CN220212894U - Optical microscopic system for intraocular pressure measurement - Google Patents
Optical microscopic system for intraocular pressure measurement Download PDFInfo
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- CN220212894U CN220212894U CN202321610229.8U CN202321610229U CN220212894U CN 220212894 U CN220212894 U CN 220212894U CN 202321610229 U CN202321610229 U CN 202321610229U CN 220212894 U CN220212894 U CN 220212894U
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Abstract
The utility model provides an optical microscopic system for intraocular pressure measurement, and relates to the technical field of optical measurement; the device comprises a space optical sensing unit, a light transmission unit, an intraocular pressure sensor, a spectrum acquisition unit and a spectrum demodulation unit; the space optical sensing unit is connected with the spectrum acquisition unit; the spectrum acquisition unit is connected with the spectrum demodulation unit through a transmission link I; the intraocular pressure sensor is provided with a Fabry-Perot microcavity; broadband light emitted by the space optical sensing unit is vertically incident into the Fabry-Perot microcavity through the light transmission unit, so that interference broadband light is obtained; the interference broadband light is transmitted to a spectrum acquisition unit; the spectrum acquisition unit converts the interference broadband light into a digital spectrum and then transmits the digital spectrum to the spectrum demodulation unit; the spectrum demodulation unit acquires the intraocular pressure according to the digital spectrum. The utility model completes the incidence of broadband light and the receiving of interference broadband light by matching the space optical sensing unit, the light transmission unit and the intraocular pressure sensor, and reduces optical elements.
Description
Technical Field
The utility model relates to the technical field of optical measurement, in particular to an optical microscopic system for intraocular pressure measurement.
Background
Glaucoma is one of three causes of blindness of human eyes, and is the first irreversible blindness disease in the world because glaucoma is extremely harmful. Intraocular pressure refers to the pressure at which the eye wall is subjected to the contents of the eye, and human eye pressure should normally be in the range of 10-21mmHg, with ocular hypertension being considered as an important risk factor for the onset of glaucoma. Thus, ocular tension is an important indicator in the clinical determination of therapeutic targets as well as the assessment of therapeutic efficacy and prognosis.
The main detection means of intraocular pressure in clinic at present is to detect the instant intraocular pressure of a patient by an instrument, and the detection instrument mainly comprises a applanation tonometer, a jet tonometer and the like; the applanation tonometer is a currently considered gold standard for measuring intraocular pressure, but the method has the defects that surface anesthesia is needed before measurement, sodium fluorescein is required to be dripped on the cornea during measurement, and the measured value is influenced by the central thickness of the cornea. Compared with a applanation tonometer, the jet tonometer simplifies the process of measuring the intraocular pressure, does not need surface anesthesia and sodium fluorescein, but has the problems that the jet tonometer impacts air flow to cause discomfort of eyes of patients, and the instrument is expensive and not portable.
In addition, there are many studies of miniature intraocular pressure sensors based on different principles, which have in common the characteristics: 1. the sensor is separated from the detection equipment, and the sensing mode is non-contact; 2. the area and the volume of the sensor are tiny, from hundreds of micrometers to a few millimeters; 3. the sensor is contacted with the eye structure and is attached to the eyeball or implanted into the eyeball.
Aiming at the proposed miniature intraocular pressure sensor, the miniature intraocular pressure sensor is classified according to a sensing principle, and mainly comprises three types of electric sensing, microfluidic sensing and optical sensing. Chen et al devised a contact lens-based intraocular pressure sensor based on capacitance-to-pressure sensitivity, with the frequency of the LC oscillator formed by capacitance and inductance also changing with changes, and the reading device was a large network analyzer. Agaoglu et al utilize a microfluidic chip to realize intraocular pressure detection, implant an artificial lens integrated with the microfluidic chip into an eyeball by utilizing a cataract surgery technology, displace the liquid-gas interface position of the artificial lens along with fluctuation of intraocular pressure, and monitor the interface position to obtain an intraocular pressure value. Electrical sensing is limited to circuit structures and materials, sub-millimeter dimensions are difficult to achieve, and reading devices are bulky and expensive. Microfluidic sensing is limited to the stringent requirements on air tightness and the principle of indirect sensing of photographed readings, making miniaturization a bottleneck. The volume of the optical sensor is generally smaller than that of the electric sensor and the microfluidic sensor, so that the optical sensor becomes a main research direction of the implantable sensor.
The existing optical measurement schemes are all based on Fabry-Perot interference structures, the Lee team uses silicon nitride as a flexible sensing film and silicon as a shell, the size of the sensor is about 1mm, and the detection precision of the sensor reaches 1.3mmHg. The Kim team further optimizes on the basis of Lee work, and ANN artificial intelligence is added in a demodulation algorithm, so that the accuracy is improved to 0.1mmHg. The size of the sensor is millimeter, and the manufacturing process is etching and assembling. This presents a great challenge for mass production and minimally invasive implantation. And the team uses and based on the professional equipment slit lamp of ophthalmology detection, reequips and expands desk-top broadband light source input interface and to the output interface of large-scale spectrum appearance, and whole system is redundant, and portability is poor and the cost is high.
In view of this, it is important to provide a non-contact optical microscope system with a simple structure.
Disclosure of Invention
The utility model aims to solve the technical problems that: in order to solve the problem of redundancy of the whole system of the optical detection device for intraocular pressure measurement in the prior art, the utility model provides the optical microscopic system for intraocular pressure measurement, which reduces optical elements by optimizing an optical path, simplifies the structure of the optical microscopic system and solves the problem of redundancy of the whole system of the optical detection device for intraocular pressure measurement in the prior art.
The technical scheme adopted for solving the technical problems is as follows:
an optical microscopic system for intraocular pressure measurement comprises a space optical sensing unit, a light transmission unit, an intraocular pressure sensor, a spectrum acquisition unit and a spectrum demodulation unit; wherein,
the space optical sensing unit is connected with the spectrum acquisition unit;
the spectrum acquisition unit is connected with the spectrum demodulation unit through a transmission link I;
a Fabry-Perot microcavity is arranged on the intraocular pressure sensor;
broadband light emitted by the space optical sensing unit vertically enters the Fabry-Perot microcavity through the light transmission unit to obtain interference broadband light;
the interference broadband light passes through the light transmission unit and the space optical sensing unit and then is transmitted to the spectrum acquisition unit;
the spectrum acquisition unit converts the interference broadband light into a digital spectrum and then transmits the digital spectrum to the spectrum demodulation unit;
the spectrum demodulation unit acquires intraocular pressure according to the digital spectrum.
Optionally, the spatial optical sensing unit comprises a broadband light source, a fiber optic circulator and a fiber optic collimator; the broadband light source is connected with the optical fiber circulator, the optical fiber circulator is connected with the optical fiber collimator, and the optical fiber circulator is connected with the spectrum acquisition device through optical fibers; the broadband light source is configured to emit the broadband light; the broadband light is sequentially input to the light transmission unit through the optical fiber circulator and the optical fiber collimator; the interference broadband light sequentially passes through the light transmission unit, the optical fiber collimator and the optical fiber circulator and then is transmitted to the spectrum acquisition unit.
Optionally, the broadband light has a wavelength in the range of 750nm to 950nm.
Optionally, the device further comprises a microscopic imaging positioning unit; the microscopic imaging positioning unit is connected with the spectrum demodulation unit through a transmission link II; the indication light emitted by the microscopic imaging positioning unit is incident into the Fabry-Perot microcavity through the light transmission unit, so that reflected indication light is obtained; and the reflected indicating light is received and imaged by the microscopic imaging positioning unit after passing through the light transmission unit, so that a real-time image is obtained, and the real-time image is transmitted to the spectrum demodulation unit.
Optionally, the microscopic imaging positioning unit comprises a CCD camera and an indication light source; the indication light source is used for emitting the indication light; and the CCD camera is in signal connection with the spectrum demodulation unit.
Optionally, the light transmission unit includes a lens group and an objective lens sequentially disposed along the light path.
Optionally, the spectrum acquisition unit comprises a light dispersion conversion module, an embedded module and a power supply driving module; the power supply driving module supplies power to the light dispersion conversion module under the control of the embedded module; the light dispersion conversion module converts the interference broadband light with different wavelengths into an electric signal through a diffraction effect and transmits the electric signal to the embedded module; the embedded module is used for digitizing the electric signal to obtain the digital spectrum.
Optionally, the spectrum demodulation unit comprises at least one central processor.
The beneficial effects of the utility model are as follows:
the optical microscopic system for intraocular pressure measurement provided by the utility model is matched with the spatial optical sensing unit, the light transmission unit and the intraocular pressure sensor, so that the incidence of broadband light and the receiving of interference broadband light are completed, the eye pressure is measured based on the Fabry-Perot interference structure, the accuracy of an intraocular pressure measurement result is ensured, meanwhile, optical elements are reduced, the structure of the optical microscopic system is simplified, and the problem of integral redundancy of optical detection equipment for intraocular pressure measurement in the prior art is solved.
Drawings
The utility model will be further described with reference to the drawings and examples.
FIG. 1 is a schematic diagram of the structure of an optical microscopy system for tonometric measurement in accordance with the present utility model;
FIG. 2 is a schematic diagram of the structure of the spectrum acquisition unit 4 in the present utility model;
FIG. 3 is a schematic diagram of a spectrum demodulation unit for performing spectrum demodulation according to the present utility model;
FIG. 4 is a diagram of raw spectral data read by a demodulation system in an embodiment of the present utility model;
FIG. 5 is a graph of interference spectrum data restored by a demodulation system in an embodiment of the utility model;
FIG. 6 is a graph of interference spectrum data at different pressures in an embodiment of the present utility model;
fig. 7 is a linear fit of the center wavelength corresponding to the interference spectrum peak to the applied pressure.
In the figure: 1-a spatial optical sensing unit; 11-a broadband light source; 12-a fiber circulator; 13-an optical fiber collimator; 2-a light transmission unit; 21-a lens group; 22-an objective lens; 3-intraocular pressure sensor; 4-a spectrum acquisition unit; 41-a light dispersion conversion module; 42-an embedded module; 43-a power drive module; a 5-spectrum demodulation unit; 6-a microscopic imaging positioning unit; 61-CCD camera; 62-indicating a light source; 7-transmission link one; 8-transmission link two.
Detailed Description
The present utility model will now be described in further detail. The embodiments described below are exemplary and intended to illustrate the utility model and should not be construed as limiting the utility model, as all other embodiments, based on which a person of ordinary skill in the art would obtain without inventive faculty, are within the scope of the utility model.
In order that the above objects, features and advantages of the utility model will be readily understood, a more particular description of the utility model will be rendered by reference to specific embodiments thereof which are illustrated in the appended drawings.
In order to solve the problem of redundancy of the whole system of optical detection equipment for intraocular pressure measurement in the prior art, the utility model provides an optical microscopic system for intraocular pressure measurement, which is shown in fig. 1, and comprises a space optical sensing unit 1, a light transmission unit 2, an intraocular pressure sensor 3, a spectrum acquisition unit 4 and a spectrum demodulation unit 5; the space optical sensing unit 1 is connected with the spectrum acquisition unit 4 through optical fibers; the spectrum acquisition unit 4 is connected with the spectrum demodulation unit 5 through a first transmission link 7, and the first transmission link 7 is a transmission link of digital electric signals, and the transmission implementation mode can be a wired transmission technology or a wireless transmission technology; notably, wired transmission techniques include, but are not limited to, serial, USB, ethernet, CAN, HDMI, displayPort, and the like; wireless transmission techniques include, but are not limited to WIFI, bluetooth, 2.4G, NFC, etc.; the intraocular pressure sensor 3 is provided with a Fabry-Perot microcavity; in the working process, broadband light emitted by the space optical sensing unit 1 vertically enters a Fabry-Perot microcavity (F-P resonant cavity) on the intraocular pressure sensor 3 through the light transmission unit 2, enters a cavity of the Fabry-Perot microcavity, is reflected by a plurality of surfaces and interferes, and interference broadband light is obtained; the obtained interference broadband light sequentially passes through the light transmission unit 2 and the space optical sensing unit 1 and then is transmitted to the spectrum acquisition unit 4; the spectrum acquisition unit 4 converts the interference broadband light into a digital spectrum and then transmits the digital spectrum to the spectrum demodulation unit 5; the spectrum demodulation unit 5 acquires the liquid environment pressure outside the Fabry-Perot microcavity on the intraocular pressure sensor 3, namely the intraocular pressure according to the digital spectrum.
The optical microscopic system for intraocular pressure measurement provided by the utility model is matched with the spatial optical sensing unit 1, the light transmission unit 2 and the intraocular pressure sensor 3, so that the incidence of broadband light and the receiving of interference broadband light are completed, the eye pressure is measured based on the Fabry-Perot interference structure, the accuracy of an intraocular pressure measurement result is ensured, meanwhile, optical elements are reduced, the structure of the optical microscopic system is simplified, and the problem of integral redundancy of optical detection equipment for intraocular pressure measurement in the prior art is solved.
The intraocular pressure sensor 3 is preferably manufactured by adopting a two-photon femtosecond laser 3D printing technology, the structure of the intraocular pressure sensor comprises an optical Fabry-Perot interference cavity, namely a Fabry-Perot microcavity, the outer reflecting surface of the cavity is a film sensitive to external pressure change, and the inner reflecting surface of the cavity is of a rigid structure and is not influenced by external pressure; by using a two-photon femtosecond laser 3D printing technology, the precise manufacture of the Fabry-Perot structure intraocular pressure sensor sensitive to pressure variation can be realized in batches under the sub-millimeter size; in the intraocular pressure sensor 3 of the present utility model, the reflecting surface on the outside of the cavity of the F-P resonant cavity, i.e., the fabry-perot microcavity, is opposed to and parallel to the reflecting surface on the inside of the cavity. The intraocular pressure sensor 3 may be a conventional intraocular pressure sensor with a fabry perot microcavity, such as the one described in patent application No. 2022104328698.
The spatial optical sensing unit 1 in the present utility model comprises a broadband light source 11, an optical fiber circulator 12 and an optical fiber collimator 13; the broadband light source 11 is connected with the optical fiber circulator 12, the optical fiber circulator 12 is connected with the optical fiber collimator 13, and the optical fiber circulator 12 is connected with the spectrum acquisition device 4 through optical fibers; the broadband light source 11 is for emitting broadband light; broadband light is sequentially input to the light transmission unit 2 through the optical fiber circulator 12 and the optical fiber collimator 13; the interference broadband light passes through the light transmission unit 2, the optical fiber collimator 13 and the optical fiber circulator 12 in sequence and then is transmitted to the spectrum acquisition unit 4.
Specifically, the broadband light emitted by the broadband light source 11 is input to a first port of the optical fiber circulator 12 through an optical fiber, and then output by a second port of the optical fiber circulator 12, and is input to the optical fiber collimator 13 through the optical fiber; the optical fiber collimator 13 is fixed at a position perpendicular to the optical axis of the light transmission unit 2, so that broadband light is collimated by the optical fiber collimator 13 and then vertically enters the Fabry-Perot microcavity of the intraocular pressure sensor 3 through the light transmission unit 2, enters the cavity of the Fabry-Perot microcavity, is reflected by a plurality of surfaces and interferes, and interference broadband light is obtained; the obtained interference broadband light sequentially enters the optical fiber collimator 13 and the optical fiber circulator 12 through the light transmission unit 2, and is output by a third port of the optical fiber circulator 12 and transmitted to the spectrum acquisition unit 4 through an optical fiber.
The optical microscopic system for intraocular pressure measurement provided by the utility model comprises a broadband light source 11, an optical fiber circulator 12, an optical fiber collimator 13, a light transmission unit 2 and a Fabry-Perot microcavity of an intraocular pressure sensor 3, wherein the Fabry-Perot microcavity structure of the intraocular pressure sensor 3, the light transmission unit 2, the optical fiber collimator 13, the optical fiber circulator 12 and a spectrum acquisition unit 4 form a transmission route of interference broadband light, and the transmission of the broadband light and the interference broadband light can be completed by fewer elements.
The wavelength range of the broadband light is preferably 750-950 nm, the light in the wavelength range is invisible to human eyes, the discomfort of a patient is not caused, and the protective actions such as blinking, eyeball rotation and the like of the patient are not caused. The light in the wave band is not absorbed by cornea, and has good penetrability, and most energy can directly reach the intraocular pressure sensor 3 in the eye. It is noted that the excitation of broadband light may be, but is not limited to, the use of LED semiconductor infrared light sources, thermal radiation infrared light sources, gas discharge infrared light sources, laser infrared light sources, liquid crystal infrared light sources, and the like.
Further, the optical microscopic system for tonometric measurement of the present utility model preferably further comprises a microscopic imaging positioning unit 6; the microscopic imaging positioning unit 6 is connected with the spectrum demodulation unit 5 through a second transmission link 8, the second transmission link 8 is a transmission link of digital signals, and the transmission implementation mode can be a wired transmission technology or a wireless transmission technology; notably, wired transmission techniques include, but are not limited to, serial, USB, ethernet, CAN, HDMI, displayPort, and the like; wireless transmission techniques include, but are not limited to WIFI, bluetooth, 2.4G, NFC, etc.; in the working process, the indication light emitted by the microscopic imaging positioning unit 6 is incident into the Fabry-Perot microcavity of the intraocular pressure sensor 3 through the light transmission unit 2, so as to obtain reflection indication light; the reflected indication light is received and imaged by the microscopic imaging positioning unit 6 after passing through the light transmission unit 2, a real-time image is obtained, the real-time image is transmitted to the spectrum demodulation unit 5, and the position of the intraocular pressure sensor 3 is monitored through the spectrum demodulation unit 5, so that the position of the indication light irradiated onto the intraocular pressure sensor 3 is monitored.
Furthermore, the transmission light path of the indication light and the broadband light in the light transmission unit 2 is preferably the same, that is, the indication light and the broadband light in the light transmission unit 2 are in the same straight line in space, so that the same incidence position of the indication light and the broadband light on the intraocular pressure sensor 3 is ensured, the incidence position of the indication light on the intraocular pressure sensor 3 can be monitored, the monitoring of the incidence position of the broadband light on the intraocular pressure sensor 3 can be realized, and an operator can conveniently adjust the position of the space optical sensing unit 1 according to the obtained real-time image.
Further, it is preferable to display a real-time image on a corresponding visual screen so as to intuitively monitor the position of the eye pressure sensor 3.
In particular, the microscopic imaging positioning unit 6 of the present utility model preferably comprises a CCD camera 61 and an indication light source 62; the indication light source 62 is for emitting indication light; wherein the indication light source 62 is fixed at a position perpendicular to the optical axis of the light transmission unit 2, and the outgoing direction of the indication light emitted by the indication light source 62 is perpendicular to the optical axis of the light transmission unit 2; the CCD camera 61 is arranged coaxially with the light transmission unit 2; the CCD camera 61 is in signal connection with the spectrum demodulation unit 5.
In the working process, the indication light emitted by the indication light source 62 passes through the light transmission unit 2 and then vertically enters the Fabry-Perot microcavity of the intraocular pressure sensor 3 to be reflected, so that reflected indication light is formed; the reflected indication light is received and imaged by the CCD camera 61 after passing through the light transmission unit 2, so as to obtain a real-time image; monitoring the position of the ocular pressure sensor 3 is achieved by feeding the real-time image to the spectral demodulation unit 5.
The Fabry-Perot microcavity of the indication light source 62, the light transmission unit 2 and the intraocular pressure sensor 3 form a transmission route of the indication light, and the Fabry-Perot microcavity, the light transmission unit 2 and the CCD camera form a transmission route of the reflection indication light, so that the position of the intraocular pressure sensor 3 is monitored.
Referring to fig. 1, the broadband light and the interference broadband light, and the indication light and the reflection indication light in the present utility model share the light transmission unit 2 to perform light transmission, so that the monitoring of the position of the intraocular pressure sensor 3 and the measurement of the intraocular pressure can be simultaneously realized without adding additional optical elements, the accuracy of intraocular pressure measurement can be improved without adding optical elements, and further the structure of the optical microscopic system can be further simplified.
In order to facilitate the transmission of light, the light transmission unit 2 in the present utility model includes a lens group 21 and an objective lens 22 sequentially arranged along the light path; wherein the lens group 21 and the objective lens 22 form a same optical axis structure; the lens group 21 may include two or more lenses, and the transmission of the broadband light, the interference broadband light, the indication light, and the reflected indication light may be achieved by respectively reflecting or transmitting the indication light and the broadband light through the two or more lenses; the lenses in the lens group 21 may be selectively transparent by plating or other treatment, that is, the same lens may reflect light in certain specific wavelength ranges and transmit light in certain specific wavelength ranges, so that separate transmission of the indication light, the reflected indication light, the broadband light and the interference broadband light may be simultaneously realized through the lens group 21; the reflectivity and the transmissivity of each lens to light in different wavelength ranges can be selected according to the light path requirements; alternatively, the individual lenses may be arranged such that the different regions are capable of reflecting or transmitting light of different wavelength ranges.
Specifically, the indication light enters the lens group 21, is reflected, enters the objective lens 22, and the objective lens 22 focuses the indication light on the surface of the intraocular pressure sensor 3; the indication light is reflected to form reflected indication light; the objective lens 22 collects the reflected indication light, which is received and imaged by the CCD camera 61 after passing through the lens group 21.
After entering the lens group 21, the broadband light is reflected and enters the objective lens 22, and the objective lens 22 gathers the broadband light to the Fabry-Perot microcavity on the intraocular pressure sensor 3 to generate interference broadband light; the objective lens 22 collects the interference broadband light, which is inputted to the optical fiber collimator 13 after passing through the lens group 21.
The present utility model preferably focuses the indication light and the broadband light at the same time perpendicularly to the same point on the ocular pressure sensor 3, and collects the returned reflected indication light and the interference broadband light at the same time.
The space optical sensing unit 1, the light transmission unit 2 and the microscopic imaging positioning unit 6 are preferably arranged as a whole, and the whole is carried by using a multi-dimensional displacement table, so that the position and the angle of a focusing light spot of the objective lens 22 on the intraocular pressure sensor 3 can be precisely adjusted by the multi-dimensional displacement table. Notably, "multidimensional" includes, but is not limited to, fore-aft, side-to-side, up-and-down, pitch, and yaw. Adjustment means include, but are not limited to, manual adjustment, electric adjustment, pneumatic adjustment, hydraulic adjustment, and the like.
The microscopic imaging positioning unit 6, the space optical sensing unit 1 and the light transmission unit 2 are integrated, so that the optical microscopic system for tonometric measurement has the advantages of good structural stability, high sensing reliability, small volume, high portability and lower cost.
Furthermore, the utility model preferably integrates the broadband light source 11, the optical fiber circulator 12, the spectrum acquisition unit 4 and the drive circuit of the indication light source 62 into a case, the whole machine is powered by an external power supply or an internal storage battery, and the two power supply modes can be switched at will.
Referring to fig. 2, the spectrum acquisition unit 4 in the present utility model includes a light dispersion conversion module 41, an embedded module 42, and a power driving module 43; wherein the power driving module 43 supplies power to the light dispersion conversion module 41 under the control of the embedded module 42; the light dispersion conversion module 41 converts interference broadband light of different wavelengths into an electric signal through a diffraction effect and transmits the electric signal to the embedded module 42; the embedded module 42 is configured to digitize the electrical signal to obtain a digital spectrum.
Specifically, the power driving module 43 is controlled by the embedded module 42, and is configured to supply power to the light dispersion conversion module 41, and implement photoelectric conversion of the light dispersion conversion module 41 at different speeds by adjusting the power supply frequency; the light dispersion conversion module 41 spatially distinguishes light of different wavelengths through diffraction effects and converts the light of different wavelengths into electric signals with corresponding intensities; the diffraction effect adopted by the light dispersion conversion module 41 is preferably a second-order diffraction effect; after the interference broadband light is subjected to the dispersion effect of two-stage diffraction, the light with different wavelengths is obviously distinguished in space, and the light with different space positions is converted into an electric signal with corresponding intensity through photoelectric conversion, so that the demodulation precision of the external liquid environment pressure based on the change of the central wavelength position is effectively improved; the embedded module 42 captures the electrical signal and digitizes it to obtain a digital spectrum.
The embedded module 42 in the utility model can control the power supply driving module 43 to adjust the frequency for supplying power to the light dispersion conversion module 41, so that measurement of different rates of the interference broadband light energy spectrum can be realized, and the requirements of different medical environments on the measurement rate can be met.
The spectrum demodulation unit 5 is used for monitoring the position of the intraocular pressure sensor 3 in the imaging of the area array CCD camera 61 in real time so that an operator can adjust the irradiation position of the indicating light in time; on the other hand, the method is used for acquiring a digital spectrum and searching a central wavelength corresponding to a spectrum peak, and the pressure of an external liquid environment, namely the intraocular pressure, is obtained in real time through the corresponding relation between the position of the central wavelength and the pressure; feedback about whether the broadband light is directed to ocular pressure sensor 3 and operational advice of the multidimensional calibration adjustment may also be given to the operator based on the quality of the real-time spectrum. Notably, the criteria for spectral quality include, but are not limited to, light intensity, free spectral range, signal to noise ratio, and frequency domain transform results. Forms of feedback and advice include, but are not limited to, sounds, text, graphics, indicators, vibration, and combinations of the above.
In order to achieve the above functions, the spectrum demodulation unit 5 of the present utility model includes at least one central processing unit, and the demodulation steps are executed in the central processing unit in the form of programs or instructions, which are stored in the permanent memory and can be called by the central processing unit at any time. Notably, central processors include, but are not limited to CPU, MCU, MPU, DSP, FPGA and ASICs, and the like. Permanent memory storage includes, but is not limited to, programmable ROM, flash ROM, optical disks, floppy disks, hard disks, and the like.
The utility model realizes a detection demodulation method of a Fabry-Perot structure intraocular pressure sensor based on an embedded system and a non-contact optical microscopic detection system.
Referring to fig. 3, the spectrum demodulation unit 5 of the present utility model acquires intraocular pressure from a digital spectrum, which includes the steps of:
s1: determining the position of an optical microscopy system;
s2: reading a digital spectrum to obtain original spectrum data;
s3: extracting the maximum value of the original spectrum data, comparing the maximum value with a preset threshold value, judging whether the maximum value is not smaller than the preset threshold value, if so, entering a step S4, otherwise, entering a step S1;
s4: performing spectrum interpolation processing on the original spectrum data, performing FFT filtering, and recovering spectrum data of interference broadband light;
s5: carrying out peak splitting on spectrum data of the interference broadband light by adopting a peak searching algorithm to obtain the central wavelength position of the spectrum data of the interference broadband light;
s6: intraocular pressure is obtained by the center wavelength position.
According to the sensing principle of the F-P resonant cavity, when the reflectivity of the two reflecting surfaces is smaller than 4%, most of light vertically entering the F-P resonant cavity can be transmitted from the other side, and only the light reflected for the first time and the second time can keep an order of magnitude in energy. Therefore, the F-P resonant cavity formed by the low-reflectivity reflecting surfaces can simplify multi-beam interference into double-beam interference; the reflected intensity of the interference light is expressed as:
wherein: i FP For reflected interference light intensity, I 0 For incident light intensity, R 1 、R 2 The reflectivity of the two surfaces is respectively, n is the refractive index of a medium between the two reflecting surfaces, L is the distance between the two reflecting surfaces, and lambda is the wavelength of light in the spectral range of the light source.
If one reflecting surface of the F-P resonant cavity is a film sensitive to pressure, the film can axially deform under the action of the pressure. The cavity length L of the F-P resonator is shortened by DeltaL. The interference spectrum introduces a phase deviation delta phi related to the cavity length variation, and the calculation formula is as follows:
wherein: n is the refractive index of the medium between the two reflecting surfaces, lambda is the wavelength of light in the spectral range of the light source, and delta L is the variation value of the cavity length of the resonant cavity; the interference spectrum exhibits a wavelength shift corresponding to the peak of the entire spectrum.
According to the theory of solid mechanics, the center of the square diaphragm can axially deform under the action of static pressure, and the relation between the maximum axial deformation delta L of the diaphragm and the static pressure P is as follows:
wherein: v is the poisson ratio of the membrane, E is the young's modulus of the membrane, t is the thickness of the membrane, and α is the side length of the membrane.
From the above formula, the pressure variation and the maximum axial deformation Δl of the diaphragm show a linear relationship, and the maximum axial deformation of the diaphragm and the wavelength shift corresponding to the spectral peak also show a linear relationship. Therefore, the system can demodulate the change condition of the corresponding pressure through the drift amount of the corresponding wavelength of the spectrum peak value.
Specifically, after the position of the optical microscope system is preliminarily determined, the spectrum demodulation unit 5 reads the digital spectrum output by the spectrum acquisition unit 4 to obtain original spectrum data; extracting the maximum value of the original spectrum data, comparing the maximum value with a preset threshold value, judging that the broadband light is not vertically incident on the intraocular pressure sensor 3 by a spectrum demodulation program if the maximum value is smaller than the original threshold value, prompting an operator by a preferred system at the moment, adjusting the space position of the broadband light focusing by combining a real-time image acquired by a microscopic imaging positioning unit 6, and redefining the position of an optical microscopic system until the maximum value of the read original spectrum data is larger than or equal to the preset threshold value, judging that the broadband light is vertically incident on the intraocular pressure sensor 3 by the system at the moment, performing spectrum interpolation processing on the original spectrum data, performing FFT filtering, and recovering spectrum data of interference broadband light; and then, carrying out peak splitting on the spectrum data of the interference broadband light by adopting a peak searching algorithm, obtaining the central wavelength position of the spectrum data of the interference broadband light, obtaining the central wavelength of the interference spectrum peak of the F-P resonant cavity in real time, and obtaining the pressure of the external liquid environment at the moment, namely the intraocular pressure, according to the corresponding relation between the central wavelength and the pressure.
The spectrum demodulation unit 5 is used for demodulating the received digital spectrum; depending on the nature of the system, the system receives the strongest specular reflected light when the broadband light impinges perpendicularly on the planar mirror. Because the surface of the intraocular pressure sensor is coarser than the reflector, the received interference broadband light intensity can only reach 50% of the specular reflection light intensity, and therefore 50% of the maximum specular reflection light intensity is set as a preset threshold, namely the preset threshold is preferably 50% of the specular reflection light intensity when broadband light vertically enters the plane reflector.
For ease of understanding, the utility model describes the complete operation of an optical microscopy system for tonometric measurements as follows:
the indication light emitted by the indication light source 62 is reflected by the lens group 21, enters the objective lens 22, is focused on the surface of the intraocular pressure sensor 3 and is reflected, the return light is received by the area array CCD camera 61 through the objective lens 22 and the lens group 21, and the generated image is transmitted to the screen of the upper computer (spectrum demodulation unit 5) in real time; the multidimensional displacement stage is adjusted so that the intraocular pressure sensor 3 appears at the midpoint of the field of view of the area array CCD camera 61.
At this time, broadband light emitted from the broadband light source 11 enters from the first port of the optical fiber circulator 12, is output from the second port of the optical fiber circulator 12, enters the optical fiber collimator 13, is reflected by the lens group 21, is focused by the objective lens 22, and is vertically incident to the F-P resonant cavity of the intraocular pressure sensor 3. Broadband light enters the cavity, is reflected by a plurality of surfaces and interferes, the formed interference broadband light is collected by the objective lens 22, is reflected by the lens group 21, enters the optical fiber collimator 13, is input from the second port of the optical fiber circulator 13, is output from the third port of the optical fiber circulator 13, and finally enters the spectrum acquisition unit 4.
The interference broadband light enters the spectrum acquisition unit 4, and the light dispersion conversion module 41 and the embedded module 42 convert the energy spectrum of the interference broadband light into a digital spectrum and transmit the digital spectrum to the spectrum demodulation unit 5.
The spectrum demodulation unit 5 demodulates the received digital spectrum, and the utility model adopts a computer as the spectrum demodulation unit 5. After the steps of spectrum interpolation, FFT filtering, threshold setting, peak searching algorithm, threshold peak splitting, spectrum single peak corresponding wavelength coordinate searching and the like are carried out on the obtained original spectrum data, the center wavelength of the interference spectrum peak of the F-P resonant cavity and the pressure corresponding to the external liquid environment at the moment, namely the intraocular pressure, are obtained, and therefore the rapid non-contact optical detection demodulation of the intraocular pressure can be achieved.
In one embodiment of the utility model, the measurement process is:
1) Placing the intraocular pressure sensor 3 in a pressure-controllable liquid container, and positioning the intraocular pressure sensor 3 using a microscopic imaging positioning unit 6; setting the single pressurizing amount to be 3.75mmHg, pressurizing from 3.75mmHg to 37.5mmHg, and executing 2 to 4 steps after each pressurizing;
2) Reading the digital spectrum output by the spectrum acquisition unit 4 to obtain original spectrum data, as shown in fig. 4;
3) Interpolation processing is carried out on the original spectrum data, FFT filtering is carried out, and interference spectrum data generated by an F-P resonant cavity of the intraocular pressure sensor under the pressure is restored, which is shown in figure 5;
4) Carrying out threshold peak separation on interference spectrum data by adopting a peak searching algorithm, and recording the coordinates of the maximum value of a single spectrum peak to obtain the central wavelength position of the spectrum peak under the pressure;
5) And performing linear fitting on the position of the spectral peak center wavelength under each pressure and the data of the corresponding pressure to obtain the sensing sensitivity of the intraocular pressure sensor 3, and obtaining the corresponding pressure, namely the intraocular pressure, according to the position of the spectral peak center wavelength and the sensing sensitivity.
The specific linear fitting process is shown in fig. 7, and the fitting result is a linear function of the spectral peak center wavelength position (y) with respect to the pressure (x): y=0.03263x+752.97241, the slope of the linear function is the sensing sensitivity of the intraocular pressure sensor 3.
The interference spectrum data detected and restored by the intraocular pressure sensor 3 under different pressures is shown in fig. 6.
As shown in fig. 7, this test experiment results in the sensing sensitivity of the intraocular pressure sensor 3 being: 32.63pm/mmHg. In addition, the demodulation accuracy of the system was tested in this embodiment, and the pressure demodulation accuracy of the demodulation system was controlled within ±1.5mmHg when the intraocular pressure sensor was at a certain fixed pressure.
With the above-described preferred embodiments according to the present utility model as an illustration, the above-described descriptions can be used by persons skilled in the relevant art to make various changes and modifications without departing from the scope of the technical idea of the present utility model. The technical scope of the present utility model is not limited to the description, but must be determined according to the scope of claims.
Claims (8)
1. An optical microscopic system for intraocular pressure measurement is characterized by comprising a space optical sensing unit (1), a light transmission unit (2), an intraocular pressure sensor (3), a spectrum acquisition unit (4) and a spectrum demodulation unit (5); wherein,
the space optical sensing unit (1) is connected with the spectrum acquisition unit (4);
the spectrum acquisition unit (4) is connected with the spectrum demodulation unit (5) through a transmission link I (7);
a Fabry-Perot microcavity is arranged on the intraocular pressure sensor (3);
broadband light emitted by the space optical sensing unit (1) vertically enters the Fabry-Perot microcavity through the light transmission unit (2) to obtain interference broadband light;
the interference broadband light passes through the light transmission unit (2) and the space optical sensing unit (1) and then is transmitted to the spectrum acquisition unit (4);
the spectrum acquisition unit (4) converts the interference broadband light into a digital spectrum and then transmits the digital spectrum to the spectrum demodulation unit (5);
the spectrum demodulation unit (5) acquires intraocular pressure from the digital spectrum.
2. Optical microscopy system for tonometric measurement according to claim 1, wherein said spatial optical sensing unit (1) comprises a broadband light source (11), a fiber optic circulator (12) and a fiber optic collimator (13); wherein the broadband light source (11) is connected with the optical fiber circulator (12), the optical fiber circulator (12) is connected with the optical fiber collimator (13), and the optical fiber circulator (12) is connected with the spectrum acquisition unit (4) through optical fibers; -said broadband light source (11) for emitting said broadband light; the broadband light is sequentially input to the light transmission unit (2) through the optical fiber circulator (12) and the optical fiber collimator (13); the interference broadband light sequentially passes through the light transmission unit (2), the optical fiber collimator (13) and the optical fiber circulator (12) and then is conveyed to the spectrum acquisition unit (4).
3. An optical microscopy system for tonometric measurement according to claim 1, wherein said broadband light has a wavelength in the range of 750nm to 950nm.
4. An optical microscopy system for tonometric measurement according to any of claims 1-3, further comprising a microscopic imaging positioning unit (6); the microscopic imaging positioning unit (6) is connected with the spectrum demodulation unit (5) through a transmission link II (8); the indication light emitted by the microscopic imaging positioning unit (6) is incident into the Fabry-Perot microcavity through the light transmission unit (2) to obtain reflection indication light; the reflected indicating light is received and imaged by the microscopic imaging positioning unit (6) after passing through the light transmission unit (2), a real-time image is obtained, and the real-time image is transmitted to the spectrum demodulation unit (5).
5. Optical microscopy system for tonometric measurement according to claim 4, wherein said microscopic imaging positioning unit (6) comprises a CCD camera (61) and an indicating light source (62); the indication light source (62) is configured to emit the indication light; the CCD camera (61) is in signal connection with the spectrum demodulation unit (5).
6. Optical microscopy system for tonometric measurement according to claim 4, wherein said light transmission unit (2) comprises a lens group (21) and an objective lens (22) arranged in succession along the optical path.
7. Optical microscopy system for tonometric measurement according to claim 4, wherein said spectrum acquisition unit (4) comprises a light dispersion conversion module (41), an embedded module (42) and a power drive module (43); wherein the power driving module (43) supplies power to the light dispersion conversion module (41) under the control of the embedded module (42); the light dispersion conversion module (41) converts the interference broadband light with different wavelengths into an electric signal through diffraction effect and transmits the electric signal to the embedded module (42); the embedded module (42) is configured to digitize the electrical signal to obtain the digital spectrum.
8. Optical microscopy system for tonometric measurement according to claim 4, wherein said spectral demodulation unit (5) comprises at least one central processor.
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