Noninvasive intraocular pressure measuring system

Abstract

The invention provides a noninvasive intraocular pressure measuring system which comprises intraocular pressure measuring equipment, a resonance circuit, environment temperature collecting equipment and an intraocular pressure measuring and correcting unit, and the intraocular pressure measuring and correcting unit obtains the environment temperature from the environment temperature collecting equipment by obtaining intraocular humidity data and intraocular pressure measuring data from the intraocular pressure measuring equipment; determining a plurality of capacitance drift distances through the intraocular humidity data, and further converting all the capacitance drift distances into frequency drift cost when the humidity is changed each time; determining a temperature-pressure regression coefficient based on linear regression characteristics, and further performing cost fitting through the temperature-pressure regression coefficient to obtain a temperature compensation cost of each intraocular pressure measurement value; and adjusting the resonant frequency according to each frequency drift cost and each temperature compensation cost, and correcting the intraocular pressure measurement result based on the adjusted resonant frequency. By the adoption of the scheme, in the process of wearing the intraocular pressure measuring equipment, the influence of changes of environmental factors on the measuring precision can be avoided, and the intraocular pressure can be stably monitored.

Description

Technical Field

[0001] The present application relates to the technical field of intraocular pressure measurement, and more specifically, to a non-invasive intraocular pressure measurement system. Background Art

[0002] Intraocular pressure measurement is a key technology in the field of ophthalmology. It is used to assess the internal pressure of the eyeball (IOP), which plays a vital role in the diagnosis and monitoring of eye diseases such as glaucoma. Intraocular pressure is the pressure difference between the intraocular fluid (aqueous humor) and the wall of the eyeball. The stability of intraocular pressure is essential to maintaining normal eye shape and function. Abnormal intraocular pressure levels may cause optic nerve damage, leading to vision impairment and even blindness. Continuous innovation in the field of intraocular pressure measurement has provided strong support for the early diagnosis and prevention of ophthalmic diseases, and also promoted the intelligent development of ophthalmic medical equipment.

[0003] Non-invasive intraocular pressure measurement is an advanced method for measuring intraocular pressure (IOP) without direct contact with the cornea or the surface of the eyeball. With the increasing concern about eye health and the discomfort and infection risks caused by traditional contact measurement methods, non-invasive intraocular pressure measurement technology has gradually become an important development direction in the field of ophthalmology. Non-invasive intraocular pressure measurement not only provides patients with a comfortable experience, but also has made significant progress in the accuracy, portability and intelligence of intraocular pressure monitoring. In the existing technology, sensors attached to the eyelids or worn around the eyes usually sense the changes in the resonant frequency of the circuit caused by slight changes in the shape of the eyeball, and then analyze the change data to achieve non-invasive measurement. Invasive intraocular pressure measurement, this non-invasive intraocular pressure measurement method has the advantage of continuous monitoring compared to other non-invasive intraocular pressure measurement methods. However, in the process of continuous monitoring of intraocular pressure, the measured intraocular pressure value may be erroneous due to the intraocular environmental factors of the wearer. For example, when the ambient temperature fluctuates, the physical properties (such as viscosity and density) of the aqueous humor and vitreous body inside the eyeball at different temperatures will change, thereby affecting the transmission mode of intraocular pressure, which in turn leads to deviations in the measurement results. Therefore, how to avoid the influence of changes in environmental factors on the measurement accuracy while wearing intraocular pressure measurement equipment and achieve stable monitoring of intraocular pressure has become a difficult problem faced by the industry. Summary of the invention

[0004] The present application provides a non-invasive intraocular pressure measurement system, which can avoid the influence of changes in environmental factors on the measurement accuracy while wearing the intraocular pressure measurement device, and realize stable monitoring of intraocular pressure.

[0005] In order to solve the above technical problems, the present application provides a non-invasive intraocular pressure measurement system, the non-invasive intraocular pressure measurement system includes an intraocular pressure measurement device and a resonant circuit connected to the intraocular pressure measurement device, the resonant circuit is used to generate a resonant frequency corresponding to the intraocular pressure, in addition, the non-invasive intraocular pressure measurement system also includes an ambient temperature acquisition device and an intraocular pressure measurement correction unit, the ambient temperature acquisition device is used to collect the ambient temperature when the target object wears the intraocular pressure measurement device, and the intraocular pressure measurement device is also used to collect intraocular humidity data and intraocular pressure measurement data when the target object wears the intraocular pressure measurement device; The intraocular pressure measurement and correction unit specifically includes: an acquisition module, a conversion module, a fitting module, and a correction module; The acquisition module is used to acquire intraocular humidity data and intraocular pressure measurement data from the intraocular pressure measurement device, and acquire ambient temperature from the ambient temperature acquisition device; The conversion module is used to determine multiple capacitance drifts of the resonant circuit after being affected by humidity through the intraocular humidity data and the dielectric characteristics of the device material, and then convert all capacitance drifts into the frequency drift cost of the resonant frequency in the resonant circuit when the humidity changes each time; The fitting module is used to determine the temperature-pressure regression coefficient of the target object's intraocular pressure based on the linear regression characteristics between the intraocular pressure measurement data and the ambient temperature, and then perform cost fitting on each intraocular pressure measurement value in the intraocular pressure measurement data through the temperature-pressure regression coefficient to obtain the temperature compensation cost of each intraocular pressure measurement value; The correction module is used to adjust the resonant frequency of the resonant circuit according to each frequency drift cost and each temperature compensation cost, and correct the intraocular pressure measurement result of the target object based on the adjusted resonant frequency.

[0006] It can be understood that the conversion module can send the frequency drift cost of the resonant frequency in the resonant circuit each time the humidity changes to the correction module; The fitting module may send the temperature compensation cost of each intraocular pressure measurement value to the correction module; The correction module can adjust the resonant frequency of the resonant circuit according to each frequency drift cost and each temperature compensation cost, so as to correct the intraocular pressure measurement result according to the adjusted resonant frequency.

[0007] The non-invasive intraocular pressure measurement system provided in the present application adjusts the resonant frequency of the resonant circuit through the frequency drift cost and the temperature compensation cost, which can avoid the influence of changes in environmental factors on the measurement accuracy during the wearing of the intraocular pressure measurement device and realize stable monitoring of intraocular pressure.

[0008] In a possible implementation, the above-mentioned conversion module may include a feature determination submodule and a drift cost determination submodule, wherein the feature determination submodule is used to determine the dielectric characteristics of the device material through the intraocular humidity data; The drift cost determination submodule is used to convert the dielectric characteristics of the device material into the frequency drift cost of the resonant frequency in the resonant circuit each time the humidity changes.

[0009] In another possible implementation, the fitting module may include a modeling submodule and a cost fitting submodule, wherein the modeling submodule is used to determine the temperature-pressure regression coefficient of the target object's intraocular pressure based on the linear regression characteristics between the intraocular pressure measurement data and the ambient temperature; The cost fitting submodule is used to perform cost fitting on each intraocular pressure measurement value in the intraocular pressure measurement data through the temperature-pressure regression coefficient to obtain the temperature compensation cost of each intraocular pressure measurement value.

[0010] Furthermore, the correction module may include an adjustment submodule and an intraocular pressure correction submodule; The adjustment submodule is used to adjust the resonant frequency of the resonant circuit according to the frequency drift cost and the temperature compensation cost; The intraocular pressure correction submodule is used to correct the intraocular pressure detection value through the adjusted resonant frequency, and then output the corrected intraocular pressure value.

[0011] In some embodiments, the intraocular pressure measuring device includes a flexible contact lens, and the humidity sensor, the resonant circuit and the ambient temperature acquisition device are arranged in the flexible contact lens.

[0012] In one example, the flexible contact lens is made of hydrogel silicone. Of course, the flexible contact lens can also be made of other materials, which is not limited here.

[0013] In some embodiments, the resonant circuit includes a pressure sensor and an LC resonant tank.

[0014] In another example, the LC resonant circuit is a circuit composed of a capacitor and an inductor connected in parallel. Of course, the LC resonant circuit can also be of other types, which is not limited here.

[0015] In another example, the pressure sensor is a pressure film sensor. Of course, the pressure sensor may also be of other types, which is not limited here.

[0016] The technical solution provided by the embodiments disclosed in this application has the following beneficial effects: In the non-invasive intraocular pressure measurement system provided by the present application, intraocular humidity data and intraocular pressure measurement data are obtained from the intraocular pressure measurement device, and the ambient temperature is obtained from the ambient temperature acquisition device; multiple capacitance drift amounts of the resonant circuit after being affected by humidity are determined by the intraocular humidity data and the dielectric characteristics of the device material, and then all capacitance drift amounts are converted into frequency drift costs of the resonant frequency in the resonant circuit at each humidity change; the temperature-pressure regression coefficient of the intraocular pressure of the target object is determined based on the linear regression characteristics between the intraocular pressure measurement data and the ambient temperature, and then the temperature-pressure regression coefficient is used to perform cost fitting on each intraocular pressure measurement value in the intraocular pressure measurement data to obtain the temperature compensation cost of each intraocular pressure measurement value; the resonant frequency of the resonant circuit is adjusted according to each frequency drift cost and each temperature compensation cost, and the intraocular pressure measurement result of the target object is corrected based on the adjusted resonant frequency.

[0017] It can be seen that in the present application, first, after obtaining the intraocular humidity data when the target object wears the intraocular pressure measurement device, the degree of deviation of the actual capacitance value relative to the reference capacitance value caused by the change in ambient humidity (i.e., the capacitance drift amount) is determined through the intraocular humidity data and the dielectric characteristics of the device material, thereby determining the degree of influence of each humidity change on the performance of the resonant circuit (i.e., the resonant frequency) (i.e., the frequency drift cost). Secondly, after collecting the intraocular pressure measurement data when the target object wears the intraocular pressure measurement device, the quantitative value of the degree of influence of the ambient temperature change on the intraocular pressure change (i.e., the temperature-pressure regression coefficient) is determined, thereby quantifying the degree of influence of external factors (such as ambient temperature changes) on the measurement data (cost fitting), and evaluating the deviation of the actual intraocular pressure value (intraocular pressure fitting value) through the quantitative value of the influence degree (temperature compensation cost), thereby adjusting the resonant frequency during the process of the target object wearing the intraocular pressure measurement device according to each frequency drift cost and each temperature compensation cost, thereby correcting the intraocular pressure measurement result of the target object based on the adjusted resonant frequency. In summary, the scheme of the present application can avoid the influence of changes in environmental factors on the measurement accuracy during the wearing of the intraocular pressure measurement device, and realize stable monitoring of intraocular pressure. BRIEF DESCRIPTION OF THE DRAWINGS

[0018] Figure 1 is a schematic structural diagram of a non-invasive intraocular pressure measurement system according to some embodiments of the present application; Figure 2 is a schematic structural diagram of an intraocular pressure measurement and correction unit according to some embodiments of the present application; Figure 3 It is a schematic diagram of the structure of the conversion module shown in some embodiments of the present application. DETAILED DESCRIPTION

[0019] In order to better understand the above technical solution, the above technical solution will be described in detail below in conjunction with the accompanying drawings and specific implementation methods.

[0020] refer to Figure 1 , which is a structural schematic diagram of a non-invasive intraocular pressure measurement system shown in some embodiments of the present application. The non-invasive intraocular pressure measurement system of the present application includes an intraocular pressure measurement device and a resonant circuit connected to the intraocular pressure measurement device, and the resonant circuit is used to generate a resonant frequency corresponding to the intraocular pressure. In addition, the non-invasive intraocular pressure measurement system also includes an ambient temperature acquisition device and an intraocular pressure measurement correction unit; the ambient temperature acquisition device is used to collect the ambient temperature when the target object wears the intraocular pressure measurement device, and the intraocular pressure measurement device is also used to collect intraocular humidity data and intraocular pressure measurement data when the target object wears the intraocular pressure measurement device.

[0021] refer to Figure 2 , which is a schematic diagram of the structure of an intraocular pressure measurement correction unit according to some embodiments of the present application. To achieve the correction of non-invasive intraocular pressure measurement results, the intraocular pressure measurement correction unit 100 may include: an acquisition module 101, a conversion module 102, a fitting module 103 and a correction module 104, which are described as follows: The acquisition module 101 in the present application is mainly used to acquire intraocular humidity data and intraocular pressure measurement data from the intraocular pressure measurement device, and acquire the ambient temperature from the ambient temperature acquisition device.

[0022] The conversion module 102 in the present application is mainly used to determine multiple capacitance drifts of the resonant circuit after being affected by humidity through the intraocular humidity data and the dielectric characteristics of the device material, and then convert all capacitance drifts into the frequency drift cost of the resonant frequency in the resonant circuit at each humidity change.

[0023] The fitting module 103 in the present application is mainly used to determine the temperature-pressure regression coefficient of the target object's intraocular pressure based on the linear regression characteristics between the intraocular pressure measurement data and the ambient temperature, and then perform cost fitting on each intraocular pressure measurement value in the intraocular pressure measurement data through the temperature-pressure regression coefficient to obtain the temperature compensation cost of each intraocular pressure measurement value.

[0024] The correction module 104 in the present application is mainly used to adjust the resonant frequency of the resonant circuit according to various frequency drift costs and various temperature compensation costs, and to correct the intraocular pressure measurement result of the target object based on the adjusted resonant frequency.

[0025] In some preferred embodiments, reference Figure 3 As shown, the conversion module 102 may specifically include: a feature determination submodule and a drift cost determination submodule; The characteristic determination submodule is used to determine the dielectric characteristics of the device material through the intraocular humidity data; The drift cost determination submodule is used to convert the dielectric characteristics of the device material into the frequency drift cost of the resonant frequency in the resonant circuit each time the humidity changes.

[0026] In a specific implementation, the feature determination submodule can determine the humidity fluctuation amount each time the intraocular pressure changes through the intraocular humidity data; and then determine the dielectric characteristics of the preparation material according to all humidity fluctuation amounts.

[0027] It should be noted that the humidity fluctuation amount described in the present application represents the degree of change of the target object's intraocular humidity between different moments. The larger the humidity fluctuation amount, the higher the degree of change of the target object's intraocular humidity at the corresponding sampling moment, and the smaller the humidity fluctuation amount, the lower the degree of change of the target object's intraocular humidity at the corresponding sampling moment. In specific implementation, the humidity fluctuation amount at each change in intraocular pressure can be determined by the intraocular humidity data in the following manner, namely: first, select an intraocular humidity value in the intraocular humidity data as the selected intraocular humidity value, then obtain the intraocular humidity value of the selected intraocular humidity value at the previous sampling moment in the intraocular humidity data, and finally, use the difference between the selected intraocular humidity value and the corresponding intraocular humidity value at the previous sampling moment as the humidity fluctuation amount corresponding to the selected intraocular humidity value, and continue to determine the humidity fluctuation amounts corresponding to the remaining intraocular humidity values ​​in the intraocular humidity data, thereby obtaining the humidity fluctuation amount at each change in intraocular pressure.

[0028] In specific implementation, the dielectric characteristics of the preparation material can be determined based on all humidity fluctuations in the following manner, namely: first, the environmental dielectric constant and the humidity-dielectric influence coefficient are obtained; secondly, each humidity fluctuation is multiplied by the humidity-dielectric influence coefficient and then added to the value of the environmental dielectric constant as the relative dielectric constant corresponding to the humidity fluctuation, thereby obtaining the relative dielectric constant of the intraocular pressure measurement device material each time the humidity in the target object's eye changes, and all relative dielectric constants are used as the dielectric characteristics of the device material.

[0029] It should be noted that after measuring the initial resonant frequency of the resonant circuit in the intraocular pressure measurement device by a spectrum analyzer, the dielectric constant of the target object's intraocular environment is calculated by the relationship between the initial resonant frequency and the dielectric constant, and the calculated dielectric constant is used as the environmental dielectric constant in the present application. In other embodiments, it can also be determined by other methods, which are not limited here. In addition, the environmental dielectric constant is a physical quantity that describes the response characteristics of the material to the electric field under a specific environment, reflecting the ability of the material to store electrical energy under the action of the electric field in a specific environment. In addition, the relative dielectric constant is used to measure the polarization degree of the material in the intraocular pressure measurement device, reflecting the energy storage capacity of the capacitor in the resonant circuit, which characterizes the degree of influence of the change in intraocular humidity of the target object on the electric field characteristics in the resonant circuit. The larger the relative dielectric constant, the higher the degree of influence of the change in intraocular humidity of the target object on the electric field characteristics in the resonant circuit, and the smaller the relative dielectric constant, the higher the degree of influence of the change in intraocular humidity of the target object on the electric field characteristics in the resonant circuit.

[0030] In addition, in a specific implementation, the drift cost determination submodule can convert the dielectric characteristics of the device material into multiple capacitance drift amounts after the resonant circuit is affected by humidity; and then convert all capacitance drift amounts into the frequency drift cost of the resonant frequency in the resonant circuit each time the humidity changes.

[0031] It should be noted that converting the dielectric characteristics of the equipment material into multiple capacitance drifts after the resonant circuit is affected by humidity can be achieved in the following manner, namely: first, obtaining the dielectric variation coefficient and the reference capacitance value of the resonant circuit, then selecting a relative dielectric constant as the selected relative dielectric constant, and secondly, taking the product of the dielectric variation coefficient and the selected relative dielectric constant as the actual capacitance value corresponding to the selected relative dielectric constant, and finally, taking the difference between the actual capacitance value and the reference capacitance value as the capacitance drift corresponding to the selected relative dielectric constant, and continuing to determine the capacitance drifts corresponding to the remaining relative dielectric constants.

[0032] It should be noted that the dielectric variation coefficient described in the present application describes the sensitivity of the relative dielectric constant to the capacitance in the resonant circuit. The larger the dielectric variation coefficient, the higher the sensitivity of the relative dielectric constant to the capacitance in the resonant circuit, and the smaller the dielectric variation coefficient, the lower the sensitivity of the relative dielectric constant to the capacitance in the resonant circuit. In some preferred embodiments, the capacitance value of the resonant circuit after being affected by different humidity can be predicted by using the dielectric variation coefficient obtained by experimental fitting under different humidity conditions, and the predicted value can be compared with the actual measured value to find the optimal dielectric variation coefficient under different humidity conditions, and the optimal dielectric variation coefficient can be used as the dielectric variation coefficient in the present application. In other embodiments, it can also be obtained by other methods, which are not limited here. Preferably, when the target object wears the intraocular pressure measurement device for the first time, the capacitance in the resonant circuit can be measured under stable temperature and humidity, and the measured result can be used as the reference capacitance value in the present application.

[0033] In addition, it should be noted that the capacitance drift described in the present application characterizes the degree of deviation of the actual capacitance value from the reference capacitance value due to changes in ambient humidity. The larger the capacitance drift, the higher the degree of deviation of the actual capacitance value from the reference capacitance value due to changes in ambient humidity. The smaller the capacitance drift, the lower the degree of deviation of the actual capacitance value from the reference capacitance value due to changes in ambient humidity.

[0034] In specific implementation, converting all capacitance drift amounts into the frequency drift cost of the resonant frequency in the resonant circuit each time the humidity changes can be achieved in the following manner, namely: first, obtaining the inductance value of the resonant circuit, then selecting a capacitance drift amount as the selected capacitance drift amount, secondly, determining the square root of the product of the inductance value and the selected capacitance drift amount, and finally, multiplying the result by the inverse of 2π as the frequency drift cost corresponding to the selected capacitance drift amount, and continuing to determine the frequency drift costs corresponding to the remaining capacitance drift amounts, thereby obtaining the frequency drift cost of the resonant frequency in the resonant circuit each time the humidity changes.

[0035] It should be noted that the frequency drift cost described in the present application reflects the degree of influence of humidity changes on the performance of the resonant circuit (resonant frequency). The greater the frequency drift cost, the higher the degree of influence of humidity changes on the performance of the resonant circuit (resonant frequency), and the smaller the frequency drift cost, the lower the degree of influence of humidity changes on the performance of the resonant circuit (resonant frequency); as a preferred embodiment, determining the frequency drift cost of the resonant frequency in the resonant circuit at each humidity change based on the inductance value and all capacitance drifts can be achieved in the following manner, namely: first, selecting a capacitance drift as the selected capacitance drift, then determining the square root of the product of the inductance value and the selected capacitance drift, and finally, multiplying the result by the inverse of 2π as the frequency drift cost corresponding to the selected capacitance drift, and continuing to determine the frequency drift costs corresponding to the remaining capacitance drifts, thereby obtaining the frequency drift cost of the resonant frequency in the resonant circuit at each humidity change.

[0036] In some preferred embodiments, the fitting module 103 in the present application may include a modeling submodule and a cost fitting submodule, wherein The modeling submodule is used to determine the temperature-pressure regression coefficient of the target object's intraocular pressure based on the linear regression characteristics between the intraocular pressure measurement data and the ambient temperature; The cost fitting submodule is used to perform cost fitting on each intraocular pressure measurement value in the intraocular pressure measurement data through the temperature-pressure regression coefficient to obtain the temperature compensation cost of each intraocular pressure measurement value.

[0037] In specific implementation, in some embodiments, the modeling submodule can determine a linear regression model between the ambient temperature and the intraocular pressure of the target object through the intraocular pressure measurement data and the ambient temperature data, and the linear regression model is the linear regression feature; finally, the linear regression model is trained to obtain the temperature-pressure regression coefficient of the target object's intraocular pressure.

[0038] It should be noted that the linear regression model described in the present application is a linear model between the measured intraocular pressure measurement data and the ambient temperature data, which characterizes the linear relationship between the intraocular pressure and the ambient temperature of the target object. As a preferred embodiment, the linear regression model between the ambient temperature and the intraocular pressure of the target object is determined by the intraocular pressure measurement data and the ambient temperature. The linear regression model, that is, the linear regression feature, can be implemented in the following manner, namely: first, the ambient temperature data of the target object when wearing the intraocular pressure measurement device is obtained, and then the intraocular pressure measurement data and the ambient temperature data are used as input, and then the linear regression model algorithm in the prior art is used to construct a linear model for the intraocular pressure measurement data and the ambient temperature data, and the obtained model is used as the linear regression model between the ambient temperature and the intraocular pressure of the target object in the present application. In other embodiments, it can also be determined by other methods, which will not be repeated here.

[0039] In addition, the temperature-pressure regression coefficient described in the present application is a quantitative value of the degree of influence of ambient temperature changes on intraocular pressure changes. The larger the temperature-pressure regression coefficient, the higher the degree of influence of ambient temperature changes on intraocular pressure changes. The smaller the temperature-pressure regression coefficient, the lower the degree of influence of ambient temperature changes on intraocular pressure changes. As a preferred embodiment, training the linear regression model to obtain the temperature-pressure regression coefficient of the target object's intraocular pressure can be achieved in the following manner, namely: first, setting the objective function based on minimizing the sum of square errors between the actual intraocular pressure value and the predicted intraocular pressure value, and then, using the least squares method in the prior art to obtain the optimal model parameters for the objective function, the obtained optimal model parameters are used as the temperature-pressure regression coefficient of the target object's intraocular pressure in the present application. In other embodiments, it can also be determined by other methods, which are not limited here.

[0040] In addition, in some preferred embodiments, the cost fitting submodule can determine multiple intraocular pressure fitting values ​​based on the ambient temperature data and the temperature-pressure regression coefficient; and then determine the temperature compensation cost of each intraocular pressure measurement value based on each intraocular pressure measurement value and all intraocular pressure fitting values ​​in the intraocular pressure measurement data.

[0041] It should be noted that when the target object wears the intraocular pressure measurement device, the change in ambient temperature will cause the intraocular fluid to expand or contract, thereby affecting the intraocular pressure measurement result. The present application considers the impact of ambient temperature on intraocular pressure, and obtains the value that the intraocular pressure measurement value should reach after temperature-pressure regression correction, that is, the intraocular pressure fitting value; preferably, determining multiple intraocular pressure fitting values ​​based on the ambient temperature data and the temperature-pressure regression coefficient can be achieved in the following manner, that is, taking the product of each ambient temperature value in the ambient temperature data and the temperature-pressure regression coefficient as the intraocular pressure fitting value corresponding to the ambient temperature value. In other embodiments, other methods can also be used to determine, which are not limited here.

[0042] In specific implementation, the temperature compensation cost of each intraocular pressure measurement value is determined according to each intraocular pressure measurement value and all intraocular pressure fitting values ​​in the intraocular pressure measurement data. This can be achieved in the following manner, namely: first, an intraocular pressure measurement value in the intraocular pressure measurement data is selected as the selected intraocular pressure measurement value, and then the difference between the selected intraocular pressure measurement value and the corresponding intraocular pressure fitting value is used as the temperature compensation cost of the selected intraocular pressure measurement value, and the temperature compensation costs of the remaining intraocular pressure measurement values ​​are continued to be determined, thereby obtaining the temperature compensation cost of each intraocular pressure measurement value. In other embodiments, the temperature compensation cost can also be determined by other methods, which are not limited here.

[0043] It should be noted that the cost fitting described in this application refers to quantifying the degree of influence of external factors (such as changes in ambient temperature) on the measurement data, and evaluating the deviation of the actual intraocular pressure value (intraocular pressure fitting value) through the quantified value of the degree of influence; the temperature compensation cost represents the error amount of intraocular pressure measurement caused by changes in ambient temperature, which reflects the deviation between the actual measured intraocular pressure value (intraocular pressure measurement value) and the theoretical intraocular pressure value (intraocular pressure fitting value) after temperature correction. The larger the temperature compensation cost, the greater the deviation between the actual measured intraocular pressure value (intraocular pressure measurement value) and the theoretical intraocular pressure value (intraocular pressure fitting value) after temperature correction. The smaller the temperature compensation cost, the smaller the deviation between the actual measured intraocular pressure value (intraocular pressure measurement value) and the theoretical intraocular pressure value (intraocular pressure fitting value) after temperature correction.

[0044] In addition, in some embodiments, the correction module 104 in the present application may include: an adjustment submodule and an intraocular pressure correction submodule, wherein The adjustment submodule is used to adjust the resonant frequency of the resonant circuit according to the frequency drift cost and the temperature compensation cost; The intraocular pressure correction submodule is used to correct the intraocular pressure detection value through the adjusted resonant frequency, and then output the corrected intraocular pressure value.

[0045] In a specific implementation, the adjustment submodule may determine the frequency loss of the resonant circuit according to the frequency drift cost and the temperature compensation cost; and then adjust the resonant frequency of the resonant circuit according to the frequency loss.

[0046] It should be noted that in the present application, determining the frequency loss of the resonant circuit by the frequency drift cost and the temperature compensation cost can be achieved in the following manner, namely: first, obtaining the coupling coefficient between the target object's intraocular pressure and the resonant frequency, and then selecting the frequency drift cost and temperature compensation cost corresponding to an intraocular pressure measurement value, and secondly, multiplying the temperature compensation cost by the coupling coefficient and adding the result to the frequency drift cost as the frequency loss component corresponding to the intraocular pressure measurement value, and continue to determine the frequency loss components corresponding to the remaining intraocular pressure measurement values, and finally, taking the average value of all frequency loss components as the frequency loss of the resonant circuit.

[0047] In addition, the coupling coefficient described in the present application is a descriptive quantity of the influence of the change in the intraocular pressure of the target object on the resonant frequency of the intraocular pressure measuring device. The larger the coupling coefficient, the greater the influence of the change in the intraocular pressure of the target object on the resonant frequency of the intraocular pressure measuring device, and the smaller the coupling coefficient, the smaller the influence of the change in the intraocular pressure of the target object on the resonant frequency of the intraocular pressure measuring device. As a preferred embodiment, after ensuring that the ambient temperature and humidity remain stable, an intraocular pressure simulator is used to set the intraocular pressure of the target object to a reference value through experimental verification, and the resonant frequency of the intraocular pressure measuring device at this time is recorded, and the intraocular pressure is gradually increased, and the resonant frequency of the intraocular pressure measuring device is recorded each time. After determining the influence of the change in the intraocular pressure of the target object on the resonant frequency of the intraocular pressure measuring device through all the recorded data, the obtained result is used as the coupling coefficient in the present application. In other embodiments, it can also be obtained by other methods, which are not limited here.

[0048] It should be noted that the frequency loss component characterizes the degree of fluctuation of the resonant frequency in the intraocular pressure measurement device due to the influence of temperature (temperature compensation cost) and humidity (frequency drift cost) when the intraocular pressure measurement device measures intraocular pressure. The larger the frequency loss component, the higher the degree of fluctuation of the resonant frequency in the intraocular pressure measurement device due to the influence of temperature (temperature compensation cost) and humidity (frequency drift cost) when the intraocular pressure measurement device measures intraocular pressure. The smaller the frequency loss component, the lower the degree of fluctuation of the resonant frequency in the intraocular pressure measurement device due to the influence of temperature (temperature compensation cost) and humidity (frequency drift cost) when the intraocular pressure measurement device measures intraocular pressure. In addition, the frequency loss characterizes the stability of the resonant frequency caused by environmental factors (temperature and humidity) during the process in which the target object wears the intraocular pressure measurement device. The larger the frequency loss, the lower the stability of the resonant frequency caused by environmental factors (temperature and humidity) during the process in which the target object wears the intraocular pressure measurement device. The smaller the frequency loss, the higher the stability of the resonant frequency caused by environmental factors (temperature and humidity) during the process in which the target object wears the intraocular pressure measurement device.

[0049] It should also be noted that, in the intraocular pressure measurement data, each intraocular pressure measurement value has a unique corresponding resonant frequency in the resonant circuit; therefore, in a specific implementation, adjusting the resonant frequency of the resonant circuit by the frequency loss can be achieved in the following manner, namely: first, selecting an intraocular pressure measurement value in the intraocular pressure measurement data, then obtaining the resonant frequency of the intraocular pressure measurement value, adding the frequency loss to the resonant frequency as the adjusted resonant frequency of the intraocular pressure measurement value in the resonant circuit, and continuing to determine the adjusted resonant frequencies of the remaining intraocular pressure measurement values ​​in the resonant circuit. In other embodiments, other methods may also be used, which are not limited here.

[0050] In specific implementation, the intraocular pressure detection value is corrected by adjusting the resonant frequency, and then the corrected intraocular pressure value is outputted in the following manner, namely: first, the coupling coefficient between the intraocular pressure and the resonant frequency is obtained, and then the adjusted resonant frequency corresponding to each intraocular pressure measurement value is multiplied by the coupling coefficient as the correction value corresponding to each intraocular pressure measurement value, and finally the correction value obtained after correction is outputted as the final intraocular pressure value.

[0051] It should be noted that in the non-invasive intraocular pressure measurement system of the present application, the influence of the intraocular pressure change of the target object on the resonant frequency of the intraocular pressure measurement device is determined, that is, after the coupling coefficient is determined, the adjusted resonant frequency is used to correct each intraocular pressure measurement value, thereby correcting the intraocular pressure measurement result of the target object, that is, by analyzing the influence of the ambient temperature when the target object wears the intraocular pressure measurement device on the target object's intraocular pressure and the influence of intraocular humidity on the resonant frequency, the intraocular pressure measurement value directly measured by the intraocular pressure measurement device is compensated, thereby improving the accuracy of intraocular pressure detection under the premise of non-invasive intraocular pressure measurement.

[0052] Although the preferred embodiments of the present application have been described, those skilled in the art may make other changes and modifications to these embodiments once they have learned the basic creative concept. Therefore, the appended claims are intended to be interpreted as including the preferred embodiments and all changes and modifications falling within the scope of the present application.

[0053] Obviously, those skilled in the art may make various changes and modifications to the present application without departing from the spirit and scope of the present application. Thus, if these modifications and variations of the present application fall within the scope of the claims of the present application and their equivalents, the present application is also intended to include these modifications and variations.

Claims

1. A non-invasive intraocular pressure measurement system, comprising an intraocular pressure measurement device and a resonant circuit connected to the intraocular pressure measurement device, wherein the resonant circuit is used to generate a resonant frequency corresponding to the intraocular pressure, characterized in that: It also includes an environmental temperature acquisition device and an intraocular pressure measurement correction unit; the environmental temperature acquisition device is used to acquire the environmental temperature when the target object wears the intraocular pressure measurement device, and the intraocular pressure measurement device is also used to acquire intraocular humidity data and intraocular pressure measurement data when the target object wears the intraocular pressure measurement device; The intraocular pressure measurement and correction unit specifically includes: an acquisition module, a conversion module, a fitting module, and a correction module; The acquisition module is used to acquire intraocular humidity data and intraocular pressure measurement data from the intraocular pressure measurement device, and acquire ambient temperature from the ambient temperature acquisition device; The conversion module is used to determine multiple capacitance drifts of the resonant circuit after being affected by humidity through the intraocular humidity data and the dielectric characteristics of the device material, and then convert all capacitance drifts into the frequency drift cost of the resonant frequency in the resonant circuit when the humidity changes each time; The fitting module is used to determine the temperature-pressure regression coefficient of the target object's intraocular pressure based on the linear regression characteristics between the intraocular pressure measurement data and the ambient temperature, and then perform cost fitting on each intraocular pressure measurement value in the intraocular pressure measurement data through the temperature-pressure regression coefficient to obtain the temperature compensation cost of each intraocular pressure measurement value; The correction module is used to adjust the resonant frequency of the resonant circuit according to each frequency drift cost and each temperature compensation cost, and correct the intraocular pressure measurement result of the target object based on the adjusted resonant frequency.

2. The non-invasive intraocular pressure measurement system according to claim 1, characterized in that: The conversion module includes a feature determination submodule and a drift cost determination submodule; The characteristic determination submodule is used to determine the dielectric characteristics of the device material through the intraocular humidity data; The drift cost determination submodule is used to convert the dielectric characteristics of the device material into the frequency drift cost of the resonant frequency in the resonant circuit each time the humidity changes.

3. The non-invasive intraocular pressure measurement system according to claim 1, characterized in that: The fitting module includes a modeling submodule and a cost fitting submodule; A modeling submodule, for determining a temperature-pressure regression coefficient of the target object's intraocular pressure based on a linear regression characteristic between the intraocular pressure measurement data and the ambient temperature; The cost fitting submodule is used to perform cost fitting on each intraocular pressure measurement value in the intraocular pressure measurement data through the temperature-pressure regression coefficient to obtain the temperature compensation cost of each intraocular pressure measurement value.

4. The non-invasive intraocular pressure measurement system according to claim 1, characterized in that: The correction module includes an adjustment submodule and an intraocular pressure correction submodule; An adjustment submodule, configured to adjust the resonant frequency of the resonant circuit by using the frequency drift cost and the temperature compensation cost; The intraocular pressure correction submodule is used to correct the intraocular pressure detection value through the adjusted resonant frequency, and then output the corrected intraocular pressure value.

5. The non-invasive intraocular pressure measurement system according to claim 1, characterized in that: The intraocular pressure measurement device includes a humidity sensor, and the humidity sensor is used to detect the intraocular humidity of the target object when the target object wears the intraocular pressure measurement device, generate intraocular humidity data and send it to the intraocular pressure measurement correction unit.

6. The non-invasive intraocular pressure measurement system according to claim 1, characterized in that: The intraocular pressure measuring device comprises a flexible contact lens, and the humidity sensor, the resonance circuit and the ambient temperature acquisition device are arranged in the flexible contact lens.

7. The non-invasive intraocular pressure measurement system according to claim 1, characterized in that: The material of the flexible contact lens is hydrogel silica gel.

8. The non-invasive intraocular pressure measurement system according to claim 1, characterized in that: The resonant circuit includes a pressure sensor and an LC resonant circuit.

9. The non-invasive intraocular pressure measurement system according to claim 1, characterized in that: The LC resonant circuit is a circuit consisting of a capacitor and an inductor connected in parallel.

10. The non-invasive intraocular pressure measurement system according to claim 1, characterized in that: The pressure sensor is a pressure film sensor.

Images