WO2018203506A1 - Appareil de tomographie en cohérence optique - Google Patents

Appareil de tomographie en cohérence optique Download PDF

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Publication number
WO2018203506A1
WO2018203506A1 PCT/JP2018/016842 JP2018016842W WO2018203506A1 WO 2018203506 A1 WO2018203506 A1 WO 2018203506A1 JP 2018016842 W JP2018016842 W JP 2018016842W WO 2018203506 A1 WO2018203506 A1 WO 2018203506A1
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WO
WIPO (PCT)
Prior art keywords
light
line image
optical
optical system
line
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Application number
PCT/JP2018/016842
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English (en)
Japanese (ja)
Inventor
英之 大番
岩永　知行
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キヤノン株式会社
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Filing date
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Application filed by キヤノン株式会社 filed Critical キヤノン株式会社
Publication of WO2018203506A1 publication Critical patent/WO2018203506A1/fr

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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

Definitions

  • the present invention relates to an optical coherence tomographic imaging apparatus that acquires an optical coherence tomographic image of an inspection object.
  • OCT optical coherence tomography
  • the Fourier domain OCT includes a spectral domain OCT (SD-OCT) and a swept source OCT (SS-OCT).
  • SD-OCT spectral domain OCT
  • SS-OCT swept source OCT
  • These Fourier domain OCTs use light from a light source having a wide wavelength band, perform signal acquisition by dispersing the obtained interference light, and perform processing such as Fourier transform on the acquired signal, thereby allowing the eye to be examined. Information on the fault is obtained.
  • SD-OCT using broadband light
  • information for each frequency is obtained by spatially spectroscopically using a spectroscope.
  • SS-OCT that uses light from a wavelength-swept light source, light from a light source that emits light having a different wavelength in time is spectrally dispersed to obtain information for each frequency.
  • a line-field OCT apparatus (hereinafter referred to as an LF-OCT apparatus) that obtains tomographic information using measurement light that is shaped into a linear shape instead of using spot-like measurement light for the purpose of shortening measurement time.
  • an LF-OCT apparatus a line-field OCT apparatus that obtains tomographic information using measurement light that is shaped into a linear shape instead of using spot-like measurement light for the purpose of shortening measurement time.
  • the light emitted from the wavelength sweep type light source 01 is guided to the line image generation system 201.
  • the emitted light is converted into parallel light by the collimator lens 02 and then formed into light that forms a line-shaped image by the first cylindrical lens 03 and the lens 04 that are arranged subsequently.
  • These configurations are arranged such that the line-shaped light forms a line image at a position that is conjugate with a predetermined diopter, for example, the fundus of the eye to be examined with 0 diopter.
  • the line-shaped light is divided into measurement light and reference light by the beam splitter 12 after molding.
  • the first cylindrical lens 03 is arranged so that the measurement light forms a line image on the fundus of the subject eye 010 having a predetermined diopter.
  • the first cylindrical lens 03 is disposed before the light emitted from the wavelength-swept light source 01 is divided into measurement light and reference light by the beam splitter 12, and is guided to the beam splitter 12 as light connecting a line image. It is burned.
  • the reference light split by the beam splitter 12 is corrected by the reference optical system 202 so that the optical path length of the measurement light with respect to the fundus of the eye 010 to be imaged is equal to the optical path length.
  • the present invention has been made in view of the above situation, and provides an LF-OCT apparatus in which the angle of the cylindrical lens arranged in the reference optical system can be easily adjusted.
  • an optical coherence tomographic imaging apparatus includes: Splitting means for splitting light from the light source into measurement light and reference light; First line image generation means arranged in the optical path of the measurement light to generate a first line image of the measurement light; A second line image generation unit that is arranged in a reference optical system that adjusts the optical path length of the reference light and generates a second line image of the reference light that has the optical path length adjusted; Interfering means for generating interference light by combining the generated first line image and the second line image on the same imaging plane via an inspection object; And a tomographic image generation unit configured to generate a tomographic image of the inspection object using the generated interference light.
  • the measurement optical system 103 includes a lens 016, a focus lens 008, a galvanometric mirror 009, and an objective lens unit 017 arranged in order from the beam splitter 012.
  • the galvanometric mirror 009 is composed of a variable angle mirror disposed at a position substantially conjugate with the anterior eye portion of the eye 010 to be examined.
  • the objective lens unit 017 is composed of two lenses, guides the measurement light to the eye 010 to be examined, and forms a line image on the fundus.
  • the reference light returned by the retroreflector is guided to the second cylindrical lens 007 through the mirror unit 021.
  • the second cylindrical lens 007 forms a line image forming lens system with an accompanying lens.
  • the reference light passes through the line image forming lens system and then passes through the beam splitter 012 to form a line image on the second imaging plane 018.
  • the LF-OCT apparatus 300 includes the above-described OCT optical system 100, sampling unit 113, memory 114, signal processing unit 115, operation input unit 116, monitor 117, and control unit 118.
  • the control unit 118 is connected to the light source 001 and the line sensor 011 described above, the sampling unit 113, the memory 114, the signal processing unit 115, the operation input unit 116, and the monitor 117.
  • the control unit 118 can be configured using a general-purpose computer, but may be configured from a dedicated computer.
  • the monitor 117 is illustrated as a separate body from the control unit 118, these may be a single configuration. That is, some or all of the configurations shown as separate bodies in FIG. 2 may be integrally formed.
  • each structure is connected by wire, it is good also as connecting this part or all by radio
  • the light emitted from the light source 001 is first divided into the reference light and the measurement light before being formed into a line shape, and the measurement light is transmitted to the eye 010 to be examined through the measurement optical path.
  • the reference light is formed into a line after the adjustment of the reference optical path length.
  • the polarization adjustment paddle 004 is provided before the reference light is converted into spatial light in the reference optical system 102. For this reason, it is possible to adjust the polarization independently of the measuring light without arranging a large number of wave plates and adjusting the angle of each of them.
  • the light from the light source 001 is split into measurement light and reference light by a coupler 002 which is an example of a splitting unit.
  • a first cylindrical lens 003 which is an example of a first line image generation unit, is disposed in the optical path of the measurement light and generates a first line image of the measurement light on the first imaging plane 015.
  • the second cylindrical lens 007 as an example of the second line image generation unit is disposed in the reference optical system 102 that adjusts the optical path length of the reference light, and the reference light passes through the reference mirror 006 and is the reference optical path length.
  • the second line image is generated by the reference light after the adjustment of.
  • These cylindrical lenses are an example of a line image generating means, and can be replaced by another optical member having the same function as long as a similar line image is obtained.
  • the beam splitter 012 is an example of an interference means for combining and interfering the first line image and the second line image on the same imaging plane, and connects the two line images on the same imaging plane. If it is possible to make the image interfere, it can be replaced by a known optical member. Further, the arrangement in the reflection direction and the transmission direction with respect to the beam splitter 012 of the measurement optical system 103 and the reference optical system 102 may be opposite to that in the embodiment.
  • a first collimator lens 013 is disposed as an example of first collimating means that uses the measurement light guided to the first line image generating means as parallel light.
  • a second collimator lens 020 is disposed as an example of second collimating means that collimates the reference light guided from the coupler 002 and emitted to the reference optical system 102. Then, the first cylindrical lens 003 and the second cylindrical lens 007 respectively generate a first line image and a second line image from parallel light.
  • These collimator lenses are examples of collimating means, and can be replaced by optical members having the same function as long as similar parallel light is obtained.
  • the light split by the reflection by the beam splitter 012 in the parallel light is used as measurement light.
  • the measurement light is guided to the line image generation system 101 ′, and a line image is formed on the first imaging plane 015 by the first cylindrical lens 003 and the lens 014 arranged in the same manner as in the first embodiment. To do.
  • the measurement light in the form of a line passes through the beam splitter 012 and is guided to the measurement optical system 103.
  • the measurement optical system 103 has the same configuration as that of the first embodiment.
  • the polarization adjusting means is arranged in the reference optical system.
  • the reference light passes through the outgoing path and the return path twice also in the polarization adjusting means, so that high mounting accuracy is required.
  • the optical path is actually made different between the forward path and the return path, and the mode of passing only once in either the forward path or the return path is used. Possible correspondence.
  • the polarization adjusting unit 025 allows the reference light to pass through when it is guided to the reference optical system 102 '. Accordingly, there is no need to pay attention to such an optical path, and such an arrangement problem does not occur.
  • the dividing means includes a beam splitter 023.
  • the reference optical system 102 ′ includes a polarization adjusting unit 025 that is disposed between the beam splitter 023 and the second cylindrical lens 007 and adjusts the polarization of the reference light.
  • the polarization adjusting unit 025 is disposed at a position where the reference light passes through the reference optical system 102 'at the beginning. However, it can be arranged at any position on the optical path of the reference light in the reference optical system 102 ′ and between the beam splitter 023 and the second cylindrical lens 007.
  • the first line image generating means is constituted by a cylindrical lens, and the cylindrical lens can be defined as a first line image forming lens having different curvatures in two orthogonal meridian directions.
  • the second line image generating means is also composed of a cylindrical lens, and the cylindrical lens can be defined as a second line image forming lens having different curvatures in two orthogonal meridian directions.
  • the line image generation means is not limited to one configured from a single cylindrical lens, and may be any apparatus that has at least one cylindrical lens and forms a line image.
  • the description has been given by taking as an example an apparatus for capturing or measuring a fundus tomographic image and a three-dimensional tomographic image.
  • the inspection object to be inspected is not limited to the fundus of the eye to be examined, and may be, for example, the anterior eye portion of the eye to be examined. It is obvious that the effect of the present invention can be obtained even if the present invention is applied to an apparatus that captures or measures the tomographic image and three-dimensional tomographic image of the anterior segment.
  • the present invention can be applied to skins and organs other than the eyes as the object to be inspected.
  • the present invention has an aspect as an optical coherence tomography apparatus that captures an image based on data obtained from a medical device such as an endoscope.
  • a wavelength sweep type (SS) light source is used as the light source, and the light from the light source is formed into a line shape, projected onto the eye to be examined, and reflected and scattered by the eye to be examined.
  • the light and the line-shaped reference light are made to interfere.
  • the line sensor obtains an interference signal from the interference light, and performs signal processing on the interference signal to obtain a tomographic image of the eye to be examined.
  • the mode of the light source is not limited to this, and a super luminescence diode (SLD) that emits light in a wavelength region of about 50 nm to 100 nm may be used as the light source.
  • SLD super luminescence diode
  • the line-shaped interference light is wavelength-resolved by a spectroscope, the separated interference light is detected for each wavelength by a two-dimensional area sensor as a detector, and signal processing is performed to obtain a tomographic image and a three-dimensional tomogram of the eye to be examined. An image can be acquired.
  • the present invention has been described above with reference to the embodiments, but the present invention is not limited to the above-described embodiments.
  • the mirror or mirror unit should be changed as appropriate in view of the space allowed for the optical system.
  • the present invention includes inventions modified within the scope not departing from the spirit of the present invention and inventions equivalent to the present invention.
  • each Example mentioned above can be combined suitably in the range which is not contrary to the meaning of this invention.
  • 001 Light source
  • 002 Coupler
  • 003 First cylindrical lens
  • 007 Second cylindrical lens
  • 012 Beam splitter
  • 013 Collimator lens
  • 020 Second collimator lens

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  • Life Sciences & Earth Sciences (AREA)
  • Health & Medical Sciences (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Ophthalmology & Optometry (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Eye Examination Apparatus (AREA)
  • Investigating Or Analysing Materials By Optical Means (AREA)

Abstract

La présente invention facilite le réglage, etc., d'une lentille cylindrique disposée dans un système optique de référence dans un appareil LF-OCT. L'appareil LF-OCT selon la présente invention comprend : un moyen de division pour diviser la lumière provenant d'une source de lumière en une lumière de mesure et une lumière de référence ; un premier moyen de génération d'image de ligne qui est disposé sur le trajet optique de la lumière de mesure et qui génère une première image de ligne de la lumière de mesure ; un second moyen de génération d'image de ligne qui est disposé dans le système optique de référence pour ajuster la longueur de trajet optique de la lumière de référence et qui génère une seconde image de ligne de la lumière de référence, dont la longueur de trajet optique a été ajustée ; un moyen d'interférence pour générer une lumière d'interférence par synthèse, sur la même surface de formation d'image, de la première image de ligne et de la seconde image de ligne générées par l'intermédiaire d'un objet inspecté ; et un moyen de génération d'image tomographique pour générer, à l'aide de la lumière d'interférence générée, une image tomographique de l'objet inspecté.
PCT/JP2018/016842 2017-05-01 2018-04-25 Appareil de tomographie en cohérence optique WO2018203506A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2017-091421 2017-05-01
JP2017091421A JP2018187038A (ja) 2017-05-01 2017-05-01 光干渉断層撮像装置

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WO2018203506A1 true WO2018203506A1 (fr) 2018-11-08

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN113518909A (zh) * 2021-05-26 2021-10-19 香港应用科技研究院有限公司 具有成本效益的直线扫描光学相干断层成像装置
WO2022246902A1 (fr) * 2021-05-26 2022-12-01 Hong Kong Applied Science and Technology Research Institute Company Limited Appareil de tomographie par cohérence optique à balayage linéaire économique

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2009527770A (ja) * 2006-02-24 2009-07-30 ザ ジェネラル ホスピタル コーポレイション 角度分解型のフーリエドメイン光干渉断層撮影法を遂行する方法及びシステム
WO2015189174A2 (fr) * 2014-06-10 2015-12-17 Carl Zeiss Meditec, Inc. Systèmes et procédés d'imagerie améliorée à base interférométrique en domaine fréquentiel
US20160209201A1 (en) * 2013-10-09 2016-07-21 Carl Zeiss Meditec Inc. Improved line-field imaging systems and methods
US20160345820A1 (en) * 2015-05-28 2016-12-01 Cylite Pty Ltd High resolution 3-d spectral domain optical imaging apparatus and method

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2009527770A (ja) * 2006-02-24 2009-07-30 ザ ジェネラル ホスピタル コーポレイション 角度分解型のフーリエドメイン光干渉断層撮影法を遂行する方法及びシステム
US20160209201A1 (en) * 2013-10-09 2016-07-21 Carl Zeiss Meditec Inc. Improved line-field imaging systems and methods
WO2015189174A2 (fr) * 2014-06-10 2015-12-17 Carl Zeiss Meditec, Inc. Systèmes et procédés d'imagerie améliorée à base interférométrique en domaine fréquentiel
US20160345820A1 (en) * 2015-05-28 2016-12-01 Cylite Pty Ltd High resolution 3-d spectral domain optical imaging apparatus and method

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN113518909A (zh) * 2021-05-26 2021-10-19 香港应用科技研究院有限公司 具有成本效益的直线扫描光学相干断层成像装置
WO2022246902A1 (fr) * 2021-05-26 2022-12-01 Hong Kong Applied Science and Technology Research Institute Company Limited Appareil de tomographie par cohérence optique à balayage linéaire économique
US11578965B2 (en) 2021-05-26 2023-02-14 Hong Kong Applied Science and Technology Research Institute Company Limited Cost-effective line-scan optical coherence tomography apparatus

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