CN100998495B - Fundus observation device - Google Patents

Fundus observation device Download PDF

Info

Publication number
CN100998495B
CN100998495B CN 200710000924 CN200710000924A CN100998495B CN 100998495 B CN100998495 B CN 100998495B CN 200710000924 CN200710000924 CN 200710000924 CN 200710000924 A CN200710000924 A CN 200710000924A CN 100998495 B CN100998495 B CN 100998495B
Authority
CN
Grant status
Grant
Patent type
Prior art keywords
fundus
unit
light
optical
oculi
Prior art date
Application number
CN 200710000924
Other languages
Chinese (zh)
Other versions
CN100998495A (en )
Inventor
大塚浩之
弓挂和彦
福间康文
Original Assignee
株式会社拓普康
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Grant date

Links

Abstract

A fundus observation device which can simultaneously capture both surface images and tomographic images of the fundus oculi is provided. The fundus observation device (1) has a fundus camera unit (1A), an OCT unit (150), and an arithmetic and control unit (200). The fundus camera unit (1A) has an illuminating optical system (100) and an imaging optical system (120). The arithmetic and control unit (200) forms the surface image of fundus oculi Ef based on signals from fundus camera unit (1A). The OCT unit (150) divides low coherence light LO into the signal light LS and the reference light LR,and detects the interference light LC that can be obtained from the signal light LS passing through fundus oculi Ef and the reference light LR passing through reference mirror (174). The arithmetic and control unit (200) forms tomographic images of fundus oculi Ef based on these detecting results. A Dichroic mirror (134) combines the optical path of the signal light LS toward fundus oculi Ef intothe optical path for imaging of the imaging optical system (120), and separates the optical path of the signal light LS towards fundus oculi Ef from the optical path for imaging.

Description

眼底观察装置 A fundus observation device

技术领域 FIELD

[0001] 本发明关于用于观察受检眼的眼底状态的眼底观察装置。 [0001] The present invention relates to a fundus observation state of the examinee's eye fundus observation device. 背景技术 Background technique

[0002] 作为眼底观察装置,先前以来广泛使用眼底相机。 [0002] As a fundus observation device, since the previously widespread use of fundus cameras. 图9表示先前普通眼底相机的外观结构的一例,图10表示内设在其中的光学系统结构的一例(例如,参照日本专利特开2004-350849号公报。)。 9 shows a general configuration of a previous one case the appearance of the retinal camera, FIG. 10 shows an example of the system configuration of a site in which an optical (e.g., refer to Japanese Patent Laid-Open Publication No. 2004-350849.). 另外,所谓“观察”,至少包含观察眼底的拍摄图像的情形(另外, 也可以包含通过肉眼而进行的眼底观察)。 Further the case of the captured image, the so-called "observation" includes at least observe the fundus (Further, the fundus may comprise carried out by visual observation).

[0003] 首先,参照图10,对先前的眼底相机1000的外观结构进行说明。 [0003] First, referring to FIG. 10, the external configuration of the fundus camera 1000 previously described. 该眼底相机1000 具备台架3,该台架3以可在前后左右方向(水平方向)滑动的方式搭载于基座2上。 The fundus camera 1000 includes a carriage 3, the carriage 3 is slidable manner around the horizontal direction (horizontal direction) is mounted to the base 2. 在该台架3上,设置有检查者用以进行各种操作的操作面板及控制杆4。 On the stage 3 is provided with a check and control lever of the manipulation panel 4 for performing various operations.

[0004] 检查者通过操作控制杆4,而能够使台架3在基座2上进行三维的自由移动。 [0004] inspection by operating the control lever 4, so that the carriage 3 can be freely moved three-dimensionally on the base 2. 在控制杆4的顶部,配置有要求执行眼底拍摄时而按下的操作按钮如。 At the top of the control rod 4 is arranged fundus photographing sometimes required to perform an operation button such as a press.

[0005] 在基座2上立设有支柱5,并且在该支柱5上,设置有用于载置被检查者的颚部的颚托6、及作为用以发出使受检眼E视线固定视的光源的外部视线固定视灯7。 [0005] 2 erected on the base strut 5, and on the strut 5, is provided for mounting the jaw holder 6 of the jaw portion of the subject, and so as to emit a fixation sight of the examinee's eye E sight external light source a fixation lamp 7.

[0006] 在台架3上,搭载有容置存储眼底相机1000的各种光学系统与或控制系统的本体部8。 [0006] In the carriage 3, there is mounted a body portion accommodating various optical systems stored in the retinal camera 1000 or the control system 8. 另外,控制系统可以设在基座2或台架3的内部等中,也可以设在连接于眼底相机1000的电脑等的外部装置中。 Further, the control system may be provided inside the base 2 or the like in the gantry 3, may be provided in an external device connected to the fundus camera 1000 in computers and the like.

[0007] 在本体部8的受检眼E侧(图9的纸面之左方向),设有与受检眼E相对向而配置的物镜部8A。 [0007] In the examinee's eye E side (FIG Zhizuo drawing direction 9) of the body portion 8, 8A provided with the objective lens unit and arranged opposite to the examinee's eye E. 又,在本体部8的检查者这一侧(图9的纸面之右方向),设有用肉眼观察受检眼E之的眼底的目镜部汕。 And, (right hand direction in the paper surface in FIG. 9), is provided with the naked eye fundus of the examinee's eye E Shantou eyepiece portion 8 in the main body portion of the side of the examiner.

[0008] 而且,本体部8上设置有:用以拍摄受检眼E眼底的静止图像照相机9 ;及用以拍摄眼底的静止图像或动态图像的电视摄像机等摄像装置10。 [0008] Further, the body portion 8 is provided: a camera for capturing a still image of the fundus of the examinee's eye E 9; and an imaging apparatus for capturing a still image or dynamic image of the fundus of the television camera 10 and the like. 静止图像照相机9及摄像装置10可安装或脱离于本体部8。 Still image camera 9 and the imaging device 10 may be mounted or detached from the main body portion 8.

[0009] 静止图像照相机9,根据检查的目的或拍摄图像的保存方法等各种条件,可以适当使用搭载有CCD (Charge Coupled Device,电荷耦合器件)或CMOS (Complementary Metal Oxide Semicondutor,互补金属氧化半导体)等摄像组件的数码相机(digital camera)、胶片相机(film camera)、一次成像相机(instant camera)等。 [0009] The still image camera 9, in accordance with various conditions like object or the storage method of checking the captured image can be appropriately used equipped with CCD (Charge Coupled Device, Charge Coupled Device) or CMOS (Complementary Metal Oxide Semicondutor, Complementary Metal Oxide Semiconductor digital cameras) and other components of the camera (digital camera), film camera (film camera), Polaroid camera (instant camera) and so on. 在本体部8设有安装部8c, 该安装部8c用于以可更换的方式安装这样的静止图像照相机9。 8 is provided in the main body portion mounting portion 8c, 8c of the mounting portion for mounting in a replaceable manner such still image camera 9.

[0010] 静止图像照像机9或摄像装置10为数码摄像方式的场合,可将该些摄影的眼底图像之影像数据,传送到与眼底相机1000连接的计算机等,在显示器上显示与观察眼底图像。 [0010] The still image camera 9 or imaging device 10 is a case where the digital camera mode, the image data may be an image of the fundus photography more, transferred to the computer connected to the retinal camera 1000, and displays on the display the fundus observation image. 又,可将图像数据传送到与眼底相机1000连接的图像记录装置,并数据库化,可用于作为制作电子病历的电子数据。 Further, to transfer the image data to the image recording apparatus is connected to the retinal camera 1000, and a database that can be used as electronic data produced EMR.

[0011] 另外,在本体部8的检查者设有触摸屏11。 [0011] Further, the body portion 8 examiner touch panel 11 is provided. 该触摸屏11上显示根据从(数字方式的)静止图像照相机9或摄像装置10输出的图像信号而制作的受检眼E的眼底像。 11 displayed on the touch screen 10 a fundus image of the image signal output from the still image camera 9 or imaging device (digital system) produced from the examinee's eye E based. 而且, 在触摸屏11上,使以其画面中央为原点的xy坐标系重叠显示在眼底像上。 Moreover, on the touch screen 11, so that its center of the screen as an origin of the xy coordinate system is superimposed and displayed on the fundus image. 当检查者在画面上触摸所要的位置时,显示与该触摸位置对应的坐标值。 When the examiner touches a desired position on the screen, display coordinate values ​​corresponding to the touch position.

[0012] 接着,参照图10,说明眼底相机1000的光学系统的结构进行。 [0012] Next, with reference to FIG. 10, the configuration of the optical system of the retinal camera 1000 is performed. 眼底相机1000中设有:照亮受检眼E的眼底Ef的照明光学系统100 ;以及将该照明光的眼底反射光引导向目镜部8b、静止图像照相机9、摄像装置10的拍摄光学系统120。 A fundus camera 1000 is provided with: illuminating a fundus Ef of the examined eye E the illumination optical system 100; and the fundus reflection light of the illumination light guide 9, the imaging means imaging optical system 120 to an eyepiece section 8B, a still image camera 10 .

[0013] 照明光学系统100包含观察光源101、聚光镜102、拍摄光源103、聚光镜104、激发滤光片105及106、环形透光板107、镜片108、液晶显示器109、照明光圈110、中继透镜111、 开孔镜片112、物镜113而构成。 [0013] The illumination optical system 100 comprises an observation light source 101, condenser lens 102, an imaging light source 103, condenser lens 104, an excitation filter 105 and 106, a ring transparent plate 107, a lens 108, a liquid crystal display 109, an illumination diaphragm 110, a relay lens 111, the lens aperture 112, objective lens 113 is configured.

[0014] 观察光源101,例如用卤素灯构成,发出观察眼底用的固定光(连续光)。 [0014] The observation light source 101, a halogen lamp, for example, emit light for fundus observation fixation (continuous light). 聚光镜102为用以将观察光源发出的固定光(观察照明光)聚光,并使该观察照明光大致均勻地照射到受检眼底的光学组件。 A condenser lens 102 is fixed to the observation light (observation illumination light) emitted from a spot light, and the observation illumination light substantially uniformly irradiated to the fundus of the subject optical assembly.

[0015] 拍摄光源103,例如由氙气灯构成,是在对眼底Ef进行拍摄时进行闪光的拍摄光源。 [0015] The imaging light source 103, for example, a xenon lamp, the light source is a flash photographing when photographing the fundus Ef. 聚光镜104是用以将拍摄光源103所发出的闪光(拍摄照明光)聚光,并使拍摄照明光均勻地照射到眼底Ef的光学组件。 The condenser lens 104 is used for flash photographing (imaging illumination light) emitted by the light source 103 is condensed, and the imaging illumination light is uniformly irradiated to the optical components of the fundus oculi Ef.

[0016] 激发滤光片105、106是在对眼底Ef的眼底像进行荧光拍摄时所使用的滤光片。 [0016] The excitation filters 105 and 106 filter the fundus when the fundus oculi Ef images used for fluorescence imaging. 激发滤光片105、106分别通过螺线管(solenoid)等驱动机构(未图示)而可插拔地设置在光路上。 Excitation filters 105 and 106 by a solenoid (Solenoid) as a drive mechanism (not shown) is detachably disposed on the optical path. 激发滤光片105在FAG(荧光素荧光造影)拍摄时配置在光路上。 Excitation filter 105 arranged on the optical path at the time of FAG (fluorescein angiography) imaging. 另一方面,激发滤光片106在ICG(靛青绿荧光造影)拍摄时配置在光路上。 On the other hand, excitation filter 106 arranged on an optical path when the ICG (indocyanine green angiography fluorescence) imaging. 另外,在进行彩色拍摄时,激发滤光片105、106—同从光路上退出。 In addition, during the shooting of color, with an excitation filter 105,106- withdraw from the optical path.

[0017] 环形透光板107具备环形透光部107a,该环形透光部107a配置在与受检眼E的瞳孔共轭的位置上,并以照明光学系统100的光轴为中心。 [0017] The ring transparent plate 107 includes an annular light transmitting portion 107a, 107a of the annular light transmitting portion disposed at a position with the pupil of the examinee's eye E on the conjugate, and the optical axis of the illumination optical system 100 as a center. 镜片108使观察光源101或拍摄光源103所发出的照明光,向拍摄光学系统120的光轴方向反射。 Lens 108 so that an observation light source 101 or the imaging illumination light emitted from the light source 103, reflected toward the optical axis direction of the photographing optical system 120. 液晶显示器109显示用以进行受检眼E的视线固定的视线固定标(未图示)。 The liquid crystal display 109 displays visual line of sight fixed standard fixed (not shown) for performing the subject eye E.

[0018] 照明光圈110是为了防闪等而阻挡一部分照明光的光圈构件。 [0018] The illumination diaphragm 110 is a diaphragm member in order to prevent flash like blocking part of the illumination light. 该照明光圈110 可以在照明光学系统100的光轴方向上移动,因此,可以调整眼底Ef的照明区域。 The illumination diaphragm 110 may be moved in the optical axis direction of the illumination optical system 100, thus, can adjust the illumination area of ​​the fundus oculi Ef.

[0019] 开孔镜片112是将照明光学系统100的光轴与拍摄光学系统120的光轴合成的光学组件。 [0019] The opening 112 is an optical lens assembly axis of the illumination optical system 100 and the optical axis of the photographing optical system 120 synthesis. 在开孔镜片112的中心区域开有孔部112a。 Opening 112 in the central area of ​​the lens opening hole portion 112a. 照明光学系统100的光轴与拍摄光学系统120的光轴在该孔部11¾的大致中心位置交叉。 The optical axis of the illumination optical system 100 and the optical axis of the photographing optical system 120 cross at substantially the center of the hole portion 11¾ position. 物镜113设在本体部8的物镜部8a 内。 An objective lens 113 provided in the lens portion 8a of the body portion 8.

[0020] 具有这样的结构的照明光学系统100,是以下面所述的形态照亮眼底Ef。 [0020] The illumination optical system 100 having such a structure, the following form is illuminated fundus Ef. 首先,在观察眼底时,点亮观察光源101,输出观察照明光。 First, at the time of fundus observation, the observation light source 101 is lit, the illumination light output was observed. 该观察照明光经过聚光镜102、104而照射环形透光板107,(此时,激发滤光片105、106从光路上退出)。 This observation illumination light is irradiated through a condenser lens 102, an annular light transmitting plate 107, (in this case, excitation filter 105, 106 to exit from the optical path). 通过环形透光板107的环形透光部107a的光由镜片108所反射,且经过液晶显示器109、照明光圈110及中继透镜111,并由开孔镜片112反射。 Transmitting plate by an annular light transmitting portion 107a of the loop 107 is reflected by the mirror plate 108, and through the liquid crystal display 109, the illumination diaphragm 110 and the relay lens 111, the lens 112 by the reflecting apertures. 由开孔镜片112反射的观察照明光沿拍摄光学系统120的光轴方向进行,经物镜113聚焦而射入受检眼E,照亮眼底Ef。 Lens 112 is reflected by the observation illumination light apertures in the optical axis direction of the shooting optical system 120 is, via the objective lens 113 and is incident on the examinee's eye focus E, to illuminate the fundus Ef.

[0021] 此时,由于环形透光板107配置在与受检眼E的瞳孔共轭的位置上,因此在瞳孔上形成射入受检眼E的观察照明光的环状像。 [0021] At this time, since the ring transparent plate 107 disposed at a position with the pupil of the examinee's eye E on the conjugate, thereby forming incident on the examinee's eye E is observed as an annular illumination light on the pupil. 观察照明光的眼底反射光,通过瞳孔上的环形像的中心暗部而从受检眼E射出。 Observe the fundus reflection light of the illumination light, emitted from the examinee's eye E through the central dark part of the ring image on the pupil. 如此,可防止射入受检眼E的观察照明光,对眼底反射光的影响。 Thus, observation is possible to prevent the illumination light incident on the examinee's eye E, the impact on the fundus reflection light.

[0022] 另一方面,在拍摄眼底Ef时,拍摄光源103进行闪光,且拍摄照明光通过同样的路径而照射到眼底Ef。 [0022] On the other hand, when photographing the fundus Ef, the flash photographing light source 103 and the imaging illumination light is irradiated onto the fundus oculi Ef through the same path. 当进行荧光拍摄时,根据是进行FAG拍摄还是进行ICG拍摄,而使激发滤光片105或106选择性地配置在光路上。 When fluorescence photography, is according to FAG imaging or ICG imaging performed, the excitation filter 105 or 106 is selectively disposed in the optical path.

[0023] 其次,说明拍摄光学系统120,拍摄光学系统120包含物镜113、开孔镜片112(的孔部112a)、拍摄光圈121、阻挡滤光片122及123、倍率可变透镜124、中继透镜125、拍摄透镜126、快速复原反射镜片(quick returnmirror)127及拍摄媒体9a而构成。 [0023] Next, the photographing optical system 120, imaging optical system 120 includes an objective lens 113, the lens aperture 112 (hole portion 112a), the photographing diaphragm 121, barrier filters 122 and 123, a variable magnification lens 124, a relay lens 125, imaging lens 126, a quick return mirror plate (quick returnmirror) 127 and imaging media 9a is configured. 另外,拍摄媒体9a是静止图像照相机9的拍摄媒体(CCD、相机胶卷、一次成像胶卷等)。 Furthermore, the photographing media 9a is a still image taken by the camera 9 of the medium (the CCD, camera film, a film image, etc.).

[0024] 通过瞳孔上的环状像的中心暗部而从受检眼E射出的照明光的眼底反射光,通过开孔镜片112的孔部11¾而入射拍摄光圈121。 [0024] through a central dark part of the ring image on the pupil of the examinee's eye E is emitted from the fundus reflection light of the illumination light, through the hole portion 112 of the lens aperture 11¾ photographic stop 121 is incident. 开孔镜片112的是反射照明光的角膜反射光,并且不使角膜反射光混入到射入拍摄光圈121的眼底反射光中。 Opening the lens 112 is reflected cornea reflection light of the illumination light and the reflected light is not mixed into the cornea imaging the fundus reflection light is incident on the diaphragm 121. 以此,可抑制观察图像或拍摄图像上产生闪烁(flare)。 In this, flicker is generated (FLARE) on the observation image or the captured image can be suppressed.

[0025] 拍摄光圈121是形成有大小不同的多个圆形透光部的板状构件。 [0025] The photographing diaphragm 121 is formed with a plurality of different sizes of circular plate-like light transmitting member portions. 多个透光部构成光圈值(F值)不同的光圈,通过未图示的驱动机构,选择性地将一个透光部配置在光路上。 A plurality of light-transmitting portions constitute different iris aperture value (F value), by a drive mechanism (not shown), a light transmitting portion selectively disposed in the optical path.

[0026] 阻挡滤光片122、123通过螺线管等的驱动机构(未图示)而可插拔地设置在光路上。 [0026] The barrier filters 122 and 123 by a drive mechanism such as a solenoid (not shown) is detachably disposed on the optical path. 在进行FAG拍摄时,使阻挡滤光片122配置在光路上,在进行ICG拍摄时,使阻挡滤光片123插在光路上。 During FAG imaging, the barrier filter 122 is disposed on the optical path, during ICG imaging, the barrier filter 123 is inserted in the optical path. 而且,在进行彩色拍摄时,阻挡滤光片122、123—同从光路上退出。 Moreover, during the shooting of color, the same blocking filter 122,123- withdraw from the optical path.

[0027] 倍率可变透镜IM可以通过未图示的驱动机构而在拍摄光学系统120的光轴方向上移动。 [0027] The variable magnification lens IM by unillustrated drive means is moved in the optical axis direction of the photographing optical system 120. 以此,可以变更观察倍率或拍摄倍率,并可以进行眼底像的聚焦等。 With this, you can change the observation magnification or shooting magnification, and can be focused fundus image and so on. 拍摄透镜126 是使来自受检眼E的眼底反射光在拍摄媒体9a上成像的透镜。 Photographing lens 126 is reflected from the fundus of the examinee's eye E in the imaging lens imaging light on the medium 9a.

[0028] 快速复原反射镜片127设置成可以通过未图示的驱动机构而绕着旋转轴127a进行旋转。 [0028] The quick return mirror plate 127 can be provided by a drive mechanism (not shown) is rotated around the rotation axis 127a. 当以静止图像照相机9进行眼底Ef的拍摄时,将斜设在光路上的快速复原反射镜片127向上方掀起,从而将眼底反射光引导向拍摄媒体9a。 When photographing the fundus oculi Ef still image camera 9, provided in the swash quick return mirror plate 127 off the optical path upwardly, so as to guide the fundus reflection light to the imaging media 9a. 另一方面,当通过摄像装置10 进行眼底拍摄时或通过检查者的肉眼进行眼底观察时,快速复原反射镜片127斜设配置在光路上,从而使眼底反射光朝向上方反射。 On the other hand, when the fundus observation by photographing a fundus image pickup device 10 by visual inspection or by the quick return mirror plate 127 disposed on the optical path as obliquely arranged, so that the reflected light toward the fundus reflected upward.

[0029] 拍摄光学系统120中更设有用以对由快速复原反射镜片127所反射的眼底反射光进行导向的向场透镜(视场透镜)128、切换镜片129、目镜130、中继透镜131、反射镜片132、拍摄透镜133及摄像组件10a。 [0029] The photographing optical system 120 is provided to more 129, an eyepiece 130, a relay lens 131 facing field lens (field lens) 128, is guided by the lens switching the quick return mirror plate 127 of the fundus reflected light, a reflective lens 132, imaging lens 133 and an imaging assembly 10a. 摄像组件IOa是内设于摄像装置10中的CXD等摄像组件。 IOa imaging assembly is internally provided CXD like imaging device 10 of the imaging assembly. 在触摸屏11上,显示由摄像组件IOa所拍摄的眼底图像Ef'。 11 on the touch screen, displaying a fundus image Ef by the imaging assembly IOa captured '.

[0030] 切换镜片1¾与快速复原反射镜片127同样,能够以旋转轴129a为中心而旋转。 [0030] handover 1¾ lens and the quick return mirror plate 127 Similarly, the rotation shaft 129a can be rotated centering. 该切换镜片1¾在通过肉眼进行观察时斜设在光路上,从而反射眼底反射光而将其引导向接目镜130。 The switching lens 1¾ when viewed by the naked eye obliquely disposed on the optical path so as to reflect the fundus reflection light which is guided to the eyepiece 130.

[0031] 另外,在使用摄像装置10拍摄眼底图像时,切换镜片1¾从光路退出,将眼底反射光导向摄像组件10a。 [0031] Furthermore, when the fundus image 10 captured using the imaging apparatus, the optical path switching 1¾ exit lens, the fundus reflection light guide imaging assembly 10a. 在此场合,眼底反射光经过中继透镜131从镜片132反射,由拍摄透镜133在摄像组件IOa上成像。 In this case, the fundus reflection light passes through the relay lens 131 from reflective lens 132, the imaging by the imaging lens 133 on the imaging assembly IOa.

[0032] 此种眼底相机1000,是用以观察眼底Ef的表面,即观察视网膜的状态的眼底观察装置。 [0032] Such a fundus camera 1000, is to observe the surface of the fundus oculi Ef, the fundus observation device that is observed in the state of the retina. 换言之,眼底相机1000,为从受检眼E的角膜方向所见的眼底Ef的二维眼底像的拍摄装置。 In other words, a fundus camera 1000, a two-dimensional fundus photographing apparatus seen in a direction from the cornea of ​​the examinee's eye E of the image of the fundus oculi Ef. 另一方面,在视网膜的深层存在称为脉络膜或巩膜的组织,希望有观察该些深层组织的状态的技术,而近来观察该些深层组织的装置之实用化已有进步(例如参照日本专利特开2003-543号公报,特开2005-241464号公报)。 On the other hand, in the presence of the deep retinal or choroidal tissue called the sclera, the state of the art these desired deep tissue was observed, while the recent observation of the practical means of these deep tissues has been progress (see Japanese Patent Laid No. 2003-543, JP-A No. 2005-241464 Gazette).

[0033] 在日本专利特开2003-543号公报、特开2005-241464号公报中所揭示的眼底观察装置,是应用了所谓的OCT (Optical Coherence Tomography,光学相干断层成像)技术的光图像计测装置(也称为光学相干断层成像装置等)。 [0033] In Japanese Patent Laid-Open Publication No. 2003-543, Laid-Open Publication No. 2005-241464 fundus oculi observation device disclosed in, is the application of a so-called OCT (Optical Coherence Tomography, optical coherence tomography) optical image technology measuring apparatus (also called an optical coherence tomographic imaging apparatus and the like). 这样的眼底观察装置是将低相干光分成两部分,将其中一部分(信号光)引导向眼底,将另一部分(参照光)引导向预定的参照物体,并且,对将经过眼底的信号光与由参照物体所反射的参照光重叠而获得的干涉光进行检测并解析,借此可以形成眼底表面乃至深层组织的断层图像,或眼底的三维图像的装置。 Such a fundus oculi observation device is a low-coherence light into two parts, in which a portion (signal light) is guided to the fundus, another portion (reference light) guided predetermined reference object to, and, on the via signal light by the fundus Referring reference light reflected by an object obtained by superimposing the interference light detected and resolved, whereby the apparatus can form a three-dimensional image of the fundus tomographic image of a fundus surface and the deep tissue, or. 此种图像称为光学CT图像或OCT图像。 Such an image is called an optical CT image or OCT image.

[0034] 为了详细把握眼底的状态(疾病的有无等),能够考虑及观察网膜等的眼底表面状态,及脉络膜或巩膜等深层组织状态双方较佳。 [0034] In order to grasp in detail the state of the fundus (the presence or absence of disease and the like), and can be considered to observe the surface state of the fundus of the omentum, and deep tissue status as choroid or sclera both preferred. 即仅观察由眼底相机所得的眼底图像,难以把握深层组织的详细状态。 That is observed only by the fundus image obtained fundus camera, difficult to grasp in detail the state of deep tissue. 又仅观察由光学图像测计装置所得的眼底图像,亦难以把握视网膜整体的详细状态。 And the obtained fundus image was observed only by an optical image measuring meter apparatus also difficult to grasp in detail the state of the entire retina.

[0035] 又为综合判断眼底的状态,最好能够考虑视网膜及深层组织双方的状态病情等。 [0035] but also for the state comprehensive evaluation of the fundus, it is best to consider both the retina and the state of the disease and other deep tissue. 即为了要提高病情等的判断精确度,希望能参考更多的信息,又能够参考由多方面的角度获得的信息最理想。 I.e., in order to improve the accuracy of the determination condition and the like, you can refer to more desirable information, and reference information can be best obtained by a variety of angles.

[0036] 因此,希望用一种眼底观察装置,能够取得眼底相机拍摄的眼底图像及光学图像测计装置所得的眼底图像两者。 [0036] Accordingly, it is desirable in a fundus observation device, a fundus image can be acquired both a fundus image obtained altimeter apparatus and an optical image of the fundus camera. 特别是,如果能够同时拍摄两者的眼底图像,则可观察在其中之一的眼底图像的拍摄中,可观察另一眼底图像的眼底状态,可实现更详细的诊断。 In particular, if both capable of capturing the fundus image while photographing a fundus image can be observed in one of which may be observed state of the other fundus image of the fundus, a more detailed diagnosis can be achieved.

[0037] 但是用先前的眼底观察装置,要获得眼底相机拍摄的眼底表面的二维图像,及由光学图像测计装置摄取的眼底的断层图像或三维图像两者极为困难。 [0037] However, with the fundus oculi observation device prior to a two-dimensional image of the fundus surface of a fundus camera and a tomographic image or a three-dimensional image is extremely difficult both by the optical image pickup apparatus altimeter fundus. 特别是要同时取得双方的眼底图像更为困难。 In particular fundus image of both sides at the same time more difficult to obtain.

[0038] 又,要形成能够获得由眼底相机的眼底图像及用光学图像测计装置的眼底图像双方的眼底观察装置,需要在信号光通过眼底相机的光学系统照射眼底的同时,将通过眼底的信号光引导与参照光重叠的构造,亦即,利用以眼底相机的光学系统引导信号光,可以取得与眼底相机拍摄的图像相同的眼底上位置的断层图像,可详细观察该眼底位置的状态。 [0038] and, to be formed at the same time possible to obtain an optical system irradiating the fundus by the fundus image of the fundus camera and a fundus image of the optical image measuring meter apparatus fundus observation device, which would require the signal light through the fundus camera, and through fundus guiding the signal light and the reference light overlap configuration, i.e., an optical system of a fundus camera to use a pilot signal light, a tomographic image can be obtained on the same fundus camera and the image capturing position of the fundus, the fundus position state of the observable detail.

[0039] 但是,在使用眼底相机的光学系统引导信号光的构造的场合,因信号光要通过比先前的光学图像测计装置更多的光学组件,故由该些光学组件的色散影响,使信号光与参照光的干涉效率减低,恐难产生足够强度的干涉光。 [0039] However, in the case of using a fundus camera configured to guide a signal light optical system, due to the signal light by an optical image measuring apparatus than the previous count more optical components, so that the influence by the dispersion of the plurality of optical components, so that the interference efficiency of the signal light and the reference light is reduced, converting an interference light of sufficient intensity. 依据如此的强度不充分的干涉光形成图像时,该OCT图像会发生对比度低且不清析的图像,或成精确度低的图像等的问题。 When insufficient interference light to form an image based on such strength, low contrast and unclear image resolution of the OCT image may occur, or a problem of low accuracy of the image or the like.

[0040] 又先前的光学图像测计装置,对信号光与参照光各别所受的色散影响的差异,虽然说在图像处理时有做修正等的处置。 [0040] and a previous optical image measuring meter device, an optical difference signal and a reference light dispersion effect in the individual suffered, although there do disposal correction like in the image processing. 但在可由眼底相机拍摄眼底图像,与由光学图像测计装置获得眼底图像双方的眼底观察装置,因信号光通过的光学组件的个数,与参照光通过的光学组件的个数有甚大差异,故对信号光的色散影响与对参照光的色散影响也有大差异,所以在图像处理时难以充分修正。 However, by the fundus camera in fundus photographing image, the fundus image is obtained both by the fundus oculi observation device of the optical image measuring meter apparatus, the number of optical components due to the number of optical components by the signal light, the reference light passing through a very big difference, Therefore, the dispersion effect on the signal light and the reference light effect on the dispersion also has a large difference, it is difficult to sufficiently corrected in image processing.

发明内容 SUMMARY

[0041] 本发明为解决上述的问题,其目的在于提供一种眼底观察装置,能够取得眼底表面的图像与眼底的断层图像双方,特别是能够同时取得双方的眼底图像。 [0041] The present invention is to solve the above problems, and its object is to provide a fundus oculi observation device, it is possible to obtain both a fundus image and a tomographic image of a fundus surface, in particular the fundus image can be acquired both simultaneously.

[0042] 又本发明的其它目的为提供一面眼底观察装置,能够获得眼底表面图像以及眼底断层图像双方,并能够抑制在光学图像测计时,信号光与参照光的干涉效率的减低。 [0042] Still other object of the present invention to provide a fundus observation device side, it is possible to obtain both a fundus image and the surface of the fundus tomographic image, and an optical image measurement timing can be suppressed, the interference efficiency of the signal light and the reference light in reduced.

7[0043] 为了达成上述目的,本发明的第一形态是一种眼底观察装置其特征为包括:第一图像形成元件、第二图像形成元件以及光路合成分离机构。 7 [0043] To attain the above object, a first aspect of the present invention is a fundus observation apparatus characterized by comprising: a first image forming element, the second image forming element, and the light path combiner and splitter means. 第一图像形成元件具有照明光学系统,其发出照亮受检眼的眼底的照明光;以及拍摄光学系统,用第一检测元件检测出通过前述眼底的照明光,其中依据前述第一检测元件的检测结果,形成前述眼底表面的二维图像。 A first image forming element having an illumination optical system that emits illumination light to illuminate the fundus of the examinee's eye; and an imaging optical system, the illumination light detected by the first detection element with the fundus, wherein the first detection element according to the a detection result, a two-dimensional image of the fundus surface. 第二图像形成元件具有光源,能够输出与前述照明光不同波长的光;干涉光发生元件,将前述光源输出的光,分割成向眼底的信号光及向参照物体的参照光,并将经过前述眼底的信号光与通过前述参照物体的参照光进行重叠而发生干涉光;以及第二检测元件,用以检测出前述发生的前述干涉光,其中依据前述第二检测元件的检测结果,形成前述眼底的断层图像。 The second image forming element having a light source capable of outputting light of the illumination light of different wavelengths; interference light generating element, light output from the light source, into reference light and signal light to the fundus of the reference object, and after the the signal light and the fundus via the reference object and the reference light overlap occurs interference light; and a second detection element for detecting the occurrence of the interference the fundus of the light, which according to the detection result of the second detection element is formed tomographic image. 光路合成分离机构,前述信号光的眼底反射光藉由前述拍摄光学系统所形成的拍摄光路被引导到前述光路合成分离机构,并由前述光路合成分离机构件从前述拍摄光路分离而射向前述第二图像形成元件。 The light path combiner and splitter means, the fundus reflected the signal light of the light by the shooting optical path the photographing optical system is formed is guided to the optical path synthesizing separating mechanism, synthetic separating mechanism member by the optical path from the photographing optical path separated toward the first second image forming element. 其中前述照明光与前述信号光,经前述拍摄光路照射前述眼底。 Wherein the illumination light and the signal light through the fundus photographing optical path of the illumination. 前述照明光学系统包括:环形透光板,配置在与前述受检眼的瞳孔为共轭的位置,且前述照明光通过前述环形透光板。 The illumination optical system comprising: a ring-shaped transparent plate disposed at a position with the pupil of the examinee's eye are conjugate, and the illumination light passes through the ring transparent plate. 前述照明光学系统与前述拍摄光学系统包括:开孔镜片,在中心区域具有孔部,前述开孔镜片使来自前述照明光学系统的照明光反射,前述照明光与前述信号光的眼底反射光通过前述孔部。 The illumination optical system and the photographing optical system comprising: a lens aperture, a hole portion in the central area, the lens aperture of the illumination light reflected from said illumination optical system, the illumination light and the fundus reflection light of the signal light by the hole.

[0044] 另外,本发明的第二形态为在第一形态的眼底观察装置中,干涉光发生元件包括色散付与元件,用以将色散量付与给前述参照光。 [0044] Further, a second aspect of the present invention in a first aspect of the fundus oculi observation device, the interference light generating element comprises a dispersive element imparting to the dispersion amount to pay and the reference light.

[0045] 本发明的第三形态为在第二形态的眼底观察装置中,前述色散付与元件付与前述参照光的色散量,与前述信号光从前述干涉光发生元件分割后到前述重叠止的期间被付与的色散量大约相等。 [0045] The third aspect of the present invention is the second aspect of the fundus observation device, the dispersion imparting device to impart the amount of dispersion the reference light, and the signal light from the element dividing the interference light occurs to during the overlap ending approximately equal to the amount of dispersion to be paid with.

[0046] 又本发明的第四形态为在第一形态的眼底观察装置中,前述干涉光发生元件从进行前述分割至前述重叠的期间,前述信号光经过多数个光学组件的色散量的合计值,与前述干涉光发生元件从进行前述分割至前述重叠的期间,前述参照光经过多数个光学组件的色散量的合计值大约相等。 During the [0046] fourth embodiment of the present invention and in a first aspect of the fundus observation device, the occurrence of interference light from the element for the division to the overlapping, the amount of dispersion of signal light through optical assembly of a plurality of sum , and the interference light from the generating element for dividing the period to the overlapping, the reference light passes through the dispersion amount of the total value of a plurality of optical components are about equal.

[0047] 本发明的第五形态为在第四形态的眼底观察装置中,前述干涉光发生元件从进行前述分割至前述重叠的期间,前述信号光被空气付与的色散量,与前述干涉光发生元件从进行前述分割至前述重叠的期间,前述参照光被空气付与的色散量大略相等。 During [0047] a fifth aspect of the present invention is the fourth aspect of the fundus oculi observation device, the occurrence of the interference light from the element for the division to the overlapping, the amount of dispersion of the signal light is imparted air, and the interference light occurs be divided from the element to the overlap period, the reference light amount dispersion of air imparted almost same.

[0048] 本发明第一形态的眼底观察装置设有第一图像形成元件,其可形成眼底的二维图像,以及第二图像形成元件,其形成眼底的断层图像。 [0048] The first aspect of the present invention is a fundus observation device is provided with a first image forming member, which can form a two-dimensional image of the fundus, and the second image forming element which forms a tomographic image of the fundus. 第一图像形成元件的拍摄光学系统形成拍摄光路。 A first photographing optical system of the image forming member forming the shooting optical path. 第二图像形成元件将通过眼底的信号光与参照光重叠以发生干涉光,并依据该干涉光形成断层图像。 The second image forming element to interfere with light superimposed signal light and the reference light by the fundus, and a tomographic image is formed according to the light interference.

[0049] 光路合成分离机构的作用是将射向眼底的信号光的光路与拍摄光路进行合成。 [0049] The effect of the light path combiner and splitter means is the optical path of the signal light toward the fundus photographing optical path combining. 该信号光经过该拍摄光路,照射眼底。 The signal light through the photographing optical path, the fundus illumination. 又该光路合成分离机构的作用是将通过眼底的信号光与拍摄光路进行分离。 Synthesis action should the optical path separating means is a separation by the signal light and the fundus photographing optical path. 该分离的信号光与参照光重叠,以发生干涉光。 Separating the signal light and the reference light overlap, to interfere light.

[0050] 藉由设置如上述的光路合成分离机构,能够取得眼底表面的二维图像与眼底的断层图像两者。 [0050] As provided by the above-described optical path combiner and splitter means, it is possible to obtain both the two-dimensional image of the fundus tomographic image of a fundus surface. 特别是在同时进行第一图像形成元件的照明光照射与第二图像形成元件的信号光照射的场合,可将通过眼底的各别的光用光路合成分离机构分离,检测各别的光形成图像。 Especially in an image forming simultaneously a first illumination light and the second image signal element where the light irradiation device is formed, may be separated by respective optical path synthesizing optical separating means fundus, the detection light to form an image of each other . 因此,依本发明的眼底观察装置,能够同时取得眼底表面的二维图像及眼底的断层图像。 Thus, the fundus observation device under this invention, it is possible simultaneously to obtain the two-dimensional tomographic image and a fundus image of the fundus surface. [0051] 更依本发明的第二形态的眼底观察装置,因设有对参照光付与色散量的色散付与元件,故对信号光在通过拍摄光路时的色散量,可至少补偿一部分。 [0051] More under this second aspect of the invention, a fundus observation device, because the reference element is provided to impart light dispersion imparting dispersion amount, so the amount of dispersion of signal light passing through the photographing optical path when, at least a portion can be compensated. 由此,能够抑制信号光与参照光的干涉效率的下降。 This can suppress a decrease in the interference efficiency of the signal light and the reference light.

[0052] 特别是在本发明第三形态的眼底观察装置,因设有色散付与元件付与参照光色散量,其略等于由干涉光发生机构分割的信号光,从分割后通过眼底到与参照光重叠的期间的色散量,故互相重叠的信号光与参照光,各别付与的色散量大略相等。 [0052] especially in the third aspect of the present invention is a fundus observation device, because with a dispersion imparting device to impart the reference light dispersion amount which roughly equal to the signal light divided by the interference light generating means, after dividing by the fundus to the reference light dispersion amount during overlap, so that overlapping of the signal light and the reference light, and the individual pay almost same amount of dispersion. 因此,能够以高干涉效率使信号光与参照光发生干涉,获得明确且精度高的断层图像(OCT图像)。 Accordingly, a high interference efficiency of the signal light and the reference light interference occurs, to obtain clear and high precision tomographic image (OCT image).

[0053] 又依本发明第四形态的眼底观察装置,因其构造可使由干涉光发生机构分割的信号光,从分割后通过眼底到与参照光重叠的期间,通过多数的光学组件的色散量的合计量, 与由该干涉光发生机构分割的参照光,从分割后到与信号光重叠的期间,通过多数的光学组件的色散量的合计值,约略相等。 [0053] The fourth aspect of the invention, and under this fundus oculi observation device, its configuration allows the signal light divided by the interference light generating means, after dividing by the reference light during the fundus to overlap, over a dispersive optical assembly majority the total amount of the reference light generated by the light splitting means of interference, the period of the signal light superimposed by the majority of the total value of dispersion amount of an optical assembly, after the divided roughly equal. 故互相重叠的信号光与参照光各别付与的色散量大约相等,可使信号光与参照光以高干涉率进行干涉。 Approximately equal amount of dispersion so that overlapping of the signal light and the reference light and the respective payment, make the signal light and the reference light to interfere with a high rate of interference.

[0054] 又依本发明第五形态的眼底观察装置,因其构造可使由干涉光发生机构分割的信号光,从分割后通过眼底到与参照光重叠的期间,该信号光因空气发生的色散量,与由该干涉光发生机构分割的参照光,从分割到与信号光重叠的期间,通过空气发生的色散量大约相等。 [0054] and under this fundus observation device of the fifth aspect of the invention, its construction allows the signal light generated by the light splitting means interference from the fundus to the period divided by overlapping the reference light, the signal light occurs due to air dispersion amount, the reference light generated by the light dividing means interference from the overlap period is divided into signal light, the amount of air passing through the dispersion occurs approximately equal. 故互相重叠的信号光与参照光各别付与的色散量更为接近,能更抑制信号光与参照光的干涉效率的降底。 The amount of dispersion so that overlapping of the signal light and the reference light and the respective pay closer, more suppression efficiency drop at the end of the interference signal light and the reference light.

[0055] 附图说明 [0055] BRIEF DESCRIPTION OF DRAWINGS

[0056] 图1是表示本发明的眼底观察装置较佳的实施形态的整体结构的一例的概略结构图。 [0056] FIG. 1 is a schematic configuration diagram showing an example of the overall configuration of a preferred embodiment of the fundus oculi observation device according to the present invention.

[0057] 图2是表示本发明的眼底观察装置较佳的实施形态中内设在眼底相机单元内的扫描单元的结构的一例的概略结构图。 [0057] FIG. 2 is a schematic configuration diagram showing an example of a configuration of a fundus observation device according to the present invention, the preferred embodiment features the scanning unit in the fundus camera unit.

[0058] 图3是表示本发明的眼底观察装置较佳的实施形态中OCT单元的结构的一例的概略结构图。 [0058] FIG. 3 is a schematic configuration diagram showing an example of configuration of a fundus oculi observation device according to the present invention, the preferred embodiment of the OCT unit.

[0059] 图4是表示本发明的眼底观察装置较佳的实施形态中演算控制装置的硬件结构的一例的概略方块图。 [0059] FIG. 4 is a schematic block diagram illustrating an example of a hardware configuration of the apparatus of the fundus oculi observation device according to the present invention, the preferred embodiment the calculation and control.

[0060] 图5是表示本发明的眼底观察装置较佳的实施形态的控制系统结构的一例的概略方块图。 [0060] FIG. 5 is a schematic block diagram illustrating an example of configuration of a control system of the preferred embodiment of the fundus oculi observation device according to the present invention.

[0061] 图6是表示本发明的眼底观察装置较佳的实施形态的信号光的扫描形态的一例的概略图。 [0061] FIG. 6 is a schematic diagram showing an example of the scanning signal light form the preferred embodiment of the fundus oculi observation device according to the present invention. 图6(A)表示从信号光相对于受检眼的入射侧观察眼底时的信号光的扫描形态的一例。 FIG 6 (A) shows an example of the signal light with respect to the morphology of the scanning signal light incident upon the subject's eye fundus is viewed. 而且,图6(B)表示各扫描线上扫描点的排列形态的一例。 Further, FIG. 6 (B) shows an example of an array pattern of each scanning line of the scanning spot.

[0062] 图7是表示本发明的眼底观察装置较佳的实施形态的信号光的扫描形态、以及沿着各扫描线而形成的断层图像形态的一例的概略图。 [0062] FIG. 7 is a schematic diagram showing a scanning signal light form the preferred embodiment of the fundus oculi observation device according to the present invention, and forms a tomographic image along each scanning line is formed.

[0063] 图8是表示本发明的眼底观察装置较佳的实施形态的控制系统结构的一例的概略方块图。 [0063] FIG. 8 is a schematic block diagram illustrating an example of configuration of a control system of the preferred embodiment of the fundus oculi observation device according to the present invention.

[0064] 图9是表示先前的眼底观察装置(眼底相机)的外观结构的一例的概略侧面图。 [0064] FIG. 9 is a schematic side view showing an example of the external configuration of the fundus oculi observation device previously (fundus camera).

[0065] 图10是表示先前的眼底观察装置(眼底相机)的内部结构(光学系统的结构) 的一例的概略图。 [0065] FIG. 10 shows a prior fundus oculi observation device (retinal camera) of an internal configuration (optical system configuration) is a schematic diagram showing an example.

[0066] 1、1000 :眼底观察装置 IA :眼底相机单元[0067] 8a :物镜部 8b :目镜部 [0066] 1000: a fundus observation device IA: retinal camera unit [0067] 8a: lens portion 8b: eyepiece portion

[0068] 8c :安装部 9 :照相机 [0068] 8c: mounting portion 9: Camera

[0069] 9a :拍摄媒体 10 :摄像装置 [0069] 9a: imaging medium 10: image pickup means

[0070] 10、12 :摄像装置 100:照明光学系统 [0070] 10, 12: imaging device 100: an illumination optical system

[0071] 101 :观察光源 103 :拍摄光源 [0071] 101: an observation light source 103: light source shooting

[0072] 120 :拍摄光学系统 134、136 :分色镜 [0072] 120: photographing optical system 134, 136: dichroic mirror

[0073] 141 :扫描单元 141AU41B :检流计镜 [0073] 141: scanning unit 141AU41B: galvanometer mirror

[0074] 142 :透镜 150 =OCT 单元 [0074] 142: lens 150 = OCT unit

[0075] 151 :连接部 152 :连接线 [0075] 151: connecting portion 152: connecting wire

[0076] 152a、161、163、164、165 :光纤 [0076] 152a, 161,163,164,165: Fiber

[0077] 160 :低相干光源 162 :光耦合器 [0077] 160: low coherence light source 162: photocoupler

[0078] 174 :参照镜片 180 :分光仪 [0078] 174: reference lens 180: spectrometer

[0079] 184 =CCD 200 :演算控制装置 [0079] 184 = 200 CCD: the calculation and control means

[0080] 201 :微处理器 208 :图像形成板 [0080] 201: 208 microprocessor: the image forming panel

[0081] 208a:眼底图像形成板 208b =OCT图像形成板 [0081] 208a: fundus image forming board 208b = OCT image forming board

[0082] 210 :控制部 220 :图像形成部 [0082] 210: control unit 220: an image forming section

[0083] 230 :图像处理部 240 :使用者接口 [0083] 230: The image processing unit 240: User Interface

[0084] 250 :修正处理部 241、242 :镜片驱动机构 [0084] 250: correction processing unit 241, 242: the lens driving mechanism

[0085] LC :干涉光 LO :低相干光 [0085] LC: interference light LO: low-coherent light

[0086] LR :参照光 LS :信号光 [0086] LR: the reference light LS: signal light

[0087] Rl〜Rm :扫描线 R :扫描区域 [0087] Rl~Rm: scanning line R: scanning region

[0088] Ri j (i = 1 〜m、j = 1 ' 〜η) :扫描点 [0088] Ri j (i = 1 ~m, j = 1 '~η): scanning spot

[0089] Gi j (i = 1 〜m、j = 1 ' 〜η) :深度方向的图像 Image depth direction: (1 '~η i = 1 ~m, j =) [0089] Gi j

[0090] E :受检眼 Gl〜 Gm:断层图像 [0090] E: examinee's eye Gl~ Gm: tomographic image

[0091] Ef:眼底 [0091] Ef: fundus

[0092] Ef':眼底图像(二维图像) [0092] Ef ': fundus image (two-dimensional image)

具体实施方式 detailed description

[0093] 以下参照图式对本发明实施形态的一例的眼底观察装置详细说明。 [0093] reference to the drawings showing an example of the fundus observation device of the embodiment of the present invention will be described. 又,对于与先前同样的构成部分,用与图9、图10同样符号。 Further, for the same components as previously described, using FIG. 9, FIG. 10 the same reference numerals.

[0094] <第1实施形态> [0094] <First Embodiment>

[0095] 首先,参照图1〜图5,对本发明的眼底观察装置的第1实施形态的结构进行说明。 [0095] First, referring to FIG. 1 ~ 5, the configuration of the first embodiment of the fundus observation device according to the present invention will be described. 图ι表示本实施形态的眼底观察装置1的整体结构。 Ι FIG. 1 shows an overall configuration of the present embodiment of the fundus observation device. 图2表示眼底相机单元IA内的扫描单元141的结构。 FIG 2 shows a configuration of the scanning unit 141 in a fundus camera unit IA. 图3表示OCT单元150的结构。 3 shows the configuration of the OCT unit 150. 图4表示演算控制装置200的硬件结构。 4 shows a hardware configuration of the arithmetic control device 200. 图5表示眼底观察装置1的控制系统的结构。 5 shows a configuration of the control system of the fundus observation device 1.

[0096] 整体结构 [0096] overall configuration

[0097] 如图1所示,眼底观察装置1包含作为眼底相机而发挥功能的眼底相机单元1A、 存储光图像计测装置(OCT装置)的光学系统的OCT单元150、执行各种控制处理等的电脑200而构成。 [0097] 1, the fundus oculi observation device 1 comprises the retinal camera and a fundus camera unit play function. 1A, the optical image measurement device is stored (OCT apparatus) of the optical system in the OCT unit 150, executes various control processes, etc. computer 200 is constituted. [0098] 该眼底相机单元1A,与演算控制装置200共同构成本发明的“第一图像形成元件” 的一例。 [0098] constitute one example of the present invention, a fundus camera unit 1A, and the calculation and control means 200 "first image forming element." 又OCT单元150与演算控制装置200共同构成本发明的“第二图像形成元件”的一例。 OCT unit 150 and an example of the "second image forming element" of the present invention, and together constitute the calculation and control device 200. 又该“第二图像形成元件”中,也包含设在眼底相机单元IA的扫描单元141等、信号光经过的各种光学构件。 What should the "second image forming element" also includes a scan unit 141 provided in the fundus camera unit IA and the like, through various optical members of the optical signals.

[0099] 连接线152的一端安装在OCT单元150上有。 [0099] One end of cable 152 is mounted on the OCT unit 150 has. 该连接线152的另一端上安装有连接部151。 The connection line 151 is attached to the other end of the connecting portion 152. 该连接部151安装在图9所示的安装部Sc。 The connecting portion 151 mounted on the mounting portion 9 as shown in FIG. Sc. 而且,在连接线152的内部导通有光纤。 Furthermore, the inner conductor connection line 152 through an optical fiber. OCT单元150与眼底相机单元IA经过连接线152而光学性连接。 OCT unit 150 and the retinal camera unit via the connection line 152 IA optically connected. 对于OCT单元150 的详细结构,以下一边参照图3 —边进行说明。 The detailed structure of the OCT unit 150, with reference to the following FIG. 3 - side will be described.

[0100] 眼底相机单元的结构 [0100] Construction of a fundus camera unit

[0101] 眼底相机单元IA具有与图9所示先前的眼底相机1000大致相同的外观结构。 [0101] IA retinal camera unit having substantially the same external configuration and the previous fundus camera 1000 shown in FIG. 9. 而且,眼底相机单元IA与图10所示先前的光学系统同样具备:照明光学系统100,对受检眼E的眼底Ef进行照明;以及拍摄光学系统120,将该照明光的眼底反射光引导向摄像装置10。 Further, the fundus camera unit 10 previously shown in FIG. IA and an optical system comprising the same: an illumination optical system 100, on examinee's eye E, the fundus Ef is illuminated; and an imaging optical system 120, and the fundus reflection light of the illumination light guided to the imaging device 10.

[0102] 另外,在后面会详述,但是在本实施形态的拍摄光学系统120的摄像装置10,为检测具有近红外区域的波长的照明光。 [0102] Further, will be described in detail later, in the imaging apparatus 120 according to the present embodiment, imaging optical system 10 for detecting the illumination light having a wavelength in the near-infrared region. 在该拍摄光学系统120中,另外设有照明光摄像装置12,用以检测具有可视光区域的波长的照明光。 In the imaging optical system 120, the illumination light is additionally provided with the imaging device 12 for detecting the illumination light having a wavelength in the visible light region. 而且,该拍摄光学系统120将由OCT单元150发出的信号光引导到眼底Ef,并且将经过眼底Ef的信号光引导到OCT单元。 Further, the imaging optical system 120 by the signal OCT unit 150 emits light to the fundus oculi Ef, and guide the signal light to the OCT unit through the fundus oculi Ef.

[0103] 照明光学系统100与先前同样,包含观察光源101、聚光镜102、拍摄光源103、聚光镜104、激发滤光片105及106、环形透光板107、镜片108、液晶显示器109、照明光圈110、 中继透镜111、开孔镜片112、物镜113而构成。 [0103] The illumination optical system 100 similar to the previous, comprising an observation light source 101, condenser lens 102, an imaging light source 103, condenser lens 104, an excitation filter 105 and 106, a ring transparent plate 107, a lens 108, a liquid crystal display 109, an illumination diaphragm 110 , a relay lens 111, the lens aperture 112, objective lens 113 is configured.

[0104] 观察光源101输出包含波长约400nm〜700nm的范围的可视区域的照明光。 [0104] comprising an observation light source 101 outputs the illumination light of a wavelength range of visible region of about 400nm~700nm. 该观察光源101相当于本发明的“可视光源”的一例。 The observation light source 101 corresponds to the example of the "visible light" in the present invention. 另外,该拍摄光源103输出包含波长约700nm〜SOOnm的范围的近红外区域的照明光。 Further, the imaging light source 103 outputs the illumination light comprises near-infrared region of wavelength in the range of about 700nm~SOOnm. 该拍摄光源103输出的近红外光,设定成较在OCT单元150使用的光的波长短(后面再述)。 Near-infrared light output from the imaging light source 103 is set shorter than the wave length of light used in OCT unit 150 (hereinafter further described below).

[0105] 拍摄光学系统120包含物镜113、开孔镜片112(的孔部11¾)、拍摄光圈121、阻挡滤光片122及123、倍率可变透镜124、中继透镜125、拍摄透镜126、分色镜134、向场透镜(视场透镜)128、半反射镜135、中继透镜131、分色镜136、拍摄透镜133、摄像装置10 (摄像组件10a)、反射镜片137、拍摄透镜138、摄像装置12 (摄像组件12a)、透镜139、及LCD (Liquid Crystal Display,液晶显示器)而构成。 [0105] The optical imaging system 120 includes an objective lens 113, the lens aperture 112 (hole portion 11¾), imaging diaphragm 121, barrier filters 122 and 123, a variable magnification lens 124, relay lens 125, imaging lens 126, divided dichroic mirror 134, a field lens (field lens) 128, a half mirror 135, a relay lens 131, dichroic mirror 136, imaging lens 133, the imaging device 10 (imaging unit 10a), a reflective lens 137, a photographing lens 138, the imaging device 12 (imaging unit 12a), a lens 139 and LCD (liquid crystal display, a liquid crystal display) is configured.

[0106] 在本实施形态的拍摄光学系统120,与图10所示的先前的拍摄光学系统120不同, 设有分色镜134、半反射镜片125、分色镜136、反射镜片137、拍摄透镜139及IXD140。 [0106] In the photographing optical system 120 of the present embodiment, and FIG. 10 is shown in the previous photographing optical system 120 is different with the dichroic mirror 134, a semi-reflective lens 125, dichroic mirror 136, a reflective lens 137, a photographing lens 139 and IXD140.

[0107] 分色镜134为用以反射照明光学系统100发出的照明光的眼底反射光(包含波长约400nm〜800nm的范围),并且为可供由OCT单元的信号光(包含波长约800nm〜900η 范围,后述)透过的构造。 [0107] The dichroic mirror 134 to the fundus reflection light of the illumination light to reflect emitted from the illumination optical system 100 (the range of wavelengths comprising from about 400nm~800nm) and for the signal light of the OCT unit (including a wavelength from about 800nm~ 900η range, to be described later) through the structure. 该分色镜134为本发明的“光路合成分离机构”的一例。 Example of the "optical path combining means separating" the dichroic mirror 134 of the present invention.

[0108] 另外,分色镜136,可透过由照明光学系统100输出的具有可视区域的波长的照明光(由观察光源101输出的波长约400nm〜700nm的可视光),并可反射具有近红外区域的波长的照明光(由拍摄光源103输出的波长约700nm〜SOOnm的近红外光)。 [0108] Further, the dichroic mirror 136, a visible light permeable region of the illumination wavelength output by the illumination optical system 100 (by the observation light source 101 outputs visible light wavelength of approximately 400nm~700nm), and reflected having a wavelength in the near infrared region of the illumination light (wavelength from the light source 103 output the captured near-infrared light of about 700nm~SOOnm). 该分色镜136相当于本发明的“光路分离元件”的一例。 The dichroic mirror 136 corresponds to the example of the "optical path separation element" of the present invention.

[0109] 在IXD 140有显示内部视线固定标等。 [0109] In a display IXD 140 fixed to the internal standard, such as the line of sight. 由该IXD 140发出的光经透镜139聚光的后,由半反射镜135反射,通过向场透镜128反射到分色镜136。 After the light is emitted from the lens IXD 140 139 condensed by the half mirror 135 is reflected by the reflective field lens 128 to the dichroic mirror 136. 然后,通过拍摄透镜126、 中继透镜125、倍率可变透镜124、开孔镜片112(的孔部11¾)、物镜113等,射入受检眼E。 Then, the photographing lens 126, a relay lens 125, the magnification variable lens 124, the lens aperture 112 (hole portion 11¾), the objective lens 113, etc., is incident on the examinee's eye E. 由此,该视线固定标等投影到受检眼E的眼底Ef。 Thus, the line of sight fixed standard, such as the subject is projected onto a fundus Ef of the eye E.

[0110] 摄像组件IOa为内藏在电视相机等的摄像装置10的CXD或CMOS等的摄像组件, 特别是检测近红外区域的波长的光(即摄像装置10为检测近红外光的红外线电视相机)。 [0110] IOa imaging assembly is incorporated in a CMOS imaging assembly CXD like a television camera or the like image pickup device 10, in particular, detecting light having a wavelength near-infrared region (i.e., the imaging device 10 detects the near infrared light is an infrared TV camera ). 该摄像装置10输出图像讯号,作为检测近红外光的结果。 The image pickup apparatus 10 outputs an image signal, as a result of detecting near-infrared light. 触摸屏11依据该图像讯号显示眼底Ef的表面的二维图像(眼底图像Ef ' )。 The touch screen 11 displays a two-dimensional image of the surface of the fundus oculi Ef (fundus image Ef ') based on the image signal. 另外,该图像讯号被送到演算控制装置200, 在其显示器(后述)显示眼底图像。 Further, the image signal is supplied to the calculation and control device 200 (described later) displayed on its display the fundus image. 又,使用该摄像装置10拍摄眼底时,可利用由照明光学系统100的拍摄光源103输出的近红外区域波长的照明光。 Also, when photographing the fundus 10 using the imaging device, may be captured with illumination light source 103 output by the illumination optical system 100 of the near-infrared wavelength region. 该摄像装置10(的摄像组件IOa)相当于本发明的“第一检测机构”的一例。 The image pickup device 10 (image pickup module IOa of) corresponds to example of the "first detecting means" of the present invention.

[0111] 另一方面,摄像组件1¾为内藏在电视相机等摄像装置12的C⑶或MOS等的摄像组件,特别是检测可视光区域波长的光(即摄像装置12为检测可见光的电视相机)。 [0111] On the other hand, the imaging component is incorporated in the imaging assembly 1¾ C⑶ like a television camera or the like or a MOS image pickup device 12, in particular light detecting visible light wavelength region (i.e., the imaging device 12 to detect a visible light TV camera ). 该摄像装置12输出图像讯号,作为检测可视光的结果。 The image pickup apparatus 12 outputs an image signal, a visible light as the detection result. 该触膜屏11依据该图像讯号显示眼底Ef的表面的二维图像(眼底图像Ef')。 The touch-sensitive screen 11 displays a two-dimensional image of the surface of the fundus oculi Ef (fundus image Ef ') based on the image signal. 另外,该图像讯号被送到演算控制装置200,在其显示器(后述)显示眼底图像。 Further, the image signal is supplied to the calculation and control device 200 (described later) displayed on its display the fundus image. 又,使用该摄像装置12拍摄眼底时,可利用从照明光系统100的观察光源101输出的可视光区域波长的照明光。 Also, when photographing the fundus 12 using the imaging device, may utilize the illumination light wavelength region from the visible light output from the observation light source 101 of the illumination optical system 100. 该摄像装置12(的摄像组件12a)相当于本发明的“第三检测机构”的一例。 The image pickup device 12 (image pickup module 12a) corresponds to the example of the "third detecting means" of the present invention.

[0112] 本实施形态中的拍摄光学系统120中设有扫描单元141及透镜142。 [0112] The present embodiment, photographing optical system 120 is provided in the scanning unit 141 and a lens 142. 扫描单元141 具备如下结构,即,在眼底Ef上扫描从OCT单元150所输出的光(信号光LS,后述)。 The scanning unit 141 includes a structure, i.e., the scanning light (light the LS signal, to be described later) outputted from the OCT unit 150 on the fundus Ef.

[0113] 透镜142使来自OCT单元150的信号光LS通过连接线152,引导成为平行光束,并将其射入扫描单元141。 [0113] lens 142 makes the signal light LS from the OCT unit 150 through the connection line 152, the guide into a parallel beam, and is incident on the scanning unit 141. 而且,透镜142的作用为使经过扫描单元141而来的信号光LS的眼底反射光聚焦。 Moreover, the action of the lens 142 such that the reflective signal light LS via the fundus of the scanning unit 141 from the light focusing.

[0114] 图2中表示扫描单元141的具体结构的一例。 In [0114] FIG. 2 shows an example of a specific configuration of the scanning unit 141. 扫描单元141包含检流计镜(galvanometer mirror) 141AU41B 以及反射镜片141C、141D 而构成。 The scanning unit 141 includes a galvanometer mirror (galvanometer mirror) 141AU41B and a reflective lenses 141C, 141D is configured.

[0115] 检流计镜141A、141B设为可以分别以旋转轴141a、141b为中心而旋转。 [0115] galvanometer mirrors 141A, 141B may be respectively set to the rotation shaft 141a, 141b as the center of rotation. 旋转轴141a、141b以相互正交的方式而配设。 The rotation shaft 141a, 141b so as to be disposed perpendicular to each other. 在图2中,检流计镜141A的旋转轴141a配设为平行于该图的纸面,且检流计镜141B的旋转轴141b配设为垂直于该图的纸面。 In FIG. 2, the galvanometer mirror 141A is set with the rotary shaft 141a parallel to the drawing of the figure, and the rotation axis galvanometer mirror 141b 141B feature set perpendicular to the paper surface of FIG. S卩,检流计镜141B可以向图2中的两侧箭头所示方向旋转,检流计镜141A可以向正交于该两侧箭头的方向旋转。 S Jie, a galvanometer mirror 141B can be rotated in the direction indicated by arrow in FIG. 2 on both sides, a galvanometer mirror 141A can be rotated in the direction orthogonal to the both sides of the arrow. 以此,该一对检流计镜141A、141B分别发挥作用,使信号光LS的反射方向变更为相互正交的方向。 In this, the pair of galvanometer mirrors 141A, 141B, respectively, play a role in the reflection direction of the signal light LS changes to a direction orthogonal to each other. 另外,检流计镜141A、141B的各个旋转动作是通过下述镜驱动机构(参考图5)而驱动。 In addition, a galvanometer mirror 141A, 141B of the respective rotational movement is driven by a mirror driving mechanism described below (refer to FIG. 5).

[0116] 由检流计镜141A、141B所反射的信号光LS,向与由反射镜片141C、141D所反射而入射至检流计镜141A时相同的方向行进。 [0116] by a galvanometer mirror 141A, 141B of the reflected signal light LS, and a reflection mirror 141C, 141D are reflected to the same direction incident on the galvanometer mirrors 141A travels.

[0117] 另外,如上所述,连接线152的内部导通有光纤15加,该光纤15¾的端面152b是与透镜142相对而配设。 [0117] As described above, the internal conductive wires 152 are connected to the optical fiber 15 increase, the end face 152b of the optical fiber 15¾ lens 142 is disposed oppositely. 从该端面152b所射出的信号光LS朝向透镜142使束径逐渐放大而行进,但通过该透镜142而成为平行光束。 Toward the lens 142 from the signal light LS emitted from this end face 152b so that the beam diameter is enlarged gradually travels, but rather through the lens 142 into a parallel beam. 相反,信号光LS的眼底反射光通过该透镜142 而朝向端面152b聚焦。 In contrast, the fundus reflection light of the signal light LS toward the end face 152b by the lens 142 focusing.

[0118] OCT单元的结构 [0118] structure of the OCT unit

[0119] 以下,参照图3,对OCT单元150的结构进行说明。 [0119] Hereinafter, with reference to FIG. 3, the configuration of the OCT unit 150 will be described. 该图所示的OCT单元150具有与先前的光图像计测装置大致相同的光学系统,且具备干涉仪,该干涉仪将从光源所输出的光分割为参照光与信号光,并使经过参照物体的参照光、与经过被测定物体(眼底Ef)的信号光重叠而产生干涉光,并且,对该干涉光的检测结果进行解析而形成被测定物体的图像。 Shown in the figure OCT unit 150 has a light image with the previous measurement device is substantially the same optical system, and includes an interferometer, the interferometer light output from the light source is divided into reference light and signal light, and through the reference reference light object, and the object to be measured via a signal (Ef of the fundus) superimposed light generated interference light, and forms an image of the object to be measured detection result of analyzing the interference light.

[0120] 低相干光源160是由输出低相干光LO的超级发光二极管(SLDduperluminescent diode)或发光二极管(LED,light-emitting diode)等的宽带光源所构成。 [0120] low coherence light source 160 is a low-coherence light LO output from the super luminescent diode (SLDduperluminescent diode) or a light emitting diode (LED, light-emitting diode) composed of a broadband light source or the like. 该低相干光LO 例如具有近红外区域的波长,并且具有数十微米左右的时间性相干长度的光。 The low-coherence light LO e.g. having a wavelength in the near infrared region, and light having several tens of micrometers temporal coherence length. 从该低相干光源160输出的低相干光L0,具有比眼底相机单元IA的照明光(波长约400nm〜800nm) 更长的波长,例如含有约SOOnm〜900nm范围的波长。 From the coherent light source 160 outputs the low low-coherence light L0, longer wavelength of the illumination light (wavelength of about 400nm~800nm) a fundus camera unit IA than, for example, containing about SOOnm~900nm wavelength range. 该低相干光源160相当于本发明的“光源”的一例。 The low coherence light source 160 corresponds to the example of the "light source" of the present invention.

[0121] 从低相干光源160所输出的低相干光L0,例如通过由单模光缆(single-mode fiber)或极化保持光纤(polarization maintainingfiber)所构成的光纤161,被引导向光耦合器(coupler) 162,由该光耦合器162将该低相干光源LO分割为参照光LR与信号光LS。 [0121] from the low-coherence light L0 output from the low coherence light source 160, for example via an optical fiber 161 composed of a single-mode fiber held (single-mode fiber) or a fiber polarization (polarization maintainingfiber), is guided to an optical coupler ( coupler) 162, which is divided by the optical coupler 162 to the low-coherence light LO reference light LR and signal light LS.

[0122] 另外,光耦合器162具有光分割元件(分光器)及光重叠的元件(耦合器)双方的功能,但惯用名叫“光耦合器”。 [0122] Further, the optical coupler 162 has a function as a light dividing element (beam splitter) and the optical element overlaps (coupling) between the two sides, but conventional called "optical coupler."

[0123] 从光耦合器162发生的参照光LR,被由单模光纤等构成的光纤163引导,从光纤端面射出,所射出的参照光LR通过准直透镜171,成为平行光束后,经过玻璃块172及密度滤光片173,并由参照镜片174(参照物体)而反射。 [0123] is, light emitted from the fiber end from the reference light LR by the optical coupler 162 occurring fiber guide made of single-mode fiber 163 and the like, reference light LR emitted by the collimator lens 171 into a parallel light beam, through a glass block 172 and the density filter 173, by referring to the lens 174 (refer to the object) is reflected.

[0124] 由参照镜片174所反射的参照光LR再次经过密度滤光片173及玻璃块172,并通过准直透镜171而在光纤163的光纤端面上聚光。 [0124] Referring to the lens 174 by the reference light LR reflected through the density filter 173 and the glass block 172 again, and by the collimator lens 171 converging in the fiber end face of the optical fiber 163. 所聚光的参照光LR通过光纤163而被引导向光耦合器162。 The converging reference light LR is guided by an optical fiber 163 to optical coupler 162.

[0125] 另外,玻璃块172及密度滤光片173,是作为用以使参照光LR与信号光LS的光路长度(光学距离)一致的延迟元件而发挥作用,而且作为用以使参照光LR与信号光LS的色散特性一致的元件而发挥作用。 [0125] Further, the glass block 172 and a density filter 173, as to the optical path length of the reference light LR and the signal light LS (optical distance) of the delay elements consistent with the role, and for causing the reference light LR as consistent with the dispersion characteristics of the signal light LS elements play a role.

[0126] 又,参照镜174为可沿参照光LR的进行方向移动的构造。 [0126] Further, the reference mirror 174 is configured to be movable along the direction of reference light LR is moved. 因此,能够对应受检眼E 的眼轴长度,确保参照光LR的光路长度。 Accordingly, corresponding to the axial length of the examinee's eye E, to ensure that the optical path length of the reference light LR. 另外,参照镜174的移动可利用含有电动等的驱动装置的驱动机构进行。 Further, reference mirror 174 may be moved by the driving mechanism comprising an electric drive apparatus or the like.

[0127] 另一方面,从光耦合器162发生的信号光LS,由单模光纤等构成的光纤164引导至连接线152的端部。 [0127] On the other hand, the signal light LS from the optical coupler 162 occurs, an optical fiber made of single-mode fiber 164 guided to the other end of the connecting line 152. 在连接线152的内部导通有光纤15加。 The inner conductor connection line 152 through an optical fiber 15 increase. 此处,光纤164与光纤15¾ 可以由单一的光纤而构成,而且,也可以是将各个端面接合而一体形成的光纤。 Here, the optical fiber 164 and the optical fiber 15¾ may be composed of a single optical fiber, and may be joined to each end face of the optical fiber are integrally formed. 总的,光纤164、15¾只要可以在眼底相机单元IA与OCT单元150之间传送信号光LS即可。 General, as long as the optical fiber 164,15¾ can transmit a signal between the fundus camera unit 150 and the OCT unit IA light LS.

[0128] 信号光LS在连接线152内部被引导而被导向眼底相机单元1A。 [0128] the signal light LS is guided to the retinal camera unit 1A is guided within the connection line 152. 而且,信号光LS 经过透镜142、扫描单元141、分色镜134、拍摄透镜126、中继透镜125、倍率可变透镜124、 拍摄光圈121、开孔镜片112的孔部11¾与物镜113,而入射受检眼E(此时,如下所述,阻挡滤光片122、123分别从光路中退出)。 Further, the signal light LS passes through the lens 142, the scanning unit 141, the dichroic mirror 134, imaging lens 126, relay lens 125, the magnification variable lens 124, the photographing diaphragm 121, a lens opening hole portion 11¾ 112 and objective lens 113, and entering the examinee's eye E (At this time, as described below, the barrier filter 122 and 123 are retracted from the optical path).

[0129] 入射受检眼E的信号光LS在眼底(视网膜)Ef上成像并反射。 [0129] the signal light LS enters the subject's eye E imaged and reflected on the fundus (retina) Ef. 此时,信号光LS 不仅被眼底Ef的表面反射,也到达眼底Ef的深部区域并在折射率边界上产生散射。 At this time, the signal light LS is not only reflected by the surface of the fundus oculi Ef, but also reaches the deep area of ​​the fundus oculi Ef and the refractive index on the boundary scattering. 以此, 信号光LS的眼底反射光成为包含反映眼底Ef的表面形态的信息、及反映在深部组织的折射率边界的背后散射(backscattering)的状态的信息的光。 In this, the fundus reflection light of the signal light LS becomes information including the surface morphology of the fundus oculi Ef is reflected, and the reflected information light scattering state behind the refractive index boundary of the deep tissue (Backscattering) a. 将该光简称为“信号光LS的眼底反射光”。 The light abbreviated as "fundus reflection light of the signal light LS."

[0130] 信号光LS的眼底反射光向上述路径的相反方向行进,在光纤15¾的端面152b上聚光,通过该光纤152而入射至OCT单元150,并通过光纤164而返回到光耦合器162。 [0130] fundus reflection light of the signal light LS in the opposite direction of the traveling path, condensed on the end face 152b of the optical fiber 15¾ through the optical fiber 152 and enters the OCT unit 150, and returns to the optical coupler 162 through the optical fiber 164 . 光耦合器162使该信号光LS与由参照镜片174所反射的参照光LR重叠,生成干涉光LC。 Optical coupler 162 such that the signal light LS overlap with the reference light 174 by the reflection of the reference lens LR, generating an interference light LC. 所生成的干涉光LC通过单摸光纤等构成的光纤165,被引导向分光仪180。 The generated interference light LC by touching a single optical fiber or the like made of 165, 180 is guided to the spectrometer.

[0131] 此处,本发明的“干涉光产生元件”由至少包含光耦合器162、光纤163、164与参照镜片174的干涉仪所构成。 [0131] Here, the present invention is the "interference light generating element" is constituted by including at least an optical coupler 162, optical fibers 163, 164 and reference interferometer 174 of the lens. 另外,本实施形态中是采用了迈克尔逊型干涉仪(Michelson interferometer),但也可以适当采用例如马赫-曾德(Mach-khnder)型等任意类型的干涉仪。 Further, the present embodiment is the use of a Michelson interferometer (Michelson interferometer), but may be appropriately employed, for example, a Mach - Zehnder any type (Mach-khnder) type interferometer and the like.

[0132] 分光仪(spectrometer) 180包含准直透镜181、衍射光栅182、成像透镜183与CCD(Charge Coupled Device,电荷耦合器件)184而构成。 [0132] spectrometer (spectrometer) 180 comprises a collimator lens 181, a diffraction grating 182, an imaging lens 183 and CCD (Charge Coupled Device, charge-coupled device) 184 is configured. 本实施形态的衍射光栅182是透过型衍射光栅,但当然也可以使用反射型衍射光栅。 A diffraction grating 182 of the present embodiment is a transmission type diffraction grating, it is of course also possible to use a reflection type diffraction grating. 而且,当然也可以应用其它光检测组件(检测机构)来代替CCD184。 Also, of course, it may be applied to other light detecting assembly (detecting means) instead CCD184. 如上述的光检测组件为相当本发明的“第二检测机构”的一例。 Light detecting unit as described above is an example of the "second detecting means" of the present invention rather.

[0133] 入射至分光仪180的干涉光LC通过准直透镜181而成为平行光束之后,被衍射光栅182分光(光谱分解)。 After [0133] the interference is incident to the spectroscope 180 and the LC light into a parallel beam by the collimator lens 181, beam splitter 182 is a diffraction grating (spectral decomposition). 所分光的干涉光LC通过成像透镜183而在(XD184的摄像面上成像。CCD184接收该干涉光LC并将其转换为电气检测信号,且将该检测信号输出到演算控制装置200中。 The spectral interference light and receiving the interference light LC in LC (XD184 imaging .CCD184 imaging plane by the imaging lens 183 and are converted into an electrical detection signal, and outputs the detected signal to the arithmetic control device 200.

[0134] 演算控制装置的构造 Configuration [0134] The calculation and control device

[0135] 其次,说明演算控制装置200的构造。 [0135] Next, the calculation and control device 200 is configured. 演算控制装置200进行以下处理:分析由OCT单元150的分光仪180的(XD184输入的检测信号,形成受检眼E的眼底Ef的断层图像。此时的分析方法与先前的傅立叶区域OCT的方法相同。 The calculation and control unit 200 performs the following process: At this point analytical methods previously Fourier OCT area tomographic image of the fundus Ef of the subject's eye E is formed by the spectrometer analysis (detection signal 150 of the OCT unit 180 XD184 input. the same.

[0136] 另外,演算控制装置200进行以下处理:依据由眼底相机单元IA的摄像装置10、 12输出的图像信号,形成眼底Ef的表面(网膜)形态的二维图像。 [0136] Further, the calculation control unit 200 performs the following process: 10 based on the image signal output from the imaging device 12 by the fundus camera unit IA, the two-dimensional image forming surface of the fundus oculi Ef (retina) form.

[0137] 而且,演算控制装置200执行眼底相机单元IA的各部分的控制、以及OCT单元150 的各部分的控制。 [0137] Further, the calculation control unit 200 executes control of each part of the retinal camera unit IA, and controls each section of the OCT unit 150.

[0138] 作为眼底相机单元IA的控制,例如进行观察光源101或拍摄光源103的照明光的输出控制、激发滤光片105、106或阻挡滤光片122、123在光路上的插入/退出动作的控制、 液晶显示器140的显示动作的控制、照明光圈110的移动控制(光圈值的控制)、拍摄光圈121的光圈值的控制、倍率可变透镜124的移动控制(倍率的控制)的控制等。 [0138] As a control the retinal camera unit IA, for example, the observation light source 101 or imaging output control of the illumination light source 103, excitation filter 105, 106, 122, 123 or the barrier filters inserted in the optical path / exit action control, controls the display operation of the liquid crystal display 140, lighting movement control (control of the diaphragm value) of the diaphragm 110, imaging aperture value of the aperture 121 controls the magnification variable lens movement control (control of the magnification) control 124, and the like . 而且,演算控制装置200对扫描单元141内的检流计镜141A、141B的旋转动作进行控制。 Moreover, the galvanometer mirrors 141A and a scanning control unit 141 of the calculation means 200 pairs, 141B rotation operation is controlled.

[0139] 另一方面,OCT单元150的控制,是进行低相干光源160的低相干光的输出控制、 参照镜174的移动控制、(XD184的蓄积时间的控制等。 [0139] On the other hand, the control of the OCT unit 150, the output is low coherence light source 160 controls the low-coherence light, movement control of reference mirror 174, (XD184 controlling the accumulation time and the like.

[0140] 参照图4,对如上所述发挥作用的演算控制装置200的硬件结构进行说明。 [0140] Referring to Figure 4, a hardware configuration of the arithmetic control device 200 to function as described above will be described. 演算控制装置200具备与先前的电脑同样的硬件结构。 The calculation and control apparatus 200 has the same hardware configuration as the previous computer. 具体而言,包含微处理器201 (CPU,MPU 等)、RAM 202、ROM 203、硬盘驱动器(HDD, HardDisk Driver) 204、键盘205、鼠标206、显示器207、图像形成板208及通信界面(I/F)209。 Specifically, it includes a microprocessor 201 (CPU, MPU, etc.), RAM 202, ROM 203, a hard disk drive (HDD, HardDisk Driver) 204, a keyboard 205, a mouse 206, a display 207, an image forming board 208, and a communication interface (I / F) 209. 这些各个部分是通过总线200a而连接。 These respective portions are connected via a bus 200a.

[0141] 微处理器201将存储在硬盘驱动器204中的控制程序20½展开到RAM202上,以此在本发明中执行特征性动作。 [0141] The microprocessor 201 control program stored in the hard disk drive 204 is 20½ to expand the RAM202, in order to perform the characteristic operation of the present invention.

[0142] 而且,CPU201执行上述装置各部分的控制、或各种运算处理等。 [0142] Further, CPU 201 executes control of each part of the device, various arithmetic processing, or the like. 而且,执行与来自键盘205或鼠标206的操作信号对应的装置各个部分的控制、显示器207的显示处理的控制、通信界面208的各种数据或控制信号等的发送接收处理的控制等。 Further, control of transmission and reception processing section performs each control from the keyboard 205 and the mouse 206 or an operation signal corresponding to the means for controlling the display process of the display 207, a communication interface 208 various types of data or control signals and the like.

[0143] 键盘205、鼠标206及显示器207是作为眼底观察装置1的用户界面而使用的。 [0143] keyboard 205, a mouse 206 and a display 207 as a user interface of the fundus observation device 1 is used. 键盘205是作为用以键入字符或数字等的设备而使用。 Keyboard 205 is used as a device for typing characters or numbers and the like. 鼠标206是作为用以对显示器207的显示画面进行各种输入操作的设备。 Mouse 206 is used as a display screen of the display 207 performs various input operations of the device.

[0144]而且,显示器 207 是LCD (Liquid Crystal Display,液晶显示器)或CRT (Cathode Ray Tube,阴极射线管)等任意的显示设备,其显示由眼底观察装置1所形成的眼底Ef的图像,或显示各种操作画面或设定画面等。 [0144] Also, display 207 is a LCD (Liquid Crystal Display, a liquid crystal display) or CRT (Cathode Ray Tube, a cathode ray tube) or the like arbitrary display device that displays an image of the fundus Ef by the fundus oculi observation device 1 formed, or displays various operation screens or setting screens and the like.

[0145] 另外,眼底观察装置1的用户界面并不限定于这样的结构,也可以使用例如轨迹球(track ball)、控制杆、触摸面板式IXD、用于眼科检查的控制面板等具备显示输出各种信息的功能以及输入各种信息的功能的任意用户界面机构而构成。 [0145] In addition, the user interface of the fundus observation device 1 is not limited to such a configuration, for example, may be a trackball (track ball), a lever, a touch panel of formula IXD, for ophthalmic examination control panel includes a display output means any functions and user interface functions to input various information, various information is constituted.

[0146] 图像形成板208为处理受检眼E的眼底Ef的图像的专用电子电路。 [0146] The image forming board 208 is a dedicated electronic circuit of the image processing of the fundus oculi Ef of the eye E of the examinee. 在该图像形成板208设有眼底图像形成板208a及OCT图像形成板208b。 In this image forming board 208 is provided with a fundus image forming board 208a and OCT image forming board 208b. 眼底图像形成板208a的动作, 为依据眼底相机单元IA的摄像装置10,或摄像装置12的图像信号形成眼底图像的专用电子电路。 Dedicated electronic circuit board 208a of the image forming operation of the fundus, forming the fundus image based on the imaging device 10 of the retinal camera unit IA, or the image signal of the imaging device 12. 又,OCT图像形成板208b的动作为依据OCT单元150的分光仪180的(XD184的检测信号形成眼底图像(断层图像)的专用电子电路。因设有上述的图像形成板208,可提高眼底图像形成处理的处理速度。 And, OCT image forming board 208b is formed in operation of the fundus image (tomographic image) according to the detection signal (XD184 an OCT unit 150 of the spectrometer 180 of the dedicated electronic circuit provided by the above-described image forming board 208, the fundus image can be improved forming processing speed of the processing.

[0147] 通信界面209进行以下处理:将来自微处理器201的控制信号发送到眼底相机单元IA或OCT单元150。 [0147] Communication interface 209 performs the following process: a control signal sent from the microprocessor 201 to the fundus camera unit or the OCT unit 150 IA. 另外,通信界面209进行以下处理:接收由眼底相机单元IA的摄像装置10、12输出的图像信号,或从OCT单元150的CXD 184输出的检测信号,进行对图像形成板208的输入等。 Further, the communication interface 209 performs a process of: receiving an image signal from the fundus camera unit IA imaging means 10, 12 output a detection signal CXD 184 or outputted from the OCT unit 150, an input plate 208 and the like image forming. 此时,通信界面209的动作为将从摄像装置10、12的图像信号输入眼底图像形成板208a,将从CCD184的检测信号输入OCT图像形成板208b。 In this case, the operation of the communication interface 209 into an image signal input from the imaging means 10, 12 fundus image forming board 208a, the detection signal is inputted from the OCT image forming board CCD184 208b.

[0148] 而且,当演算控制装置200连接于LAN (Local Area Network,局域网)或互联网等网络时,在通信界面209中可以具备局域网卡等网络适配器(network adapter)或调制解调器(modem)等通信设备,并能够经过该网络而进行数据通信。 [0148] Further, when calculating the control apparatus 200 is connected to a LAN (Local Area Network, LAN), or other Internet network, the communication interface 209 may include a LAN card, a network adapter (network adapter) or modem (Modem) like a communication device and can perform data communication through the network. 此时,可以设置用于存储控制程序20½的服务器,并且,将演算控制装置200构成为该服务器的客户终端。 At this time, you may be provided for storing a control program 20½ server, and the calculation and control device 200 for client terminal of the server.

[0149] 控制系统的结构 [0149] Structure Control

[0150] 参照图5,对具有如上所述结构的眼底观察装置1的控制系统的结构进行说明。 [0150] Referring to Figure 5, the structure of the control system of apparatus 1 will be described observation of the fundus of the configuration described above. 图5尤其选择眼底观察装置1所具备的结构中,表示关于本发明的动作或处理的部分。 In particular, FIG. 5 Select fundus oculi observation device 1 is provided with a structure, the operation of the present invention on a partially or processing.

[0151] 眼底观察装置1的控制系统是以演算控制装置200的控制部210为中心而构成的。 Control System [0151] The fundus oculi observation device 1 is the control arithmetic unit 210 of the control apparatus 200 as a center thereof. 控制部210包含CPU 201、RAM 202、ROM 203、硬盘驱动器204 (控制程序20½)、通信界面209而构成。 The control unit 210 includes CPU 201, RAM 202, ROM 203, hard disk drive 204 (control program 20½), a communication interface 209 configured.

[0152] 控制部210通过根据控制程序20½而动作的CPU201,执行上述控制处理。 [0152] The control unit 210 operates the control program 20½ CPU201, executes the control process. 尤其是, 通过分别控制眼底相机单元IA的镜片驱动机构MU42,从而能够使检流计镜141A、141B 分别独立动作。 In particular, by controlling the lens driving mechanism of the retinal camera unit IA MU42, thereby enabling a galvanometer mirror 141A, 141B operate independently.

[0153] 而且,控制部210执行如下控制:将由眼底观察装置1所拍摄的两种图像,即,通过眼底相机单元IA所获得的眼底Ef表面的二维图像(眼底图像Ef')、以及基于由OCT单元150所获得的检测信号而形成的眼底Ef的图像,并列显示在用户界面MO的显示器207 上。 [0153] Further, the control unit 210 performs the following controls: two kinds of images captured by a fundus observation device, i.e., two-dimensional image of the surface of the fundus oculi Ef obtained by the retinal camera unit IA (fundus image Ef '), based on the image of the fundus Ef by the detection signal obtained by OCT unit 150 is formed, side by side on the display a user interface 207 for MO. 该些眼底图像,可分别在显示器207显示,也可以并排同时显示。 The plurality of fundus image can be displayed on the display 207, respectively, may be simultaneously displayed side by side.

[0154] 影像形成部220为进行依据眼底相机单元IA的摄像装置10、12的图像信号,形成眼底图像的处理,以及依据OCT单元150的CCD 184的检测信号,形成眼底图像的处理,故其构成含有图像形成板208。 [0154] unit 220 to perform image-forming apparatus according to a fundus camera imaging unit 10, 12 an image signal IA, a fundus image forming process, and according to the detection signal of the CCD 184 of the OCT unit 150, the fundus image forming process, so the containing 208 constituting the image forming panel.

[0155] 图像处理部230为进行对图像形成部220形成的眼底图像,实施各种图像处理的装置。 [0155] The image processing unit 230 to perform the image forming fundus image forming portion 220, the image processing apparatus of the various embodiments. 例如,进行依据由OCT单元150的检测信号,依据眼底Ef的断层图像,形成眼底Ef 的三维图像的处理,或进行眼底图像的亮度调整等各种修正处理等。 For example, according to the detection signal OCT unit 150, and the fundus oculi Ef based on the tomographic image, a three-dimensional image forming process of the fundus oculi Ef, or adjust the brightness of the other fundus image correction processing and the like.

[0156] 用户界面(User hterface,UI) 240具备键盘205或鼠标206等操作设备、及显示器207等显示设备。 [0156] User Interface (User hterface, UI) 240 comprises a keyboard 205 or mouse 206 and the like operating device, a display device and a display 207.

[0157] 以下,分别说明利用控制部210所进行的信号光LS的扫描的控制形态,以及利用图像形成部220与图像处理部230对OCT单元150的检测信号的处理状态。 [0157] Hereinafter, the control mode respectively illustrate scanning of the signal light LS is performed by the control unit 210, and the detection signal processed by the image forming unit 220 and the image processing section 230 of the OCT unit 150. 另外,对眼底相机单元IA的图像信号的图像形成部220等的处理,与先前的处理相同,故省略。 Further, processing of the image forming unit 220 an image signal of a fundus camera unit IA, the same as the previous process, is omitted.

[0158] 关于信号光的扫描 [0158] Scanning of the signal light on

[0159] 信号光LS的扫描如上所述,是通过变更眼底相机单元IA的扫描单元141的检流计镜141A、141B的反射面的朝向而进行。 [0159] As described above the scanning signal light LS is performed by changing the scanning unit 141 of the retinal camera unit IA galvanometer mirrors 141A, 141B of the reflection surface facing. 控制部210分别控制镜片驱动机构M1J42,以此分别变更检流计镜141A、141B的反射面的朝向,从而在眼底Ef上扫描信号光LS。 The control unit 210 controls the lens driving mechanism are M1J42, respectively, in order to change a galvanometer mirror 141A, 141B toward the reflection surface, thereby scanning the signal light LS on the fundus Ef.

[0160] 当变更检流计镜141A的反射面的朝向时,在眼底Ef的水平方向上(图1的χ方向)扫描信号光LS。 [0160] When changing the direction of the reflecting surface of the galvanometer mirrors 141A and, in the horizontal direction of the fundus oculi Ef ([chi] direction in FIG. 1) scans the signal light LS. 另一方面,当变更检流计镜141B的反射面的朝向时,在眼底Ef的垂直方向(图1的y方向)上扫描信号光LS。 On the other hand, when changing the galvanometer mirror toward the reflection surface 141B of the count, the fundus Ef in the vertical direction (y direction in FIG. 1) scans the signal light LS. 而且,同时变更检流计镜141A、141B两者的反射面的朝向,以此可以在将χ方向与y方向合成的方向上扫描信号光LS。 Further, while changing a galvanometer mirror 141A, 141B toward the reflective surface of both of the signal light LS may be scanned in order in the direction of the direction of the y-direction χ synthesis. S卩,通过控制这两个检流计镜141A、141B,可以在xy平面上的任意方向上扫描信号光LS。 S Jie, by controlling these two galvanometer mirrors 141A, 141B, the signal light LS may be scanned in an arbitrary direction in the plane xy.

[0161] 图6表示用以形成眼底Ef的图像的信号光LS的扫描形态的一例。 [0161] FIG. 6 shows one case to form a scanning signal light LS image the fundus oculi Ef is formed. 图6 (A)表示从信号光LS入射受检眼E的方向观察眼底Ef (也就是从图1的-ζ方向观察+ζ方向)时, 信号光LS的扫描形态的一例。 Figure 6 (A) indicates the direction of observed light LS from the fundus oculi Ef of the subject's eye E is incident signal (i.e. observed from the + ζ direction -ζ direction in FIG. 1), one case of scanning the signal light LS to form. 而且,图6 (B)表示眼底Ef上的各扫描线上扫描点的排列形态的一例。 Further, FIG. 6 (B) shows an example of an array pattern of each scanning line on the fundus Ef of the scanning spot.

[0162] 如图6(A)所示,在预先设定的矩形扫描区域R内扫描信号光LS。 [0162] FIG. 6 (A), in a rectangular scanning region R set in advance of the scanning signal light LS. 在该扫描区域R 内,在X方向上设定有多条(m条)扫描线Rl〜Rm。 Within this scanning region R, setting (m bar) Rl~Rm plurality of scanning lines in the X-direction. 当沿着各扫描线Ri (i = 1〜m)扫描信号光LS时,产生干涉光LC的检测信号。 When along each scanning line Ri (i = 1~m) scanning the signal light LS, generates a detection signal of the interference light LC.

[0163] 此处,将各扫描线Ri的方向称为“主扫描方向”,将与该方向正交的方向称为“副扫描方向”。 [0163] Here, the direction of each scanning line Ri will be referred to as "main scanning direction", a direction perpendicular to this direction is called "sub-scanning direction." 因此,在主扫描方向上扫描信号光LS是通过变更检流计镜141A的反射面的朝向而进行,在副扫描方向上的扫描是通过变更检流计镜141B的反射面的朝向而进行。 Thus, the scanning signal light LS in the main scanning direction is performed by changing the facing reflective surface of the galvanometer mirror 141A, and scanning in the sub-scanning direction is performed by changing the galvanometer toward the reflective surface of the galvanomirror and 141B.

[0164] 在各扫描线Ri上,如图6(B)所示,预先设定有多个(η个)扫描点Ril〜Rin。 [0164] On each scanning line Ri, as shown in FIG 6 (B), the previously set plurality of scan points Ril~Rin (a [eta]).

[0165] 为了执行图6所示的扫描,控制部210首先控制检流计镜141A、141B,将对眼底Ef 的信号光LS的入射目标设定为第1扫描线Rl上的扫描开始位置RS(扫描点Rll)。 [0165] In order to perform a scan shown in FIG. 6, the control section 210 first controls the galvanometer mirrors 141A, 141B, will fundus oculi Ef of the signal light LS enters the destination to the scan start position RS on the first scanning line Rl (scanning point Rll). 接着, 控制部210控制低相干光源160,使低相干光LO闪光,并使信号光LS入射于扫描开始位置RS。 Next, the control unit 210 controls the low coherence light source 160, a low-coherence light LO flash, and the signal light LS entering the scan start position RS. CXD 184接收该信号光LS的扫描开始位置RS上因眼底反射光而来的干涉光LC,并将检测信号输出至控制部210。 The scan start position RS CXD 184 receives the signal light LS by the fundus reflection light from the interference light LC and outputs a detection signal to the control unit 210.

[0166] 接着,控制部210控制检流计镜141A,并在主扫描方向上扫描信号光LS,将该入射目标设定为扫描点R12,使低相干光LO闪光而使信号光LS入射到扫描点R12。 [0166] Next, the control unit 210 controls the galvanometer mirror 141A, and scanning the signal light LS in the main scanning direction and set the incident target of the scanning point R12, makes the low-coherence light LO flashing signal light LS incident scanning point R12. CXD 184接收该信号光LS的扫描点R12上因眼底反射光而来的干涉光LC,并将检测信号输出至控制部210。 CXD 184 receives the signal light LS to the scanning point R12 due to the fundus reflection light from the interference light LC and outputs a detection signal to the control unit 210.

[0167] 控制部210同样,一边将信号光LS的入射目标依次移动为扫描点R13、R14、…、 Rl (n-1)、Rln, 一边在各扫描点上使低相干光LO闪光,以此获取与各扫描点的干涉光LC相对应地从CXD 184所输出的检测信号。 [0167] Control unit 210 Similarly, while the incident target of the signal light LS is sequentially moved to a scanning point R13, R14, ..., Rl (n-1), Rln, while the low-coherence at each scan point light LO fires to this detection signal acquiring the interference light LC for each scanning point corresponding to the output from the CXD 184.

[0168] 当第1扫描线Rl的最后的扫描点Rln上的计测结束时,控制部210同时控制检流计镜141A、141B,使信号光LS的入射目标沿着换线扫描r而移动到第2扫描线R2最初的扫描点R21为止。 [0168] Upon completion of the measurement on the last scanning spot Rl Rln first scan line, the control unit 210 while controlling the galvanometer mirror 141A, 141B, the incident target of the signal light LS is moved along a scan line changing r to the second scanning line R2 until the original scanning spot R21. 而且,对该第2扫描线R2的各扫描点R2j (j = 1〜η)进行上述计测,以此分别获取对应于各扫描点R2j的检测信号。 Also, each scanning point the second scanning line R2, R2j (j = 1~η) measuring the above, in order to obtain respectively corresponding to each scanning point detection signal R2 j.

[0169] 同样,分别对第3扫描线R3、…、第m-1扫描线R(m_l)、第m扫描线Rm进行计测, 从而获取对应于各扫描点的检测信号。 [0169] Similarly, each of the third scanning line R3, ..., m-1 the first scanning line R (m_l), for the m-th scanning line Rm is measured, thereby obtaining corresponding to each of the scanning spot detection signals. 另外,扫描线Rm上的符号RE是对应于扫描点Rmn 的扫描结束位置。 Furthermore, the symbol RE on a scanning line Rm is a scan of scanning point Rmn correspond to the end position.

[0170] 以此,控制部210获取对应于扫描区域R内的mXη个扫描点Rij (i = 1〜m,j = 1〜η)的mXn个检测信号。 [0170] In this, the control unit 210 acquires corresponding to the scanning region R of mXη scanning points Rij (i = 1~m, j = 1~η) mXn the detection signals. 以下,将对应于扫描点Ri j的检测信号表示为Di j。 Hereinafter, the scanning point corresponding to the detection signal Ri j is represented as Di j.

[0171] 如上所述的扫描点的移动与低相干光LO的输出的连动控制,例如,可以通过使控制信号相对于镜片驱动机构M1J42的发送时序(timing)、与控制信号(输出要求信号) 相对于低相干光源160的发送时序互相同步而实现。 Interlocking control [0171] the scanning spot moves as described above, the low-coherence light LO output, for example, by the control signal relative to the lens driving mechanism M1J42 transmission timing (Timing), and the control signal (output request signal ) with respect to the low coherence light source 160 transmits a timing synchronized with each other is achieved.

[0172] 当控制部210如上所述使各检流计镜141A、141B动作时,存储有各扫描线Ri的位置或各扫描点Rij的位置(xy坐标系中的坐标),作为表示其动作内容的信息。 [0172] When the control unit 210 as described above so that each of the galvanometer mirror 141A, 141B during operation, stores a position of each scanning line Ri or the position of each scanning point Rij (the coordinate in the xy coordinate system), as represented by its operation information content. 该存储内容(扫描位置信息)与先前同样用于图像形成处理中。 This stored content (scan position information) of the previous image forming process for same.

[0173] 关于图像形成处理 [0173] For the image forming processing

[0174] 以下,针对图像处理部220及图像形成处理部230的OCT图像有关的处理,说明其中之一例。 [0174] Here, the processing relating to OCT images processing section 230 for forming an image and an image processing unit 220, an example of which.

[0175] 图像处理部220执行沿着各扫描线Ri (主扫描方向)的眼底Ef的断层图像形成处理。 [0175] The image processing unit 220 performs a tomographic image formed along each scanning process line Ri (main scanning direction) of the fundus oculi Ef. 另外,图像处理部230进行基于图像形成部220形成的断层图像的眼底Ef的三维图像的形成处理等。 Further, the image processing unit 230 performs three-dimensional image formation process of a tomographic image of the fundus oculi Ef is formed by the image forming portion 220 and the like based.

[0176] 图像形成部220的断层图像的形成处理与先前同样,包含两阶段的运算处理。 Forming process [0176] tomographic image of the image forming portion 220 similar to the previous, comprising two stages of arithmetic processing. 在第1阶段的运算处理,根据对应于各扫描点Rij的检测信号Dij,形成在该扫描点Rij的眼底Ef的深度方向(图1所示ζ方向)的图像。 In the first stage of arithmetic processing according to the scanning point Rij corresponding to the detection signal Dij of, formed in the image of the fundus Ef of the scanning point Rij depth direction ([zeta] direction shown in FIG. 1).

[0177] 图7表示由图像处理部220所形成的断层图像的形态。 [0177] FIG. 7 shows a form of a tomographic image by the image processing section 220 is formed. 在第2阶段的运算处理, 对于各扫描线Ri,根据其上的η个扫描点Ri 1〜Rin上的深度方向的图像,形成沿着该扫描线Ri的眼底Ef的断层图像G i。 In the second stage of the calculation process, for each scanning line Ri, the image in the depth direction η scanning points thereon Ri 1~Rin, forming the fundus oculi Ef along this scanning line Ri tomographic image G i. 此时,图像形成部220参照各扫描点Ril〜Rin的位置信息(上述扫描位置信息),决定各扫描点Ril〜Rin的排列及间隔,并形成该扫描线Ri。 In this case, the location information 220 with reference to each of the scanning spot in the image forming portion Ril~Rin (the aforementioned scan position information) of each scanning point Ril~Rin determined arrangement and spacing, and forming the scanning line Ri. 经过以上的处理,可获得副扫描方向(y方向)上不同位置上的m个断层图像Gl〜Gm。 Through the above process, is obtained sub scanning direction (y direction) of m number of tomographic images at different positions on Gl~Gm.

[0178] 接着,说明图像处理部230的眼底Ef的三维图像的形成处理。 [0178] Next, a process of forming a three-dimensional image of the fundus Ef of an image processing unit 230. 眼底Ef的三维图像是根据通过上述运算处理所获得的m个断层图像而形成。 Three-dimensional image of the fundus oculi Ef is formed in accordance with the m tomographic images obtained by the above-described arithmetic processing. 图像处理部220进行在邻接的断层图像Gi、G(i+l)之间内插图像的众所周知的内插处理等,从而形成眼底Ef的三维图像。 The image processing unit 220 performs a tomographic image Gi of the adjacent, between the interpolation images G (i + l) is well known interpolation processing and the like, to thereby form a three-dimensional image of the fundus oculi Ef. [0179] 此时,图像处理部230参照各扫描线Ri的位置信息而决定各扫描线Ri的排列及间隔,从而形成该三维图像。 [0179] In this case, the image processing unit 230 with reference to the position information of each scanning line Ri is determined and the arrangement interval between the scanning lines Ri, thereby forming the three-dimensional image. 该三维图像中,根据各扫描点Rij的位置信息(上述扫描位置信息)与深度方向的图像的ζ坐标,设定三维坐标系(x、y、z)。 The three-dimensional image, the position information of each scanning point Rij ζ coordinates of the image (the scanning position information) in the depth direction, setting a three-dimensional coordinate system (x, y, z).

[0180] 而且,图像处理部230根据该三维图像,可以形成主扫描方向(χ方向)以外的任意方向的剖面上眼底Ef的断层图像。 Tomographic image of the fundus Ef on a cross section in an arbitrary direction [0180] Moreover, the image processing unit 230 based on the three-dimensional image can be formed in the main scanning direction (direction [chi]) outside. 当指定剖面时,图像处理部230确定该指定剖面上的各扫描点(及/或所内插的深度方向的图像)的位置,并从三维图像中抽取各确定位置上深度方向的图像(及/或所内插的深度方向的图像),且通过将所抽取的多个深度方向的图像进行排列而形成该指定剖面上眼底Ef的断层图像。 When the specified cross-sectional image processing unit 230 determines the position of each scanning point (and / or image in the depth direction is interpolated by) on the designated cross-section, and extracts an image in the depth direction of the respective determined positions on the three-dimensional image (and / within the image or the interpolated depth direction), and form a tomographic image of the designated cross section are arranged on the fundus oculi Ef by the image of the plurality of extracted depth direction.

[0181] 另外,图7所示的图像Gmj表示扫描线Rm上的扫描点Rmj上深度方向(ζ方向) 的图像。 [0181] Furthermore, the image Gmj shown in FIG. 7 shows a scanning spot on the scanning line Rm Rmj image in the depth direction ([zeta] direction). 同样,可用“图像Gij”表示在上述第1阶段的运算处理中所形成的、各扫描线Ri 上的各扫描点Rij上深度方向的图像。 Similarly, the available "image Gij" represents each of the scanning points on each scanning line Ri in the above-described second stage of arithmetic processing image Rij is formed in the depth direction.

[0182] 作用与效果 [0182] Function and effect

[0183] 以下,说明上述构造的本施形态的眼底观察装置1的作用及效果。 [0183] Hereinafter, operations and effects of the present apparatus 1 constructed as described above is applied to form a fundus observation.

[0184] 该眼底观察装置1包括:眼底相机单元1A,用以获得表示眼底Ef的表面状态的二维图像的眼底相机;以及OCT单元150,用以获得眼底Ef的断层图像(及三维图像)的光学图像计测装置。 [0184] The fundus oculi observation device 1 comprises: the retinal camera unit. 1A, to obtain a surface state of the fundus oculi Ef represents fundus camera the two-dimensional image; OCT unit 150, for obtaining a tomographic image of the fundus oculi Ef (and three-dimensional image) the optical image measurement device.

[0185] 用OCT单元150形成图像使用的信号光的光路,被眼底相机单元IA的拍摄光学系统120形成的光路(拍摄光路)合成,引导至受检眼E。 Light path [0185] used for forming an image of the signal light by the OCT unit 150, an optical path is formed by a fundus camera unit 120 IA of the photographing optical system (photographing optical path) synthesis, directed to the examinee's eye E. 该光路的合成由分色镜134进行。 Synthesis of the optical path by the dichroic mirror 134.

[0186] 又,信号光LS的眼底反射光沿拍摄光路被引导到分色镜134,并且由该分色镜134 从该拍摄光路分离射向OCT单元150。 [0186] In addition, the fundus reflection light of the signal light LS along the photographing optical path is guided to the dichroic mirror 134, the dichroic mirror 134 and separated by the OCT unit directed from the photographing optical path 150.

[0187] 如此,因设有分色镜134(光路分离合成元件)将眼底相机单元IA的拍摄光路与信号光LS的光路进行合成、分离,能够获取的眼底Ef的表面的二维图像以及眼底Ef的断层图像(及三维图像)两者。 [0187] Thus, because with the dichroic mirror 134 (optical path separating a composite member) to the photographing optical path of the signal light path of the light LS in the fundus camera unit IA are synthesized, separated, the two-dimensional image of the surface of the fundus oculi Ef can be acquired and fundus both the tomographic image Ef (and three-dimensional image).

[0188] 尤其是,即使在眼底相机单元IA的照明光与OCT单元150的信号光LS同时对受检眼E照射时,亦可用分色镜134将各别的眼底反射光分离,能够各别检测形成图像。 [0188] In particular, even when the signal light LS in the fundus camera unit IA of illumination light of the OCT unit 150 while simultaneously irradiating the examinee's eye E, the dichroic mirror 134 can also be used to separate respective fundus reflection light can be individual detecting the formation of an image. 故能够同时拍摄眼底Ef的表面的二维图像以及眼底Ef的断层图像两者。 It is possible to simultaneously photographing a tomographic image of both the two-dimensional image of the surface of the fundus oculi Ef and the fundus oculi Ef.

[0189] 此时,从OCT单元150的信号光LS及同时照射的照明光,可用由拍摄光源103发出的近红外光,也可用由观察光源射出的可见光。 [0189] At this time, the signal light from the OCT unit LS 150 and simultaneously irradiated illumination light is available near-infrared light emitted by the imaging light source 103, can also be used by the observation light source emits visible light.

[0190] 变形例 [0190] Modification

[0191] 以上详述的构造,只不过是本发明的眼底观察装置的一个较好的实施例。 [0191] The configuration described in detail above, but is preferably a fundus observation device according to the present embodiment of the invention. 因此,在本发明的要旨的范围内,可适宜地实施任意的变形。 Thus, within the scope of the gist of the present invention may be implemented in any suitably modified.

[0192] 例如在上述的实施形态中,使用波长约800nm〜900nm的近红外光作为低相干光L0,但为进行眼底Ef的更深区域的图像检测,可备吏用波长更长的光,例如约900nm〜 IOOOnm的波长的近红外光,或使用波长约IOOOnm〜IlOOnm的近红外光。 [0192] For example, in the embodiment described above, the wavelength of near-infrared light of about 800nm~900nm as low-coherence light L0, for the image detection but deeper region of the fundus oculi Ef, can be prepared by officials having a longer wavelength, e.g. near infrared light, or a wavelength of about IOOOnm~IlOOnm near-infrared light of a wavelength of about 900nm~ IOOOnm.

[0193] 另外,在使用波长约900nm〜IOOOnm的低相干光LO的场合,可使用例如波长约700nm〜900nm的近红外光为眼底相机单元IA的照明光。 [0193] Further, in the case of using a wavelength of about 900nm~IOOOnm low-coherence light LO is, for example, a wavelength of the illumination light may be used from about near-infrared light 700nm~900nm fundus camera unit of IA. 又在使用波长约IOOOnm〜IlOOnm 的近红外光为低相干光LO的场合,可使用例如波长约850nm〜IOOOnm的近红外光为眼底相机单元IA的照明光。 And a wavelength of about IOOOnm~IlOOnm using near-infrared light for the case of low-coherence light LO is, for example, a wavelength of about 850nm~IOOOnm using near-infrared light as the illumination light of the retinal camera unit IA. 此处,在任一种场合,都希望将低相干光LO的波长设定成较眼底相机单元IA的照明光的波长更长,但是也可以应用到波长的长短关系相反的构造。 Here, in either case, all the low-coherence light LO desired wavelength set to a wavelength of the illumination light of the retinal camera unit IA than longer, but the opposite configuration can also be applied to the relationship between the length of the wavelength. [0194] 又,本发明的眼底观察装置的第一图像形成机构,不限定使用于眼底相机(单元),任何可形成眼底表面的二维图像的眼科装置皆可以应用。 [0194] Further, the first image of the fundus oculi observation device according to the present invention, the forming means is not limited to the use of a fundus camera (unit), any ophthalmic device forming a two-dimensional image of a fundus surface are applicable. 例如缝隙灯(slit lamp,细隙灯显微镜装置)等亦可当做第一图像形成机构使用。 E.g. slit lamp (slit lamp, the fine slit lamp microscope) and the like may also be used as a first image forming means.

[0195] 另外,在上述的实施形态,用图像形成部220 (图像形成板208)进行眼底图像的形成处理,再用控制部210(微处理器201等)进行各种控制处理。 [0195] Further, in the embodiment described above, the fundus image forming process performed using 220 (image forming board 208) of the image forming section, then the control unit 210 (microprocessor 201, etc.) for various control processes. 但亦可用将该双方的处理用一台或多数台的计算机处理的构造。 However, the process can also be used with both the computer configuration or a majority processing station.

[0196] 第二实施形态 [0196] Second Embodiment

[0197] 以下说明本发明第二实施形态的眼底观察装置。 [0197] The following description of the second embodiment of the present invention is a fundus observation device. 本实施形态的眼底观察装置,与第一实施形态的眼底观察装置1有同样的构造(参考图1〜图4)。 The present embodiment fundus oculi observation device, the fundus observation device of the first embodiment 1 has the same configuration (refer to FIG. 1 ~ FIG. 4). 另外,本实施形态的眼底观察装置的信号光的扫描形态或断层图像的形成形态,与图6与图7相同。 In addition, a form or forms a tomographic image of the scanning signal light a fundus observation device according to the present embodiment, the same as in FIG. 6 and FIG. 7. 以下以本实施形态的眼底观察装置,与第一实施形态的不同的点为重心说明。 In the following the present embodiment fundus oculi observation device, the points different from the first embodiment described the center of gravity.

[0198] 图8表示本实施形态的眼底观察装置的控制系统的构造的一例。 [0198] FIG. 8 shows an example of configuration of a control system of the fundus observation device of the present embodiment. 该图所示的眼底观察装置20,与第一实施形态同样地设有眼底相机单元1A、OCT单元150、以及演算控制装置200。 A fundus observation apparatus shown in FIG. 20, 150 provided the same shape, and the calculation and control means retinal camera unit 1A, OCT unit 200 in the first embodiment.

[0199] 此处,对参照光LR的光路构造说明。 [0199] Here, description of the configuration of the reference light LR optical path. 首先说明引导参照光LR的光纤163,其对参照光LR的色散影响,设定成大约等于从光耦合器162发生的信号光LS,经过眼底Ef至与参照光LR重叠的期间所受的色散影响。 First, the reference light LR guided to the optical fiber 163, the influence on the dispersion of the reference light LR, is set to be approximately equal to the signal light LS generated from the optical coupler 162, suffered after a period of the fundus oculi Ef and the reference light LR to overlap dispersion influences.

[0200] 亦即,参照光LR因该光纤163的芯心的色散影响,被引导而付与像差。 [0200] That is, the reference light LR by the influence of dispersion of the optical fiber core spindle 163, is guided to pay aberration. 另外,信号光LR经过光纤164、连接线152内部的光纤152a、透镜142、扫描单元141,分色镜134、拍摄透镜126、中继透镜125、倍率可变透镜124、拍摄光圈121、开孔镜片112的孔部11¾以及物镜113,入射到受检眼E。 Further, the signal light LR through the optical fiber 164, optical fiber 152 inside the connection line 152a, the lens 142, the scanning unit 141, the dichroic mirror 134, imaging lens 126, relay lens 125, the magnification variable lens 124, the photographing diaphragm 121, opening lens 112 and an objective lens 11¾ hole portion 113, is incident on the examinee's eye E. 从受检眼E射出的信号光LS,由该路径逆转回到光耦合器162。 The signal light LS is emitted to the examinee's eye E by reversing the path back to the optical coupler 162. 此时,该信号光LS在通过光纤164、15¾、透镜142、分色镜134、拍摄透镜126、中断透镜125、 倍率可变透镜1¾与物镜113的各光学组件时,由该些光学组件的色散影响付与像差。 At this time, when the signal light LS by the optical fiber 164,15¾, a lens 142, a dichroic mirror 134, imaging lens 126, a lens 125 interrupt, 1¾ magnification variable lens 113 of the objective lens with the optical components of the optical assembly of the plurality of dispersion on pay and aberrations. 该些各光学组件发生的色散影响(色散量),可依据形成该光学组件的材料特性(折射率等) 计算。 Material properties (refractive index, etc.) affect the dispersion (chromatic dispersion amount) of each of the plurality of optical components occur, the optical assembly may be formed according to calculation. 又,测量光的色散量的装置也已被广用。 And, means for measuring the amount of light dispersion have also been widely used.

[0201] 引导参照光LR的光纤163是被形成具有一光纤长,其使该些光学组件付与信号光LS的色散量的合计值大约相等于参照光LR被付与的色散量。 [0201] guiding the reference light LR 163 is an optical fiber having a fiber length is formed, so that the plurality of optical components to pay the sum with the amount of dispersion of the signal light LS is approximately equal to the reference amount to be paid and the dispersion of light LR. 此时,该光纤163的长度为减去前述玻璃块172或密度滤光片173所付与的色散量后所得的长度。 In this case, the length of the optical fiber 163 is a length obtained by subtracting the amount of dispersion of the density filter 172 and the glass block 173 and the payment. 亦即,光纤163、玻璃172及密度滤光片173付与的参照光LR的色散量,设计成与该些光学组件付与信号光LS的色散量大约相等。 That is, the optical fiber 163, the amount of dispersion of glass 172 and the density filter 173 to pay the reference light LR, designed to impart the plurality of optical components is about equal to the amount of dispersion of the signal light LS.

[0202] 另外,信号光LS也受其光路(信号光路)上的空气发生的色散影响,参照光LR的光路(参照光路)亦设计成空气付与参照光LR的色散量,与空气付 [0202] Further, the signal light LS is also subject to the optical path (signal light path) dispersion effect of air on the occurrence of the optical path (reference light path) of the reference light LR is also designed to disperse the amount of air to impart the reference light LR, and the air Fu

[0203] 与信号光的色散量大约相等的构造。 [0203] and the amount of dispersion of the signal light is approximately equal configuration. 又,因该空气付与的色散影响,与该些光学组件的色散影响比较非常的小。 Further, because the influence of the dispersion of air imparted, and the influence of the dispersion of these optical components is very small in comparison. 因此,本发明的眼底观察装置的构造,也可只考虑光学组件的色散影响。 Thus, the configuration of the fundus observation device according to the present invention, the dispersion may only consider the influence of the optical assembly. 在本实施形态,也考虑该空气的色散影响,以更提高图像的观测精度。 In the present embodiment, consider the influence of the dispersion of air to more improve the accuracy of the observation image. 另外,在参照光路上的玻璃172或密度滤光片173,是使参照光LR的色散量与信号光路付与信号光LS的色散量大约相等的装置,但因该玻璃块172等的存在,信号光路与参照光路的光路长度发生差异。 Further, the glass in the optical path of the reference density filter 172 or 173, a reference light LR and the signal light path dispersion amount means the amount of dispersion of the signal light LS is approximately equal to pay, but the presence of such a glass block 172, the signal the optical path length of the light path and the reference light path difference occurs. 该光路长度的差异,在将参照光路的光路长度与信号光路的光路长度重叠时,就可消除。 This difference in optical path length, when the optical path length of the optical path length of the reference light path of the signal light path overlap can be eliminated. 例如,在设计参照光路时,使参照光LR通过空气的距离与信号光LS通过空气的距离大约相等(例如,适宜设计玻璃块172等的配置间隔),以消除光路长度的差异。 For example, in the design of the reference optical path, reference light LR and the signal light LS by the distance equal to the distance of the air around the air (e.g., a suitable design of the glass block intervals 172, etc.) to eliminate the difference in optical path length.

[0204] 在演算控制装置200的硬盘驱动器204 (参照图4)中,除了记忆控制程序20½外, 记忆例如与患者有关的信息(患者信息)等各种信息。 [0204] In the hard disk drive 204 of the arithmetic control device 200 (see FIG. 4), in addition to the control program 20½ external memory, memories such as various information related to patient information (patient information) and the like. 例如包含患者ID(识别信息)或患者性名等以及受检眼的眼球光学系统的球面度数,乱视度数、乱视轴角度、角膜曲率半径, 像差等的检查资料等,作为该患者信息。 For example, spherical power of the eyeball optical system comprises a patient ID (identification information) or the name of the patient, and the like of the subject eye, depending on the degree of disorder, visual disorder axis angle, the radius of curvature of the cornea, other aberrations examination information, etc., as the patient information .

[0205] 本实施形态的演算控制装置200具备修正处理部250。 The calculation and control unit [0205] 200 of the present embodiment includes a correction processing unit 250. 该修正处理部250依据在控制部210的硬盘驱动器204中所记忆的受检眼的眼球光学系统的像差,进行眼底Ef的OCT图像(断层图像或三维图像)的修正处理。 OCT image (tomographic image or a three-dimensional image) of the correction processing section 250 in accordance with the aberration of the optical system of the eye of the examinee's eye 210 controls the hard disk drive 204 of the memory of the fundus Ef correction process. 例如,修正处理部250对各断层图像GiJf 正受检眼E的眼球光学系统的像差产生的影响。 For example, the influence of the aberration correcting processing section 250 for each tomographic image of the subject's eye E n GiJf eye generated by the optical system. 此处,受检眼的眼球光学系统的像差,例如可利用本专利申请人的日本专利特开2002-306416号公报揭露的眼特性测定装置等检测。 Here, the aberration of the eyeball optical system of the examinee's eye, for example, may be utilized by the applicant in Japanese Laid-Open Patent Publication No. 2002-306416 discloses an eye characteristic measuring device and the like is detected. 又,该眼特性测定装置能检测眼球光学系统的多维像差。 In addition, the eye characteristic measurement apparatus capable of detecting multi-dimensional eye aberrations of the optical system. 使用修正处理部250进行OCT图像的像差修正,可适宜地使用既存的任意方法。 Correction processing unit 250 using the OCT image aberration correction, can be suitably used any of the existing methods. 该修正处理部250,做为本发明的“修正元件”的一例发挥其作用。 The correction processing unit 250, as an example of the "correcting device" of the present invention exerts its effect.

[0206] 以下说明本实施形态的眼底观察装置20的作用及效果。 [0206] The following description and effects of the apparatus 20 according to the present embodiment fundus observation.

[0207] 本实施形态的眼底观察装置20,包括:眼底相机单元1A,做为拍摄眼底Ef的表面状态和二维图像的眼底相机;以及OCT单元150,当做摄取眼底Ef的断层图像(及三维图像)的光学图像测计装置。 [0207] This embodiment 20 fundus oculi observation device, comprising: a fundus camera unit. 1A, the surface state of the camera as a fundus photographing the fundus oculi Ef and the two-dimensional image; OCT unit 150, a tomographic image pickup as the fundus oculi Ef (and D image), an optical image measuring meter apparatus.

[0208] OCT单元150进行图像形成使用的信号光的光路,与眼底相机单元IA的拍摄光学系统130形成的光路(拍摄光路)合成被引导到受检眼E。 [0208] OCT unit 150 performs image formation using the optical path of the signal light, the optical path (photographing optical path) and the photographing optical system of a fundus camera unit IA 130 is directed to the synthesis of the examinee's eye E. 该光路的合成由分色镜134施行。 Synthesis of the optical path by the dichroic mirror 134 is performed.

[0209] 另外,信号光LS的眼底反射光,被引导沿拍摄光路到分色镜134,再由该分色镜134从拍摄光路分离,射向OCT单元150。 [0209] Further, the fundus reflection light of the signal light LS is guided along the shooting optical path to the dichroic mirror 134, and then separated by the dichroic mirror 134 from the photographing optical path toward the OCT unit 150.

[0210] 如上述,因设置分色镜134进行眼底相机单元IA的拍摄光路,与信号光LS的光路的合成、分离作用,能够获取眼底Ef表面的二维图像及眼底Ef的断层关系(及三维图像) 两者。 [0210] As described above, by providing the dichroic mirror 134 for imaging the optical path of the fundus camera unit IA, synthetic, separating action of the optical path of the signal light LS is possible to obtain a tomographic relationship dimensional image and the fundus oculi Ef Ef surface of the fundus (and three-dimensional image) both.

[0211] 特别是,对受检眼E同时照射眼底相机单元IA的照明光及OCT单元150的信号光LS,仍可用分色镜134将各别的眼底反射光分离,分别检测形成图像。 [0211] In particular, while the illumination light and the fundus camera unit IA OCT unit of the signal light LS 150, the dichroic mirror 134 will still respective fundus reflection light of the examinee's eye separation E, respectively, detecting the formation of an image. 故能够同时拍摄眼底Ef表面的二维图像及眼底Ef的断层图像两者。 It is possible to simultaneously capturing two-dimensional tomographic image and a fundus image Ef surface of the fundus oculi Ef.

[0212] 此时,由OCT单元150输出的信号光LS及同时照射的照明光,可使用拍摄光源103的近红外光,也可用由观察光源101的可视光。 [0212] At this time, the signal light LS 150 and the output from the OCT unit simultaneously irradiated illumination light may be near-infrared light imaging source 103, it can also be used by the observation light source 101 of visible light.

[0213] 本实施形态的眼底观察装置20配设具一光纤长度的光纤163,其使参照光LR的色散量与光耦合器162发生的信号光LS,从通过眼底Ef到与参照光LR重叠的期间所付与的色散量大约相等。 [0213] This embodiment is provided with a fundus oculi observation device 20 having a fiber length of the fiber 163, which causes the reference light LR and the optical coupler dispersion amount of the signal light LS 162 occurs, from the overlap by the fundus oculi Ef and the reference light LR approximately equal to the amount paid and the dispersion period. 而且,在参照光LR设有付与色散量的玻璃块172及密度滤光片173。 Further, the reference light LR imparting dispersion amount is provided a glass block 172 and the density filter 173. 另外,由于付与参照光色散量的光纤163或玻璃块172等,使信号光路的光路长度与参照光路的光路长度发生差异,但此差异可在设计参照光路时,使参照光LR通过空气中的距离,与信号光LS通过空气中的距离大约相等,以消除该光路长度的差异。 Further, since the pay reference light dispersion amount in the optical fiber 163 and glass block 172 and the like, the signal light path length of the light path and the optical path length of the reference optical path difference occurs, but this difference may be in the design of the reference optical path, reference light LR through the air distance, the signal light LS by approximately the same distance in air, to eliminate differences in the optical path length.

[0214] 亦即该眼底观察装置20的构造,除信号光LS通过多数个光学组件的色散量的合计值,与参照光LR通过多数个光学组件的色散量的合计值大略相等之外,亦形成信号光路长度与参照光的光路长度大略相等的构造。 [0214] i.e., the fundus oculi observation device 20 is constructed, in addition to the signal light LS by the amount of dispersion of the plurality of optical components total value of the reference light LR roughly equal to the total value of dispersion amount by a plurality of optical components, and also forming the optical path length of the signal light and the reference light path length roughly equal to the construction. [0215] 依如上述的眼底观察装置20,因信号光LS的色散影响与参照光的色散影响大约相等,能够将信号光LS与参照光LR以高干涉效率干涉,能发生十分强度的干涉光LC。 [0215] according to claim 20, dispersion-Effect Dispersion on the reference light of the signal light LS is approximately equal to the above-described fundus observation device, the signal light LS and the reference light LR capable of interfering with high interference efficiency, can the interference light is intensity occurs LC. 因此,能够防止因OCT图像对比降低使图像不清楚或图像的准确度降低的情况。 Therefore, the situation can be prevented that the image contrast by reducing the accuracy of the OCT image unclear or reduced image.

[0216] 此外,如上述的构造的光纤163、玻璃块172、密度滤光片173、参照光路,各个皆为相当于本发明的“色散付与元件”的一例。 [0216] Further, as the above-described structure of the optical fiber 163, a glass block 172, the density filter 173, a reference optical path, are all equivalent to each of the "dispersion-imparting element" of the present invention is an example.

[0217] 本实施形态的眼底观察装置20的构造,可依据受检眼E的眼球光学系统的像差, 修正眼底Ef的OCT图像(断层图像或三维图像)。 [0217] The present embodiment of the fundus observation device 20 of the configuration can be based on the aberration of the optical system of the eye E of the examinee's eye, the correction OCT image (tomographic image or a three-dimensional image) of the fundus oculi Ef. 能够更提高OCT图像的清晰度或准确度。 It is possible to more improve clarity or accuracy of the OCT image.

[0218] 以下说明本实施形态的眼底观察装置20的变形例。 [0218] The following description of the present embodiment is a modification of the fundus 20 of the embodiment of the observation apparatus.

[0219] 在上述的实施形态,使用引导参照光LR的光纤163,或玻璃块172、或密度滤光片173或参照光路,作为本发明的“色散付与元件”,但该些之中至少使用一项就足够。 [0219] In the embodiment described above, the reference light LR guided using an optical fiber 163, or a glass block 172, or the density filter 173 or reference optical path, as the "dispersion-imparting element" of the present invention, but the use of at least some among one is enough. 另外如下所述,该些之外,其它的能够给与参照光LR色散影响的任何形态的色散付与机构亦可能适用。 Further below, the plurality of outside, the other can be administered also may apply the dispersion imparting means any form of dispersion influence of the reference light LR.

[0220] 首先,玻璃块172可用例如菱形透镜等能付与光色散作用的任意光学构件构成。 [0220] First, a glass block 172 can be used to pay for example diamond lens constituting the optical member with any light dispersion effect. 另外,也可以使用例如丙烯基树脂等的任意素材形成的色散付与元件,代替玻璃块172。 Further, the dispersion may be used to pay any element with acrylic resin or the like material is formed, for example, instead of the glass block 172.

[0221] 另外,色散付与元件,可作成能调整对光付与色散量的构造,例如由可变棱镜(variable prism)等构成。 [0221] Further, the dispersion imparting member, adjustment can be made to pay for the light dispersion amount configuration, for example, a variable prism (variable prism) and the like. 另外,也可能使用水等液体适量充填框体之内,作为调整光色散量的光学构件。 Further, also possible to use the right amount of liquid such as water filling the housing, as the optical member to adjust the amount of light dispersion.

[0222] 又,因信号光LS通过受检眼E的眼球内再经过眼底Ef,所以“信号光LS所付与的色散量”不仅考虑信号光LS经过眼底观察装置20内的光学组件,尚需包含受检眼E的眼球光学系统付与的色散量,由此可提高色散量的修正精度。 [0222] Further, because the signal light LS via the fundus oculi Ef and then through the eye of the subject eye E, the "signal light LS and the dispersion amount paid" consider not only signal light LS via the fundus observation optical components within the device 20, yet to the amount of dispersion of the eye comprising the optical system imparting a subject eye E, thereby improving dispersion amount correction accuracy. 该眼球光学系统付与的色散量,可依据受检眼E的折射率或眼轴长度等的光学特性值推算。 The amount of dispersion imparting eyeball optical system can be calculated based on the value of refractive index and optical characteristics of the axial length of the examinee's eye E.

[0223] 此处,受检眼E的折射率或眼轴长度,也可用其它的眼科装置事先测量取得,也可在眼底观察装置20搭载测量该些光学特性值的功能求得。 [0223] Here, the refractive index or the axial length of the examinee's eye E, an ophthalmic device may also be other measurements taken previously, apparatus 20 is mounted can also be observed measurements of the plurality of optical characteristic values ​​obtained in the fundus. 另外,也可用临床资料计算折射率或眼轴长度的统计值(平均值等),也可以利用该统计值取得眼球光学系统付与的色散量。 In addition, clinical data can also be used, or the refractive index calculated statistical value (average value) of the axial length, may be acquired using the count value to pay the amount of dispersion of the optical system with the eye. 再者,也可以利用临床数据计算眼球光学系统付与的色散量的统计值,再用该统计值进行修正处理。 Further, the statistical value may be the clinical data calculated using the amount of dispersion of the eye and the optical system to pay, then the correction processing statistics.

[0224] 又,依各受检眼个别考虑眼球光学系统的色散量的场合,该色散付与元件需有能够对应眼球光学系统发生的色散量,变更对参照光LS付与色散量的构造。 [0224] Further, according to the examinee's eye each individual case to consider the amount of dispersion of the optical system of the eye, the dispersion-imparting element capable of corresponding to the amount of dispersion for an optical system of the eye occurs, the reference light LS changes configuration imparting dispersion amount. 因此,设置例如上述的可变棱镜的可调整色散量的色散付与元件,利用控制部210控制该色散付与机构, 能够对参照光LR付与适当的色散量。 Thus, for example, disposed above the adjustable dispersion amount of variable dispersion prism imparting element, the control unit 210 controls the dispersion imparting means, it is possible with an appropriate amount of dispersion of the reference light LR pay.

[0225] 用上述的色散付与元件供给参照光LR色散量,能够补偿至少一部分拍摄光路上的光学组件或空气付与信号光LS的色散量,能够抑制信号光LS与参照光LR的干涉效率的减低。 [0225] Fu dispersion amount of light LR and the component feeding reference to the above-described dispersion can be compensated at least part of imaging reduce the optical path of the optical assembly or air-imparting amount of dispersion of the signal light LS, it is possible to suppress the interference efficiency of the signal light LS and the reference light LR is . 由此能抑制OCT图像的对比或准确度的降低。 Or contrast can be suppressed thereby reducing the accuracy of the OCT image.

[0226] 又,在第一实施形态说明的变形例,也可应用到本实施形态的眼底观察装置20。 [0226] Further, in the modification described in the first embodiment can also be applied to the present embodiment of the fundus observation device 20.

Claims (16)

  1. 1. 一种眼底观察装置,其特征包括:第一图像形成元件,具有照明光学系统,发出照亮受检眼的眼底的照明光;及拍摄光学系统,用第一检测元件检测出通过前述眼底的照明光,其中依据前述第一检测元件的检测结果,形成前述眼底表面的二维图像;第二图像形成元件,具有光源,能够输出与前述照明光不同波长的光;干涉光发生元件,将前述光源输出的光,分割成向前述眼底的信号光及向参照物体的参照光,并将经过前述眼底的信号光与通过前述参照物体的参照光进行重叠而发生干涉光;及第二检测元件, 用以检测出前述发生的前述干涉光,其中依据前述第二检测元件的检测结果,形成前述眼底的断层图像;以及光路合成分离机构,前述信号光的眼底反射光藉由前述拍摄光学系统所形成的拍摄光路被引导到前述光路合成分离机构,并由前述光路 A fundus observation device characterized by comprising: a first image forming element, an illumination optical system that emits illumination light to illuminate the fundus of the examinee's eye; and the photographing optical system, is detected by a first detecting element through the fundus illumination light, wherein based on the detection result of the first detection element, a two-dimensional image of the fundus surface; a second image forming member, having a light source capable of outputting light of the illumination light of different wavelengths; interference light generating element, the the light source the light output into the signal light and the reference light to the fundus of the reference object and the signal light through the fundus of the reference object and by overlapping the reference light optical interference occurs; and a second detecting element , a tomographic image for detecting the occurrence of the interference light, wherein the detection result based on the second detection element, forming the fundus; and an optical path separating mechanism synthesis, the fundus reflection light of the signal light by the optical imaging system photographing optical path formed by the optical path is guided to the separating mechanism synthesized by the optical path 合成分离机构从前述拍摄光路分离而射向前述第二图像形成元件,其中前述照明光与前述信号光,经前述拍摄光路照射前述眼底; 前述照明光学系统包括:环形透光板,配置在与前述受检眼的瞳孔为共轭的位置,且前述照明光通过前述环形透光板,前述照明光学系统与前述拍摄光学系统包括:开孔镜片,在中心区域具有孔部,前述开孔镜片使来自前述照明光学系统的照明光反射,前述照明光与前述信号光的眼底反射光通过前述孔部。 Synthesis separating mechanism from the photographing optical path toward the separation of the second image forming element, wherein the illumination light and the signal light, the photographing optical path by irradiating the fundus; the illumination optical system comprises: an annular light transmissive plate, disposed with the pupil of the examinee's eye is a position conjugate, and the illumination light passes through the ring transparent plate, the illumination optical system and the photographing optical system comprising: a lens aperture, a hole portion in the central region, from the opening so that the lens reflecting the illumination light of the illumination optical system, the illumination light and the fundus reflection light of the signal light through the aperture portion.
  2. 2.如权利要求1所述的眼底观察装置,其特征在于:由前述第一图像形成元件的前述照明光与前述第二图像形成元件的前述光源所输出的光,为分别具有近红外区域的波长的光。 2. The fundus oculi observation device according to claim 1, wherein: the light output by the light source element is formed by the illumination of the light element of the first image and the second image are formed, each having a near-infrared region the wavelength of light.
  3. 3.如权利要求2所述的眼底观察装置,其特征在于:由前述光源所输出的光的波长,较前述照明光的波长长。 A fundus observation device according to claim 2, wherein: the wavelength of light generated by the light source output, wavelength longer than the illumination light.
  4. 4.如权利要求3所述的眼底观察装置,其特征在于: 前述照明光具有包含范围700nm〜800nm的波长,且前述光源输出的光具有包含范围800nm〜900nm的波长。 4. The fundus oculi observation device according to claim 3, wherein: the illumination light having a wavelength in the range containing 700nm~800nm, and outputting the light source comprising a light having a wavelength in the range 800nm~900nm.
  5. 5.如权利要求3所述的眼底观察装置,其特征在于: 前述照明光具有包含范围850nm〜IOOOnm的波长,且前述光源输出的光具有包含范围IOOOnm〜IlOOnm的波长。 5. The fundus oculi observation device according to claim 3, wherein: the illumination light having a wavelength in the range containing 850nm~IOOOnm, and the light source output light has a wavelength range containing the IOOOnm~IlOOnm.
  6. 6.如权利要求1所述的眼底观察装置,其特征在于: 前述光路合成分离机构是分色镜。 6. The fundus oculi observation device according to claim 1, wherein: the optical path separating means is a dichroic mirror synthesis.
  7. 7.如权利要求2所述的眼底观察装置,其特征在于:前述第一图像形成元件的前述照明光学系统更包括可视光源,输出具有可视区域的波长的照明光;以及前述拍摄光学系统更包括第三检测元件,以检测出经过前述眼底的具有前述可视区域的波长的照明光;其中前述第一图像形成元件依据前述第三检测元件的检测结果,形成前述眼底的表面的二维图像。 7. The fundus oculi observation device according to claim 2, wherein: the first image forming element of the illumination optical system further comprises a visible light source, the illumination light having an output wavelength of the visible region; and the imaging optical system further comprising a third detecting element for detecting the illumination light having a wavelength region of the visible through the fundus; wherein the first image-forming element according to the detection result of the third detecting element, the surface of the formed two-dimensional fundus image.
  8. 8.如权利要求7所述的眼底观察装置,其特征在于:前述拍摄光学系统更包括光路分离元件,用以将具有前述红外区域的波长的照明光的光路以及具有前述可视区域的波长的照明光的光路进行分离。 8. The fundus oculi observation device according to claim 7, wherein: the photographing optical system further comprising a wavelength light path separation element for the optical path of the illumination light having an infrared wavelength region and a visible region of the the optical path of the illumination light is separated.
  9. 9.如权利要求1所述的眼底观察装置,其特征在于:前述干涉光发生元件包含色散付与元件,用以将色散量付与给前述参照光。 9. The fundus oculi observation device according to claim 1, wherein: the interference light generating element comprises a dispersion-imparting member for imparting the dispersion amount to said reference light.
  10. 10.如权利要求9所述的眼底观察装置,其特征在于前述色散付与元件付与前述参照光的色散量,与前述信号光从前述干涉光发生元件分割后到前述重叠的期间被付与的色散量大约相等。 10. The fundus oculi observation device according to claim 9, characterized in that the amount of the dispersion during dispersion amount of the dispersion imparting device to impart the reference light and the signal light from the element dividing the interference light generator to the overlapping is paid with approximately equal.
  11. 11.如权利要求9所述的眼底观察装置,其特征在于: 前述色散付与元件包含光纤,以引导前述参照光,前述光纤具有光纤长度,使其付与前述参照光的色散量大约等于前述信号光被付与的色散量。 11. The fundus oculi observation device according to claim 9, characterized in that: the fiber comprises a dispersion-imparting element to guide the reference light, the optical fiber having a fiber length, the amount of dispersion so as to impart the reference light is approximately equal to the signal light They are paid and the amount of dispersion.
  12. 12.如权利要求9所述的眼底观察装置,其特征在于:前述色散付与元件包含玻璃块,能够将预定的色散量付与给前述参照光。 12. The fundus oculi observation device according to claim 9, wherein: the dispersive element comprises a glass block imparting, a predetermined amount of dispersion can be paid and to the reference light.
  13. 13.如权利要求9所述的眼底观察装置,其特征在于:前述色散付与元件包含密度滤光片,能够将预定的色散量付与给前述参照光。 13. The fundus oculi observation device according to claim 9, wherein: the element comprises a dispersion imparting density filter, a predetermined amount of dispersion can be paid and to the reference light.
  14. 14.如权利要求9所述的眼底观察装置,其特征在于:更包括修正元件,依据前述受检眼的眼球光学系统的像差,修正由前述第二图像形成元件形成的前述眼底的断层图像。 14. The fundus oculi observation device according to claim 9, characterized in that: further comprising a correcting element, according to the aberration of the optical system of the eye of the examinee's eye, the fundus tomographic image correction element is formed by said second image is formed .
  15. 15.如权利要求1所述的眼底观察装置,其特征在于:前述干涉光发生元件从进行前述分割至前述重叠的期间,前述信号光经过多数个光学组件的色散量的合计值,与前述干涉光发生元件从进行前述分割至前述重叠的期间,前述参照光经过多数个光学组件的色散量的合计值大约相等。 The amount of dispersion of signal light through the plurality of optical assemblies of the total value, the interference with the interference light generator to split from the period for the overlap: 15. The fundus oculi observation device according to claim 1, characterized in that generating element for dividing the light from the to the overlapping period, the reference light passes through the dispersion amount of the total value of a plurality of optical components are about equal.
  16. 16.如权利要求15所述的眼底观察装置,其特征在于:前述干涉光发生元件从进行前述分割至前述重叠的期间,前述信号光被空气付与的色散量,与前述干涉光发生元件从进行前述分割至前述重叠的期间,前述参照光被空气付与的色散量大略相等。 16. The fundus oculi observation device according to claim 15, wherein: the amount of dispersion from the interference light generating element for dividing the to the overlapping period, the signal light is paid with air, and the interference light from the generating element for said splitting to the overlapping period, the reference light amount of air is dispersed to impart the almost same.
CN 200710000924 2006-01-10 2007-01-08 Fundus observation device CN100998495B (en)

Priority Applications (4)

Application Number Priority Date Filing Date Title
JP2006-003066 2006-01-10
JP2006003066A JP2007181632A (en) 2006-01-10 2006-01-10 Fundus observation device
JP2006003065A JP2007181631A (en) 2006-01-10 2006-01-10 Fundus observation system
JP2006-003065 2006-01-10

Publications (2)

Publication Number Publication Date
CN100998495A true CN100998495A (en) 2007-07-18
CN100998495B true CN100998495B (en) 2012-01-25

Family

ID=38257373

Family Applications (1)

Application Number Title Priority Date Filing Date
CN 200710000924 CN100998495B (en) 2006-01-10 2007-01-08 Fundus observation device

Country Status (2)

Country Link
JP (1) JP2007181631A (en)
CN (1) CN100998495B (en)

Families Citing this family (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP4869757B2 (en) * 2006-03-24 2012-02-08 株式会社トプコン Fundus observation device
FI120958B (en) * 2007-10-19 2010-05-31 Optomed Oy Illuminating body
DE102008000225B3 (en) * 2008-02-01 2009-03-26 Linos Photonics Gmbh & Co. Kg fundus
JP4732541B2 (en) 2008-10-24 2011-07-27 キヤノン株式会社 Adapter, an optical tomographic imaging apparatus, a program, an ophthalmic apparatus
JP5610706B2 (en) 2009-05-22 2014-10-22 キヤノン株式会社 An imaging apparatus and an imaging method
WO2011153275A1 (en) * 2010-06-01 2011-12-08 Optovue, Inc. Method and apparatus for enhanced eye measurement
CN102525404B (en) * 2010-11-05 2015-09-30 尼德克株式会社 Ophthalmic device
CN102389290B (en) * 2011-08-01 2013-07-03 温州医学院眼视光研究院 Frequency-domain optical coherence tomography system
JP6143421B2 (en) * 2012-03-30 2017-06-07 キヤノン株式会社 Optical coherence tomography apparatus and method
DE102012019469A1 (en) * 2012-09-28 2014-04-03 Carl Zeiss Meditec Ag Process for the implementation of OCT and other video recordings of an eye
US9723978B2 (en) 2014-03-31 2017-08-08 Nidek Co., Ltd. Fundus photography device
CN105011900B (en) * 2014-04-30 2018-02-02 卡尔蔡司医疗技术公司 The method of generating a wide field of view of the optical coherence tomogram, and means for

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5506634A (en) 1994-07-05 1996-04-09 Carl Zeiss, Inc. Fundus illumination apparatus formed from three, separated radiation path systems
US5537162A (en) 1993-12-17 1996-07-16 Carl Zeiss, Inc. Method and apparatus for optical coherence tomographic fundus imaging without vignetting
CN1348738A (en) 2001-11-16 2002-05-15 清华大学 Measuring arm of optical coherent tomographic eye examining instrument used together with slit lamp
US6826359B1 (en) 1999-04-27 2004-11-30 Kabushiki Kaisha Topcon Fundus camera
CN1694644A (en) 2002-06-28 2005-11-09 Oti眼技术股份有限公司 Optical mapping apparatus with adjustable depth resolution and multiple functionality

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP3653582B2 (en) * 1996-07-21 2005-05-25 株式会社トプコン Ophthalmic apparatus
JP2001275980A (en) * 2000-03-31 2001-10-09 Nidek Co Ltd Eyeground camera
JPWO2002022005A1 (en) * 2000-09-11 2004-01-22 興和株式会社 The subject's eye imaging apparatus
DE10128219A1 (en) * 2001-06-11 2002-12-12 Zeiss Carl Jena Gmbh Topographic measurement of the eye structure, such as the cornea and eye lens by use of coherence-topography with depth measurements insensitive to longitudinal and transverse movements of the reference arm of the instrument
GB0324062D0 (en) * 2003-10-14 2003-11-19 Univ Kent Canterbury Spectral interferometry method and apparatus
JP4545418B2 (en) * 2003-11-06 2010-09-15 株式会社トプコン Fundus camera

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5537162A (en) 1993-12-17 1996-07-16 Carl Zeiss, Inc. Method and apparatus for optical coherence tomographic fundus imaging without vignetting
US5506634A (en) 1994-07-05 1996-04-09 Carl Zeiss, Inc. Fundus illumination apparatus formed from three, separated radiation path systems
US6826359B1 (en) 1999-04-27 2004-11-30 Kabushiki Kaisha Topcon Fundus camera
CN1348738A (en) 2001-11-16 2002-05-15 清华大学 Measuring arm of optical coherent tomographic eye examining instrument used together with slit lamp
CN1694644A (en) 2002-06-28 2005-11-09 Oti眼技术股份有限公司 Optical mapping apparatus with adjustable depth resolution and multiple functionality

Also Published As

Publication number Publication date Type
JP2007181631A (en) 2007-07-19 application
CN100998495A (en) 2007-07-18 application

Similar Documents

Publication Publication Date Title
US6267477B1 (en) Three dimensional imaging apparatus and a method for use thereof
EP1775545A2 (en) Optical image measuring device, optical image measuring program, fundus observation device, and fundus observation program
US20070285619A1 (en) Fundus Observation Device, An Ophthalmologic Image Processing Unit, An Ophthalmologic Image Processing Program, And An Ophthalmologic Image Processing Method
US20100194757A1 (en) Fundus oculi observation device, ophthalmologic image processing device, and program
JP2008154704A (en) Fundus oculi observation device, fundus oculi image display device, and program
US20070222945A1 (en) Fundus Observation Device
US20080259275A1 (en) Eye movement measuring apparatus, eye movement measuring method and recording medium
JP2009183332A (en) Fundus observation apparatus, fundus image processing device, and program
US7566128B2 (en) Fundus observation device, fundus image display device and fundus observation program
US20080151256A1 (en) Optical image measurement device
US20080084538A1 (en) Fundus oculi observation device, a fundus oculi image display device and a fundus oculi image display method
JP2008073099A (en) Fundus observation apparatus, fundus image display device, and fundus observation program
US7604351B2 (en) Optical image measurement device and optical image measurement method
US7370966B2 (en) Opthalmologic apparatus
US20070222946A1 (en) Fundus Observation Device
US20110080561A1 (en) Optical image measuring device
US20100039616A1 (en) Optical image measurement device and program for controlling the same
US20100149489A1 (en) Fundus oculi observation device and program for controlling the same
US20080234972A1 (en) Optical image measurement device and image processing device
US20120327365A1 (en) Ophthalmologic apparatus and control method for the same
JP2008206684A (en) Fundus oculi observation device, fundus oculi image processing device and program
US20080030680A1 (en) Fundus observation device and a program controlling the same
JP2008237237A (en) Fundus oculi observing system, ophthalmologic image display system, and program
US7777893B2 (en) Optical image measurement device
US20130188129A1 (en) Ophthalmologic apparatus, control method therefore, and recording medium storing method

Legal Events

Date Code Title Description
C06 Publication
C10 Request of examination as to substance
C14 Granted
C17 Cessation of patent right