JP5209143B2 - Fundus observation device - Google Patents

Description

  The present invention relates to a fundus oculi observation device used for observing the fundus oculi of a subject eye.

  Conventionally, fundus cameras have been widely used as fundus oculi observation devices. FIG. 8 shows an example of the external configuration of a conventional general fundus camera, and FIG. 9 shows an example of the configuration of an optical system built in the fundus camera (see, for example, Patent Document 1). Note that “observation” includes at least a case where a photographed image of the fundus is observed (others may include fundus observation with the naked eye).

  First, the external configuration of a conventional fundus camera 1000 will be described with reference to FIG. The fundus camera 1000 includes a gantry 3 mounted on a base 2 so as to be slidable in the front-rear and left-right directions (horizontal direction). The gantry 3 is provided with an operation panel 3a and a joystick 4 for the examiner to perform various operations.

  The examiner can move the gantry 3 three-dimensionally on the base 2 by operating the joystick 4. On the top of the joystick 4, an operation button 4a that is pressed when photographing the fundus is disposed.

  A support column 5 is erected on the base 2. The column 5 is provided with a chin rest 6 for mounting the subject's jaw and an external fixation lamp 7 for emitting light for fixing the eye E.

  On the gantry 3, a main body 8 that stores various optical systems and control systems of the fundus camera 1000 is mounted. The control system may be provided inside the base 2 or the gantry 3 or may be provided in an external device such as a computer connected to the fundus camera 1000.

  On the eye E side of the main body 8 (the left direction in FIG. 8), an objective lens unit 8a is provided so as to face the eye E. Further, an eyepiece 8b for observing the fundus of the eye E to be examined with the naked eye is provided on the examiner side of the main body 8 (the right direction in FIG. 8).

  Further, the main body 8 is provided with a still camera 9 for capturing a still image of the fundus of the eye E and an imaging device 10 such as a television camera for capturing a still image or a moving image of the fundus. Yes. The still camera 9 and the imaging device 10 are detachably attached to the main body 8.

  As the still camera 9, a digital camera equipped with an image sensor such as a charge coupled device (CCD) or a complementary metal oxide semiconductor (CMOS), or a film camera, depending on various conditions such as the purpose of inspection and the method of storing a captured image In addition, an instant camera or the like can be appropriately attached and used. The main body portion 8 is formed with a mounting portion 8c for selectively mounting such various still cameras 9.

  When the still camera 9 or the imaging device 10 is of a digital imaging system, the image data of the fundus image captured by the still camera 9 or the imaging device 10 is transmitted to a computer or the like connected to the fundus camera 1000, and the fundus image is displayed on the display. Can be observed. Further, the image data can be transmitted to an image recording apparatus connected to the fundus camera 1000 to form a database and used as electronic data for creating an electronic medical chart, for example.

  A touch panel monitor 11 is provided on the examiner side of the main body 8. On the touch panel monitor 11, a fundus image of the eye E to be examined that is created based on a video signal output from the (digital type) still camera 9 or the imaging device 10 is displayed. The touch panel monitor 11 displays an xy coordinate system with the center of the screen as the origin on the fundus image. When the examiner touches a desired position on the screen, a coordinate value corresponding to the touched position is displayed.

  Next, the configuration of the optical system of the fundus camera 1000 will be described with reference to FIG. The fundus camera 1000 is provided with an illumination optical system 100 that illuminates the fundus oculi Ef of the eye E, and an imaging optical system 120 that guides the fundus reflection light of the illumination light to the eyepiece unit 8b, the still camera 9, and the imaging device 10. It has been.

  The illumination optical system 100 includes an observation light source 101, a condenser lens 102, a photographing light source 103, a condenser lens 104, exciter filters 105 and 106, a ring translucent plate 107, a mirror 108, an LCD 109, an illumination diaphragm 110, a relay lens 111, and a perforated mirror. 112 and an objective lens 113 are included.

  The observation light source 101 is constituted by a halogen lamp, for example, and outputs steady light (continuous light) for fundus observation. The condenser lens 102 is an optical element that collects steady light (observation illumination light) emitted from the observation light source 101 and illuminates the observation illumination light almost evenly on the fundus.

  The imaging light source 103 is composed of, for example, a xenon lamp, and emits flash light when imaging the fundus oculi Ef. The condenser lens 104 is an optical element that collects flash light (imaging illumination light) emitted from the imaging light source 103 and uniformly irradiates the fundus oculi Ef with the imaging illumination light.

  The exciter filters 105 and 106 are filters used when performing fluorescence imaging of a fundus image of the fundus oculi Ef. Each of the exciter filters 105 and 106 can be inserted into and removed from the optical path by a drive mechanism (not shown) such as a solenoid. The exciter filter 105 is disposed on the optical path during FAG (fluorescein fluorescence imaging) imaging. On the other hand, the exciter filter 106 is disposed on the optical path during ICG (Indocyanine Green Fluorescence Imaging) imaging. Note that the exciter filters 105 and 106 are both retracted from the optical path during color photographing.

  The ring translucent plate 107 is disposed at a position conjugate with the pupil of the eye E to be examined, and includes a ring translucent portion 107 a centering on the optical axis of the illumination optical system 100. The mirror 108 reflects the illumination light emitted from the observation light source 101 and the photographing light source 103 in the optical axis direction of the photographing optical system 120. The LCD 109 displays a fixation target (not shown) for fixing the eye E to be examined.

  The illumination stop 110 is a stop member that blocks part of the illumination light for preventing flare and the like. The illumination stop 110 is configured to be movable in the optical axis direction of the illumination optical system 100, thereby adjusting the illumination area of the fundus oculi Ef.

  The aperture mirror 112 is an optical element that combines the optical axis of the illumination optical system 100 and the optical axis of the photographing optical system 120. A hole 112 a is opened in the center region of the perforated mirror 112. The optical axis of the illumination optical system 100 and the optical axis of the photographing optical system 120 intersect at a substantially central position of the hole 112a. The objective lens 113 is provided in the objective lens portion 8 a of the main body portion 8.

  The illumination optical system 100 having such a configuration illuminates the fundus oculi Ef in the following manner. First, at the time of fundus observation, the observation light source 101 is turned on and observation illumination light is output. This observation illumination light irradiates the ring translucent plate 107 through the condenser lenses 102 and 104 (the exciter filters 105 and 106 are retracted from the optical path). The light that has passed through the ring translucent portion 107 a of the ring translucent plate 107 is reflected by the mirror 108 and reflected by the perforated mirror 112 via the LCD 109, the illumination stop 110, and the relay lens 111. The observation illumination light reflected by the aperture mirror 112 travels in the optical axis direction of the imaging optical system 120, is focused by the objective lens 113, and enters the eye E to illuminate the fundus oculi Ef.

  At this time, since the ring translucent plate 107 is disposed at a position conjugate to the pupil of the eye E, a ring-shaped image of observation illumination light incident on the eye E is formed on the pupil. The fundus reflection light of the observation illumination light is emitted from the eye E through the central dark part of the ring-shaped image on the pupil. In this manner, the influence of the observation illumination light incident on the eye E on the fundus reflection light of the observation illumination light is prevented.

  On the other hand, when photographing the fundus oculi Ef, the photographing light source 103 emits flash light, and the photographing illumination light is irradiated onto the fundus oculi Ef through a similar route. In the case of fluorescent photographing, the exciter filter 105 or 106 is selectively arranged on the optical path depending on whether FAG photographing or ICG photographing.

  Next, the photographing optical system 120 will be described. The photographing optical system 120 includes an objective lens 113, a perforated mirror 112 (hole 112a), a photographing aperture 121, barrier filters 122 and 123, a variable power lens 124, a relay lens 125, a photographing lens 126, a quick return mirror 127, and a photographing. The medium 9a is included. Here, the imaging medium 9a is an arbitrary imaging medium (an imaging element such as a CCD, a camera film, an instant film, etc.) used for the still camera 9.

  The fundus reflection light of the illumination light emitted from the eye E through the central dark part of the ring-shaped image on the pupil enters the photographing aperture 121 through the hole 112a of the aperture mirror 112. The perforated mirror 112 reflects the corneal reflection light of the illumination light and acts so as not to mix the corneal reflection light into the fundus reflection light incident on the photographing aperture 121. Thereby, the occurrence of flare in the observed image or the photographed image is suppressed.

  The photographing aperture 121 is a plate-like member in which a plurality of circular translucent portions having different sizes are formed. The plurality of light-transmitting portions constitute diaphragms having different aperture values (F values), and the light-transmitting portions are alternatively arranged on the optical path by a driving mechanism (not shown).

  Each of the barrier filters 122 and 123 can be inserted into and removed from the optical path by a drive mechanism (not shown) such as a solenoid. When performing FAG imaging, the barrier filter 122 is disposed on the optical path, and when performing ICG imaging, the barrier filter 123 is disposed on the optical path. When performing color photography, both the barrier filters 122 and 123 are retracted from the optical path.

  The variable magnification lens 124 can be moved in the optical axis direction of the photographing optical system 120 by a driving mechanism (not shown). Thereby, it is possible to change the observation magnification and the imaging magnification, focus the fundus image, and the like. The photographing lens 126 is a lens that forms an image of fundus reflected light from the eye E on the photographing medium 9a.

  The quick return mirror 127 is rotatably provided around the rotation shaft 127a by a driving mechanism (not shown). When photographing the fundus oculi Ef with the still camera 9, the fundus reflected light is guided to the photographing medium 9a by jumping up the quick return mirror 127 obliquely provided on the optical path. On the other hand, when photographing the fundus with the imaging device 10 or observing the fundus with the examiner's naked eye, the fundus reflected light is reflected upward with the quick return mirror 127 obliquely arranged on the optical path. Yes.

  The photographing optical system 120 further includes a field lens (field lens) 128, a switching mirror 129, an eyepiece lens 130, a relay lens 131, a reflection mirror 132, for guiding the fundus reflection light reflected by the quick return mirror 127. A photographing lens 133 and an image sensor 10a are provided. The imaging element 10 a is an imaging element such as a CCD built in the imaging apparatus 10. On the touch panel monitor 11, a fundus oculi image Ef ′ photographed by the image sensor 10a is displayed.

  As with the quick return mirror 127, the switching mirror 129 is rotatable around the rotation shaft 129a. The switching mirror 129 reflects the fundus reflection light toward the eyepiece lens 130 while being obliquely provided on the optical path during observation with the naked eye.

  Further, when a fundus image is captured using the imaging device 10, the switching mirror 129 is retracted from the optical path to guide the fundus reflection light toward the imaging element 10a. In this case, the fundus reflection light is reflected by the mirror 132 via the relay lens 131 and imaged on the image sensor 10 a by the photographing lens 133.

  Such a fundus camera 1000 is a fundus oculi observation device used for observing the surface of the fundus oculi Ef, that is, the state of the retina. In other words, the fundus camera 1000 is a device for obtaining a two-dimensional fundus image when the fundus oculi Ef is viewed from the cornea direction of the eye E to be examined. On the other hand, there are tissues such as the choroid and sclera in the deep layer of the retina, and a technique for observing the state of these tissues has been desired. In recent years, a device for observing these deep tissues has been put into practical use. (For example, see Patent Documents 2 and 3).

  The fundus oculi observation device disclosed in Patent Documents 2 and 3 is a device (referred to as an optical image measurement device, an optical coherence topography device, or the like) that applies so-called OCT (Optical Coherence Tomography) technology. Such a fundus oculi observation device bisects low-coherence light, guides one (signal light) to the fundus, guides the other (reference light) to a predetermined reference object, and transmits the signal light via the fundus and the reference object. An apparatus capable of forming a tomographic image of the surface of the fundus or deep tissue or a three-dimensional image based on the tomographic image by detecting and analyzing the interference light obtained by superimposing the reflected reference light. It is.

JP 2004-350849 A JP 2003-543 A Japanese Patent Laying-Open No. 2005-241464

  In order to grasp in detail the state of the fundus (such as the presence or absence of disease), it is desirable to consider both the state of the fundus surface such as the retina and the state of deep tissue such as the choroid and sclera. That is, it is difficult to grasp the detailed state of the deep tissue only by observing the fundus image obtained by the fundus camera, and by observing only the fundus image obtained by the optical image measuring device, it is difficult to obtain details of the retina and the like. It is difficult to grasp the state over a wide range.

  In order to comprehensively determine the state of the fundus, it is desirable to determine a medical condition or the like in consideration of both the retina state and the deep tissue state. That is, in order to improve the accuracy of determination of a medical condition or the like, it is desirable to be able to refer to more information, and it is desirable to be able to refer to information from more multifaceted angles.

  For this purpose, it is desirable to use a fundus oculi observation device that can acquire both a fundus image obtained by a fundus camera and a fundus image obtained by an optical image measurement device. In particular, if it is possible to capture both fundus images at the same time, it is considered that the state of the fundus can be observed by the other fundus image while one fundus image is being captured, and a more detailed diagnosis can be realized.

  However, with a conventional fundus oculi observation device, it has been difficult to acquire both a two-dimensional image of the fundus surface by a fundus camera and a tomographic image or a three-dimensional image of the fundus by an optical image measurement device. In particular, it was difficult to acquire both fundus images at the same time.

  The present invention has been made in order to solve such a problem, and it is possible to acquire both an image of the fundus surface and a tomographic image of the fundus. An object of the present invention is to provide a fundus oculi observation device that enables simultaneous acquisition.

  In order to achieve the above object, the invention described in claim 1 is directed to an illumination optical system for irradiating illumination light to the fundus of the eye to be examined, and imaging optical for detecting illumination light passing through the fundus by a first detection means. A first image forming unit that forms a two-dimensional image of the surface of the fundus oculi based on a detection result by the first detection unit, and a light source that outputs light having a wavelength different from that of the illumination light And interference light generation means for generating interference light by dividing the light output from the light source into signal light and reference light directed to the fundus and superimposing the signal light passing through the fundus and the reference light And a second detection means for detecting the generated interference light, and a second image forming means for forming a tomographic image of the fundus based on a detection result by the second detection means, An imaging optical path formed by the imaging optical system and a signal toward the fundus And an optical path combining / separating means for separating the optical path of the light and the optical path of the signal light passing through the fundus, and the light output by the light source is included in a range of 1000 nm to 1100 nm The combined signal light in the imaging optical path is irradiated onto the fundus through the imaging optical path, and the signal light separated from the imaging optical path is generated by the interference light generation means The fundus oculi observation device is superposed on the reference light.

  The invention according to claim 2 is the fundus oculi observation device according to claim 1, wherein the light output from the light source has a longer wavelength than the illumination light.

  The invention according to claim 3 is the fundus oculi observation device according to claim 2, wherein the illumination light has a wavelength included in a range of 850 nm to 1000 nm.

  According to the fundus oculi observation device according to the present invention, it is possible to acquire both the image of the fundus surface and the tomographic image of the fundus, and in particular, it is possible to acquire both of these fundus images simultaneously.

It is a schematic block diagram showing an example of the whole structure of suitable embodiment of the fundus oculi observation device concerning the present invention. It is a schematic block diagram showing an example of a structure of the scanning unit incorporated in the fundus camera unit in a preferred embodiment of the fundus oculi observation device according to the present invention. It is a schematic block diagram showing an example of a structure of the OCT unit in suitable embodiment of the fundus oculi observation device concerning the present invention. It is a schematic block diagram showing an example of the hardware constitutions of the calculation control apparatus in suitable embodiment of the fundus oculi observation device concerning the present invention. It is a schematic block diagram showing an example of the structure of the control system of suitable embodiment of the fundus oculi observation device concerning the present invention. It is the schematic showing an example of the scanning aspect of the signal light by suitable embodiment of the fundus oculi observation device concerning the present invention. FIG. 6A illustrates an example of a scanning mode of the signal light when the fundus is viewed from the incident side of the signal light with respect to the eye to be examined. FIG. 6B shows an example of an arrangement mode of scanning points on each scanning line. It is the schematic showing an example of the scanning aspect of the signal light by the suitable embodiment of the fundus oculi observation device concerning the present invention, and the aspect of the tomographic image formed along each scanning line. It is a schematic side view showing an example of the appearance composition of the conventional fundus oculi observation device (fundus camera). It is the schematic showing an example of the internal structure (structure of an optical system) of the fundus observation apparatus (fundus camera) in the past.

  An example of a preferred embodiment of a fundus oculi observation device according to the present invention will be described in detail with reference to the drawings. Note that the same reference numerals as those in FIGS. 8 and 9 are used for the same components as in the prior art.

  First, the configuration of the fundus oculi observation device according to the present embodiment will be described with reference to FIGS. FIG. 1 illustrates the overall configuration of a fundus oculi observation device 1 according to the present embodiment. FIG. 2 shows the configuration of the scanning unit 141 in the fundus camera unit 1A. FIG. 3 shows the configuration of the OCT unit 150. FIG. 4 shows the hardware configuration of the arithmetic and control unit 200. FIG. 5 shows the configuration of the control system of the fundus oculi observation device 1.

[overall structure]
As shown in FIG. 1, a fundus oculi observation device 1 includes a fundus camera unit 1A that functions as a fundus camera, an OCT unit 150 that stores an optical system of an optical image measurement device (OCT device), and various arithmetic processes and control processes. Etc., and an arithmetic and control unit 200 that executes the above.

  The fundus camera unit 1A, together with the arithmetic and control unit 200, constitutes an example of the “first image forming unit” in the present invention. The OCT unit 150, together with the arithmetic and control unit 200, constitutes an example of the “second image forming unit” in the present invention. In addition, the “second image forming unit” includes various optical members through which signal light passes, such as a scanning unit 141 provided in the fundus camera unit 1A.

  One end of a connection line 152 is attached to the OCT unit 150. A connector portion 151 is attached to the other end of the connection line 152. This connector portion 151 is attached to the attachment portion 8c shown in FIG. In addition, an optical fiber is conducted inside the connection line 152. The OCT unit 150 and the fundus camera unit 1A are optically connected via a connection line 152. The detailed configuration of the OCT unit 150 will be described later with reference to FIG.

[Configuration of fundus camera unit]
The retinal camera unit 1A has an appearance configuration substantially similar to that of the conventional retinal camera 1000 shown in FIG. In addition, the fundus camera unit 1A, like the conventional optical system shown in FIG. And an optical system 120.

  In addition, although mentioned later for details, the imaging device 10 in the imaging | photography optical system 120 of this embodiment detects the illumination light which has a wavelength of a near infrared region. The photographing optical system 120 is separately provided with an imaging device 12 for detecting illumination light having a wavelength in the visible region. Further, the photographing optical system 120 guides the signal light from the OCT unit 150 to the fundus oculi Ef and guides the signal light passing through the fundus oculi Ef to the OCT unit 150.

  The illumination optical system 100 includes an observation light source 101, a condenser lens 102, a photographing light source 103, a condenser lens 104, exciter filters 105 and 106, a ring translucent plate 107, a mirror 108, an LCD 109, an illumination stop 110, as in the conventional case. A relay lens 111, a perforated mirror 112, and an objective lens 113 are included.

  The observation light source 101 outputs illumination light having a wavelength in the visible region included in the range of about 400 nm to 700 nm. This observation light source 101 corresponds to an example of a “visible light source” of the present invention. The imaging light source 103 outputs illumination light having a wavelength in the near infrared region included in a range of about 700 nm to 800 nm. The near-infrared light output from the imaging light source 103 is set to be shorter than the wavelength of light used in the OCT unit 150 (described later).

  The photographing optical system 120 includes an objective lens 113, a perforated mirror 112 (hole 112a), a photographing aperture 121, barrier filters 122 and 123, a variable power lens 124, a relay lens 125, a photographing lens 126, a dichroic mirror 134, Field lens (field lens) 128, half mirror 135, relay lens 131, dichroic mirror 136, photographing lens 133, imaging device 10 (imaging device 10a), reflection mirror 137, photographing lens 138, photographing device 12 (imaging device 12a), A lens 139 and an LCD (Liquid Crystal Display) 140 are included.

  Unlike the conventional photographing optical system 120 shown in FIG. 9, the photographing optical system 120 according to the present embodiment has a dichroic mirror 134, a half mirror 135, a dichroic mirror 136, a reflection mirror 137, a photographing lens 138, a lens 139, and an LCD 140. Is provided.

  The dichroic mirror 134 reflects the fundus reflection light (having a wavelength included in the range of about 400 nm to 800 nm) of the illumination light from the illumination optical system 100 and the signal light LS (about 800 nm to 900 nm of the OCT unit 150). It has a wavelength included in the range; The dichroic mirror 134 corresponds to an example of “optical path combining / separating means” of the present invention.

  Further, the dichroic mirror 136 transmits illumination light having a wavelength in the visible region from the illumination optical system 100 (visible light having a wavelength of about 400 nm to 700 nm output from the observation light source 101) and changes the wavelength in the near infrared region. The illumination light (the near infrared light having a wavelength of about 700 nm to 800 nm output from the photographing light source 103) is reflected. The dichroic mirror 136 corresponds to an example of “optical path separating means” of the present invention.

  On the LCD 140, an internal fixation target or the like is displayed. The light from the LCD 140 is collected by the lens 139, reflected by the half mirror 135, and then reflected by the dichroic mirror 136 via the field lens 128. Then, the light enters the eye E through the photographing lens 126, the relay lens 125, the variable power lens 124, the aperture mirror 112 (the aperture 112 a), the objective lens 113, and the like. Thereby, an internal fixation target or the like is projected onto the fundus oculi Ef of the eye E to be examined.

  The image pickup device 10a is an image pickup device such as a CCD or a CMOS built in the image pickup device 10 such as a television camera, and particularly detects light having a wavelength in the near infrared region (that is, the image pickup device 10 is It is an infrared TV camera that detects near-infrared light.) The imaging device 10 outputs a video signal as a result of detecting near infrared light. The touch panel monitor 11 displays a two-dimensional image (fundus image Ef ′) of the surface of the fundus oculi Ef based on this video signal. The video signal is sent to the arithmetic and control unit 200, and a fundus image is displayed on the display (described later). It should be noted that illumination light having a wavelength in the near-infrared region output from the imaging light source 103 of the illumination optical system 100 is used during fundus imaging by the imaging apparatus 10. This imaging device 10 (image sensor 10a thereof) corresponds to an example of “first detection means” of the present invention.

  On the other hand, the image pickup device 12a is an image pickup device such as a CCD or a CMOS built in the image pickup device 12 such as a TV camera, and particularly detects light having a wavelength in the visible region (that is, the image pickup device 12 is TV camera that detects visible light.) The imaging device 12 outputs a video signal as a result of detecting visible light. The touch panel monitor 11 displays a two-dimensional image (fundus image Ef ′) of the surface of the fundus oculi Ef based on this video signal. The video signal is sent to the arithmetic and control unit 200, and a fundus image is displayed on the display (described later). It should be noted that illumination light having a wavelength in the visible region output from the observation light source 101 of the illumination optical system 100 is used when photographing the fundus using the imaging device 12. The image pickup device 12 (the image pickup element 12a) corresponds to an example of the “third detection means” in the present invention.

  The photographing optical system 120 of the present embodiment is provided with a scanning unit 141 and a lens 142. The scanning unit 141 has a configuration that scans light (signal light LS; described later) output from the OCT unit 150 on the fundus oculi Ef.

  The lens 142 makes the signal light LS guided from the OCT unit 150 through the connection line 152 enter the scanning unit 141 as a parallel light beam. The lens 142 acts to focus the fundus reflection light of the signal light LS that has passed through the scanning unit 141.

  FIG. 2 shows an example of a specific configuration of the scanning unit 141. The scanning unit 141 includes galvanometer mirrors 141A and 141B and reflection mirrors 141C and 141D.

  The galvanometer mirrors 141A and 141B are rotatable about the rotation shafts 141a and 141b, respectively. The rotating shafts 141a and 141b are disposed so as to be orthogonal to each other. In FIG. 2, the rotation shaft 141a of the galvano mirror 141A is arranged in a direction parallel to the paper surface of FIG. 2, and the rotation shaft 141b of the galvano mirror 141B is orthogonal to the paper surface of FIG. Arranged in the direction. That is, the galvano mirror 141B is configured to be rotatable in a direction indicated by a double-sided arrow in FIG. 2, and the galvano mirror 141A is configured to be rotatable in a direction orthogonal to the double-sided arrow. Accordingly, the pair of galvanometer mirrors 141A and 141B act so as to change the reflection direction of the signal light LS to directions orthogonal to each other. In addition, each rotation operation | movement of the galvanometer mirror 141A, 141B is driven by the below-mentioned mirror drive mechanism (refer FIG. 5).

  The signal light LS reflected by the galvanometer mirrors 141A and 141B is reflected by the reflection mirrors 141C and 141D and travels in the same direction as when incident on the galvanometer mirror 141A.

  As described above, the optical fiber 152 a is electrically connected to the inside of the connection line 152, and the end surface 152 b of the optical fiber 152 a is disposed so as to face the lens 142. The signal light LS emitted from the end surface 152b travels toward the lens 142 while expanding the beam diameter, but is converted into a parallel light beam by the lens 142. On the contrary, the signal light LS passing through the fundus oculi Ef is focused toward the end surface 152b by the lens 142.

[Configuration of OCT unit]
Next, the configuration of the OCT unit 150 will be described with reference to FIG. The OCT unit 150 shown in the figure has an optical system that is almost the same as that of a conventional optical image measurement device, divides light output from a light source into reference light and signal light, and performs reference via a reference object. An interferometer that generates interference light by superimposing light and signal light that has passed through the object to be measured (fundus Ef) is generated, and an image of the object to be measured (fundus Ef) is analyzed by analyzing the detection result of the interference light. Is formed.

  The low coherence light source 160 is configured by a broadband light source such as a super luminescent diode (SLD) or a light emitting diode (LED) that outputs low coherence light L0. The low coherence light L0 is, for example, light having a wavelength in the near infrared region and a temporal coherence length of about several tens of micrometers. The low coherence light L0 output from the low coherence light source 160 has a wavelength longer than the illumination light (wavelength of about 400 nm to 800 nm) of the fundus camera unit 1A, for example, a wavelength included in a range of about 800 nm to 900 nm. . This low coherence light source 160 corresponds to an example of the “light source” of the present invention.

  The low coherence light L0 output from the low coherence light source 160 is guided to an optical coupler 162 through an optical fiber 161 made of, for example, a single mode fiber or a PM fiber (Polarization maintaining fiber). The optical coupler 162 splits the low coherence light L0 into the reference light LR and the signal light LS.

  The optical coupler 162 has both functions of a means for splitting light (splitter) and a means for superposing light (coupler), but here it is conventionally referred to as “optical coupler”. .

  The reference light LR generated by the optical coupler 162 is guided by an optical fiber 163 made of a single mode fiber or the like and emitted from the end face of the fiber. The emitted reference light LR is collimated by the collimator lens 171 and then reflected by the reference mirror 174 (reference object) via the glass block 172 and the density filter 173.

  The reference light LR reflected by the reference mirror 174 passes through the density filter 173 and the glass block 172 again, and is condensed on the fiber end surface of the optical fiber 163 by the collimator lens 171. The collected reference light LR is guided to the optical coupler 162 through the optical fiber 163.

  The glass block 172 and the density filter 173 are used as delay means for matching the optical path lengths (optical distances) of the reference light LR and the signal light LS, and as means for matching the dispersion characteristics of the reference light LR and the signal light LS. It is working.

  The reference mirror 174 is configured to be movable along the traveling direction of the reference light LR. Thereby, the optical path length of the reference light LR corresponding to the axial length of the eye E to be examined is secured. The reference mirror 174 is moved by a drive mechanism including a drive device such as a motor.

  On the other hand, the signal light LS generated by the optical coupler 162 is guided to the end of the connection line 152 by an optical fiber 164 made of a single mode fiber or the like. An optical fiber 152 a is conducted inside the connection line 152. Here, the optical fiber 164 and the optical fiber 152a may be configured by a single optical fiber, or may be integrally formed by joining the respective end faces. In any case, it is sufficient that the optical fibers 164 and 152a are configured to transmit the signal light LS between the fundus camera unit 1A and the OCT unit 150.

  The signal light LS is guided through the connection line 152 and guided to the fundus camera unit 1A. Then, the eye E is passed through the lens 142, the scanning unit 141, the dichroic mirror 134, the photographing lens 126, the relay lens 125, the variable magnification lens 124, the photographing aperture 121, the hole 112a of the aperture mirror 112, and the objective lens 113. (At this time, the barrier filters 122 and 123 are respectively retracted from the optical path).

  The signal light LS incident on the eye E is imaged and reflected on the fundus (retina) Ef. At this time, the signal light LS is not only reflected by the surface of the fundus oculi Ef, but also reaches the deep region of the fundus oculi Ef and is scattered at the refractive index boundary. Therefore, the signal light LS passing through the fundus oculi Ef is light including information reflecting the surface morphology of the fundus oculi Ef and information reflecting the state of backscattering at the refractive index boundary of the deep fundus tissue. This light may be simply referred to as “fundus reflected light of the signal light LS”.

  The fundus reflection light of the signal light LS travels in the reverse direction in the above path, is condensed on the end surface 152b of the optical fiber 152a, enters the OCT unit 150 through the optical fiber 152, and returns to the optical coupler 162 through the optical fiber 164. Come. The optical coupler 162 superimposes the signal light LS and the reference light LR reflected by the reference mirror 174 to generate interference light LC. The generated interference light LC is guided to the spectrometer 180 through an optical fiber 165 made of a single mode fiber or the like.

  Here, the “interference light generating means” of the present invention is configured by an interferometer including at least an optical coupler 162, optical fibers 163 and 164, and a reference mirror 174. In the present embodiment, a Michelson interferometer is used. However, for example, any type of interferometer such as a Mach-Zehnder type can be appropriately used.

  The spectrometer (spectrometer) 180 includes a collimator lens 181, a diffraction grating 182, an imaging lens 183, and a CCD 184. The diffraction grating 182 of the present embodiment is a transmission diffraction grating, but of course, a reflection diffraction grating can also be used. Of course, other photodetecting elements can be used instead of the CCD 184. Such a light detection element corresponds to an example of the “second detection means” of the present invention.

  The interference light LC incident on the spectrometer 180 is converted into a parallel light beam by the collimator lens 181 and then split (spectral decomposition) by the diffraction grating 182. The split interference light LC is imaged on the imaging surface of the CCD 184 by the imaging lens 183. The CCD 184 receives this interference light LC and converts it into an electrical detection signal, and outputs this detection signal to the arithmetic and control unit 200.

[Configuration of arithmetic control unit]
Next, the configuration of the arithmetic and control unit 200 will be described. The arithmetic and control unit 200 analyzes a detection signal input from the CCD 184 of the spectrometer 180 of the OCT unit 150 and performs a process of forming a tomographic image of the fundus oculi Ef of the eye E to be examined. The analysis method at this time is the same as the conventional Fourier domain OCT method.

  In addition, the arithmetic and control unit 200 performs a process of forming a two-dimensional image indicating the form of the surface (retina) of the fundus oculi Ef based on the video signals output from the imaging devices 10 and 12 of the fundus camera unit 1A.

  Furthermore, the arithmetic and control unit 200 executes control of each part of the fundus camera unit 1A and control of each part of the OCT unit 150.

  Control of the fundus camera unit 1A includes, for example, output control of illumination light by the observation light source 101 and the imaging light source 103, control of insertion / retraction operations of the exciter filters 105, 106 and barrier filters 122, 123 on the optical path, LCD 139, etc. Display control, movement control of the aperture stop 110 (control of the aperture value), control of the aperture value of the photographing aperture 121, control of movement of the variable power lens 124 (control of magnification), and the like. The arithmetic and control unit 200 controls the rotation operation of the galvanometer mirrors 141A and 141B in the scanning unit 141.

  On the other hand, as control of the OCT unit 150, output control of low coherence light by the low coherence light source 160, movement control of the reference mirror 174, control of the accumulation time of the CCD 184, and the like are performed.

  An example of the hardware configuration of the arithmetic and control unit 200 that operates as described above will be described with reference to FIG. The arithmetic and control unit 200 has a hardware configuration similar to that of a conventional computer. Specifically, a microprocessor 201 (CPU, MPU, etc.), RAM 202, ROM 203, hard disk drive (HDD) 204, keyboard 205, mouse 206, display 207, image forming board 208, and communication interface (I / F) 209 are included. It consists of These units are connected via a bus 200a.

  The microprocessor 201 executes an operation characteristic of the present embodiment by expanding the control program 204 a stored in the hard disk drive 204 on the RAM 202.

  Further, the microprocessor 201 executes control of each part of the device described above, various arithmetic processes, and the like. Also, control of each part of the device corresponding to operation signals from the keyboard 205 and mouse 206, control of display processing by the display 207, control of transmission / reception processing of various data and control signals by the communication interface 209, and the like are executed.

  The keyboard 205, the mouse 206, and the display 207 are used as a user interface of the fundus oculi observation device 1. The keyboard 205 is used as a device for inputting, for example, letters and numbers. The mouse 206 is used as a device for performing various input operations on the display screen of the display 207.

  The display 207 is an arbitrary display device such as an LCD or a CRT (Cathode Ray Tube), displays an image of the fundus oculi Ef formed by the fundus oculi observation device 1, and displays various operation screens and setting screens. To do.

  Note that the user interface of the fundus oculi observation device 1 is not limited to such a configuration. For example, a function for displaying and outputting various information such as a trackball, a joystick, a touch panel LCD, a control panel for ophthalmic examination, and the like. Any user interface means having a function of inputting various information can be used.

  The image forming board 208 is a dedicated electronic circuit that performs processing for forming an image of the fundus oculi Ef of the eye E. The image forming board 208 is provided with a fundus image forming board 208a and an OCT image forming board 208b. The fundus image forming board 208a is a dedicated electronic circuit that operates to form a fundus image based on video signals from the imaging device 10 and the imaging device 12 of the fundus camera unit 1A. The OCT image forming board 208b is a dedicated electronic circuit that operates to form a fundus image (tomographic image) based on a detection signal from the CCD 184 of the spectrometer 180 of the OCT unit 150. By providing such an image forming board 208, the processing speed of processing for forming a fundus image can be improved.

  The communication interface 209 performs a process of transmitting a control signal from the microprocessor 201 to the fundus camera unit 1A or the OCT unit 150. The communication interface 209 receives video signals from the imaging devices 10 and 12 of the fundus camera unit 1 </ b> A and detection signals from the CCD 184 of the OCT unit 150 and inputs them to the image forming board 208. At this time, the communication interface 209 operates to input video signals from the imaging devices 10 and 12 to the fundus image forming board 208a and input detection signals from the CCD 184 to the OCT image forming board 208b.

  When the arithmetic and control unit 200 is connected to a network such as a LAN (Local Area Network) or the Internet, the communication interface 209 is equipped with a network adapter such as a LAN card and a communication device such as a modem. It is possible to configure to perform data communication via a network. In that case, a server for storing the control program 204a can be installed, and the arithmetic and control unit 200 can be configured as a client terminal of the server.

[Control system configuration]
The configuration of the control system of the fundus oculi observation device 1 having the above configuration will be described with reference to FIG. FIG. 5 shows a particular selection of the part related to the operation and processing according to the present invention from the configuration of the fundus oculi observation device 1.

  The control system of the fundus oculi observation device 1 is configured around the control unit 210 of the arithmetic and control unit 200. The control unit 210 includes a microprocessor 201, a RAM 202, a ROM 203, a hard disk drive 204 (control program 204a), a communication interface 209, and the like.

  The control unit 210 executes the above-described control process by the microprocessor 201 that operates based on the control program 204a. In particular, the galvanometer mirrors 141A and 141B are independently operated by controlling the mirror drive mechanisms 241 and 242 of the fundus camera unit 1A, respectively.

  The control unit 210 also detects two types of images captured by the fundus oculi observation device 1, that is, a two-dimensional image (fundus image Ef ′) of the surface of the fundus oculi Ef by the fundus camera unit 1A and the detection obtained by the OCT unit 150. Control for displaying an image of the fundus oculi Ef formed based on the signal on the display 207 of the user interface 240 is performed. These fundus images can be individually displayed on the display 207, or they can be displayed side by side.

  The image forming unit 220 forms a fundus image based on video signals from the imaging devices 10 and 12 of the fundus camera unit 1A, and forms a fundus image based on a detection signal from the CCD 184 of the OCT unit 150. The image forming board 208 is included.

  The image processing unit 230 performs various types of image processing on the fundus image formed by the image forming unit 220. For example, processing for forming a three-dimensional image of the fundus oculi Ef based on a tomographic image of the fundus oculi Ef based on a detection signal from the OCT unit 150, various correction processing such as brightness adjustment of the fundus oculi image, and the like are executed.

  The user interface (UI) 240 includes operation devices such as a keyboard 205 and a mouse 206, and a display device such as a display 207.

  Hereinafter, the control mode of scanning of the signal light LS by the control unit 210 and the mode of processing of the detection signal from the OCT unit 150 by the image forming unit 220 and the image processing unit 230 will be described. Note that the processing of the image forming unit 220 and the like with respect to the video signal from the fundus camera unit 1A is the same as the conventional processing, and thus the description thereof will be omitted.

[Scanning signal light]
As described above, the scanning of the signal light LS is performed by changing the direction of the reflecting surfaces of the galvanometer mirrors 141A and 141B of the scanning unit 141 of the fundus camera unit 1A. The control unit 210 controls the mirror driving mechanisms 241 and 242 to change the directions of the reflecting surfaces of the galvanometer mirrors 141A and 141B, respectively, and scans the signal light LS on the fundus oculi Ef.

  When the direction of the reflecting surface of the galvanometer mirror 141A is changed, the signal light LS is scanned in the horizontal direction (x direction in FIG. 1) on the fundus oculi Ef. On the other hand, when the direction of the reflecting surface of the galvanometer mirror 141A is changed, the signal light LS is scanned in the vertical direction (y direction in FIG. 1) on the fundus oculi Ef. Further, the signal light LS can be scanned in a direction in which the x direction and the y direction are combined by simultaneously changing the directions of the reflecting surfaces of both the galvanometer mirrors 141A and 141B. That is, by controlling these two galvanometer mirrors 141A and 141B, the signal light LS can be scanned in an arbitrary direction on the xy plane.

  FIG. 6 illustrates an example of a scanning mode of the signal light LS for forming an image of the fundus oculi Ef. FIG. 6A shows an example of a scanning mode of the signal light LS when the fundus oculi Ef is viewed from the direction in which the signal light LS is incident on the eye E (that is, when viewed from the −z direction to the + z direction in FIG. 1). Represents. FIG. 6B illustrates an example of an arrangement mode of scanning points (positions where image measurement is performed) on each scanning line on the fundus oculi Ef.

  As shown in FIG. 6A, the signal light LS is scanned in a rectangular scanning region R set in advance. In this scanning region R, a plurality (m) of scanning lines R1 to Rm are set in the x direction. When the signal light LS is scanned along each scanning line Ri (i = 1 to m), a detection signal of the interference light LC is generated.

  Here, the direction of each scanning line Ri is referred to as a “main scanning direction”, and a direction orthogonal to the direction is referred to as a “sub-scanning direction”. Therefore, scanning in the main scanning direction of the signal light LS is executed by changing the direction of the reflecting surface of the galvano mirror 141A, and scanning in the sub-scanning direction changes the direction of the reflecting surface of the galvano mirror 141B. Executed by.

  On each scanning line Ri, as shown in FIG. 6B, a plurality (n) of scanning points Ri1 to Rin are set in advance.

  In order to execute the scan illustrated in FIG. 6, the control unit 210 first controls the galvanometer mirrors 141A and 141B to set the incidence target of the signal light LS on the fundus oculi Ef as the scan start position RS ( Set to scan point R11). Subsequently, the control unit 210 controls the low coherence light source 2, causes the low coherence light L0 to flash, and causes the signal light LS to enter the scanning start position RS. The CCD 184 receives the interference light LC based on the fundus reflection light at the scanning start position RS of the signal light LS and outputs a detection signal to the control unit 210.

  Next, the control unit 210 controls the galvanometer mirror 141A, scans the signal light LS in the main scanning direction, sets the incident target at the scanning point R12, flashes the low coherence light L0, and scans the scanning point. The signal light LS is incident on R12. The CCD 184 receives the interference light LC based on the fundus reflection light at the scanning point R12 of the signal light LS, and outputs a detection signal to the control unit 210.

  Similarly, the controller 210 sequentially flashes the low coherence light L0 at each scanning point while sequentially moving the incident target of the signal light LS from the scanning points R13, R14,..., R1 (n−1), R1n. By emitting light, a detection signal output from the CCD 184 corresponding to the interference light LC for each scanning point is acquired.

  When the measurement at the last scanning point R1n of the first scanning line R1 is completed, the control unit 210 controls the galvanometer mirrors 141A and 141B at the same time so that the incident target of the signal light LS is changed along the line changing scan r. The second scanning line R2 is moved to the first scanning point R21. And the detection signal corresponding to each scanning point R2j is each acquired by performing the above-mentioned measurement about each scanning point R2j (j = 1-n) of this 2nd scanning line R2.

  Similarly, measurement is performed for each of the third scanning line R3,..., The m−1th scanning line R (m−1), and the mth scanning line Rm, and a detection signal corresponding to each scanning point. To get. Note that the symbol RE on the scanning line Rm is a scanning end position corresponding to the scanning point Rmn.

  Thereby, the control unit 210 acquires m × n detection signals corresponding to m × n scanning points Rij (i = 1 to m, j = 1 to n) in the scanning region R. Hereinafter, the detection signal corresponding to the scanning point Rij may be represented as Dij.

  The linked control of the scanning point movement and the output of the low-coherence light L0 as described above is performed, for example, by transmitting a control signal to the mirror driving mechanisms 241 and 242 and a control signal (output request signal) for the low-coherence light source 2. This can be realized by synchronizing the transmission timing with each other.

  When the galvanometer mirrors 141A and 141B are operated as described above, the control unit 210 stores the position of each scanning line Ri and the position of each scanning point Rij (coordinates in the xy coordinate system) as information indicating the operation content. It has come to keep. This stored content (scanning position information) is used in the image forming process as in the prior art.

[About image processing]
Next, an example of processing related to an OCT image by the image forming unit 220 and the image processing unit 230 will be described.

  The image forming unit 220 executes a process of forming a tomographic image of the fundus oculi Ef along each scanning line Ri (main scanning direction). Further, the image processing unit 230 executes a process for forming a three-dimensional image of the fundus oculi Ef based on the tomographic image formed by the image forming unit 220.

  The tomographic image forming process by the image forming unit 220 is configured to include a two-stage arithmetic process, as in the prior art. In the first stage of arithmetic processing, an image in the depth direction (z direction shown in FIG. 1) of the fundus oculi Ef at the scanning point Rij is formed based on the detection signal Dij corresponding to each scanning point Rij.

  FIG. 7 shows an aspect of a tomographic image formed by the image forming unit 220. In the second stage arithmetic processing, a tomographic image Gi of the fundus oculi Ef along this scanning line Ri is formed for each scanning line Ri based on the image in the depth direction at the n scanning points Ri1 to Rin above it. . At this time, the image forming unit 220 determines the arrangement and interval of the scanning points Ri1 to Rin with reference to the positional information (scanning position information described above) of the scanning points Ri1 to Rin, and forms the scanning line Ri. It is supposed to be. Through the above processing, m tomographic images G1 to Gm at different positions in the sub-scanning direction (y direction) are obtained.

  Next, a process for forming a three-dimensional image of the fundus oculi Ef by the image processing unit 230 will be described. A three-dimensional image of the fundus oculi Ef is formed based on the m number of tomographic images obtained by the above arithmetic processing. The image processing unit 230 forms a three-dimensional image of the fundus oculi Ef by performing a known interpolation process for interpolating an image between adjacent tomographic images Gi and G (i + 1).

  At this time, the image processing unit 230 determines the arrangement and interval of each scanning line Ri with reference to the position information of each scanning line Ri, and forms this three-dimensional image. In this three-dimensional image, a three-dimensional coordinate system (x, y, z) is set based on the position information (the above-described scanning position information) of each scanning point Rij and the z coordinate in the image in the depth direction. .

  Further, the image processing unit 230 can form a tomographic image of the fundus oculi Ef in a cross section in an arbitrary direction other than the main scanning direction (x direction) based on the three-dimensional image. When a cross section is designated, the image processing unit 230 identifies the position of each scanning point (and / or the interpolated depth direction image) on the designated cross section, and the depth direction image (and / or at each specific position). (Or an interpolated image in the depth direction) is extracted from the three-dimensional image, and a plurality of extracted images in the depth direction are arranged to form a tomographic image of the fundus oculi Ef in the designated cross section.

  Note that an image Gmj shown in FIG. 7 represents an image in the depth direction (z direction) at the scanning point Rmj on the scanning line Rm. Similarly, an image in the depth direction at each scanning point Rij on each scanning line Ri, which is formed in the above-described first stage arithmetic processing, is represented as “image Gij”.

[Action / Effect]
The operation and effect of the fundus oculi observation device 1 according to this embodiment having the above-described configuration will be described.

  The fundus oculi observation device 1 includes a fundus camera unit 1A that functions as a fundus camera for obtaining a two-dimensional image representing the surface state of the fundus oculi Ef, and an optical image for obtaining a tomographic image (and a three-dimensional image) of the fundus oculi Ef. And an OCT unit 150 acting as a measuring device.

  The optical path of the signal light used for image formation by the OCT unit 150 is combined with the optical path (imaging optical path) formed by the imaging optical system 130 of the fundus camera unit 1A and guided to the eye E to be examined. This optical path is synthesized by the dichroic mirror 134.

  Further, the fundus reflection light of the signal light LS is guided to the dichroic mirror 134 along the imaging optical path, and is separated from the imaging optical path by the dichroic mirror 134 and is directed to the OCT unit 150.

  In this way, by providing the dichroic mirror 134 (optical path separation / synthesis means) that combines and separates the imaging optical path of the fundus camera unit 1A and the optical path of the signal light LS, the two-dimensional surface of the fundus oculi Ef is provided. Both an image and a tomographic image (and a three-dimensional image) of the fundus oculi Ef can be acquired.

  In particular, even if irradiation of illumination light by the fundus camera unit 1A and irradiation of the signal light LS by the OCT unit 150 are simultaneously performed on the eye E, each fundus reflection light is separated by the dichroic mirror 134, respectively. Therefore, it is possible to simultaneously capture both a two-dimensional image of the surface of the fundus oculi Ef and a tomographic image of the fundus oculi Ef.

  At this time, the illumination light irradiated simultaneously with the signal light LS from the OCT unit 150 may be near infrared light from the imaging light source 103 or visible light from the observation light source 101.

[Modification]
The configuration detailed above is merely an example for favorably implementing the fundus oculi observation device according to the present invention. Therefore, arbitrary modifications within the scope of the present invention can be appropriately made.

  For example, in the above embodiment, near infrared light having a wavelength of about 800 nm to 900 nm is used as the low coherence light L0, but in order to perform image measurement of a deeper region of the fundus oculi Ef, Light can be used. For example, near infrared light having a wavelength of about 900 nm to 1000 nm can be used, or near infrared light having a wavelength of about 1000 nm to 1100 nm can be used.

  When using low coherence light L0 having a wavelength of about 900 nm to 1000 nm, near infrared light having a wavelength of about 700 nm to 900 nm, for example, can be used as illumination light in the fundus camera unit 1A. When using near-infrared light having a wavelength of about 1000 nm to 1100 nm and low-coherence light L0, for example, near-infrared light having a wavelength of about 850 nm to 1000 nm is used as illumination light in the fundus camera unit 1A. Can do. Here, in any case, it is desirable to set the wavelength of the low-coherence light L0 to be longer than the wavelength of the illumination light of the fundus camera unit 1A, but a configuration in which the relationship between the wavelengths is reversed is applied. Is also possible.

  The first image forming means of the fundus oculi observation device according to the present invention is not limited to the fundus camera (unit), and any ophthalmologic apparatus capable of forming a two-dimensional image of the fundus oculi surface is applied. Is possible. For example, a slit lamp (slit lamp microscope apparatus) or the like can be used as the first image forming means.

  In the above embodiment, the fundus image is formed by the image forming unit 220 (the image forming board 208) and various control processes are performed by the control unit 210 (the microprocessor 201 or the like). Both of these processes can be performed by one or a plurality of computers.

DESCRIPTION OF SYMBOLS 1 Fundus observation apparatus 1A Fundus camera unit 8c Mounting part 10, 12 Imaging device 100 Illumination optical system 101 Observation light source 103 Imaging light source 120 Imaging optical system 134, 136 Dichroic mirror 141 Scan unit 141A, 141B Galvano mirror 142 Lens 150 OCT unit 151 Connector Unit 152 connection line 152a, 161, 163, 164, 165 optical fiber 160 low coherence light source 162 optical coupler 174 reference mirror 180 spectrometer 184 CCD
200 Arithmetic Control Device 201 Microprocessor 208 Image Forming Board 208a Fundus Image Forming Board 208b OCT Image Forming Board 210 Control Unit 220 Image Forming Unit 230 Image Processing Unit 240 User Interfaces 241 and 242 Mirror Drive Mechanism L0 Low Coherence Light LR Reference Light LS Signal Optical LC Interference light R Scanning region R1 to Rm Scanning line Rij (i = 1 to m, j = 1 to n) Scanning point G1 to Gm Tomographic image Gij (i = 1 to m, j = 1 to n) in the depth direction Image E Eye to be examined Ef Fundus Ef ′ Fundus image (two-dimensional image)

Claims (3)

An illumination optical system that irradiates illumination light to the fundus of the eye to be examined and an imaging optical system that detects illumination light passing through the fundus by a first detection unit, based on a detection result by the first detection unit First image forming means for forming a two-dimensional image of the fundus surface;
A light source that outputs light having a wavelength different from that of the illumination light; and the light output from the light source is divided into signal light and reference light that travel toward the fundus, and signal light and reference light that pass through the fundus And a second detection unit for detecting the generated interference light, and based on a detection result by the second detection unit, the tomographic image of the fundus A second image forming means for forming an image;
An optical path combining / separating unit that combines the imaging optical path formed by the imaging optical system and the optical path of the signal light toward the fundus and separates the imaging optical path and the optical path of the signal light passing through the fundus;
With
The light output by the light source has a wavelength included in the range of 1000 nm to 1100 nm,
The combined signal light in the imaging optical path is irradiated to the fundus through the imaging optical path,
The signal light separated from the imaging optical path is superimposed on the reference light by the interference light generation means,
A fundus oculi observation device characterized by that. The light output by the light source has a longer wavelength than the illumination light.
The fundus oculi observation device according to claim 1. The illumination light has a wavelength included in a range of 850 nm to 1000 nm.
The fundus oculi observation device according to claim 2.

Images