WO2017222086A1 - Système de tomographie à cohérence optique multifocale à base de détecteur unique - Google Patents

Système de tomographie à cohérence optique multifocale à base de détecteur unique Download PDF

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Publication number
WO2017222086A1
WO2017222086A1 PCT/KR2016/006593 KR2016006593W WO2017222086A1 WO 2017222086 A1 WO2017222086 A1 WO 2017222086A1 KR 2016006593 W KR2016006593 W KR 2016006593W WO 2017222086 A1 WO2017222086 A1 WO 2017222086A1
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WIPO (PCT)
Prior art keywords
polarization
light
contrast
splitter
surface portion
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Ceased
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PCT/KR2016/006593
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English (en)
Korean (ko)
Inventor
정현우
이영진
박상수
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Industry Academic Cooperation Foundation of Eulji University
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Industry Academic Cooperation Foundation of Eulji University
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/102—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for optical coherence tomography [OCT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging

Definitions

  • the present invention relates to a multifocal optical tomography system, and to a single detector based multifocal optical tomography system.
  • OCT optical coherence tomography
  • Republic of Korea Patent No. 1232315 discloses a dual focusing optical coherence imaging device.
  • the speed of the maximum spectral detector is reduced by half because the optical switch transmits the image information of the two corneas and the retinas sequentially to the spectroscopic detector once to enable simultaneous imaging of the two images. There is a problem.
  • the present invention has been proposed to solve the above problems, and an object of the present invention is to provide a single detector-based multifocal optical tomography system capable of simultaneously measuring the retina and cornea.
  • problems are exemplary, and the scope of the present invention is not limited thereby.
  • a light source for generating a low coherence light (light source); An isolator or an optical fiber circulator for protecting the light source; A first optical splitter for distributing the low coherent light beams passing through the optical isolator or the optical fiber circulator into surface contrast light rays and deep contrast light rays; The surface contrast beam and the deep contrast light beam distributed from the first optical splitter are distributed to a sample arm and a reference arm, respectively, and a sample signal and a reference signal obtained from the sample stage and the reference stage.
  • a second optical splitter and a third optical splitter for generating an interference signal by using After having the plurality of polarizing splitters, the surface contrast light beam and the deep contrast light beam respectively incident from the second light splitter and the third light splitter are converted into parallel light by a collimator, and then pass through the polarizer splitter or reflected horizontally. Or a sample arm for obtaining a sample signal of the surface portion and the core portion using the surface portion contrast polarization of the vertical component and the deep portion polarization polarization of the component orthogonal to the surface portion contrast polarization.
  • the surface contrast light beam and the deep contrast light beam respectively incident from the second light splitter and the third light splitter are converted into parallel light by a collimator, and then pass through the polarizer splitter or reflected horizontally.
  • a reference arm for generating a reference signal
  • a spectrometer for converting the interference signal into an image signal
  • a computer for implementing the image signal into an image, a single detector based multifocal optical tomography system is provided.
  • FIG. 1 is a schematic diagram schematically showing the structure of a multi-detector optical tomography imaging system based on a single detector capable of simultaneously measuring the retina and cornea according to an embodiment of the present invention.
  • FIG. 2 is a side view schematically showing the shape of a spectrometer of a single detector based multifocal optical tomography imaging system according to an embodiment of the present invention.
  • FIG. 3 is a diagram showing incident light in a line using a high speed camera having a multi-pixel surface sensor instead of a dual line scanning camera in a spectroscope of a single detector based multifocal optical tomography system of the present invention.
  • FIG. 4 is a schematic diagram illustrating another embodiment of a reference arm of the single detector based multifocal optical tomography system of the present invention.
  • FIG. 5 is a schematic diagram illustrating another embodiment of a reference arm of the single detector based multifocal optical tomography imaging system of the present invention.
  • FIG. 6 is a schematic diagram showing another embodiment of a single detector based multifocal optical tomography system of the present invention.
  • OCT optical coherence tomography
  • cornea is a transparent membrane on the eye's surface, a transparent, bloodless tissue on the anterior surface of the eye, often referred to as a black spot.
  • the cornea not only protects the eyes from the outside, but also plays a role in allowing light to pass through and be refracted.
  • retina is a transparent neural tissue that covers the innermost part of the eye, and light entering the eye is sensed through the inner layer of the retina to the cells of the retina.
  • the optic cells convert light information back into electrical information, and the information can be seen through the process of being transmitted to the brain through the optic nerve through the cells of the inner layer of the retina.
  • a light source for generating a low coherence light (light source); An isolator or an optical fiber circulator for protecting the light source; A first optical splitter for distributing the low coherent light beams passing through the optical isolator or the optical fiber circulator into surface contrast light rays and deep contrast light rays; The surface contrast beam and the deep contrast light beam distributed from the first optical splitter are distributed to a sample arm and a reference arm, respectively, and a sample signal and a reference signal obtained from the sample stage and the reference stage.
  • a second optical splitter and a third optical splitter for generating an interference signal by using After having the plurality of polarizing splitters, the surface contrast light beam and the deep contrast light beam respectively incident from the second light splitter and the third light splitter are converted into parallel light by a collimator, and then pass through the polarizer splitter or reflected horizontally. Or a sample arm for obtaining a sample signal of the surface portion and the core portion using the surface portion contrast polarization of the vertical component and the deep portion polarization polarization of the component orthogonal to the surface portion contrast polarization.
  • the surface contrast light beam and the deep contrast light beam respectively incident from the second light splitter and the third light splitter are converted into parallel light by a collimator, and then pass through the polarizer splitter or reflected horizontally.
  • a reference arm for generating a reference signal
  • a spectrometer for converting the interference signal into an image signal
  • a computer for implementing the image signal into an image, a single detector based multifocal optical tomography system is provided.
  • the sample arm comprises a first polarization controller for controlling the optical power of light incident from the second and third optical splitters, respectively; A second polarization controller; A first collimator and a second collimator for forming the surface portion contrast ray and the deep portion contrast ray that have passed through the first polarization regulator and the second polarization regulator into collimated light; A first polarization distributor selectively passing only the surface contrast polarization in the parallel light and reflecting the deep contrast polarization to a scanning mirror; A scanning mirror scanning the surface portion contrast polarization and the deep portion contrast polarization; A second polarization splitter selectively passing only the surface contrast polarization reflected by the scanning mirror and reflecting the deep contrast polarization; A third polarization divider for selectively passing only the surface contrast polarization passing through the second polarization divider and reflecting the deep contrast polarization; A first reflector and a second reflector for reflecting the deep contrast polarization reflected by the second polarizer and sending the
  • the reference arm includes optical power of a surface reference beam and a core reference beam respectively incident from the second and third optical splitters.
  • a third polarization controller and a fourth polarization controller for adjusting the polarization;
  • a third collimator and a fourth collimator for forming the surface portion reference ray and the core portion reference ray that have passed through the third polarization controller and the fourth polarization controller, respectively, into collimated light;
  • a fourth polarization splitter configured to selectively pass only the surface reference polarization in the parallel light and reflect the core reference polarization;
  • a fifth polarization divider for selectively passing only the surface-referenced polarized light that has passed through the fourth polarized light distributor and sending it to a third reflecting mirror, and reflecting the core-referenced polarized light reflected by the fourth polarized light distributor;
  • a second gold mirror provided at a position corresponding to a surface portion on which the polarization of the surface portion reference reflected by the third reflection mirror is
  • a seventh polarization splitter may be further provided between the fifth polarization splitter and the third reflection mirror to selectively pass only the polarization for the surface reference.
  • a first ND filter is further provided between the reflector and the third lens to minimize image distortion caused by excessive light intensity caused by the first gold mirror, and between the fourth reflector and the fourth lens.
  • a second ND filter may be further provided to minimize image distortion caused by excessive light intensity caused by the second gold mirror.
  • a fifth polarization controller and a sixth polarization controller for adjusting light intensity of the deep contrast interference signal are included in the single detector based multifocal optical tomography system.
  • the spectroscope is configured to form a surface portion contrast interference signal and a deep portion contrast interference signal that have passed through the fifth polarization controller and the sixth polarization controller, respectively, into parallel light.
  • a camera for converting the focused optical signal into an image signal wherein the camera is equipped with a dual line sensor module and converts the surface contrast interference signal and the deep contrast interference signal from the transmission diffraction grating into a video signal. It can be a dual shipper camera.
  • the optical signal information may be converted by a frame grabber of the dual line scanning camera, and the camera may be a high speed camera having a multi-pixel plane sensor. have.
  • the surface portion may be a cornea and the core portion may be a retina.
  • first, second, etc. are used herein to describe various members, parts, regions, layers, and / or parts, these members, parts, regions, layers, and / or parts are defined by these terms. It is obvious that not. These terms are only used to distinguish one member, part, region, layer or portion from another region, layer or portion. Thus, the first member, part, region, layer or portion, which will be discussed below, may refer to the second member, component, region, layer or portion without departing from the teachings of the present invention.
  • top or “above” and “bottom” or “bottom” may be used herein to describe the relationship of certain elements to other elements as illustrated in the figures. It may be understood that relative terms are intended to include other directions of the device in addition to the direction depicted in the figures. For example, if the device is turned over in the figures, elements depicted as present on the face of the top of the other elements are oriented on the face of the bottom of the other elements. Thus, the exemplary term “top” may include both “bottom” and “top” directions depending on the particular direction of the figure. If the device faces in the other direction (rotated 90 degrees relative to the other direction), the relative descriptions used herein can be interpreted accordingly.
  • FIG. 1 is a schematic diagram schematically illustrating a multi-detector optical tomography system 100 based on a single detector capable of simultaneously measuring the retina and cornea according to an embodiment of the present invention. As shown, the configuration of a single detector-based multifocal optical tomography system 100 firstly protects light incident from a low coherence source and distributes it to other systems.
  • the sample arm (150) for imaging the cornea or retina with the light distributed from the light splitter 120, the light to meet the sample signal (cornea or retina) to form a coherence (coherence)
  • It consists of a reference arm (180) to provide a and a spectrometer (spectrometer, 130) for realizing the optical signal information through a computer by spectroscopy and converting the incident light.
  • the conventional dual imaging system sequentially transmits the tomography image information of the cornea and retina to the camera (detector) in the spectroscope one by one by a high-speed optical switch.
  • the maximum speed of the camera is reduced by half, which reduces the imaging speed of the entire imaging system by half. It remains a fatal problem for medical imaging devices that make imaging speed vital.
  • the present inventors have developed a single focusing system based dual focusing high speed optical tomography system by transmitting the tomographic image information of the cornea and retina to the camera in the spectrometer as a result of recognizing this problem and diligently. This basically overcomes the problem of having two spectroscopic detectors for imaging the retina and cornea, and has developed a single detector based multifocal optical tomography system 100 capable of simultaneously measuring the retina and cornea.
  • the single detector-based multifocal optical tomography system 100 of the present invention has a disadvantage in that the imaging speed is halved by sequentially transmitting image information of two regions (cornea and retina) by the optical switch one by one to the spectroscope camera.
  • the imaging speed is halved by sequentially transmitting image information of two regions (cornea and retina) by the optical switch one by one to the spectroscope camera.
  • the light from the low coherence light source 102 configured in the light splitter 120 is directed in one direction to protect the light source.
  • a first optical splitter (111r) 111 that passes through a light isolator 105 that transmits light only and distributes the low coherent light beam that has passed through the light isolator 105 into cornea contrast light and retina contrast light. It is distributed in half (50:50) to the second optical splitter coupler2 and 112 for obtaining cornea image information and the third optical splitter coupler3 and 113 for obtaining retina image information.
  • the optical isolator 105 serves to protect the light source 102, it can be replaced by a fiber circulator of the optical fiber type. Thereafter, the light passing through the second optical splitter 112 is positioned to have a path difference between the sample stage 150 where the eyeball 190 is located and the corneal image information. (169,167) is distributed to the reference stage 180 is configured.
  • the corneal contrast beam and the retinal contrast beam (indicated by the dotted green line) that move from the second light splitter 112 to the sample stage 150 pass through the first polarization controller 121 and then the first collimator ( 131, which is formed into collimated light, and which is reflected from the scanning mirror 162 and the scanning mirror 162 by the first polarizer (PBS, 141) for scanning the corneal contrast and the retinal contrast polarization.
  • PBS first polarizer
  • a second polarization divider selectively passing only contrast polarization and reflecting the retinal contrast polarization 142, a third polarization divider selectively passing only the corneal contrast polarization passing through the second polarization divider, and reflecting the retinal contrast polarization ( 143 and the first lens 153 are focused on the eyeball 190 to image the cornea.
  • the corneal contrast beam and the retinal contrast beam (dotted green line) distributed from the third light splitter 113 to the reference stage 180 pass through the third polarization controller 124 and the second collimator 135, and then Only the light of the horizontally polarized light (P) component for corneal contrast is passed through the four polarizer splitter 144, the fifth polarizer splitter 145, and the sixth polarizer splitter 146, and passes through the fourth reflector 167 to pass the first ND filter ( After passing through the third lens 155 through 171, the light focused and reflected on the first gold mirror 182 passes through the above-described lens and three polarization splitters, and then is sampled by the second optical splitter 112. It meets with the signal (cornea) to form a coherence signal.
  • the corneal contrast beam and the retinal contrast beam that have passed from the first light splitter 111 to the third light splitter 113 are respectively provided to the sample stage 150 and the reference stage 180, similarly to the second optical splitter 112. Is distributed.
  • the light moving from the third light splitter 113 to the sample stage 150 passes through the second polarization controller 124 and the third collimator 132 to become parallel light, and thus, the first polarized light splitter PBS 141.
  • Incident light is transmitted through the second mirror 162 through the scanning mirror 162, the second polarization splitter 142, and passes through the second lens 152 to be reflected to the first reflector 163 and the second reflector 165.
  • the first lens 153 After passing through the third polarization divider 143, the first lens 153 enters parallel light into the eye and is focused on the retina by the lens to be imaged.
  • the corneal reference light beam and the retina reference light beam going from the third light splitter 113 to the reference stage 180 pass through the fourth polarization controller 126 and the fourth collimator 136 and then the fourth polarizer 144.
  • the fifth polarization splitter 145 and the seventh polarizer splitter 147 pass only the light of the vertically polarized light (S) component and are reflected by the third reflector 169 so as to reflect the second ND filter 175 and the fourth lens 154.
  • the second gold mirror 185 positioned at an optical path for imaging the retina. Thereafter, the reflected light is reflected by the three polarizers PBS described above, and then meets the sample signal (retina) in the third optical distributor 113 to form an interference signal.
  • the polarization controllers 121 and 124 of the sample stage 150 serve to adjust the optical power of light incident on the sample stage 150 to meet safety standards
  • the reference stage 180 The polarization controllers 125 and 126 serve to correct for proper formation of the interference signal.
  • light incident on the reference stage 180 is incident on the first gold mirror 182 and the second gold mirror 185, and then the light reflected from the gold mirrors 182 and 185 and the cornea of the sample stage 150.
  • the ND filters 171 and 175 of the reference stage 180 serve to adjust the optical power appropriately in order to minimize image distortion caused by excessive light intensity caused by the mirror.
  • the image information of the sample stage 150 for imaging the cornea or the retina and the reference stage 180 for forming the coherence signal together with the cornea or the retina signal are passed through the optical splitters 112 and 113.
  • the spectrometer 130 moves through each path.
  • the interference signal formed by the second optical splitter 112 passes through the fifth polarization controller 122 and the fifth collimator 133 and the third optical splitter 113.
  • the interference signal formed in the N-S is transmitted to the spectroscope 130 through the sixth polarization controller 123 and the sixth collimator 134, respectively.
  • the two image information incident on the spectrometer 130 are irradiated to the transmission grating 164 by two collimated light beams by the collimators 133 and 134, respectively, and spectroscopically passed through the fifth lens 156.
  • the two optical signals are focused by a dual line scan camera 109 equipped with a line sensor module.
  • the focused optical signal information is A / D converted by the frame grabber of the dual pre-scan camera 109 (which can be used by mounting an external separate frame grabber to the computer) to the computer 119.
  • the program in the computer 119 undergoes k-domain calibration and inverse fast fourier transform (IFFT) to maintain the maximum speed by a graphics processing unit (GPU) based ultra fast parallel processing algorithm.
  • IFFT inverse fast fourier transform
  • Simultaneous real-time imaging is possible, enabling simultaneous imaging of the retina and cornea.
  • This is a simple multi-focus light that can greatly reduce the operation trigger control of complex hardware and software, as well as a large cost reduction effect compared to the technology (registered using the high-speed optical switch, Korean Patent No. 1262315) filed by the present inventors.
  • the imaging system has the advantage of being possible.
  • the single-detector-based multifocal optical tomography system 100 is a dual focusing system capable of imaging two areas at the same time, but this is only possible for the eyeball and irradiates the focusing light to the corneal area and for retinal imaging. By irradiating parallel light to the eye, it is a structure that naturally focuses on the retina by the lens of the eye serving as a lens.
  • FIG. 3 is a view showing an optical line by an ultra-high speed camera having a multi-pixel plane sensor, and two spectrometers using an area camera equipped with a plane sensor instead of the dual line scanning camera 109 of the spectroscope 130 described above.
  • the incident light is focused on only two lines, and the software is configured to use only pixels of a desired sensor, so that it can be used like a dual line sensor. Therefore, by selecting and selecting two desired lines (two red lines in FIG. 3), the light incident by the two collimators 133 and 134 may be focused on the two lines to acquire a multifocal image.
  • FIG. 4 and 5 are schematic diagrams illustrating another embodiment of the reference stage 180 of the single detector based multifocal optical tomography system 100, respectively.
  • the configuration of the reference stage 180 uses two fourth polarizers 144 and a fifth polarizers 145, or as shown in FIG. 5, the fourth polarizers 144.
  • the second gold mirror 185 and the fourth lens 154 can be configured as a single device, and a software-based algorithm solves the physico-optical light dispersion problem that occurs as the number of optical components decreases. It can be solved by correction by.
  • FIG. 6 is a schematic diagram illustrating a structure of a single detector based multifocal optical tomography system 200 capable of imaging two depth regions of a sample 192 in addition to an eyeball.
  • the lens of the sample stage 150 is moved to a position before the third polarization splitter 143, which is located at the end, so that the light of the vertical polarization component S and the horizontal polarization component P of the sample stage 150 Since only one lens is used for each path, light is focused to two areas by the two paths, so that two portions of samples 192 having different depths may be focused even if they are not eyes.
  • the sample 192 may be a biological tissue such as skin or cancer tissue, and two regions having different depths may be, for example, a surface and a bottom or a portion of a predetermined depth desired in the sample 192.
  • the light of the reference stage 180 is generated in the second optical splitter 112 and the third optical splitter 113 and then passes through the polarization controllers 122 and 123 to the two collimators 133 and 134.
  • image information of two regions is simultaneously transmitted and implemented in real time through a computer.
  • the single-detector-based multifocal optical tomography system is an ultra-fast ophthalmic dual imaging system capable of simultaneously imaging the cornea and retina.
  • Small camera modules such as semiconductors and mobile phones require industrial technologies that require multifocal optical tomography systems. Or the like.

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Abstract

La présente invention concerne un système de tomographie à cohérence optique multifocale à base de détecteur unique comprenant : une source de lumière pour générer un rayon de lumière à faible cohérence ; un isolateur optique ou un circulateur à fibre optique pour protéger la source de lumière ; un premier distributeur optique ; un deuxième distributeur optique ; un troisième distributeur optique ; un bras d'échantillon conçu de telle sorte qu'un rayon de lumière destiné à contraster une partie surface et un rayon de lumière destiné à contraster une partie centrale, qui sont incidents à partir respectivement, du deuxième distributeur optique et du troisième distributeur optique, sont convertis en lumière parallèle par un collimateur et passent à travers un distributeur de polarisation ou sont réfléchis par ce dernier, et la lumière polarisée obtenue pour contraster la partie surface, qui a un élément horizontal ou vertical, et une lumière polarisée pour contraster la partie centrale, qui a un élément perpendiculaire à la lumière polarisée pour contraster la partie surface, sont utilisées pour obtenir des signaux d'échantillon de la partie surface et de la partie centrale, respectivement ; un bras de référence ayant une pluralité de distributeurs de polarisation de telle sorte que le rayon de lumière destiné à contraster la partie surface et le rayon de lumière destiné à contraster la partie centrale, qui sont incidents à partir respectivement, du deuxième distributeur optique et du troisième distributeur optique, sont convertis en lumière parallèle par le collimateur et passent à travers les distributeurs de polarisation ou sont réfléchis par ces derniers, et la lumière polarisée obtenue pour le référencement de la partie surface, qui a un élément horizontal ou vertical, et une lumière polarisée pour le référencement de la partie centrale, qui a un élément perpendiculaire à la lumière polarisée pour le référencement de la partie surface, sont utilisées pour obtenir des signaux de référence réfléchis par des miroirs réfléchissants de référence disposés dans des positions correspondant à celles de la partie surface et de la partie centrale, respectivement ; un spectromètre pour convertir les signaux d'interférence en signaux d'image ; et un ordinateur pour réaliser des images à partir des signaux d'image.
PCT/KR2016/006593 2016-06-20 2016-06-22 Système de tomographie à cohérence optique multifocale à base de détecteur unique Ceased WO2017222086A1 (fr)

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KR102360753B1 (ko) * 2020-07-01 2022-02-10 주식회사 브릴리온포토닉스 다초점 브릴루앙 산란광 기반 분광법을 수행하기 위한 시스템
CN113520298B (zh) * 2021-06-15 2023-04-28 上海应用技术大学 一种眼前后节一体光学相干断层结构/功能成像系统

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KR100868439B1 (ko) * 2007-01-15 2008-11-11 광주과학기술원 편광민감 광결맞음 생체영상기기용 간섭 시스템
JP2010268990A (ja) * 2009-05-22 2010-12-02 Canon Inc 光干渉断層撮像装置およびその方法
WO2012105780A2 (fr) * 2011-02-01 2012-08-09 고려대학교 산학협력단 Système d'imagerie par cohérence optique à double focalisation
US20120281236A1 (en) * 2011-05-04 2012-11-08 The Johns Hopkins University Four-dimensional optical coherence tomography imaging and guidance system
US20150055090A1 (en) * 2012-03-21 2015-02-26 Utsunomiya University Three-dimensional retina image generator

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR100868439B1 (ko) * 2007-01-15 2008-11-11 광주과학기술원 편광민감 광결맞음 생체영상기기용 간섭 시스템
JP2010268990A (ja) * 2009-05-22 2010-12-02 Canon Inc 光干渉断層撮像装置およびその方法
WO2012105780A2 (fr) * 2011-02-01 2012-08-09 고려대학교 산학협력단 Système d'imagerie par cohérence optique à double focalisation
US20120281236A1 (en) * 2011-05-04 2012-11-08 The Johns Hopkins University Four-dimensional optical coherence tomography imaging and guidance system
US20150055090A1 (en) * 2012-03-21 2015-02-26 Utsunomiya University Three-dimensional retina image generator

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