Optical devices for intraocular measurement

Abstract

A system and method for intraocular measurements is provided. Apparatus and methods are described that include an illumination apparatus (300) configured to direct light into a subject's eye. An optical device (100) is positioned inside the subject's eye, the optical device including a Fabry-Perot interferometer (106) having at least two mirrors (162, 164), the distance between the mirrors (162, 164) configured to change as an intraocular parameter of the subject's eye changes. A retroreflector (140) is configured to automatically reflect light transmitted through the Fabry-Perot interferometer (106) out of the subject's eye. A readout device (400) is configured to detect the light reflected out of the subject's eye. Other applications are also described.

Description

Technical Field

[0001] Cross - reference to Related Applications This application claims priority to U.S. Provisional Patent Application No. 63 / 038,834 by Arieli entitled "Optical measurement of intraocular pressure", filed on June 14, 2020, U.S. Provisional Patent Application No. 63 / 090,290 by Arieli entitled "Optical device for intraocular pressure measurement", filed on October 12, 2020, and U.S. Provisional Patent Application No. 63 / 128,200 by Arieli entitled "Optical device for intraocular pressure measurement", filed on December 21, 2020. The above - mentioned U.S. provisional applications are hereby incorporated herein by reference.

[0002] The present invention relates to systems and methods for intraocular measurement. Specifically, some applications of the present invention relate to intraocular pressure measurement and / or detection of substances inside the eye using an optical device.

Background Art

[0003] Glaucoma is an eye disease that causes damage to the optic nerve and leads to vision loss. The most common type is open - angle glaucoma, which progresses slowly over a long time and is painless. In open - angle glaucoma, vision is gradually lost from peripheral vision to central vision. Another type is closed - angle glaucoma, which can progress slowly or rapidly and may be accompanied by severe eye pain, blurred vision, mid - dilation of the pupil, eye redness, and / or nausea. Vision loss due to glaucoma is permanent.

[0004] Risk factors for glaucoma include genetic predisposition, high intraocular pressure (IOP), and high blood pressure. While IOP above 21 mmHg or 2.8 kPa is often associated with a higher risk, some people have high IOP for many years without developing any problems.

[0005] There are many methods for measuring intraocular pressure, both contact and non-contact. One known method is the Goldmann applanation tonometry, which is considered the "absolute standard" for measuring intraocular pressure. In this test, the eye is anesthetized and a dye is added to it. A small tip is then placed in contact with the surface of the eye, and the intraocular pressure is measured based on the force required to flatten a certain area of ​​the cornea. However, this test can be affected by corneal thickness and / or other biomechanical properties.

[0006] In dynamic contour tonometry (DCT), contour matching is performed. A tip, which has a shape similar to the cornea and contains a hollow portion with a pressure sensor at its center, is pressed against the cornea. The tip is designed to prevent corneal deformation during measurement, so it is not significantly affected by corneal thickness and other biomechanical properties. However, because the tip shape is designed for a normal corneal shape, it is susceptible to the effects of corneal curvature.

[0007] In a rebound tonometer, intraocular pressure is measured by bouncing a small metal probe with a plastic tip against the cornea.

[0008] In air tonometry, intraocular pressure is measured using an air pressure sensor. Filtered air is injected into a piston and passes through a small fenestrated membrane at one end, which is positioned attached to the cornea. The balance between the airflow and the resistance to the airflow from the cornea affects the movement of the piston, and this movement is used to calculate the intraocular pressure.

[0009] Non-contact intraocular pressure measurement uses rapid air pulses to flatten or deform the cornea, and corneal applanation is detected by an electro-optical system. Intraocular pressure is estimated by detecting the force of the air jet during applanation or deformation.

[0010] The presence and / or concentration of various substances within the eye (e.g., glucose, amino acids, vitamins, electrolytes, etc.) can be interpreted as indicators of various physiological and / or medical conditions, such as the glucose concentration in the subject's body or the presence of viruses. Determining the presence and / or concentration of such substances within the eye may be useful in determining the patient's physiological and / or medical condition. [Overview of the Initiative]

[0011] According to some applications of the present invention, an optical device (e.g., an optical element and / or optical sensor) is placed at a location inside the subject's eye, for example, in the posterior chamber and / or anterior chamber and / or vitreous humor. In some applications, the optical device is attached to the ciliary muscle, cornea, intraocular lens, artificial cornea, or any other part inside the eye. Generally, the optical device is an optical sensor that is sensitive to intraocular parameters (such as intraocular pressure) at its intraocular location, and the optical properties of the optical sensor change when the intraocular pressure changes.

[0012] Generally, optical devices comprise a Fabry-Perot interferometer and a retroreflector. Typically, a Fabry-Perot interferometer comprises two mirrors (usually translucent mirrors). More commonly, a Fabry-Perot interferometer is configured such that the distance between the two mirrors changes as ambient pressure changes. The spectral reflection of the Fabry-Perot interferometer (e.g., its resonant frequency) also changes as a function of the distance between the two mirrors. Therefore, when an illumination device illuminates the Fabry-Perot interferometer from outside the eye, the spectrum of the reflected light changes, which is detected by a signal readout device also located outside the eye. A computer processor derives intraocular parameters by analyzing the reflected light.

[0013] Generally, optical devices include a retroreflector coupled to the Fabry-Perot interferometer. In some cases, the direction of the optical axis of the Fabry-Perot interferometer can change within the eye (in the absence of a retroreflector) because some of the light rays incident on the Fabry-Perot interferometer are reflected, and the reflected rays do not coincide with the line connecting the pupil and the interferometer. By providing a retroreflector, light rays incident on and passing through the Fabry-Perot interferometer are reflected back in the direction from which they came and pass through the Fabry-Perot interferometer again along the reflected path. Thus, light rays that illuminate the Fabry-Perot interferometer and pass through it are reflected back and directed towards the readout device.

[0014] Without a retroreflector, the resonant frequency of the Fabry-Perot interferometer would be transmitted through the optical device rather than reflected. The computer processor would then have to determine the resonant frequency of the Fabry-Perot interferometer by identifying the trough in the reflected light signal. Generally, detecting a trough in a reflected light signal is more difficult than identifying a peak. Therefore, in some applications, including a retroreflector in the optical device facilitates the analysis of the reflected light signal by the computer processor by making the resonant frequency of the interferometer easier to detect.

[0015] In some applications, a reference optical device is coupled to the optical device such that the optical axes of the optical device and the reference optical device are parallel to each other. Generally, the reference optical device has a structure that is roughly similar to that of the optical device. However, since the walls defining the chamber that defines the gap between the mirrors of the Fabry-Perot interferometer are all rigid, the distance between the mirrors of the reference Fabry-Perot interferometer is constant. Because the distance between the mirrors of the reference Fabry-Perot interferometer is constant, the reflected light signal from the reference optical device does not change as a function of ambient pressure and is generally used as a reference for calibrating the reflected light signal detected from the optical device. In this way, the computer processor can account for changes in the reflected light signal detected from the optical device due to the measurement angle between the optical axis of the Fabry-Perot interferometer and the optical axis of the readout device. Alternatively or additionally, the computer processor can thus account for other optical effects within the eye.

[0016] In some applications, the optical device comprises one or more additional Fabry interferometers in series with a Fabry-Perot interferometer sensitive to changes in ambient pressure. In some such applications, at least one of the additional Fabry-Perot interferometers is configured such that the distance between its mirrors is constant. Because the distance between the mirrors of the additional Fabry-Perot interferometers is constant, the reflected light signal from the additional Fabry-Perot interferometer does not change as a function of ambient pressure. In some applications, the additional Fabry-Perot interferometer is used as a reference to calibrate the reflected light signal detected from the Fabry-Perot interferometer sensitive to changes in ambient pressure. Thus, the additional Fabry-Perot interferometer functions as a reference optical device. Using the reference optical device as described above, a computer processor can account for changes in the reflected light signal detected from the optical device due to the measurement angle between the optical axis of the Fabry-Perot interferometer and the optical axis of the readout device. Alternatively or additionally, the computer processor can thus account for other optical effects within the eye. According to some applications of the present invention, the optical device is used for intraocular pressure measurement. In some applications, the optical device for intraocular pressure measurement is placed inside the eye of the subject. In some applications, the optical device is mounted on the ciliary muscle, cornea, intraocular lens, artificial cornea, or any other part inside the eye, either anterior or posterior to the pupil. In some applications, the optical device is sensitive to intraocular pressure, as its optical properties change as a result of intraocular pressure. In some applications, the optical device signal is read out by illuminating the optical device from outside the eye and detecting the reflected light. In some applications, the optical device is illuminated from outside the eye using any electromagnetic source of any spectral region and / or any polarization state and / or any spectral bandwidth, and using monochromatic, polychromatic, and / or broadband light sources. In some applications, the optical properties of the optical device, which change with intraocular pressure, may change the intensity and / or spectrum and / or phase and / or polarization state of the reflected light. In some applications, the optical device signal is read out by any known sensing device.

[0017] In some applications, additional optical elements, such as retroreflectors, mirrors, and / or other known optical elements, are placed inside the subject's eye. In some applications, the optical elements are illuminated from outside the eye, and the reflected light is detected. In some applications, the optical elements are illuminated from outside the eye using any electromagnetic source of any spectral region and / or any polarization state and / or any spectral bandwidth, as well as monochromatic, polychromatic, and / or broadband light sources. In some applications, the optical properties of the light reflected from the optical elements (such as intensity and / or spectrum and / or phase and / or polarization) vary depending on the presence and / or concentration of various substances inside the eye. In some applications, the presence and / or concentration of such substances inside the eye is detected by analyzing the intensity and / or spectrum and / or phase and / or polarization of the reflected light. Alternatively or additionally, the reflected light is detected when the subject's eyelids are closed. The optical properties of light reflected from an optical element (such as intensity and / or spectrum and / or phase and / or polarization) change based on the parameters of the blood in the blood vessels of the subject's eyelid. This is because the eyelid is thin enough for incident and reflected light to pass through, and as light passes through the eyelid, it generally passes through the blood vessels of the eyelid. In some applications, one or more parameters of the subject's blood (such as oxygen saturation) are detected by analyzing the intensity and / or spectrum and / or phase and / or polarization of the reflected light.

[0018] Therefore, according to some application examples of the present invention, A lighting device configured to direct light into the subject's eyes, An optical device configured to be placed inside the eye of a subject, A Fabry-Perot interferometer comprising at least two mirrors, configured such that the distance between the mirrors changes when the intraocular parameters of the subject's eye change, An optical device comprising a retroreflector configured such that light passing through a Fabry-Perot interferometer is automatically reflected out of the subject's eye, A device is provided comprising a readout device configured to detect light reflected outward from the subject's eyes.

[0019] In some application examples, the device is for use with an intraocular lens, and the optical device is configured to be coupled to the intraocular lens.

[0020] In some application examples, the device is for use with an intraocular lens, and the optical device is configured to be disposed inside the subject's eye during the procedure in which the intraocular lens is placed in the subject's eye.

[0021] In some application examples, the optical device is configured to be coupled to the ciliary body of the subject's eye.

[0022] In some application examples, the Fabry - Perot interferometer is configured such that the distance between the mirrors changes when the intraocular pressure of the subject's eye changes.

[0023] In some application examples, the Fabry - Perot interferometer is configured such that the distance between the mirrors changes when the intraocular temperature of the subject's eye changes.

[0024] In some application examples, the optical device includes two or more additional mirrors, and the optical device functions as a plurality of cascaded Fabry - Perot interferometers.

[0025] In some application examples, the device further comprises a computer processor configured to detect parameters of the subject's blood by analyzing light reflected out from the subject's eye when the subject's eyelids are closed.

[0026] In some application examples, the device further comprises a computer processor configured to analyze light reflected out from the subject's eye to determine intraocular parameters of the subject's eye by identifying the resonant frequency of the Fabry - Perot interferometer.

[0027] In some applications, the illumination system is equipped with a swept monochromatic light source, and a computer processor is configured to identify the resonant frequency of the Fabry-Perot interferometer by detecting the frequency of the light reflected out of the subject's eyes.

[0028] In some applications, the illumination device is equipped with a multicolor light source having known spectral characteristics, and the computer processor is configured to identify the resonant frequency of the Fabry-Perot interferometer based on the known spectral characteristics of the light source and the spectrum of light reflected out of the subject's eyes.

[0029] In some applications, the illumination device is equipped with a broadband light source, and a computer processor is configured to identify the resonant frequency of the Fabry-Perot interferometer by analyzing the spectrum of light reflected out of the subject's eyes using a fast Fourier transform to detect the distance between peaks in the reflected signal.

[0030] In some applications, the readout device is configured to detect light at the resonant frequency of the Fabry-Perot interferometer that is reflected outward from the subject's eye when the optical axis of the readout device is parallel to the optical axis of the illumination device.

[0031] In some applications, the readout device is configured to be movable relative to the illumination device, and the readout device is configured to detect light that is not at the resonant frequency of the Fabry-Perot interferometer and is reflected out of the subject's eye when the optical axis of the readout device is not parallel to the optical axis of the illumination device.

[0032] In some applications, the device further comprises a computer processor configured to detect the presence and / or concentration of substances inside the subject's eye by analyzing light reflected out of the subject's eye when the optical axis of the readout device is not parallel to the optical axis of the illumination device.

[0033] In some applications, the device further comprises a reference Fabry-Perot interferometer comprising at least two reference mirrors, the distance between the reference mirrors being constant as the intraocular parameters of the subject's eye change.

[0034] In some applications, a reference Fabry-Perot interferometer is in series with a Fabry-Perot interferometer whose mirror-to-mirror distance is configured to change as the intraocular parameters of the subject's eye change.

[0035] In some applications, the device further includes a computer processor configured to analyze light reflected outward from the subject's eyes and to take into account changes in the angle between the optical axis of an optical device and the optical axis of an illumination device and / or readout device by calibrating measurements made on light reflected from a reference Fabry-Perot interferometer using measurements made on light reflected from a reference Fabry-Perot interferometer.

[0036] In some applications, the apparatus is coupled to an optical device and further comprises a reference optical device equipped with a reference Fabry-Perot interferometer.

[0037] In some applications, the reference optical device is coupled to the optical device such that the optical axes of the optical device and the reference optical device are parallel to each other.

[0038] In some applications, the reference optical device includes a retroreflector configured to automatically reflect light transmitted through the reference Fabry-Perot interferometer away from the subject's eyes.

[0039] According to some applications of the present invention, A lighting device configured to direct light into the subject's eyes, An optical device configured to be placed inside the eye of a subject, comprising a first Fabry-Perot interferometer having at least two mirrors, the distance between the mirrors being configured to change when the intraocular parameters of the subject's eye change, A reference Fabry-Perot interferometer comprising at least two reference mirrors, wherein the distance between the reference mirrors remains constant as the intraocular parameters of the subject's eye change, The apparatus is further provided, comprising a readout device configured to detect light reflected outward from the subject's eyes.

[0040] In some applications, the reference Fabry-Perot interferometer is in series with the first Fabry-Perot interferometer.

[0041] In some applications, the first Fabry-Perot interferometer is configured such that the distance between the mirrors changes when the intraocular pressure in the subject's eye changes.

[0042] In some applications, the first Fabry-Perot interferometer is configured such that the distance between the mirrors changes when the intraocular temperature of the subject's eye changes.

[0043] In some applications, the optical device functions as multiple Fabry-Perot interferometers in series with each other by including two or more additional mirrors.

[0044] In some applications, the optical device further includes a retroreflector configured to automatically reflect light transmitted through the first Fabry-Perot interferometer away from the subject's eyes.

[0045] In some applications, the device further includes a computer processor configured to detect parameters of the subject's blood by analyzing the light reflected outward from the subject's eye when the subject's eyelids are closed.

[0046] In some applications, the apparatus is coupled to an optical device and further comprises a reference optical device equipped with a reference Fabry-Perot interferometer.

[0047] In some applications, the reference optical device is coupled to the optical device such that the optical axes of the optical device and the reference optical device are parallel to each other.

[0048] In some applications, the reference optical device includes a retroreflector configured to automatically reflect light transmitted through the reference Fabry-Perot interferometer away from the subject's eyes.

[0049] In some applications, the device further comprises a computer processor configured to analyze light reflected out of the subject's eye in order to determine intraocular parameters of the subject's eye by identifying the resonant frequency of a first Fabry-Perot interferometer.

[0050] In some applications, the computer processor is configured to account for changes in the angle between the optical axis of an optical device and the optical axis of an illumination device and / or readout device by calibrating measurements made on light reflected from a first Fabry-Perot interferometer using measurements made on light reflected from a reference Fabry-Perot interferometer.

[0051] In some applications, the optical device further includes a retroreflector configured to automatically reflect light transmitted through the first Fabry-Perot interferometer away from the subject's eyes.

[0052] In some applications, the illumination device is equipped with a swept monochromatic light source, and a computer processor is configured to identify the resonant frequency of a first Fabry-Perot interferometer by detecting the frequency of the light reflected out of the subject's eyes.

[0053] In some applications, the illumination device is equipped with a multicolor light source having known spectral characteristics, and a computer processor is configured to identify the resonant frequency of a first Fabry-Perot interferometer based on the known spectral characteristics of the light source and the spectrum of light reflected out of the subject's eyes.

[0054] In some applications, the illumination device is equipped with a broadband light source, and a computer processor is configured to identify the resonant frequency of a first Fabry-Perot interferometer by analyzing the spectrum of light reflected out of the subject's eyes using a fast Fourier transform to detect the distance between peaks in the reflected signal.

[0055] In some applications, the readout device is configured to detect light at the resonant frequency of the first Fabry-Perot interferometer that is reflected outward from the subject's eye when the optical axis of the readout device is parallel to the optical axis of the illumination device.

[0056] In some applications, the readout device is configured to be movable relative to the illumination device, and the readout device is configured to detect light that is not at the resonant frequency of the first Fabry-Perot interferometer and is reflected out of the subject's eye when the optical axis of the readout device is not parallel to the optical axis of the illumination device.

[0057] In some applications, the device further comprises a computer processor configured to detect the presence and / or concentration of substances inside the subject's eye by analyzing light reflected out of the subject's eye when the optical axis of the readout device is not parallel to the optical axis of the illumination device.

[0058] According to some applications of the present invention, Directing light into the subject's eyes, An optical device placed inside the eye of the subject, A Fabry-Perot interferometer comprising at least two mirrors, configured such that the distance between the mirrors changes when the intraocular parameters of the subject's eye change, Receiving reflected light from an optical device equipped with a retroreflector configured so that light passing through a Fabry-Perot interferometer is automatically reflected out of the subject's eye, and A method is further provided that includes determining intraocular parameters of a subject's eye by analyzing reflected light.

[0059] According to some applications of the present invention, A method comprising placing an optical device inside the eye of a subject, wherein the optical device is A Fabry-Perot interferometer comprising at least two mirrors, configured such that the distance between the mirrors changes when the intraocular parameters of the subject's eye change, A method is further provided that includes a retroreflector configured such that light transmitted through the Fabry-Perot interferometer is automatically reflected out of the subject's eyes.

[0060] According to some applications of the present invention, Directing light into the subject's eyes, Receiving reflected light from an optical device, which is placed inside the eye of a subject and comprises a first Fabry-Perot interferometer having at least two mirrors, the distance between the mirrors being configured to change when the intraocular parameters of the subject's eye change. Receiving reflected light from a reference Fabry-Perot interferometer equipped with at least two reference mirrors, wherein the distance between the reference mirrors remains constant as the intraocular parameters of the subject's eye change, and A method is further provided which includes determining intraocular parameters of a subject's eye by analyzing reflected light from a first Fabry-Perot interferometer and reflected light from a reference Fabry-Perot interferometer.

[0061] According to some applications of the present invention, An optical device comprising a first Fabry-Perot interferometer having at least two mirrors, configured such that the distance between the mirrors changes as the intraocular parameters of the subject's eye change, is placed inside the subject's eye, and A method is further provided which includes placing a reference Fabry-Perot interferometer inside the eye of a subject, the reference mirrors having at least two reference mirrors, the distance between the reference mirrors being constant as the intraocular parameters of the subject's eye change.

[0062] The present invention will be better understood from the following detailed description of embodiments of the invention in conjunction with the drawings. [Brief explanation of the drawing]

[0063] [Figure 1] This is a schematic diagram of an optical system for measuring intraocular pressure, relating to a partial application example of the present invention. [Figure 2] This is a schematic diagram of an optical device for measuring intraocular pressure, relating to some application examples of the present invention. [Figure 3] This is a schematic diagram of a flexible film attached to a mirror, viewed from above, according to one of the applications of the present invention. [Figure 4] This is a schematic diagram of a flexible film attached to a mirror, according to one of the applications of the present invention. [Figure 5] This is a schematic diagram of a Fabry-Perot interferometer relating to some alternative applications of the present invention. [Figure 6] This is a schematic diagram of an optical device for measuring intraocular pressure, relating to some application examples of the present invention. [Figure 7] This is a schematic diagram of an optical device for measuring intraocular pressure, relating to an alternative application of some parts of the present invention. [Figure 8] This is a schematic diagram of an optical device for measuring intraocular pressure, coupled with a reference optical device, according to a partial application example of the present invention. [Figure 9] This graph shows a typical spectral profile of an optical signal detected by a readout device, according to some application examples of the present invention. [Modes for carrying out the invention]

[0064] Hereafter, we will refer to Figure 1, a schematic diagram of an optical system 50 for measuring intraocular pressure according to some applications of the present invention. Generally, at least one optical device 100 (e.g., an optical element and / or optical sensor) is positioned at a location inside the subject's eye 200, for example, in the posterior chamber and / or anterior chamber and / or vitreous humor. In some applications, the optical device is attached to the ciliary muscle, cornea, intraocular lens, artificial cornea, or any other part inside the eye. Generally, the optical device 100 is an optical sensor that is sensitive to intraocular pressure at that location inside the eye, and the optical properties of the optical sensor change when the intraocular pressure changes. Alternatively or additionally, the optical device 100 includes one or more types of optical elements, such as mirrors, retroreflectors, polarizers, and / or any other types of optical elements and / or optical systems configured to reflect light directed towards the optical device.

[0065] In some applications, the optical device 100 is injected into the eye (for example, using a dedicated syringe). In some such applications, the optical device is bonded to a part of the patient's eye (e.g., the ciliary muscle) using bonding elements (such as pins, barbs, and / or sutures) and / or biocompatible adhesives. In some applications, the optical device is bonded to an intraocular lens (not shown). Alternatively or additionally, the optical device is implanted in the patient's eye as part of cataract surgery in which an intraocular lens is implanted in the patient's eye.

[0066] Generally, the illumination device 300 illuminates the optical device from outside the eye (e.g., through the pupil 220). More generally, the illumination device comprises one or more light sources (such as LEDs, lasers, monochromatic light sources, sweeping light sources, polychromatic light sources, and / or broadband light sources). In some applications, the illumination device comprises additional optical elements, such as lenses and polarizers. The readout device 400 generally detects the light reflected from the optical device 100 and returning (e.g., through the pupil 220). Generally, the readout device comprises a photodetector such as a camera, a light intensity sensor, and / or a spectrometer. In some applications, the device comprises a beam splitter configured to direct the reflected light to the photodetector. Generally, the illumination device and / or the readout device communicate with a computer processor 450. For example, the computer processor may drive the illumination device to illuminate the optical device, and / or the computer processor may analyze the light reflected from the optical device and detected by the readout device 400.

[0067] As described above, the optical device 100 is generally an optical sensor that is sensitive to intraocular pressure at a specific location within the eye, and the optical properties of the optical sensor change when the intraocular pressure changes. Therefore, the signal detected by the readout device 400 generally changes with changes in intraocular pressure at the location of the optical device 100. Changes in the signal detected by the readout device 400 may include changes in any one of the following: intensity, spectrum, polarization, and / or phase of the signal detected by the readout device 400. By analyzing the optical properties of the signal detected by the readout device 400, the computer processor is generally configured to measure the intraocular pressure of the eye.

[0068] In some applications, the optical device 100 comprises one or more types of optical elements, such as mirrors and / or retroreflectors, configured to reflect light directed toward the optical device. In some such applications, the optical properties of the signal detected by the readout device 400 (signal intensity, spectrum, polarization, and / or phase, etc.) change based on the presence and / or concentration of various substances inside the eye. By analyzing the optical properties of the signal detected by the readout device 400, the computer processor is generally configured to detect the presence and / or concentration of various substances inside the eye. In some such applications, based on the above analysis, the computer processor is configured to estimate various physiological and medical conditions of the subject, such as the presence and / or concentration of the subject's blood glucose levels, viruses, amino acids, and vitamins. In some applications, the computer processor is configured to thereby derive the subject's physiological and / or medical conditions that affect the presence and / or concentration of such substances.

[0069] Alternatively or additionally, reflected light is detected by the readout device when the subject's eyelids are closed. In some such applications, the optical properties of the signal detected by the readout device 400 (signal intensity, spectrum, polarization, and / or phase, etc.) change based on the parameters of the blood in the blood vessels of the subject's eyelids. This is because the eyelids are thin enough for incident and reflected light to pass through, and as light passes through the eyelids, it generally passes through the blood vessels of the eyelids. By analyzing the optical properties of the signal detected by the readout device 400, the computer processor is generally configured to determine one or more parameters of the subject's blood (such as oxygen saturation) by, for example, analyzing the intensity and / or spectrum and / or phase and / or polarization of the reflected light. In some such applications, based on the above analysis, the computer processor is configured to estimate various physiological and medical conditions of the subject. The following refers to Figure 2, a schematic diagram of an optical device 100 according to some applications of the present invention. Generally, incident light (directed from the illuminator 300 through the pupil into the eye) enters the optical device through a generally transparent window 120. In some applications, the optical device comprises a Fabry-Perot interferometer 160 and a retroreflector 140. Generally, the Fabry-Perot interferometer comprises two mirrors 162, 164 (generally translucent mirrors). The two mirrors 162, 164 are generally mounted on flexible films 130 and 132 that are parallel to each other. For example, one surface of each film may be covered with a translucent reflective coating (films covered in this manner are described herein as examples of translucent mirrors), or a mirror (e.g., a translucent mirror) may be coupled to each central region of the film, or a mirror (e.g., a translucent mirror) may be positioned in a central region cut out from the flexible film. In some applications, both sides of each film may be covered with a translucent reflective coating, or translucent mirrors may be attached to both sides of the film. Thus, chamber 124 functions as multiple Fabry-Perot interferometers connected in a cascade configuration.

[0070] In some applications, additional parts of the optical device are coated with a reflective coating (e.g., a translucent reflective coating) and / or have coupled mirrors (e.g., translucent mirrors), so that the optical device functions as multiple Fabry-Perot interferometers in series with respect to multiple pairs of mirrors. For example, window 120 may be coated on both sides with a translucent reflective coating, or translucent mirrors may be coupled to each face of window 120, so that window 120 functions as a Fabry-Perot interferometer, and the optical device functions as multiple Fabry-Perot interferometers in series with respect to each other. Generally, the scope of this application includes optical devices with additional mirrors for mirrors 162, 164, so that the optical device functions as multiple Fabry-Perot interferometers in series with respect to each other. Note that in such applications, the multiple Fabry-Perot interferometers do not necessarily have the same characteristics as each other. Generally, this generates additional data that a computer processor analyzes to derive characteristics of the eye (such as intraocular pressure) compared to when the optical device has only a single Fabry-Perot interferometer. However, it should be noted that the scope of this application includes optical devices with only a single Fabry-Perot interferometer. In some applications, one or more additional Fabry-Perot interferometers are configured to function as reference optical devices, as described in more detail below with reference to Figure 8.

[0071] Generally, at least one of the two membranes 130 and 132 is sealed with respect to gas and fluid. In some applications, in addition to defining the wall of chamber 124, the two membranes 130 and 132 define the walls of chambers 122 and 126. Generally, the two membranes 130 and 132 constitute the flexible walls of the three chambers 122, 124, and 126, while the other walls of the chambers (e.g., the side walls 112 of the chambers) are generally rigid. For example, the membranes may be located inside a rigid housing 166 that defines the side walls of the chambers. Chambers 122 and 126 are generally sealed and filled with a clear and flexible fluid (e.g., gas or liquid).

[0072] In some applications, the chamber 124 is sealed and filled with a fluid (e.g., gas or liquid). Alternatively, the chamber 124 is open to ambient conditions through one or more openings 110 (e.g., openings in the side wall 112 of the illustrated chamber), and as a result, the pressure inside the chamber 124 is the ambient pressure P 周囲 It is approximately equal to . Therefore, when the ambient pressure changes, the distance between the two interferometer mirrors 162 and 164 changes. The spectral reflectance of the Fabry-Perot interferometer (e.g., its resonant frequency) also changes as a function of the distance between the two mirrors. Thus, when the illumination device 300 (shown in Figure 1) illuminates the Fabry-Perot interferometer from outside the eye, the spectrum of the reflected light changes, which is detected by a signal detected by a readout device 400 (shown in Figure 1), which is also outside the eye.

[0073] Generally, the optical device includes a retroreflector 140 coupled to a Fabry-Perot interferometer 160. More generally, the retroreflector is located on the opposite side of the optical device from the side where the window 120 of the optical device is located. In some applications, a corner cube retroreflector is used, as illustrated. Alternatively or additionally, different types of retroreflectors, such as cat-eye retroreflectors, are used. In some examples, the direction of the optical axis of the Fabry-Perot interferometer 160 may be such that (without a retroreflector) some of the light rays incident on the Fabry-Perot interferometer are reflected, and the reflected light rays do not coincide with the line connecting the pupil and the interferometer, causing them to change within the eye. By providing a retroreflector, light rays incident on and passing through the Fabry-Perot interferometer are reflected back in the direction from which they came and pass through the Fabry-Perot interferometer again along their reflection path. Thus, light rays that illuminate the Fabry-Perot interferometer and pass through the Fabry-Perot interferometer are reflected back and directed towards the readout device. In some applications, a beam splitter (not shown) is added to direct the reflected light rays towards a readout device. In some applications, the retroreflector 140 is manufactured as part of the optical device such that the chamber 126 is defined by the film 130 and the retroreflector (i.e., the retroreflector defines the walls of the chamber 126). In some such applications, the film 130 is a hard film. Alternatively, the retroreflector is a standalone device coupled to the Fabry-Perot interferometer (e.g., after the chamber 126). In some applications, the retroreflector provides additional advantages, such as those described below with reference to Figure 9.

[0074] Hereafter, we will refer to Figure 3, a schematic diagram of a flexible membrane 132 and a mirror 164 according to some application examples of the present invention. As described above, in some application examples, the flexible membrane 132 is disposed inside the rigid housing 166. In some application examples, the outer edge of the membrane is bonded to the inside of the rigid housing. In some application examples, the membrane 132 is made of a flexible material (e.g., a corrugated sheet of flexible material). In some application examples, the mirror 164 is a flat sheet bonded to the central region of the membrane 132. Alternatively, the central region of the membrane is cut out and the mirror is disposed in the central region of the membrane. Generally, the membrane 130 and the mirror 162 have a structure that is generally similar to the structure of the membrane 132 and the mirror 164. In some application examples, only one of the two membranes moves in response to changes in ambient pressure, because only one of the membranes 130 and 132 is flexible and the other is rigid. Generally, the membrane deforms due to changes in the pressure difference between the two surfaces of each membrane, and as a result, the distance between the mirrors changes.

[0075] Next, we will refer to Figure 4, a schematic cross-sectional view of a flexible film 132 and a mirror 164 relating to a partial application example of the present invention. In this embodiment, the film 132 is attached to the rigid housing 166 of the optical device shown in Figure 2. The film 132 is composed of an accordion shape made from a flexible material. A translucent mirror or translucent reflective coating is generally disposed on the inner and / or outer surface of the central region 133 having a flat shape of the flexible film. Generally, the film 132 and the mirror 164 have a structure that is generally similar to that of the film 130 and the translucent mirror 162. Generally, the film deforms due to a change in the pressure difference between each of the two surfaces of the film, and as a result, the distance between the translucent mirrors changes.

[0076] Next, we refer to Figure 5, a schematic cross-sectional view of a Fabry-Perot interferometer 160 relating to some applications of the present invention. In some applications, the membranes 130 and / or 132 are rigid and flat, and the housing 166 is flexible, for example, having an accordion shape and made of a flexible material. Translucent mirrors or translucent coatings are generally disposed on the inner and / or outer surfaces of the membranes 130 and 132. Changes in the pressure difference between the internal and external pressures of the chamber 124 distort the housing 166 and, consequently, the distance between the translucent mirrors.

[0077] It should be noted that this application is not limited to specific embodiments of the Fabry-Perot interferometer 106 shown and / or described herein. For example, the embodiments in Figures 4 and 5 may be combined such that both the membranes 130, 132 and the housing 166 have an accordion shape and / or are flexible (as shown, for example, in Figure 6). Similarly, the scope of this application includes accordion shapes having any number of folds (periods), any shape (including various shapes between different periods), and various frequencies and sizes between periods. Likewise, the thickness of the membranes or housing may differ from each other, may vary, and may be of any thickness.

[0078] We now refer to Figure 6, a schematic diagram of an optical device 100 relating to some applications of the present invention. The optical device 100 shown in Figure 6 is generally similar to that shown in Figure 2, except that in the embodiment shown in Figure 6, the chamber 124 is sealed. In some applications, the side wall 112 (or a portion thereof) of the chamber 124 is flexible and does not define an opening 110 (the opening 110 is shown in Figure 1). The chamber 124 is generally sealed and filled with a transparent and flexible fluid (e.g., gas or liquid). Therefore, when the ambient pressure changes, the side wall changes its structure, and the distance between the mirrors 162 and 164 of the two interferometers changes. As described above, the optical device generally includes a retroreflector 140, the function of which is described above with reference to Figure 2 and / or below with reference to Figure 9. In some applications, the optical device includes a beam splitter (not shown) that directs the reflected light rays to a readout device.

[0079] The following references to Figure 7, a schematic diagram of an optical device 100 relating to some applications of the present invention. The optical device 100 shown in Figure 7 is generally similar to that shown in Figure 2, except that in the embodiment shown in Figure 7, there is no window 120 between the mirror 164 and the front of the optical device. The chamber 124 is generally sealed and filled with a transparent and flexible fluid (e.g., gas or liquid). At least one of the two membranes 130 and 132 is flexible. Generally, in some applications, the chamber 126 (displaced behind the chamber 124 relative to the illumination device) is open to ambient conditions, for example, through an opening 142. Therefore, when the ambient pressure changes, the distance between the mirrors 162 and 164 of the two interferometers changes. As described above, the optical device generally includes a retroreflector 140, the function of which is described above with reference to Figure 2 and / or below with reference to Figure 9. In some applications, the optical device includes a beam splitter (not shown) that directs the reflected light rays to a readout device.

[0080] As described above, the scope of this application includes optical devices having any number of Fabry-Perot interferometers. Generally, at least one of the Fabry-Perot interferometers (Fabry-Perot interferometer 106) has an ambient pressure-dependent resonant frequency. The mirrors of a Fabry-Perot interferometer having an ambient pressure-dependent resonant frequency are generally arranged on films 130 and 132 that define two mutually parallel walls of a chamber 124. The distance between the chamber walls may be made ambient pressure-dependent by the film 130 being flexible and / or the film 132 being flexible and / or the side walls of the chamber 124 being flexible. In some applications, the distance between the walls of the chamber 124 becomes sensitive to ambient pressure by defining an opening (e.g., an opening 110 shown in Figure 2) in the chamber 124. The mirrors of the Fabry-Perot interferometer may include translucent mirrors and / or films covered with a translucent reflective coating.

[0081] Next, refer to Figure 8, a schematic diagram of an optical device 100 for measuring intraocular pressure coupled with a reference optical device 100R, which relates to some application examples of the present invention. In some application examples, the reference optical device is coupled to the optical device such that the optical axes of the optical device and the reference optical device are parallel to each other. Generally, the optical device 100 has the structure and function described above, and at least a portion of the wall of the chamber 124 (i.e., the chamber that defines the gap between the mirrors of the Fabry-Perot interferometer) is flexible, so that the distance between the mirrors of the Fabry-Perot interferometer changes when the ambient intraocular pressure changes. For example, as shown in the figure, the membranes 130 and 132 of the optical device 100 are flexible. Generally, the reference optical device 100R has a structure that is generally similar to that of the optical device 100. However, the distance between the mirrors of the reference Fabry-Perot interferometer is constant because all the walls defining the chamber 124R (i.e., the chamber that defines the gap between the mirrors of the Fabry-Perot interferometer and corresponds to the chamber 124 of the optical device 100) are rigid. Both optical device 100 and reference optical device 100R generally include a retroreflector 140, the function of which is described above with reference to Figure 2 and / or below with reference to Figure 9.

[0082] Since the distance between the mirrors of the Fabry-Perot interferometer of the reference optical device 100R is constant, the reflected light signal from the reference optical device 100R does not change as a function of ambient pressure and is generally used as a reference for calibrating the reflected light signal detected from optical device 100. In this way, the computer processor can take into account the change in the reflected light signal detected from optical device 100 due to the measurement angle between the optical axis of the Fabry-Perot interferometer and the optical axis of the readout device. Alternatively or additionally, the computer processor can thus take into account other optical effects within the eye. In some applications, each optical device is equipped with a polarizer that generates each polarization state so that the computer processor can distinguish between the reflected light signal from optical device 100 and the reflected light signal from optical device 100R, and the computer processor measures the polarization state of the reflected light signal to determine which signal is from optical device 100 and which signal is from reference optical device 100R. Alternatively, two different wavelength bandwidths are used so that the computer processor can distinguish between the reflected light signal from optical device 100 and the reflected light signal from optical device 100R.

[0083] As described above, in some applications, the optical device comprises one or more additional Fabry interferometers in series with the Fabry-Perot interferometer 106 (sensitive to changes in ambient pressure). In some such applications, at least one of the additional Fabry-Perot interferometers is configured such that the distance between its mirrors is constant. Because the distance between the mirrors of the additional Fabry-Perot interferometers is constant, the reflected light signal from the additional Fabry-Perot interferometer does not change as a function of ambient pressure. In some applications, the additional Fabry-Perot interferometer is used as a reference for calibrating the reflected light signal detected from the Fabry-Perot interferometer 106 (sensitive to changes in ambient pressure). Thus, the additional Fabry-Perot interferometer functions as a reference optical device. As described above, using the reference optical device, the computer processor can account for changes in the reflected light signal detected from the optical device due to the measurement angle between the optical axis of the Fabry-Perot interferometer 106 and the optical axis of the readout device. Alternatively or additionally, the computer processor can also account for other optical effects within the eye in this manner.

[0084] The scope of this application includes combining any one embodiment of the optical device 100 described herein with the reference optical device 100R as shown in Figure 8, with necessary modifications.

[0085] Next, refer to Figure 9, a graph showing a typical spectral profile (i.e., intensity vs. frequency) of an optical signal detected by a readout device, given the distance between the two mirrors of a Fabry-Perot interferometer equipped with a retroreflector, which relates to a partial application example of the present invention. As described above, the optical device 100 generally includes a retroreflector configured to return the optical signal transmitted through the interferometer to the readout device. When the optical axis of the optical device does not coincide with the optical axes of the illumination device and the readout device, light that does not pass through the Fabry-Perot interferometer is generally reflected at different angles of reflection according to the law of reflection. Therefore, as shown in Figure 9, when the optical axis of the optical device does not coincide with the optical axes of the illumination device and the readout device, and when a broadband light source is used, the reflected light signal generally contains multiple peaks indicating the resonant frequencies of the Fabry-Perot interferometer, and the computer processor is configured to determine intraocular pressure and / or other intraocular parameters by deriving the distance between the mirrors of the interferometer based on this. Note that in the absence of a retroreflector, the resonant frequencies of the Fabry-Perot interferometer will pass through the optical device rather than be reflected from it. The computer processor then has to determine the resonant frequency by identifying the trough in the reflected light signal. Generally, detecting the trough in the reflected light signal is more difficult than identifying the peak. Therefore, in some applications, including a retroreflector in the optical device facilitates the analysis of the reflected light signal by the computer processor by making it easier to detect the resonant frequency of the interferometer.

[0086] The scope of this application includes combining any one embodiment of the optical device 100 described herein with a retroreflector 140, with necessary modifications, as shown in Figures 2 and 9.

[0087] Generally, when the distance between the two mirrors of a Fabry-Perot interferometer changes, the distance between the peaks of the reflected signal changes (with respect to either frequency or wavelength). Generally, the distance between the peaks of the reflected signal also changes as a function of the angle θ between the optical axis of the Fabry-Perot interferometer and the optical axis of the illuminator and readout device. This is because the effective distance between the two mirrors is now d eff This is because = dcosθ. When the angle is small and / or the distance is short, this effect may be negligible. In some applications, by coupling the reference optical device 101 to the optical device 100, this effect may be considered as described above with reference to Figure 8.

[0088] As described above, the illumination device 300 generally includes light sources such as LEDs, lasers, monochromatic light sources, swept light sources, polychromatic light sources, and / or broadband light sources. Generally, when a monochromatic light source is used, it is a swept monochromatic light source that changes the frequency of light over time. Generally, a computer processor determines intraocular pressure and / or other intraocular parameters by detecting the transmission frequency at which light is reflected from the optical device in order to derive the resonant frequency of the Fabry-Perot interferometer.

[0089] Generally, when a multicolor light source with limited bandwidth is used, a single peak exists in the reflected signal. The peak in the Fabry-Perot interferometer reflected signal scans the light frequency of the illumination, and the spectrum of the reflected light changes. Generally, a computer processor detects the change in the reflected light spectrum by either spectral measurement or intensity measurement. More generally, the light source has known spectral characteristics, and based on these known spectral characteristics of the light source and the spectrum of the reflected light, the computer processor determines intraocular pressure and / or other intraocular parameters by deriving the resonant frequency of the Fabry-Perot interferometer.

[0090] Generally, when a broadband illumination source with a relatively large bandwidth is used, the number of spectral peaks in the Fabry-Perot interferometer reflected signal within the illumination source bandwidth is detected. Generally, by counting this number, a computer processor can perform pressure measurements with a large dynamic range. In some such applications, the computer processor determines intraocular pressure and / or other intraocular parameters by analyzing the spectrum of the reflected light using a Fast Fourier Transform to detect the frequencies of the reflected signal peaks (i.e., the spectral distance between the reflected signal peaks) and deriving the resonant frequency of the Fabry-Perot interferometer.

[0091] Generally, optical devices are calibrated so that the relationship between the resonant frequency of the Fabry-Perot interferometer and each intraocular pressure (and / or other intraocular parameters) is known. Therefore, computer processors generally perform calculations that automatically output intraocular pressure (and / or other intraocular parameters), rather than performing a first calculation to derive the resonant frequency of the Fabry-Perot interferometer and another calculation to determine the intraocular pressure and / or other intraocular parameters.

[0092] It should be noted that the graph shown in Figure 9 represents one method of performing an analysis of the signal output by the optical device 100 based on spectral analysis of the signal. However, the scope of this application includes other types of analysis, such as phase analysis and intensity analysis, with necessary modifications. Such alternative types of analysis are generally applicable when the optical device 100 comprises multiple Fabry-Perot interferometers in series, as described above. For example, when the optical device 100 comprises multiple Fabry-Perot interferometers in series, a computer processor may determine intraocular pressure and / or other intraocular parameters by determining the intensity and / or spectrum of the reflected light signal and deriving the resonant frequency of the Fabry-Perot interferometer.

[0093] Generally, other wavelengths of light that are not at the resonant frequency of the Fabry-Perot interferometer are reflected by the front mirror of the Fabry-Perot interferometer according to the law of reflection. More generally, in order to perform the above Fabry-Perot interferometer measurements, the axes of the illuminator and the readout device are parallel to each other. Therefore, unless the optical axis of the Fabry-Perot interferometer coincides with the illumination axis, other wavelengths of light will be reflected elsewhere and will not propagate to the pupil and the readout device. In some applications, as a result of a change in the direction of the optical axis of the readout device relative to the illuminator, other wavelengths of light that are not at the resonant frequency of the Fabry-Perot interferometer are reflected by the front mirror of the Fabry-Perot interferometer, and as a result, are detected by the readout device and analyzed by a computer processor. Generally, by analyzing the intensity and / or spectrum and / or phase and / or polarization of the reflected wavelengths, the presence and / or concentration of various substances inside the eye can be detected. By analyzing this data, various physiological and medical conditions, such as sugar levels, the presence of viruses, amino acids, vitamins, and physiological and medical conditions that affect the presence and / or concentration of substances, can be estimated. Alternatively or additionally, reflected light is detected by the readout device when the subject's eyelids are closed. In some such applications, the optical properties of the signal detected by the readout device 400 (such as signal intensity, spectrum, polarization, and / or phase) change based on the parameters of the blood in the blood vessels of the subject's eyelids. This is because the eyelids are thin enough for incident and reflected light to pass through, and as light passes through the eyelids, it generally passes through the blood vessels of the eyelids. By analyzing the optical properties of the signal detected by the readout device 400, the computer processor is generally configured to determine one or more parameters of the subject's blood (such as oxygen saturation) by analyzing, for example, the intensity and / or spectrum and / or phase and / or polarization of the reflected light. In some such applications, based on the above analysis, the computer processor is configured to estimate various physiological and medical conditions of the subject.

[0094] It should be noted that any optical sensor having optical properties sensitive to intraocular pressure and / or other intraocular parameters may be used to perform one or more of the above analyses. For example, a retroreflector and / or mirror may be used in optical device 100. The presence and / or concentration of various substances inside the eye may be detected by analyzing the intensity and / or spectrum and / or phase and / or polarization of the reflected wavelength. Measurements may be repeated in various directions and / or various light sources and / or spectral regions and / or polarization and / or bandwidth. In some applications, an optical device configured to perform intraocular pressure measurement may be coupled with an additional optical device configured to detect the presence and / or concentration of various substances inside the eye, and the coupled device may be placed inside the subject's eye.

[0095] In some applications, the apparatus and methods described herein are used to detect alternative or additional intraocular parameters. For example, the apparatus and methods described herein may be used to detect intraocular temperature, and the Fabry-Perot interferometer may be configured such that the distance between the mirrors of the interferometer changes detectably in response to changes in ambient temperature. For example, by using materials with varying coefficients of thermal expansion in the Fabry-Perot interferometer, the distance between the mirrors of the interferometer changes detectably in response to changes in ambient temperature. In some applications, the optical device configured in this manner is placed in the eye together with a reference optical device 100R as shown in Figure 8, with necessary modifications. In some applications, the optical device configured in this manner is placed in the eye together with a retroreflector 140 as shown in Figures 2 and 9, with necessary modifications.

[0096] In some applications, alternative or additional optical elements are used within the optical device 100. For example, the optical device may include one or more of the following optical elements, which are illustrative and not limiting: a. One or more lenses for focusing illumination light and / or imaging the light source onto a Fabry-Perot interferometer. b. One or more polarizers corresponding to the polarization of illumination and / or reflected light in order to increase the signal-to-noise ratio in the measurement and / or to distinguish the signal from optical device 100 from the signal from reference optical device 100R. c. One or more beam splitters that direct illuminating and / or reflected light in various directions.

[0097] In some applications, the apparatus and methods described herein are used to detect pressure in different parts of a subject's body and / or pressure in different elements. For example, the apparatus and methods described herein may be used to detect pressure in an industrial environment.

[0098] Those skilled in the art will understand that the present invention is not limited to what has been specifically shown and described above. Rather, the scope of the present invention includes both combinations and partial combinations thereof of the various features described in the above specification, as well as modifications and variations thereof that are not in the prior art and will be conceivable to those skilled in the art by reading the above description.

Claims

1. An illumination device that directs light into the subject's eyes, An optical device placed inside the eye of the subject, A first Fabry-Perot interferometer comprising at least two mirrors, configured such that the distance between the mirrors changes when the intraocular parameters of the subject's eye change, An optical device comprising: a retroreflector configured such that light transmitted through the first Fabry-Perot interferometer is automatically reflected out of the subject's eyes; A reference Fabry-Perot interferometer comprising at least two reference mirrors, wherein the distance between the reference mirrors is constant when the intraocular parameters of the subject's eye change, A readout device for detecting the light reflected outward from the subject's eye, A device equipped with.

2. The apparatus according to claim 1, wherein the apparatus is used together with an intraocular lens, and the optical device is coupled to the intraocular lens.

3. The apparatus according to claim 1, wherein the apparatus is used in conjunction with an intraocular lens, and the optical device is positioned inside the eye of the subject during the procedure in which the intraocular lens is placed inside the eye of the subject.

4. The apparatus according to claim 1, wherein the optical device is coupled to the ciliary body of the subject's eye.

5. The apparatus according to claim 1, wherein the first Fabry-Perot interferometer is configured such that the distance between the mirrors changes when the intraocular pressure of the subject's eye changes.

6. The apparatus according to claim 1, wherein the first Fabry-Perot interferometer is configured such that the distance between the mirrors changes when the intraocular temperature of the subject's eye changes.

7. The apparatus according to claim 1, wherein the optical device comprises two or more additional mirrors, thereby functioning as a plurality of cascaded first Fabry-Perot interferometers.

8. The apparatus according to any one of claims 1 to 7, further comprising a computer processor for analyzing the light reflected out of the subject's eye in order to determine the intraocular parameters of the subject's eye by identifying the resonant frequency of the first Fabry-Perot interferometer.

9. The apparatus according to claim 8, wherein the illumination device is equipped with a swept monochromatic light source, and the computer processor identifies the resonant frequency of the first Fabry-Perot interferometer by detecting the frequency of light reflected outward from the subject's eye.

10. The apparatus according to claim 8, wherein the illumination device comprises a multicolor light source having known spectral characteristics, and the computer processor identifies the resonant frequency of the first Fabry-Perot interferometer based on the known spectral characteristics of the light source and the frequency of the light reflected outward from the subject's eye.

11. The apparatus according to claim 8, wherein the illumination device is equipped with a broadband light source, and the computer processor identifies the resonant frequency of the first Fabry-Perot interferometer by analyzing the frequency of the light reflected outward from the subject's eye using a fast Fourier transform to detect the distance between peaks of the reflected signal.

12. The apparatus according to claim 8, wherein the reading device detects light at the resonant frequency of the first Fabry-Perot interferometer that is reflected outward from the subject's eye when the optical axis of the reading device is parallel to the optical axis of the illumination device.

13. The apparatus according to claim 1, wherein the reference Fabry-Perot interferometer is in series with the first Fabry-Perot interferometer, which is configured such that the distance between its mirrors changes when the intraocular parameters of the subject's eye change.

14. The apparatus according to claim 1, further comprising a computer processor that analyzes the light reflected outward from the eyes of the subject, and takes into account the change in angle between the optical axis of the optical device and the optical axis of the illumination device and / or the readout device by calibrating the measurement performed on the light reflected from the first Fabry-Perot interferometer using the measurement performed on the light reflected from the reference Fabry-Perot interferometer.

15. The apparatus according to claim 1, further comprising a reference optical device coupled to the optical device and equipped with the reference Fabry-Perot interferometer.

16. The apparatus according to claim 15, wherein the reference optical device is coupled to the optical device such that the optical axes of the optical device and the reference optical device are parallel to each other.

17. The apparatus according to claim 15, wherein the reference optical device comprises a retroreflector configured such that light transmitted through the reference Fabry-Perot interferometer is automatically reflected away from the subject's eyes.

18. Directing light into the subject's eyes, An optical device located inside the eye of the subject, A first Fabry-Perot interferometer comprising at least two mirrors, configured such that the distance between the mirrors changes when the intraocular parameters of the subject's eye change, A retroreflector configured such that light transmitted through the first Fabry-Perot interferometer is automatically reflected outwards from the subject's eyes, Receiving reflected light from an optical device comprising: a reference Fabry-Perot interferometer having at least two reference mirrors, wherein the distance between the reference mirrors is constant when the intraocular parameters of the subject's eye change; and The intraocular parameters of the subject's eye are determined by analyzing the reflected light. A method that includes this.

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