WO2019194283A1 - Dispositif ophtalmique et élément réfléchissant concave - Google Patents

Dispositif ophtalmique et élément réfléchissant concave Download PDF

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Publication number
WO2019194283A1
WO2019194283A1 PCT/JP2019/015001 JP2019015001W WO2019194283A1 WO 2019194283 A1 WO2019194283 A1 WO 2019194283A1 JP 2019015001 W JP2019015001 W JP 2019015001W WO 2019194283 A1 WO2019194283 A1 WO 2019194283A1
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Prior art keywords
light
concave reflecting
concave
reflecting surface
optical system
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PCT/JP2019/015001
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English (en)
Japanese (ja)
Inventor
泰士 田邉
泰史 西
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株式会社ニコン
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Publication of WO2019194283A1 publication Critical patent/WO2019194283A1/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 disclosed technology relates to an ophthalmic apparatus and a concave reflecting member.
  • Patent Document 1 discloses an apparatus that scans light from a light source with a fundus and acquires a fundus image based on return light from the fundus of a subject's eye.
  • a free-form mirror having a free-form surface is used as a reflecting mirror formed so as to send light to the eye to be examined and detect return light from the fundus.
  • An ophthalmologic apparatus is an ophthalmologic apparatus that includes an imaging optical system for imaging the fundus of a subject's eye.
  • the imaging optical system includes a concave reflecting member, and the concave reflecting member includes a concave reflecting surface and its concave reflecting surface. And a non-polarizing material layer provided thereon.
  • a scanning laser ophthalmoscope is referred to as “SLO”.
  • an optical coherence tomography is referred to as “OCT”.
  • an ophthalmic system 100 includes an ophthalmologic apparatus 110, an axial length measuring apparatus 120, a management server apparatus (hereinafter referred to as “management server”) 140, and an image display apparatus (hereinafter referred to as “image viewer”). 150).
  • the ophthalmologic apparatus 110 acquires a fundus image and a tomographic image of a patient's eye to be examined.
  • the axial length measuring device 120 measures the axial length of the patient's eye.
  • the management server 140 stores a plurality of fundus images, axial lengths, and tomographic images obtained by photographing the fundus of a plurality of patients by the ophthalmologic apparatus 110 corresponding to the patient IDs.
  • the image viewer 150 displays the fundus image and the tomographic image acquired by the management server 140.
  • the ophthalmologic apparatus 110, the axial length measuring apparatus 120, the management server 140, and the image viewer 150 are connected to each other via the network 130.
  • the axial length measurement device 120 has two modes, a first mode and a second mode, for measuring the axial length, which is the length in the axial direction of the eye to be examined.
  • a first mode light from a light source (not shown) is guided to the eye to be inspected, and then interference light between the reflected light from the fundus and the cornea is received, and based on an interference signal indicating the received interference light.
  • the second mode is a mode for measuring the axial length using an ultrasonic wave (not shown).
  • the axial length measurement device 120 transmits the axial length measured in the first mode or the second mode to the management server 140.
  • the axial length may be measured in the first mode and the second mode, and in this case, the average of the axial length measured in both modes is transmitted to the management server 140 as the axial length.
  • a scanning laser opthalmoscope is referred to as “SLO”.
  • the optical coherence tomography is referred to as “OCT”.
  • the ophthalmologic apparatus 110 includes an imaging device 14 and a control device 16.
  • the imaging device 14 includes an SLO unit 18 and an OCT unit 20 and acquires a fundus image of the fundus F of the eye 12 to be examined.
  • an image acquired by the SLO unit 18 is referred to as an SLO image.
  • An image acquired by the OCT unit 20 is referred to as an OCT image.
  • the control device 16 is realized by a computer having a CPU (Central Processing Unit) 16A, a RAM (Random Access Memory) 16B, a ROM (Read-Only memory) 16C, and an input / output (I / O) port 16D.
  • CPU Central Processing Unit
  • RAM Random Access Memory
  • ROM Read-Only memory
  • the control device 16 includes an input / display device 16E connected to the CPU 16A via the I / O port 16D.
  • the input / display device 16E has a graphic user interface that displays an image of the eye 12 to be examined and receives various instructions from the user. Examples of the graphic user interface include a touch panel display.
  • the control device 16 includes an image processing device 17 connected to the I / O port 16D.
  • the image processing device 17 generates an image of the eye 12 to be examined based on the data obtained by the imaging device 14.
  • the control device 16 is connected to the network 130 via the communication interface 15.
  • the data processing program is stored in the ROM 16C or the RAM 16B, and is read at the time of initial setting or startup.
  • the data processing program has a shooting control function, a display control function, an image processing function, and a processing function.
  • the CPU 16A executes the data processing program having these functions, the CPU 16A functions as a photographing control unit 202, a display control unit 204, an image processing control unit 206, and a processing unit 208 as shown in FIG.
  • the control device 16 of the ophthalmologic apparatus 110 includes the input / display device 16E, but the technology of the present disclosure is not limited to this.
  • the control device 16 of the ophthalmic apparatus 110 may not include the input / display device 16E, but may include a separate input / display device that is physically independent of the ophthalmic device 110.
  • the display device includes an image processing processor unit that operates under the control of the display control unit 204 of the CPU 16A of the control device 16, and the image processing processor unit is based on an image signal instructed to be output by the display control unit 204. An SLO image or the like may be displayed.
  • the imaging device 14 operates under the control of the imaging control unit 202 of the control device 16.
  • the imaging device 14 includes an SLO unit 18, an imaging optical system 19, and an OCT unit 20.
  • the photographing optical system 19 includes a first optical scanner 22, a second optical scanner 24, a third optical scanner 29, and a wide-angle optical system 28 as an objective optical system.
  • the photographing optical system 19 includes a combining unit 26 such as a dichroic mirror that combines the light from the SLO unit 18 and the light from the OCT unit 20 and separates the light into the SLO unit 18 and the light into the OCT unit 20.
  • the first optical scanner 22 scans the light emitted from the SLO unit 18 in the Y direction (for example, the vertical direction).
  • the second optical scanner 24 similarly scans the light emitted from the OCT unit 20 in the Y direction.
  • the third optical scanner 29 arranged in the wide-angle optical system 28 as a common optical system converts the light emitted from the SLO unit 18 and the light emitted from the OCT unit 20 in the X direction (for example, the horizontal direction). To scan. Therefore, the SLO light and the OCT light can be two-dimensionally scanned by the fundus F of the eye 12 by the third optical scanner 29 in cooperation with the first optical scanner 22 and the second optical scanner 24. It is configured as follows.
  • Each optical scanner may be any optical element that can deflect the angle of the light beam. For example, a polygon mirror, a galvanometer mirror, or the like can be used.
  • the wide-angle optical system 28 realizes observation in the fundus F with a wide field of view (FOV: Field of View) 12A.
  • the FOV 12A indicates a range that can be captured by the imaging device 14.
  • the FOV 12A can be expressed as a viewing angle.
  • the viewing angle can be defined by the internal irradiation angle and the external irradiation angle.
  • the external irradiation angle is an irradiation angle of a light beam irradiated from the ophthalmologic apparatus 110 toward the center of the pupil 27 to the eye 12 to be examined.
  • the internal irradiation angle is an irradiation angle that defines the irradiation angle of the light beam applied to the fundus F with reference to the center O of the eyeball.
  • the external irradiation angle and the internal irradiation angle have a correspondence relationship. For example, when the external irradiation angle is 120 degrees, the internal irradiation angle corresponds to about 160 degrees.
  • UWFSLO fundus image obtained by photographing at an internal field angle of 160 ° or more is referred to as a UWFSLO fundus image.
  • UWF is an abbreviation for Ultra-Widefield (super wide angle).
  • the SLO system is realized by a control device 16, an SLO unit 18, and a photographing optical system 19, as shown in FIG. Since the SLO system includes the wide-angle optical system 28, fundus imaging with a wide FOV 12A is possible.
  • the SLO unit 18 includes a light source 18A, a detection element 18B, and a beam splitter 18C. The light emitted from the light source 18A passes through the beam splitter 18C and enters the photographing optical system 19.
  • the light source 18A includes an R light (red light) light source, a G light (green light) light source, a B light (blue light) light source, an IR light (infrared (near infrared light)) light source, and a white light source. And a light source that emits light or a combination of light sources that emit light, such as a mode that emits R light and G light, and a mode that emits infrared light (for example, near infrared light).
  • the light source may not include all of the above, and may be an R light (red light) light source, a G light (green light) light source, and an infrared light (IR light) light source. Are possible.
  • the light from the SLO unit 18 incident on the photographing optical system 19 is scanned in the Y direction by the first optical scanner 22.
  • the scanning light is further scanned in the X direction by the third optical scanner 29 in the wide-angle optical system 28, and is irradiated to the fundus F through the pupil 27.
  • the reflected light reflected by the fundus F enters the SLO unit 18 via the wide-angle optical system 28, the third optical scanner 29, and the first optical scanner 22.
  • the reflected light incident on the SLO unit is reflected by the beam splitter 18C and received by the detection element 18B.
  • the detection element 18B has a plurality of detection elements corresponding to the wavelength (for example, an R light receiving element corresponding to red light, a G light receiving element corresponding to green light, an IR light receiving element corresponding to near infrared light).
  • the image processing device 17 operating under the control of the image processing control unit 206 generates an SLO image based on the signal detected by the detection element 18B.
  • the OCT system is realized by a control device 16, an OCT unit 20, and an imaging optical system 19, as shown in FIG. Since the OCT system also includes the wide-angle optical system 28, fundus imaging with a wide FOV 12A is possible.
  • the OCT unit 20 includes a light source 20A, a detection element 20B, an optical coupler 20C, a reference optical system 20D, and a collimating lens 20E.
  • the light emitted from the light source 20A is branched by the optical coupler 20C.
  • One of the branched lights is converted into parallel light by the collimator lens 20E as measurement light and then incident on the photographing optical system 19.
  • the measurement light is two-dimensionally scanned in the X and Y directions on the fundus F of the eye 12 to be examined by the second optical scanner 24, the third optical scanner 29, and the wide-angle optical system 28 via the pupil 27.
  • the measurement light reflected by the fundus F is incident on the OCT unit 20 via the wide-angle optical system 28, the third optical scanner 29, and the second optical scanner 24.
  • the other light branched by the optical coupler 20C enters the reference optical system 20D as reference light.
  • the measurement light reflected from the fundus F and the reference light are interfered by the optical coupler 20F to generate interference light.
  • the interference light is received by the detection element 20B. It operates under the control of the image processing control unit 206.
  • the image processing device 17 generates an OCT image based on the signal detected by the detection element 20B.
  • SS-OCT Session-Source OCT
  • SD-OCT Spectral-Domain OCT
  • a wide-angle optical system 28 as a common optical system includes an elliptical mirror (slit mirror) 30, an elliptical mirror 32, and a third optical scanner 29 disposed between the two.
  • Both the elliptical mirror (slit mirror) 30 and the elliptical mirror 32 have so-called spheroidal reflecting surfaces 30A and 32A.
  • the spheroidal surface is a surface formed by rotating around an axis connecting two focal points inherent to the ellipse, and both are shown as part of the ellipse in FIG.
  • the elliptical mirror 30 reflects only the scanning light in the Y direction so as to reflect the X direction.
  • the width at may be small.
  • the elliptical mirror 30 has an elongated shape extending in the Y direction and is called a slit mirror.
  • the elliptical mirror 30 may be referred to as a slit mirror 30.
  • the combining unit 26 such as a dichroic mirror, the slit mirror 30, and the elliptical mirror 32 are shown as side sectional views, but their positions are not accurate because they are for the purpose of showing the order of arrangement.
  • the reflective surface 30A of the slit mirror 30 has a first focal point P1 and a second focal point P2.
  • the first optical scanner 22 and the second optical scanner 24 are respectively arranged to coincide with the first focal point P1 via a combining unit 26 such as a dichroic mirror.
  • a third optical scanner 29 is disposed at the second focal point P2.
  • the reflecting surface 32A of the elliptical mirror 32 also has two focal points P3 and P4, one of which coincides with the focal point P2 of the reflecting surface of the slit mirror, and the other focal point P4 has a position of the eye l2 to be examined.
  • the center of the pupil is positioned.
  • the first optical scanner 22, the second optical scanner 24, and the third optical scanner 29 are each configured to have a conjugate positional relationship with the center of the pupil of the eye 12 to be examined.
  • the imaging optical system 19 in which the two elliptical mirrors 30 and 32 and the three optical scanners 22, 24 and 29 are combined, the fundus can be scanned with a light beam having an extremely wide external irradiation angle in both SLO and OCT. It has become.
  • the ophthalmologic apparatus 110 provided with an elliptical mirror can perform fundus observation with a very wide field of view as a UWF with an extremely wide external illumination angle.
  • Concave mirrors such as elliptical mirrors generally form a transparent protective film such as a resin on the metal film in order to suppress peeling of the formed metal film, for example, when the reflecting surface is formed by vapor deposition with a metal film. Is.
  • the polarization state may change due to reflection.
  • the polarization state of the signal light reflected by the reflecting surface of the elliptical mirror and the polarization state of the return light of the signal light change.
  • the resin that is the material of the protective film has birefringence
  • the protective film has light properties such as birefringence. This is probably because the polarization state is changed.
  • the amount of change in the polarization state varies depending on the reflection position of the elliptical mirror due to the stress generated when the protective film is formed, for example, pasting, and the thickness of the protective film. This is presumably because the optical path length in the protective film differs and the phase shift differs because the incident angle of light on the protective film differs depending on the incident position.
  • incident light is irradiated onto the elliptical mirror at various scanning angles by a scanning device, and reflected light from the fundus is reflected by the elliptical mirror. Reflects at various positions.
  • the light reflected by the elliptical mirror has various polarization states that differ depending on the reflection position and reflection angle.
  • the image quality is deteriorated when an OCT image is acquired.
  • the polarization state of the reference light is kept constant, the polarization directions of the signal light and the reference light are different, and the contrast of the interference light is lowered.
  • the contrast of the interference light changes, the contrast fluctuates in the entire B-Scan image, and unevenness occurs in the OCT image.
  • the elliptical mirror 32 includes a base material 32C on which a reflective surface 32A is formed, and a protective layer 32D is formed on the reflective surface 32A.
  • Non-polarizing resin for example, ultra-low birefringence resin
  • the protective layer 32D examples include resins having suppressed birefringence such as Iupizeta EP series resin manufactured by Mitsubishi Gas Chemical and OKP manufactured by Osaka Gas Chemical.
  • An example of the reflecting surface 32A is a metal reflecting surface, and examples of the metal reflecting surface include a surface reflecting mirror deposited with aluminum, gold, silver, or the like.
  • the elliptical mirror 32 is an example of a concave reflecting member according to the technique of the present disclosure.
  • the non-polarizing resin is an example of a non-polarizing material according to the technique of the present disclosure.
  • the protective layer 32D By forming the protective layer 32D with a non-polarizing resin (for example, an ultra-low birefringent resin), the birefringence in the protective layer 32D is suppressed, and the change in the polarization state when light is transmitted is suppressed.
  • a non-polarizing resin for example, an ultra-low birefringent resin
  • the birefringence in the protective layer 32D is suppressed, changes in the polarization state due to the reflection position and reflection angle in the elliptical mirror 32 are also suppressed. Therefore, the change in polarization state caused by the difference in scanning angle is suppressed by the birefringence of the protective layer 32D. Therefore, the optical performance of the elliptical mirror 32 itself can be improved.
  • the rotation direction of the circularly polarized light changes on the reflecting surface 32A.
  • signal light in a polarization state by clockwise circularly polarized light hereinafter referred to as right circularly polarized light
  • a path of measurement light and return light of the measurement light hereinafter, referred to as “measurement light” in the photographing optical system 19 is described.
  • the direction of circularly polarized light sequentially changes.
  • the polarization state of the OCT measurement light becomes counterclockwise circularly polarized light (hereinafter referred to as left circularly polarized light) reflected by the second optical scanner 24, and is slit.
  • Reflected by the mirror 30 becomes clockwise circularly polarized light (hereinafter referred to as right circularly polarized light)
  • reflected by the third optical scanner 29 becomes left circularly polarized light
  • reflected by the elliptical mirror 32 becomes right circularly polarized light.
  • the fundus reflection of the eye 12 becomes left circularly polarized light
  • the elliptical mirror 32 reflects right circularly polarized light
  • the third optical scanner 29 reflects left circularly polarized light
  • the slit mirror 30 reflects right circularly polarized light.
  • a polarization adjusting unit for example, a polarization conversion element by changing a wavelength plate such as a half-wave plate is inserted in the incident side of the optical coupler 20F, for example, a reference optical path, and the reference light is changed to a left circularly polarized light state. It is necessary to make the polarization state of the light coincide with the polarization state of the measurement light. As a result, good interference between the reference light and the measurement light can be maintained, and a clearer and higher contrast image can be generated.
  • the optical performance of the elliptical mirror 32 itself can be improved by forming the protective layer 32D with a non-polarizing resin (for example, an ultra-low birefringent resin), and image quality degradation can be reduced.
  • a non-polarizing resin for example, an ultra-low birefringent resin
  • image quality degradation can be reduced.
  • a suppressed OCT image and an OCT image in which a decrease in contrast is suppressed can be obtained.
  • the polarization state is only set by a polarization adjusting unit such as a half-wave plate, for example.
  • a polarization adjusting unit such as a half-wave plate
  • the reflecting member it is possible to reflect the scanning light having an external irradiation angle of 100 ° or more toward the eye to be examined and to receive the reflected light from the eye to be examined at the angle of 100 ° or more. It is possible to realize the above super-wide-angle optical system. Even in an ultra-wide-angle optical system exceeding 140 °, changes in the polarization state can be suppressed, and an excellent fundus cross-sectional image can be formed by so-called UWF.
  • the protective layer 32D is formed of a non-polarizing resin (for example, an ultra-low birefringent resin).
  • the protective layer is formed of a glass material instead of the protective layer 32D. .
  • the elliptical mirror 32 includes a base material 32C on which a reflective surface 32A that is a metal reflective surface is formed, and a protective layer 32E is formed on the reflective surface 32A.
  • the protective layer 32E is formed of a glass material having the same outer surface as the surface shape of the reflecting surface 32A. That is, in the elliptical mirror 32, a protective layer 32E formed of a glass material is attached to the reflecting surface 32A of the base material 32C.
  • An example of the glass material is optical glass such as quartz glass.
  • Optical glass like the non-polarizing resin, can suppress birefringence and can suppress a change in polarization state when light is transmitted. Therefore, due to the suppressed birefringence of the protective layer 32E, the change in the polarization state caused by the difference in scanning angle is suppressed, and the optical performance of the elliptical mirror 32 itself can be improved.
  • the elliptical mirror 32 as the concave reflecting member is a reflecting member provided with a metal reflecting surface on a base material. And the reflective surface was provided in the concave surface of the base material, the concave reflective surface was formed, and the said signal light which injects into the said concave reflective surface of the said reflective base material was reflected by the said concave reflective surface.
  • the material of the substrate could be an opaque material such as metal or an opaque glass.
  • the concave reflection member is a reflection member in which a metal reflection surface is formed on a base material made of a transparent glass material, and the reflection surface is provided on the convex surface of the base material.
  • An internal reflection surface is formed on the concave surface inside the material.
  • FIG. 7 An example of the third embodiment is shown in FIG. As shown in FIG. 7, in the elliptical mirror 32 as a concave reflecting member, a metal reflecting surface 32F as a reflecting layer is formed on an outer surface 32B of a base material 32E made of a transparent glass material.
  • the base material 32E itself made of a glass material is formed on the reflecting surface 32A and functions as a protective layer for the reflecting surface and also functions as a non-polarizing material layer.
  • the concave inner surface reflecting surface is formed by forming the metal reflecting surface 32F on the outer surface 32B as the convex surface of the base material 32E formed of the transparent glass material.
  • the glass material itself constituting the transparent substrate is a non-polarizing material, so that birefringence when transmitting light can be suppressed, and the structure of the elliptical mirror 32 can be simplified only by the glass material.
  • the metal reflecting surface 32F functions as an inner surface reflecting surface of the base material 32E made of a transparent glass material.
  • a protective film for preventing deterioration of the reflecting surface itself is preferably provided outside the reflecting surface.
  • the ophthalmologic system 100 including the ophthalmologic apparatus 110, the axial length measuring apparatus 120, the management server 140, and the image viewer 150 has been described as an example, but the technology of the present disclosure is not limited thereto.
  • the ocular axial length measuring device 120 may be omitted, and the ophthalmic apparatus 110 may further have the function of the axial axial length measuring device 120.
  • the ophthalmologic apparatus 110 may further have at least one function of the management server 140 and the image viewer 150. Thereby, at least one of the management server 140 and the image viewer 150 corresponding to the function of the ophthalmic apparatus 110 can be omitted.
  • the management server 140 may be omitted, and the image viewer 150 may execute the function of the management server 140.

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  • Ophthalmology & Optometry (AREA)
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Abstract

La présente invention améliore les performances d'un système optique d'imagerie pour capturer une image tomographique d'une rétine tout en amenant la lumière de signal à balayer. En formant une couche de matériau non polarisant sur une surface réfléchissante (32A) d'un élément réfléchissant concave dans un système optique d'imagerie, une variation de l'état de polarisation entre la lumière incidente et la lumière réfléchie est supprimée.
PCT/JP2019/015001 2018-04-04 2019-04-04 Dispositif ophtalmique et élément réfléchissant concave WO2019194283A1 (fr)

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JP2018072563 2018-04-04

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2020103425A (ja) * 2018-12-26 2020-07-09 株式会社トプコン 眼科装置、及びその制御方法

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JPH0943408A (ja) * 1995-08-03 1997-02-14 Canon Inc 無偏光反射鏡
JPH10332913A (ja) * 1997-05-27 1998-12-18 Asahi Optical Co Ltd 多層膜コートミラー
JPH11160013A (ja) * 1997-12-02 1999-06-18 Ricoh Co Ltd シアリング干渉計
JP2007510143A (ja) * 2003-10-27 2007-04-19 ザ・ジェネラル・ホスピタル・コーポレイション 周波数ドメイン干渉測定を利用して光学撮像を実行する方法および装置
JP2008070349A (ja) * 2006-08-15 2008-03-27 Fujifilm Corp 光断層画像化装置
JP2015534482A (ja) * 2012-10-01 2015-12-03 オプトス ピーエルシー 走査型レーザー・オフサルモスコープにおける改良または走査型レーザー・オフサルモスコープに関する改良
JP2016126326A (ja) * 2014-12-26 2016-07-11 富士フイルム株式会社 反射材、光学部材、ディスプレイおよび画像表示装置

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH0943408A (ja) * 1995-08-03 1997-02-14 Canon Inc 無偏光反射鏡
JPH10332913A (ja) * 1997-05-27 1998-12-18 Asahi Optical Co Ltd 多層膜コートミラー
JPH11160013A (ja) * 1997-12-02 1999-06-18 Ricoh Co Ltd シアリング干渉計
JP2007510143A (ja) * 2003-10-27 2007-04-19 ザ・ジェネラル・ホスピタル・コーポレイション 周波数ドメイン干渉測定を利用して光学撮像を実行する方法および装置
JP2008070349A (ja) * 2006-08-15 2008-03-27 Fujifilm Corp 光断層画像化装置
JP2015534482A (ja) * 2012-10-01 2015-12-03 オプトス ピーエルシー 走査型レーザー・オフサルモスコープにおける改良または走査型レーザー・オフサルモスコープに関する改良
JP2016126326A (ja) * 2014-12-26 2016-07-11 富士フイルム株式会社 反射材、光学部材、ディスプレイおよび画像表示装置

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2020103425A (ja) * 2018-12-26 2020-07-09 株式会社トプコン 眼科装置、及びその制御方法
JP7231405B2 (ja) 2018-12-26 2023-03-01 株式会社トプコン 眼科装置、及びその制御方法

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