the accuracy and repeatability of multiple measurements, which is especially unfriendly to children and sensitive patients.

[0005] 2. Limitations of single, discrete measurements: Traditional devices can only perform single-point, discrete measurements within a hospital setting, failing to capture the dynamic fluctuations of intraocular pressure (IOP) under daily activities and circadian rhythms. However, continuous 24-hour IOP monitoring is crucial for accurate glaucoma diagnosis, treatment efficacy evaluation, and personalized medication. Therefore, this invention proposes a non-invasive IOP monitoring device. Summary of the Invention

[0006] The purpose of this invention is to provide a non-invasive intraocular pressure monitoring device to solve the problems of poor patient discomfort and cooperation, as well as the limitations of single and discrete measurements mentioned in the background art.

[0007] To achieve the above objectives, the present invention provides the following technical solution:

[0008] Non-invasive intraocular pressure monitoring devices include:

[0009] The mirror body is constructed to be worn by the user.

[0010] A multi-functional probe is fixed to the inside of the lens body and positioned directly facing the user's cornea when worn. The multi-functional probe integrates an OCT unit, an acoustic excitation and sensing unit, and an ambient temperature sensing unit.

[0011] A signal processing and control unit is located on the front side of the mirror body and is electrically connected to the multifunctional probe;

[0012] A battery unit is located on the top of the mirror body and is electrically connected to the signal processing and control unit and the multifunctional probe to power the entire device.

[0013] A data communication unit is located on the side of the signal processing and control unit;

[0014] The user interaction unit is located inside the mirror and on the top side near the user's forehead;

[0015] The signal processing and control unit is configured to synchronously drive the acoustic excitation and sensing unit and the OCT unit, and calculate the intraocular pressure value based on the corneal dynamic deformation data obtained from the OCT unit, the acoustic feedback signal obtained from the acoustic excitation and sensing unit, and the temperature data obtained from the ambient temperature sensing unit, through a pre-trained calculation model.

[0016] Optionally, the OCT unit includes a broadband light source, a micro-interferometer, and an optical lens assembly, used to achieve high-speed and high-precision measurement of corneal micro-deformation.

[0017] Optionally, the acoustic excitation and sensing unit includes a piezoelectric ceramic transducer and an acoustic receiver for generating safe acoustic pulses and receiving acoustic feedback signals from the cornea.

[0018] Optionally, the ambient temperature sensing unit is a digital temperature sensor, whose detection surface is exposed on the surface of the multifunctional probe, for directly measuring the microenvironmental temperature in front of the cornea.

[0019] Optionally, the acoustic wave emitting axis of the acoustic wave excitation and sensing unit and the optical detection axis of the OCT unit are arranged in a virtual coaxial manner, so that the acoustic wave and the detection light act on the same target area of ​​the cornea.

[0020] Optionally, the data communication unit is a Bluetooth or Wi-Fi module, used to wirelessly transmit the calculated intraocular pressure value and fluctuation trend data to an external terminal device.

[0021] Optionally, the user interaction unit includes a miniature vibration motor and an LED indicator light to provide tactile and visual alerts to the user when abnormal intraocular pressure is detected.

[0022] Optionally, the pre-trained computational model is a deep learning-based artificial intelligence model that achieves accurate calculation of intraocular pressure through multimodal data fusion.

[0023] Optionally, the side of the mirror body is provided with a fixing strip, and a first connecting strip is fastened to the fixing strip by a connecting buckle. The other end of the first connecting strip is provided with a connecting seat, and a plug is provided in the connecting seat.

[0024] Optionally, an adjustment assembly is also included, comprising a second connecting strip and a mounting base. The end face of the second connecting strip near the first connecting strip is provided with a snap-fit ​​groove that mates with the insert rod. The other end faces of both sides of the second connecting strip are provided with straight slot holes. The upper and lower sides of the straight slot holes on both sides are respectively provided with toothed edges. A gear is rotatably connected to the mounting base, and a knob cap is mounted on the outer side of the mounting base. The center of the inner end face of the knob cap is provided with a rotating shaft, and the rotating shaft is fixedly connected to the gear. Both sides of the second connecting strip are sleeved on the outside of the gear through the straight slot holes and mesh with the upper and lower parts of the gear respectively through the toothed edges. The outer end face of the gear is provided with a limiting cover to prevent the second connecting strip from falling off.

[0025] The beneficial effects of this invention are:

[0026] This invention uses OCT technology to capture the dynamic deformation process of the cornea under acoustic excitation with high precision. Simultaneously, it analyzes the acoustic feedback signal through an acoustic sensor, characterizing the biomechanical state of the cornea from both optical mechanics and acoustic impedance dimensions. This significantly reduces measurement errors caused by individual differences in corneal characteristics. Furthermore, by introducing an ambient temperature sensor for real-time compensation, it effectively eliminates the impact of ambient temperature changes on corneal tissue elasticity and sound wave propagation speed, solving the problem of decreased accuracy of traditional devices when used in different environments. By integrating the monitoring module into smart glasses and using a multi-functional sensing probe, it continuously monitors changes in corneal curvature, enabling continuous intraocular pressure monitoring in daily scenarios, which is particularly suitable for long-term disease tracking of glaucoma patients. Attached Figure Description

[0027] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in this invention. For those skilled in the art, other drawings can be obtained based on these drawings.

[0028] Figure 1 This is a schematic diagram of the non-invasive intraocular pressure monitoring device of the present invention;

[0029] Figure 2 This is a schematic diagram of the structure of the mirror body of the present invention from another perspective;

[0030] Figure 3 This is a schematic diagram of the structure of the first connecting strip of the present invention;

[0031] Figure 4 This is a schematic diagram of the structure of the second connecting strip of the present invention;

[0032] Figure 5 This is a partial structural diagram of the regulating component of the present invention;

[0033] Figure 6 This is a flowchart illustrating the operation of the intraocular pressure monitoring device of the present invention.

[0034] The numbers on the map are:

[0035] 1. Lens body; 2. Multifunctional probe; 3. Signal processing and control unit; 4. Battery unit; 5. Data communication unit; 6. User interaction unit;

[0036] 7. Fixed joint strip;

[0037] 8. First connecting belt; 801. Connecting buckle; 802. Connecting seat; 803. Insert rod;

[0038] 9. Adjustment component; 901. Second connecting strip; 902. Snap-fit ​​groove; 903. Straight slot hole; 904. Toothed edge; 905. Knob cap; 906. Mounting base; 907. Gear; 908. Limit cover. Detailed Implementation

[0039] To make the technical means, creative features, objectives and effects of this invention easier to understand, the invention will be further described below in conjunction with specific embodiments.

[0040] As attached Figure 1 To be continued Figure 6 As shown, the present invention provides a non-invasive intraocular pressure monitoring device, comprising:

[0041] The device comprises: a lens 1, constructed for user wear, made of lightweight, biocompatible materials, and its basic form being smart glasses; a multi-functional probe 2, fixed inside the lens 1 and positioned directly facing the user's cornea during wear, integrating an OCT unit, an acoustic excitation and sensing unit, and an ambient temperature sensing unit; a signal processing and control unit 3, located on the front of the lens 1 and electrically connected to the multi-functional probe 2; a battery unit 4, located on the top of the lens 1 and electrically connected to the signal processing and control unit 3 and the multi-functional probe 2, for powering the entire device; a data communication unit 5, located on the side of the signal processing and control unit 3; and a user interaction unit 6, located inside the lens 1 and near the top of the user's forehead.

[0042] The signal processing and control unit 3 is configured to synchronously drive the acoustic excitation and sensing unit and the OCT unit, and calculate the intraocular pressure value based on the corneal dynamic deformation data obtained from the OCT unit, the acoustic feedback signal obtained from the acoustic excitation and sensing unit, and the temperature data obtained from the ambient temperature sensing unit through a pre-trained calculation model.

[0043] In one embodiment of the present invention, the OCT unit includes a broadband light source, a micro-interferometer, and an optical lens assembly, which is used to realize high-speed and high-precision measurement of corneal micro-deformation. Using PIC and MEMS technology, the broadband light source, micro-interferometer, and detector are integrated into a chip with a size ≤5mm×5mm. The optical lens assembly uses aspherical microlenses, and the overall volume is controlled within 1cm³, ensuring that it can be embedded in the multifunctional probe 2 inside the lens body 1 without affecting the user's wearing comfort.

[0044] Specifically, the OCT unit is based on optical coherence tomography (OCT) technology, which utilizes the interference characteristics of low-coherence light to achieve high-precision imaging of the corneal structure. Low-coherence light emitted from a broadband light source is split into two beams by a micro-interferometer: one beam is a reference beam (directed towards a fixed reference mirror), and the other beam is a sample beam (focused onto the corneal epithelium by an optical lens group). After being reflected by the cornea, the sample beam re-merges with the reference beam. Due to the different optical path differences between the two beams, an interference signal is generated, which is captured by the detector and converted into a digital signal, ultimately reconstructing a tomographic image of the cornea.

[0045] When sound waves excite the cornea to produce micron-level deformation, the OCT unit continuously acquires corneal tomographic images through high-speed scanning. By comparing images at different times, it calculates the corneal deformation amplitude (such as the maximum deformation in the central region), deformation rate (the rate of change of deformation over time), and rebound time (the time it takes to recover from the maximum deformation to the initial state). These parameters directly reflect the biomechanical characteristics of the cornea, and the corneal biomechanical characteristics are strongly correlated with intraocular pressure, providing core data support for intraocular pressure calculation.

[0046] In one embodiment of the present invention, the acoustic excitation and sensing unit includes a piezoelectric ceramic transducer and an acoustic receiver for generating safe acoustic pulses and receiving acoustic feedback signals from the cornea.

[0047] Specifically, the piezoelectric ceramic transducer generates mechanical vibration under the drive of an electrical signal, emitting a short-duration, low-energy sound wave pulse of a specific frequency. When this pulse acts on the corneal surface, it causes the cornea to undergo controllable elastic deformation, and the energy is far lower than the airflow impact of a traditional jet tonometer, so it will not cause blink reflex or discomfort to the user.

[0048] The acoustic receiver simultaneously receives the acoustic echo reflected from the cornea and the residual vibration signal generated by corneal deformation. On the one hand, by analyzing the attenuation rate of the echo (the degree of attenuation of acoustic energy with the propagation distance), the hardness of the cornea can be determined (the higher the intraocular pressure, the greater the corneal hardness and the lower the acoustic attenuation rate). On the other hand, by analyzing the phase change and vibration frequency of the residual vibration, corneal biomechanical information (such as the corneal elastic modulus) can be supplemented, complementing the deformation data obtained by the OCT unit and improving the accuracy of intraocular pressure calculation.

[0049] In one embodiment of the present invention, the ambient temperature sensing unit is a digital temperature sensor, the detection surface of which is exposed on the surface of the multifunctional probe 2, for directly measuring the microenvironmental temperature in front of the cornea.

[0050] Specifically, temperature changes affect the biomechanical properties of the cornea (e.g., the corneal elastic modulus increases by approximately 2% for every 1°C decrease in temperature), leading to deviations in deformation data measured by the OCT unit at the same intraocular pressure. Simultaneously, temperature changes affect the speed of sound propagation in air (the speed of sound increases by approximately 0.6 m / s for every 1°C increase in temperature), causing errors in the echo analysis of the acoustic wave sensing unit. Therefore, the ambient temperature sensing unit collects the microenvironmental temperature in front of the cornea in real time and inputs the temperature data into a pre-trained computational model. The model uses a built-in temperature compensation algorithm to correct the deviation between the deformation data and the acoustic data, eliminating systematic measurement errors.

[0051] It is worth further describing that two miniature temperature sensors are set on the surface of the multi-functional probe 2, and the average value of the two measurements is taken as the final temperature data. This avoids measurement errors caused by single sensor failure or local temperature anomalies and improves the reliability of temperature data.

[0052] In one embodiment of the present invention, the acoustic wave emission axis of the acoustic excitation and sensing unit and the optical detection axis of the OCT unit are set together in a virtual coaxial manner, so that the acoustic wave and the detection light act on the same target area of ​​the cornea, ensuring that the deformation area captured by the optical is the area where the acoustic wave energy is most concentrated, and achieving a high degree of consistency of measurement in space.

[0053] In one embodiment of the present invention, the data communication unit 5 is a Bluetooth or Wi-Fi module, used to wirelessly transmit the calculated intraocular pressure value and fluctuation trend data to an external terminal device.

[0054] In one embodiment of the present invention, the user interaction unit 6 includes a miniature vibration motor and an LED indicator, which are used to provide tactile and visual alarms to the user when abnormal intraocular pressure is detected. When the signal processing and control unit 3 determines that the intraocular pressure value exceeds the preset personal safety threshold, it will immediately drive the vibration motor to generate a mild tactile alarm and control the LED indicator to flash, so as to achieve an immediate and discreet warning without disturbing daily activities.

[0055] In one embodiment of the present invention, the pre-trained computational model is a deep learning-based artificial intelligence model, which achieves accurate calculation of intraocular pressure through multimodal data fusion.

[0056] Specifically, through training with a large amount of clinical data (including samples with different intraocular pressure values, different temperatures, and different corneal characteristics), the complex nonlinear mapping relationship between "corneal deformation characteristics (OCT data) + acoustic characteristics (sound wave data) + temperature data" and "true intraocular pressure value (measured by Goldmann applanation tonometer as the gold standard)" is learned.

[0057] First, the input multimodal raw data is preprocessed (deformation curve features are extracted from OCT data, attenuation rate and phase change features are extracted from acoustic data, and temperature data is standardized). Second, local key features of each modality data are extracted through a CNN layer (such as the peak value and slope of the deformation curve), and temporal change features of deformation and acoustic signals are captured through an LSTM layer (such as the time series of the rebound process). Third, the multimodal features are weighted and fused through an attention mechanism (focusing on features highly correlated with intraocular pressure, such as deformation amplitude and acoustic attenuation rate), and finally, a precise intraocular pressure value with temperature compensation is output.

[0058] It is worth further describing that the system supports receiving new clinical data sent from external terminals via data communication unit 5, performing incremental training locally, continuously optimizing model parameters, and improving the accuracy of long-term monitoring.

[0059] What needs to be further described in this invention is that the multifunctional probe 2 has a set of micro-motion mechanisms integrated inside, which can automatically fine-tune the probe angle until the optical detection axis of the OCT unit is precisely aligned with the center of the cornea.

[0060] Working principle: The user wears the lens 1 on their head and rotates the knob cap 905 through the adjustment component 9 to adapt the first connecting strap 8 and the second connecting strap 901 to the head circumference, ensuring that the multi-functional probe 2 is initially aligned with the corneal area. After wearing, the battery unit 4 powers all units, including the signal processing and control unit 3 and the multi-functional probe 2. The signal processing and control unit 3 first performs a self-test. After the self-test is passed, the signal processing and control unit 3 drives the OCT unit to perform a low-power wide-angle scan. By analyzing the contour features of the cornea in the OCT image, the position of the central corneal area is accurately located. If the positioning finds that the multi-functional probe 2 is offset from the center of the cornea, the signal processing and control unit 3 finely adjusts the probe angle through the micro-motion mechanism built into the multi-functional probe 2 until the optical detection axis of the OCT unit is aligned with the center of the cornea. The probe is adjusted to the measurement position and ready to enter the data acquisition stage.

[0061] The signal processing and control unit 3 generates a synchronization timing command, simultaneously triggering the OCT unit, acoustic excitation and sensing unit, and ambient temperature sensing unit within the multi-functional probe 2. This ensures that the data acquisition of the three units is strictly aligned in time. The acoustic excitation and sensing unit responds to the command, emitting a low-energy acoustic pulse at a specific frequency through its piezoelectric ceramic transducer, which acts on the central region of the cornea. Simultaneously, the acoustic receiver begins acquiring the acoustic echo reflected from the cornea and residual vibration signals, with the acquisition duration matching the duration of the acoustic pulse. The OCT unit responds to the command, initiating a high-speed scan while the acoustic pulse acts on the cornea, continuously acquiring tomographic images of the cornea under acoustic excitation, recording the complete dynamic process of corneal deformation and recovery. The ambient temperature sensing unit responds to the command, simultaneously acquiring the microenvironmental temperature data in front of the cornea, recording the current temperature value as a basis for subsequent temperature compensation. The data acquired by the three units are transmitted in real-time to the buffer module of the signal processing and control unit 3 via electrical connection, completing the acquisition of multimodal raw data.

[0062] The signal processing and control unit 3 reads the multimodal raw data from the cache. First, it performs data preprocessing, including noise reduction and image alignment of the OCT image data, and then extracts corneal deformation features (such as maximum deformation amplitude, deformation speed, and rebound time constant). It filters and amplifies the sound wave signal to extract acoustic features (such as sound wave attenuation rate, phase change, and time of flight). It also standardizes the temperature data. The preprocessed multimodal features (deformation features, acoustic features, and temperature data) are input into the pre-trained AI intraocular pressure calculation model. The model uses an attention mechanism to perform weighted fusion of the multimodal features, focusing on features highly correlated with intraocular pressure (such as deformation amplitude and sound wave attenuation rate). At the same time, it calls the built-in temperature compensation algorithm to correct the impact of temperature changes on corneal biomechanical properties and sound wave propagation speed. The model calculates through forward inference and outputs the accurate intraocular pressure value after temperature compensation. The calculation result is stored in the Flash memory of the signal processing and control unit 3.

[0063] The signal processing and control unit 3 stores the intraocular pressure value along with the corresponding timestamp, temperature data, and raw feature data in local Flash memory. Simultaneously, it drives the data communication unit 5 to wirelessly transmit the data to an external terminal device. The mobile app generates an intraocular pressure trend chart based on the received historical data. The signal processing and control unit 3 compares the current intraocular pressure value with a preset threshold. If the intraocular pressure is normal, the LED indicator on the user interaction unit 6 lights up green, indicating that the measurement is complete and there are no abnormalities. If the intraocular pressure is abnormal, the miniature vibration motor of the user interaction unit starts, and the LED indicator lights up red, providing the user with tactile and visual alerts. The data communication unit 5 simultaneously pushes the abnormal information to the user's mobile phone. If the user has linked a doctor's account, the abnormal information will also be sent to the doctor's device simultaneously, facilitating timely intervention by the doctor.

[0064] After completing the measurement and feedback, the system enters a low-power standby mode, waiting for the next measurement. This allows for continuous monitoring until the user manually shuts down the system or the battery is depleted.

[0065] like Figure 1 and 3 As shown in Figure 5, in one embodiment of the present invention, the side of the mirror body 1 is provided with a fixing strip 7, and a first connecting strip 8 is fastened to the fixing strip 7 by a connecting buckle 801. The other end face of the first connecting strip 8 is provided with a connecting seat 802, and a plug 803 is provided in the connecting seat 802.

[0066] In one embodiment of the present invention, an adjustment component 9 is further included. The adjustment component 9 includes a second connecting band 901 and a mounting base 906. The end face of the second connecting band 901 near the first connecting band 8 is provided with a snap-fit ​​groove 902 that cooperates with the insertion rod 803. The other end face of the two second connecting bands 901 is provided with a straight slot hole 903. The upper and lower sides of the straight slot holes 903 on both sides are respectively provided with toothed edges 904. A gear 907 is rotatably connected to the mounting base 906, and a knob cap 905 is installed on the outer side of the mounting base 906. A rotating shaft is provided at the center of the inner end face of the knob cap 905, and the rotating shaft is fixedly connected to the gear 907. The two second connecting bands 901 on both sides are sleeved on the outside of the gear 907 through the straight slot holes 903, and respectively mesh with the upper and lower parts of the gear 907 through the toothed edges 904. The outer end face of the gear 907 is provided with a limiting cover 908 to prevent the second connecting band 901 from falling off.

[0067] Specifically, when the user wears the device, rotating the knob cap 905 causes the rotating shaft and gear 907 to rotate synchronously. Since the straight slots 903 of the second connecting straps 901 on both sides have toothed edges 904 that mesh with the upper and lower parts of the gear 907 respectively, the rotation of the gear 907 will drive the second connecting straps 901 on both sides to move synchronously in opposite directions. When the knob cap 905 is rotated clockwise, the connecting straps on both sides contract towards the middle, making the lens 1 fit more snugly; when rotated counterclockwise, the connecting straps stretch outward, making the fit looser, and it will not shift due to unilateral adjustment, achieving centered symmetrical stepless adjustment, which can adapt to users with different head circumferences, ensuring that the multi-functional probe 2 is always facing the cornea, and avoiding measurement deviations caused by loose fit.

[0068] It should be further described that a friction damping plate is provided at the connection between the gear 907 and the mounting base 906. When the user stops turning the knob cap 905, the friction force generated by the damping plate can prevent the gear 907 from rotating on its own, ensuring that the tightness after adjustment remains stable and that the connecting belt will not loosen due to user activity.

[0069] The foregoing has only described certain exemplary embodiments of the present invention by way of illustration. Undoubtedly, those skilled in the art can modify the described embodiments in various ways without departing from the spirit and scope of the present invention. Therefore, the foregoing drawings and descriptions are illustrative in nature and should not be construed as limiting the scope of protection of the claims of the present invention.

Claims

1. A non-invasive intraocular pressure monitoring device, characterized in that, include: The mirror body (1) is constructed to be worn by the user; The multi-functional probe (2) is fixed to the inside of the lens body (1) and is located in front of the user's cornea when worn. The multi-functional probe (2) integrates an OCT unit, an acoustic excitation and sensing unit, and an ambient temperature sensing unit. The signal processing and control unit (3) is located on the front side of the mirror body (1) and is electrically connected to the multifunctional probe (2); The battery unit (4) is located on the top of the mirror body (1) and is electrically connected to the signal processing and control unit (3) and the multi-functional probe (2) to power the entire device. The data communication unit (5) is located on the side of the signal processing and control unit (3); The user interaction unit (6) is located inside the mirror body (1) and close to the top side of the user's forehead; The signal processing and control unit (3) is configured to synchronously drive the acoustic excitation and sensing unit and the OCT unit, and calculate the intraocular pressure value based on the corneal dynamic deformation data obtained from the OCT unit, the acoustic feedback signal obtained from the acoustic excitation and sensing unit, and the temperature data obtained from the ambient temperature sensing unit through a pre-trained calculation model.

2. The non-invasive intraocular pressure monitoring device according to claim 1, characterized in that: The OCT unit includes a broadband light source, a micro-interferometer, and an optical lens assembly, used to achieve high-speed and high-precision measurement of corneal micro-deformation.

3. The non-invasive intraocular pressure monitoring device according to claim 2, characterized in that: The acoustic excitation and sensing unit includes a piezoelectric ceramic transducer and an acoustic receiver, used to generate safe acoustic pulses and receive acoustic feedback signals from the cornea.

4. The non-invasive intraocular pressure monitoring device according to claim 3, characterized in that: The ambient temperature sensing unit is a digital temperature sensor, and its detection surface is exposed on the surface of the multifunctional probe (2) for directly measuring the microenvironmental temperature in front of the cornea.

5. The non-invasive intraocular pressure monitoring device according to claim 4, characterized in that: The acoustic wave emission axis of the acoustic wave excitation and sensing unit and the optical detection axis of the OCT unit are set together in a virtual coaxial manner, so that the acoustic wave and the detection light act on the same target area of ​​the cornea.

6. The non-invasive intraocular pressure monitoring device according to claim 1, characterized in that: The data communication unit (5) is a Bluetooth or Wi-Fi module, used to wirelessly transmit the calculated intraocular pressure value and fluctuation trend data to an external terminal device.

7. The non-invasive intraocular pressure monitoring device according to claim 1, characterized in that: The user interaction unit (6) includes a miniature vibration motor and an LED indicator, which are used to provide tactile and visual alerts to the user when abnormal intraocular pressure is detected.

8. The non-invasive intraocular pressure monitoring device according to claim 1, characterized in that: The pre-trained computational model is a deep learning-based artificial intelligence model that achieves accurate calculation of intraocular pressure through multimodal data fusion.

9. The non-invasive intraocular pressure monitoring device according to claim 1, characterized in that: The side of the mirror body (1) is provided with a fixing strip (7), and a first connecting strip (8) is fastened to the fixing strip (7) by a connecting buckle (801). The other end of the first connecting strip (8) is provided with a connecting seat (802), and a plug (803) is provided in the connecting seat (802).

10. The non-invasive intraocular pressure monitoring device according to claim 1, characterized in that: It also includes an adjustment component (9), which includes a second connecting strip (901) and a mounting base (906). The second connecting strip (901) has a snap-fit ​​groove (902) that mates with the insert rod (803) on one end face near the first connecting strip (8). The other end faces of the second connecting strip (901) on both sides are provided with straight slot holes (903). The upper and lower sides of the straight slot holes (903) on both sides are respectively provided with toothed edges (904). A gear is rotatably connected to the mounting base (906). 907), and a knob cap (905) is installed on the outside of the mounting base (906). The center of the inner end face of the knob cap (905) is provided with a rotating shaft, and the rotating shaft is fixedly connected to the gear (907). The second connecting strips (901) on both sides are sleeved on the outside of the gear (907) through the straight slot hole (903), and mesh with the upper and lower parts of the gear (907) respectively through the tooth edge (904). The outer end face of the gear (907) is provided with a limiting cover (908) to prevent the second connecting strip (901) from falling off.

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