JP2006055248A - Ophthalmologic imaging device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an ophthalmologic imaging device with which an eye fundus image without flare can easily be acquired in the eye fundus imaging of an eye to be examined in which an intraocular lens is fitted. <P>SOLUTION: This ophthalmologic imaging device is equipped with an illumination optical system 100, an imaging optical system 120, a solenoid 33b, and a controlling section 30. The illumination optical system 100 has an iris collimator member 107B having an iris collimator 107b-1 for sound eye and an iris collimator 107b-2 for IOL (intraocular lens), which make the cross section of an illumination light a ring shape. The imaging optical system 120 photographs the eye fundus image by detecting an eye fundus reflective light by the illumination light with which the eye E to be examined is irradiated. The solenoid 33b controls the iris collimator member 107B in such a manner that the iris collimator 107b-2 for IOL may be arranged on the optical axis of the illumination optical system 100 when the eye E to be examined in which the intraocular lens is fitted is irradiated with the illumination light. The controlling section 30 controls the motion of the solenoid 33b. The outer diameter of a ring slit Rs' of the iris collimator 107b-2 for IOL has a smaller diameter than a ring slit Rs of the iris collimator 107b-1 for sound eye. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to an ophthalmologic photographing apparatus for photographing a subject's eye, and particularly to a technique for suitably performing fundus photographing of a subject's eye on which an intraocular lens (IOL) is attached.

  In recent years, as many IOL transplant operations for diseases such as cataracts have been carried out, opportunities for observing and photographing the eye to be examined wearing the IOL have increased. In particular, using a fundus camera or the like to observe and photograph the fundus of an eye to be examined on which an IOL is mounted has been widely performed.

  The IOL is a lens that is transplanted in place of the lens extracted in an operation for an eye disease such as cataract. The IOL generally includes a lens main body made of a lens having refractive power and a support portion that supports the lens main body in the eye (for example, see Patent Document 1).

  The lens body of the IOL generally has an effective diameter of about 5 mm in diameter, and the edge portion of the lens body is formed in various shapes such as a circle and an ellipse (see, for example, Patent Documents 1 and 2). In addition, as the lens body, those having various spectral transmission characteristics such as a non-colored clear type and a colored type in which a pigment is mixed are used (for example, see Patent Document 3).

  Also, the IOL support part is made of a pair of flat elastic bodies formed integrally with the lens body, or made of a pair of wire members molded separately from the lens body and joined to the lens body. Etc. (see, for example, Patent Document 1).

  It has been pointed out that a good fundus image cannot be obtained due to the following causes when fundus photography is performed on the eye to be examined with such an IOL. First, the illumination light that illuminates the fundus is scattered at the edge of the lens body and the support that supports the lens body, and this scattered light may cause flare in the photographed fundus image, thereby creating a clear fundus image. Sometimes it was not possible. When flare occurs in the fundus image in this way, a skilled operation for removing the flare is necessary.

  In addition, since fundus photography is performed based on the light flux that has passed through the lens body of the IOL, the acquired fundus image changes color due to the spectral transmission characteristics of the lens body, making it difficult to read the fundus image and adversely affecting the findings. There was to give. That is, in the clear type IOL, a lot of short wavelength components are transmitted through the crystalline lens of the human eye, so that the fundus image tends to be a bluish image, whereas in the colored type IOL, the fundus image is a strong color image. Will be obtained. For example, in a yellow coloring type IOL, depending on the degree of coloring, a fundus image with a strong yellowishness is photographed with a lens body having a strong yellowishness. As described above, since the color of the fundus image to be photographed differs depending on the type of IOL, it may be difficult to perform accurate and effective medical care. In this case, the color of the fundus image is corrected. It was necessary to perform image processing for this purpose.

JP 2002-29176A (paragraphs [0009], [0010], [0012], FIGS. 1 and 2) JP-A-6-189985 (Claim 1) JP 2003-84242 A (Claims 1 to 13)

  The present invention has been made in view of such circumstances, and provides an ophthalmologic photographing apparatus capable of easily acquiring a fundus image without flare in fundus photographing of an eye to be examined with an intraocular lens. With the goal.

  In addition, the present invention provides an ophthalmologic photographing apparatus capable of easily acquiring a fundus image having a hue close to a photographed image of a human eye crystalline lens in the fundus photographing of the eye to be examined wearing an intraocular lens. For other purposes.

  In order to achieve the above object, the invention described in claim 1 includes a light source that emits illumination light, outer diameter limiting means that is disposed substantially conjugate with the pupil of the eye to be examined and limits the outer diameter of the cross section of the illumination light. An illumination optical system that irradiates the eye to be inspected with the illumination light that has passed through the outer diameter limiting means, and a photographing optical system that detects fundus reflected light from the illuminated illumination light and photographs a fundus image, An ophthalmologic photographing apparatus comprising: the outer diameter so that the outer diameter of the illumination light applied to the eye to be examined with an intraocular lens is smaller than the outer diameter of the illumination light for a healthy eye An outer diameter changing means for controlling the diameter limiting means is provided.

  The invention according to claim 2 is the ophthalmologic photographing apparatus according to claim 1, wherein the illumination optical system is arranged substantially conjugate with the crystalline lens of the eye to be examined and shields a central region of a section of the illumination light. A central light shielding means for irradiating the eye to be inspected with the illumination light having a cross-sectional ring shape via the outer diameter limiting means and the central light-shielding means. An inner diameter changing means for controlling the central light shielding means to make the inner diameter of the cross section of the illumination light smaller than the inner diameter of the illumination light with respect to a healthy eye when the diameter is changed to be smaller by the outer diameter changing means; It is characterized by having.

  The invention described in claim 3 is the ophthalmologic photographing apparatus according to claim 1 or 2, wherein the outer diameter limiting means includes a first light transmitting portion and the first light transmitting portion. A diaphragm member formed with a second light-transmitting portion having a smaller diameter, and the outer diameter changing means is configured to apply the second light when irradiating the eye to be examined with an intraocular lens. Drive means for driving the diaphragm member so as to dispose the light transmitting portion on the optical axis of the illumination optical system.

  The invention according to claim 4 is the ophthalmologic photographing apparatus according to claim 2, wherein the central light shielding means has a first central light shielding part and a diameter smaller than that of the first central light shielding part. A diaphragm member formed with a second central light-shielding portion, wherein the inner diameter changing means is configured to change the second central light-shielding portion when the outer diameter of the illumination light is changed to be smaller by the outer diameter changing means. It includes drive means for driving the diaphragm member so as to be arranged on the optical axis of the illumination optical system.

  An invention according to claim 5 is the ophthalmologic photographing apparatus according to any one of claims 1 to 4 for inputting that an intraocular lens is attached to the eye to be examined. Input means is provided, and the outer diameter changing means controls the outer diameter limiting means when the input is made by the input means.

  The invention according to claim 6 is the ophthalmologic photographing apparatus according to any one of claims 1 to 7, wherein the outer diameter of the illumination light is changed to be smaller by the outer diameter changing means. And a correction means for correcting the color balance of the fundus image photographed by the photographing optical system to match the color balance of the photographed fundus image with respect to a normal eye.

  The invention described in claim 7 includes an illumination optical system that irradiates the eye to be inspected with illumination light, and an imaging optical system that includes an imaging unit that detects fundus reflected light from the illumination light and captures a fundus image. An ophthalmologic imaging apparatus, wherein the color balance of the fundus image taken by the imaging means when an intraocular lens is attached to the eye to be examined is determined for the eye image to be taken with respect to the eye to be examined having a human eye lens. Correction means for correcting the color balance is provided.

  The invention described in claim 8 is the ophthalmologic photographing apparatus according to claim 7, further comprising an input means for inputting that an intraocular lens is attached to the eye to be examined, wherein the correcting means is The color balance of the photographed fundus image is corrected in response to the input by the input means.

  The invention according to claim 9 is the ophthalmologic photographing apparatus according to claim 7 or claim 8, wherein the storage means for storing the spectral characteristic information of a plurality of types of intraocular lenses in advance, A type input unit for inputting a type, and the correction unit selects the spectral characteristic information corresponding to the input type of intraocular lens from the storage unit, and the selected spectral The color balance of the photographed fundus image is corrected based on characteristic information.

  The invention according to claim 10 is the ophthalmologic photographing apparatus according to claim 9, wherein the spectral characteristic information includes reference colors obtained when the light transmitted through the intraocular lens is separated into a plurality of reference colors. The intensity ratio of the components, wherein the storage means stores in advance the intensity ratio of each reference color component of the light transmitted through the human eye lens, and the imaging means stores the fundus reflection light in the plurality of reference colors. An image sensor that detects the intensity of each reference color component by decomposing the image, and the correction means captures the image based on the intensity ratio of the selected intraocular lens and the intensity ratio of the human eye lens. The color balance of the photographed fundus image is corrected by changing the intensity of each reference color component detected by an element.

  The invention according to claim 11 is the ophthalmologic photographing apparatus according to claim 9, wherein the spectral characteristic information includes each reference color when light transmitted through the intraocular lens is separated into a plurality of reference colors. A correction coefficient for adjusting the intensity ratio of the component to the intensity ratio of each reference color component of the light transmitted through the human eye lens, and the imaging unit decomposes the fundus reflection light into the plurality of reference colors An image sensor that detects the intensity of each reference color component is provided, and the correction unit changes the intensity of each reference color component detected by the image sensor using the correction coefficient, thereby correcting the captured fundus image. The color balance is corrected.

  The invention according to claim 12 is the ophthalmologic photographing apparatus according to any one of claims 9 to 11, wherein the storage means has spectral characteristic information corresponding to the lens color of the intraocular lens. In advance, and further comprising lens color input means for inputting the lens color of the intraocular lens, wherein the correction means stores the spectral characteristic information corresponding to the inputted lens color of the intraocular lens. The color balance of the photographed fundus image is corrected based on the selected spectral characteristic information.

  The invention according to claim 13 is the ophthalmologic photographing apparatus according to any one of claims 7 to 12, wherein the type of the intraocular lens is a product name of the intraocular lens. It is characterized by.

  The invention according to claim 14 is the ophthalmologic photographing apparatus according to claim 7 or claim 8, wherein the imaging means of the photographing optical system detects anterior ocular segment reflected light by the illumination light. And taking an image of the intraocular lens attached to the eye to be examined, and the correcting means analyzing the taken image of the intraocular lens to obtain spectral characteristic information of the intraocular lens. And the color balance of the photographed fundus image is corrected based on the acquired spectral characteristic information.

  The invention described in claim 15 is the ophthalmologic photographing apparatus according to claim 14, wherein the imaging means separates each of the anterior ocular segment reflected light and the fundus reflected light into a plurality of reference colors. An image sensor that detects the intensity of each reference color component, and the analysis unit obtains the intensity ratio of each reference color component based on the detection result of the reflected light from the anterior segment as the spectral characteristic information. And storing means for storing in advance the intensity ratio of each of the reference color components of the light reflected by the human eye lens, wherein the correction means uses the acquired intensity ratio of the intraocular lens as the human eye. Correcting the color balance of the photographed fundus image by changing the intensity of each reference color component of the fundus reflected light detected by the imaging device so as to match the intensity ratio of the crystalline lens. Features .

  The invention described in claim 16 is the ophthalmologic photographing apparatus according to claim 10, 11 or 15, wherein the plurality of reference colors are RGB.

  The invention according to claim 17 is the ophthalmologic photographing apparatus according to claim 10, 11 or 15, wherein the image pickup device of the image pickup means is a CCD.

  According to the ophthalmologic photographing apparatus according to any one of claims 1 to 6, when photographing an eye to be examined with an intraocular lens attached, the outer diameter of illumination light restricted by the outer diameter restricting means is healthy. Since the outer diameter of the cross section of the illumination light is automatically controlled to be smaller than when photographing with respect to the eye, scattering of illumination light at the edge portion and support portion of the lens body of the intraocular lens is suppressed. Is done. Therefore, it is possible to easily obtain a suitable fundus image without flare.

  In particular, according to the ophthalmologic photographing apparatus according to claim 2, the outer diameter of the illumination light is changed to be small when irradiating the fundus of the eye to be examined with the intraocular lens attached with the ring-shaped illumination light, and Since the inner diameter is also changed to be small, it is possible to suppress a decrease in the amount of illumination light. Thereby, it is possible to capture a bright fundus image without flare.

  According to the ophthalmologic photographing apparatus according to any one of claims 7 to 17, when an intraocular lens is attached to the eye to be examined, the color balance of the photographed fundus image is adjusted according to the type of the intraocular lens. Since correction means for correcting to match the color balance of the fundus image with respect to the human eye lens is provided, it is easy to obtain a fundus image with a hue close to that of a normal eye in the fundus imaging of the eye to be examined with the intraocular lens attached. It is possible to obtain.

  In particular, according to the ophthalmologic photographing apparatus according to any one of claims 9 to 13, storage means for storing the spectral characteristic information of the intraocular lens, and type input means for inputting the type (particularly, product name) of the intraocular lens; And is configured to correct the color balance of the fundus image based on spectral characteristic information selected according to the input type of intraocular lens, so color balance correction according to the type of intraocular lens Can be carried out effectively.

  Furthermore, according to the ophthalmologic photographing apparatus of the twelfth aspect, the type of intraocular lens cannot be acquired, or the spectral characteristic information corresponding to the type of intraocular lens is not stored in the storage means. In addition, it is convenient because the color balance correction of the fundus image can be executed by simply inputting the lens color of the intraocular lens using the spectral characteristic information corresponding to the lens color.

  In addition, according to the ophthalmologic photographing apparatus according to claim 14 or 15, the spectral characteristic information of the intraocular lens is obtained by taking an image of the intraocular lens attached to the eye to be examined and analyzing the image. Since it is configured to acquire and correct the color balance of the fundus image based on the spectral characteristic information, it is possible to easily perform color balance correction according to the intraocular lens actually mounted.

  An example of a preferred embodiment of an ophthalmologic photographing apparatus according to the present invention will be described in detail with reference to the drawings.

  An object of the present invention is to suitably perform imaging (especially fundus imaging) of an eye to be examined with an intraocular lens (IOL) attached thereto. Hereinafter, in the first embodiment, ophthalmic imaging capable of suppressing the occurrence of flare in a captured image by controlling the diaphragm (illumination diaphragm) of the illumination optical system at the time of examination of the eye to be examined with the IOL mounted. The apparatus will be described. Further, in the second and third embodiments, it is possible to acquire a fundus image having a suitable hue regardless of the type of IOL attached to the eye to be examined (for example, the product of each company, the color of the lens body, etc.). An ophthalmologic photographing apparatus will be described.

<First Embodiment>
[Appearance configuration]
FIG. 1 shows an external configuration of a fundus camera 1 as an example of an ophthalmologic photographing apparatus according to the present invention. The fundus camera 1 includes a base 2 and a mount 3 mounted on the base 2 so as to be slidable in the front-rear and left-right directions (horizontal direction).

  A joystick 4 is installed on the gantry 3, and the examiner can freely move the gantry 3 on the base 2 by operating the joystick 4. An operation button 4a is arranged at the tip of the joystick 4, and fundus photographing is performed by pressing this button. On the gantry 3, a control panel 3 a is provided that includes buttons, keys, switches, and the like for performing input related to various operations of the fundus camera 1 such as setting input for shooting mode and setting input for IOL mode. . The control panel 3a can also be configured with a touch panel type liquid crystal panel or the like.

  A support column 5 is erected on the base 1, and a chin rest 6 a for placing the subject's chin, a forehead rest 6 b against which the subject's forehead abuts, and an eye E to be examined are fixed. An external fixation lamp 7 is provided as a light source for the purpose.

  On the gantry 3, a main body 8 that stores various optical systems and control systems of the fundus camera 1 is mounted. The control system may be provided inside the base 2 or the gantry 3. The main body portion 8 is provided with an objective lens portion 8a disposed to face the eye E, and an eyepiece portion 8b for the examiner to observe the eye E and the like. The main body portion 8 is connected to the gantry 3 via a joint portion 8c. The joint portion 8c stores a mechanism that allows the orientation of the main body portion 8 to be changed up, down, left, and right as in the conventional art.

  The main body 8 is connected to an imaging device 9 for capturing a still image of the anterior segment and fundus of the eye E and a television camera 10 for capturing an observation image of the anterior segment and fundus. Has been. The imaging device 9 and the television camera 10 are detachably connected to the main body unit 8. In particular, as the imaging device 9, a television camera, a digital camera, a film camera (for example, 35 mm), an instant camera, or the like equipped with a CCD is selectively applied depending on the purpose of inspection. In addition, an image captured by the imaging device 9 or the television camera 10 can be transmitted to and stored in an image recording device such as a computer provided outside the fundus camera.

  Further, on the examiner side of the main body 8, a monitor 11 that displays an anterior ocular segment image and a fundus oculi image Ef ′ of the eye E based on a video signal acquired by the television camera 10 is provided. The monitor 11 constitutes display means according to the present invention, and is constituted by a thin (preferably lightweight) type liquid crystal monitor, for example. As the monitor 11, for example, a touch panel monitor is used, and an XY coordinate system with the origin at the center of the screen is superimposed on the fundus image Ef ′ and the like, and coordinate values corresponding to the position touched on the screen are displayed. It has become.

[Configuration of optical system]
FIG. 2 shows the configuration of the optical system of the fundus camera 1. The fundus camera 1 receives an illumination optical system 100 that illuminates the anterior eye part and the fundus oculi Ef of the eye E and the anterior eye part and the fundus oculi Ef by receiving the anterior eye part reflected light and the fundus reflected light of the illumination light. A photographing optical system 120 for observing and photographing is provided.

[Illumination optics]
The illumination optical system 100 includes a halogen lamp 101, a condenser lens 102, a xenon lamp 103, a condenser lens 104, exciter filters 105 and 106, ring slit plates 107a, 107b, 107c, a mirror 108, a liquid crystal display 109, a relay lens 111, a hole. An opening mirror 112 and an objective lens 113 are provided.

  The halogen lamp 101 is an observation light source that emits steady light (observation illumination light). The condenser lens 102 is an optical element that collects steady light emitted from the halogen lamp 101 and irradiates the eye E (especially the fundus oculi Ef) evenly. The xenon lamp 103 is a photographing light source that emits flash when photographing the fundus oculi Ef. The condenser lens 104 is an optical element that collects flash light (imaging illumination light) emitted from the xenon lamp 103 and irradiates the fundus oculi Ef evenly.

  The exciter filters 105 and 106 are used when performing fluorescence photographing of the fundus image of the fundus oculi Ef, and are inserted into and removed from the optical path by a solenoid (not shown). An exciter filter 105 is inserted on the optical path during FAG imaging, and an exciter filter 106 is inserted on the optical path during ICG imaging. Further, at the time of color photographing, both the exciter filters 105 and 106 are retracted from the optical path.

  The ring slit plates 107a to 107c act as an illumination stop that blocks a part of the illumination light, and limit the cross-sectional shape of the illumination light to a ring shape in order to remove flare in an observation image or a captured image. is there. Note that the “cross section” of illumination light represents a cross section in a plane orthogonal to the traveling direction of the illumination light (the optical axis direction of the illumination optical system 100).

  As shown in FIG. 3, each of the ring slit plates 107 a to 107 c includes a peripheral light shielding portion Ra that shields a peripheral region of the cross section of the illumination light, and a central light shielding portion Rb that shields a central region of the cross section of the illumination light. Yes. The peripheral light-shielding part Ra and the central light-shielding part Rb are formed so as to form concentric circles with the optical axis of the illumination optical system 100 as the center. The illumination light is transmitted through a ring slit Rs formed between the peripheral light-shielding portion Ra and the central light-shielding portion Rb, and the cross section is formed in a ring shape. Note that the peripheral light-shielding portion Ra and / or the central light-shielding portion Rb of each of the ring slit plates 107a to 107c are formed in different sizes. In other words, the ring slits Rs of the ring slit plates 107a to 107c have different sizes, that is, different outer diameters and / or inner diameters.

  Each of the ring slit plates 107 a to 107 c is movable in the optical axis direction of the illumination optical system 100. At the time of examination, the position of the ring slit plate 107b is adjusted so as to be conjugate with the pupil (iris), and then the position of the ring slit plates 107a, 107c is adjusted so as to be conjugate with the cornea and the crystalline lens (rear surface). . Thereby, the position of the ring slit plates 107a to 107c can be adjusted according to the difference in the thickness of the cornea and the lens for each person, or the difference in the distance between the cornea and the rear surface of the lens.

  The movement of the ring slit plates 107a to 107c in the direction of the optical axis of the illumination optical system 100 can be manually performed, or can be configured to be electrically performed by a driving device such as a pulse motor. You can also. In the present embodiment, the latter configuration (drive device) is adopted so that the positions of the ring slit plates 107a to 107c can be finely adjusted. Each driving device drives each ring slit plate 107a to 107c in response to an operation on the control panel 3a or the joystick 4, for example.

  Hereinafter, the ring slit plate 107a disposed substantially conjugate to the cornea of the eye E is referred to as a corneal diaphragm, and the ring slit plate 107b disposed substantially conjugate to the iris is referred to as an iris diaphragm, and is disposed substantially conjugate to the rear surface of the lens. The ring slit plate 107c to be used may be referred to as a crystalline lens diaphragm. These three stops may be collectively referred to as an illumination stop 107.

  The corneal stop 107a and / or the crystalline lens stop 107c do not need to be a ring slit plate having a ring-shaped light transmitting portion (ring slit Rs), and may be a light blocking plate having only a central light blocking portion Rb. Further, the iris diaphragm 107b need not be a ring slit plate having a ring-shaped light transmitting portion, and a light shielding plate having only a peripheral light shielding portion Ra may be applied. Therefore, for example, it is possible to employ a configuration in which the outer diameter of the illumination light is limited only by the iris diaphragm 107b, and the inner diameter of the illumination light is determined by the three diaphragms 107a to 107c.

  Further, at least the iris diaphragm 107b and the lens diaphragm 107c include a plurality of ring slit plates having different sizes of light transmitting portions, and are configured to be selectively switched and arranged on the optical axis of the illumination optical system. (Details will be described later). FIG. 4 shows the configuration of the iris diaphragm 107b and the lens diaphragm 107c in the present embodiment. FIG. 4A shows a configuration of an iris diaphragm member 107B that forms the iris diaphragm 107b, and FIG. 4B shows a configuration of a lens diaphragm member 107C that forms the lens diaphragm 107c.

  The iris diaphragm member 107B is configured based on a transparent plate-like member that transmits illumination light, and is a healthy eye that is used when observing and photographing a subject eye having a human eye lens (referred to as a healthy eye). And an IOL iris diaphragm 107b-2 used when observing and photographing the eye to be examined with the IOL mounted thereon. The iris diaphragm member 107B constitutes the “outer diameter limiting means” of the present invention that limits the outer diameter of the illumination light at the iris (pupil) position of the eye E.

  The iris diaphragm 107b-1 for normal eyes and the iris diaphragm 107b-2 for IOL are alternatively arranged on the optical path of the illumination light by an outer diameter changing means (solenoid or the like) described later, and each of the iris diaphragm ( It functions as a ring slit plate) 107b.

  As shown in FIG. 3, the iris diaphragm 107b-1 for normal eyes is provided with a peripheral light shielding portion Ra, a central light shielding portion Rb, and a ring slit Rs formed therebetween. Similarly, the IOL iris diaphragm 107b-2 is also provided with a peripheral light shielding portion Ra ′, a central light shielding portion Rb, and a ring slit Rs ′.

  Here, the peripheral light-shielding part Ra ′ of the IOL iris diaphragm 107b-2 is formed in a wider area than the peripheral light-shielding part Ra of the normal-eye iris diaphragm 107b-1, and therefore, the IOL iris diaphragm 107b-2. The ring slit Rs ′ has a smaller outer diameter than the ring slit Rs of the iris diaphragm 107b-1 for normal eyes. Therefore, the illumination light transmitted through the IOL iris diaphragm 107b-2 is a ring-shaped light beam having an outer diameter smaller than that when transmitted through the healthy eye iris diaphragm 107b-1. The ring slit Rs of the iris diaphragm 107b-1 for normal eyes constitutes the “first translucent portion” of the present invention, and the ring slit Rs ′ of the iris diaphragm 107b-2 for IOL corresponds to the “second slit” of the present invention. It constitutes a “translucent part”.

  The size of the outer diameter of the ring slit Rs ′ of the IOL iris diaphragm 107b-2 is such that the illumination light passes through the edge of the lens body of the general IOL and the support part that supports the lens body. Is set to

  On the other hand, the lens diaphragm member 107C is also configured on the basis of a transparent plate-like member, and the lens diaphragm 107c-1 for healthy eyes used when observing and photographing a healthy eye, and the eye to be inspected to which the IOL is mounted. And an IOL lens diaphragm 107c-2 used when performing observation and photographing. The lens diaphragm member 107C constitutes “center light shielding means” of the present invention that shields the central region of the illumination light and determines the inner diameter of the illumination light at the position of the rear surface of the lens.

  The normal eye lens aperture 107c-1 and the IOL lens aperture 107c-2 are alternatively arranged on the optical path of the illumination light by an inner diameter changing means (solenoid or the like), which will be described later. Acts as a slit plate 107c.

  As shown in FIG. 3, the lens block 107c-1 for normal eyes is provided with a peripheral light-shielding portion Ra, a central light-shielding portion Rb, and a ring slit Rs formed therebetween. Similarly, a peripheral light-shielding portion Ra, a central light-shielding portion Rb ′, and a ring slit Rs ′ are also provided for the IOL lens stop 107c-2.

  Here, the central light-shielding portion Rb ′ of the IOL lens diaphragm 107c-2 is formed to be smaller than the central light-shielding portion Rb of the healthy eye lens diaphragm 107c-1, and thus the ring of the IOL lens diaphragm 107c-2 is formed. The slit Rs ′ is formed to have a smaller inner diameter than the ring slit Rs of the normal-eye lens diaphragm 107c-1. Accordingly, the illumination light transmitted through the IOL lens diaphragm 107c-2 is a ring-shaped light beam having a smaller inner diameter than when transmitted through the healthy eye lens diaphragm 107c-1. The central light shielding portion Rb of the lens stop 107c-1 for normal eyes constitutes the “first central light transmitting portion” of the present invention, and the ring slit Rs ′ of the lens stop 107c-2 for IOL is the “first slit” of the present invention. 2 central translucent portions ”.

  Now, the mirror 108 of the illumination optical system 100 is a reflecting mirror that reflects the illumination light transmitted through the illumination stop 107 and having a cross-sectional ring shape in the optical axis direction of the imaging optical system 120. The liquid crystal display 109 is a transmissive liquid crystal panel that displays a fixation target for promoting fixation of the eye E.

  The perforated mirror 112 is an optical element that synthesizes the optical axis of the illumination optical system 100 and the optical axis of the photographing optical system 120, and includes a hole portion 112a that has both optical axes substantially in the center. The objective lens 113 is a lens that is arranged to face the eye E and is provided in the objective lens portion 8 a of the main body portion 8.

  By such an illumination optical system 100, the anterior eye part and the fundus oculi Ef of the eye E are illuminated as follows. When observing the anterior segment or the fundus, observation illumination light is emitted from the halogen lamp 101, and this observation illumination light is applied to the illumination stop 107 via the condenser lenses 102 and 104. The observation illumination light that has passed through the ring slit RS of each of the ring slit plates 107a to 107c and formed into a cross-section ring-shaped light beam is reflected by the mirror 108, passes through the liquid crystal display 109 and the relay lens 111, and is opened. 112 is reflected and combined with the optical axis of the photographic optical system 120 and focused by the objective lens 113 to illuminate the eye E.

  Here, since the ring slit plates 107a, 107b, and 107c are respectively arranged almost conjugate with the cornea, pupil, and crystalline lens (rear surface) of the eye E, the corresponding ring slits are respectively provided to the cornea, the pupil, and the crystalline lens. A ring slit image is formed by the plate. The fundus reflection light of the illumination light is emitted from the eye E through the central dark part (the area shielded by the central light shielding parts Rb and Rb ′) of each ring slit image and enters the imaging optical system 120. Further, when observing the anterior segment of the eye E, the fundus reflection light of the observation illumination light enters the imaging optical system 120.

  Further, at the time of fundus photography, the xenon lamp 103 emits flash light and illuminates the fundus oculi Ef through the same optical path. In the case of fluorescence photography, the exciter filter 105 or 106 is selectively placed on the optical path depending on whether FAG photography or ICG photography.

[Photographing optical system]
The photographing optical system 120 includes an objective lens 113, a perforated mirror 112 (hole 112 a thereof), a photographing aperture 121, barrier filters 122 and 123, a zoom lens 124, a relay lens 125, a photographing lens 126, and a quick return mirror 127. Consists of. Reference numeral 9a represents an imaging medium (CCD (imaging device), camera film, instant film, etc.) of the imaging device 9.

  The photographing aperture 121 is composed of, for example, a disk-shaped member in which a plurality of light-transmitting portions having different sizes are formed, and each light-transmitting portion is selectively placed on the optical path by being rotated by a stepping motor or the like. It is arranged and the aperture value is changed. The aperture value of the shooting aperture 121 is changed according to the shooting mode (color shooting, FAG shooting, ICG shooting), observation magnification or shooting magnification (field angle), or observation depth or shooting depth.

  The barrier filters 122 and 123 can be inserted into and removed from the optical path by a solenoid or the like. The barrier filter 122 is inserted into the optical path during FAG imaging, and the barrier filter 123 is inserted into the optical path during ICG imaging. During color photography, the barrier filters 122 and 123 are both retracted from the optical path.

  The variable magnification lens 124 can be moved in the optical axis direction by a drive mechanism (not shown), and is used for changing the observation magnification and photographing magnification, and focusing the fundus image. The photographing lens 126 is a lens that forms an image of fundus reflected light from the eye E on the imaging medium 9a.

  The quick return mirror 127 is provided so as to be rotatable around a rotation shaft 127a. The quick return mirror 127 is obliquely arranged on the optical path when observing the eye E, and reflects the fundus reflection light to guide the eyepiece 130 and the TV camera 10 in the direction. Further, the quick return mirror 127 is controlled so that when the imaging device 9 captures the fundus, it is flipped up momentarily to guide the fundus reflected light temporarily to the imaging medium 9a.

  The photographing optical system 120 includes a field lens (field lens) 128, a switching mirror 129, an eyepiece lens 130, a relay lens 131, a reflection mirror 132, and a relay lens 133 that guide fundus reflected light reflected by the quick return mirror 127. Is provided.

  Similarly to the quick return mirror 127, the switching mirror 129 may rotate about the rotation shaft 129a and be inserted into and removed from the optical path. It should be noted that the insertion / removal of the switching mirror 129 with respect to the optical path may be performed manually, or may be configured to be automatically performed in conjunction with the observation mode switching operation.

  The switching mirror 129 is disposed obliquely on the optical path when the examiner looks into the eye E while looking into the eyepiece unit 8 b and guides the light beam to the eyepiece 130.

  Further, when the eye E is photographed by the television camera 10, the switching mirror 129 is retracted from the optical path. The anterior ocular segment reflected light and the fundus oculi reflected light from the eye E are projected onto the imaging device (CCD) 10a via the relay lens 131, the mirror 132, and the relay lens 133.

  On the monitor 11, an anterior segment image and a fundus oculi image Ef ′ captured by the television camera 10 are displayed. The examiner observes the display image and observes the anterior segment and the fundus of the eye E. Note that when a television camera or a digital camera using an imaging element such as a CCD as the imaging medium 9 a is applied as the imaging device 9, an image captured by the imaging device 9 may be displayed on the monitor 11.

[Control system configuration]
FIG. 5 shows a schematic configuration of a control system of the fundus camera 1 of the present embodiment. The control system of the fundus camera 1 is provided, for example, in the main body 8 as described above.

  The control system of the fundus camera 1 includes a control unit 30, an IOL mode setting key 31 provided on the control panel 3a, pulse motors 32a, 32b, and 32c, and solenoids 33b and 33c. When a computer apparatus is connected to the fundus camera 1 and operated as a system, the CPU or the like of the computer apparatus can be configured as the control unit 30.

  The control unit 30 is configured to include an arithmetic control device such as a CPU, and by executing a computer program stored in a storage device such as a ROM or a hard disk drive (not shown), all of which are not shown, the halogen lamp 101 Control of illumination light switching by the xenon lamp 103, control of optical path switching by the quick return mirror 127 or switching mirror 129, control of insertion / extraction of the exciter filters 105, 106 and barrier filters 122, 123, driving of the variable magnification lens 124 Control, shooting control by the imaging device 9 and the television camera 10, display control of a shot image by the monitor 11, and the like are performed. Further, the control unit 30 controls each part of the apparatus in accordance with the tilting operation of the joystick 4, and in particular performs control so as to execute fundus photographing in response to pressing of the operation button 4a of the joystick 4.

  The IOL mode setting key 31 is operated when the IOL is attached to the eye E to be examined and photographed by the fundus camera 1. When the IOL mode setting key 31 is operated, a signal indicating that the IOL is attached to the eye E is input from the IOL mode setting key 31 to the control unit 30. The IOL mode setting key 31 corresponds to “input means” according to the present invention.

  The pulse motors 32a, 32b, and 32c drive the corneal stop 107a, the iris stop member 107B, and the crystalline lens stop member 107C, respectively, in the optical axis direction of the illumination optical system 100. The pulse motors 32a, 32b, and 32c are controlled by the control unit 30 in accordance with, for example, operations on the control panel 3a and the joystick 4.

  The solenoid 33b constitutes the “outer diameter changing means” and “driving means” of the present invention, and controls the iris diaphragm member 107B to drive the iris diaphragm 107b-1 for normal eyes and the iris diaphragm 107b- for IOL. 2 are alternatively arranged on the optical axis of the illumination optical system 100. Similarly, the solenoid 33c constitutes “inner diameter changing means” and “driving means” of the present invention, and controls the lens diaphragm member 107C to control the lens diaphragm 107c-1 for normal eyes and the lens diaphragm for IOL. 107c-2 is alternatively arranged on the optical axis of the illumination optical system 100. The solenoids 33b and 33c are controlled by the control unit 30, respectively.

[Mode of operation]
An example of the operation mode of the fundus camera 1 having the above configuration will be described.

  When the IOL is attached to the eye E to be observed and photographed by the fundus camera 1, the examiner operates the IOL mode setting key 31 of the control panel 3a. When receiving the input signal from the IOL mode setting key 31, the control unit 30 sets the state of the illumination stop 107 to the following IOL mode. Here, preliminary processing such as alignment of the optical system with respect to the eye E and position adjustment of the corneal diaphragm 107a, iris diaphragm member 107B, and lens diaphragm member 107C by the pulse motors 32a, 32b, and 32c has been completed. To do.

  When receiving the input signal from the IOL mode setting key 31, the control unit 30 controls the solenoid 33b to place the IOL iris diaphragm 107b-2 on the optical axis of the illumination optical system 100 and also controls the solenoid 33c. Then, the IOL lens stop 107c-2 is disposed on the optical axis of the illumination optical system 100.

  In the state where the illumination stop 107 is set to such an IOL mode, observation and photographing are performed on the eye E. When the fundus photographing of the subject eye E is completed, for example, the examiner displays the photographed fundus image on the monitor 11 or the like, selects a fundus image to be stored for diagnosis or the like, and performs a storage process. For example, the fundus image is stored in the electronic medical record of the subject managed by a computer device or a server connected to the fundus camera 1. When the fundus image storage process is completed, the control unit 30 controls the solenoids 33b and 33c to place the healthy eye iris diaphragm 107b-1 and the healthy eye lens diaphragm 107c-1 on the optical axis of the illumination optical system 100. Arrange.

  Note that a key or the like for canceling the IOL mode may be provided on the control panel 3a or the like and operated to switch from the IOL mode to the normal eye mode. Alternatively, the normal eye mode may be automatically set when the fundus camera 1 is turned on. In addition, when continuously inspecting an eye to be inspected with an IOL, the eye may be temporarily fixed in the IOL mode. As an operation for fixing to the IOL mode, for example, the IOL mode may be fixed by operating the IOL mode setting key 31 twice in succession.

[Action, effect]
According to the fundus camera 1 that executes such an operation, the following operations and effects are achieved.

  First, since the ring slit Rs ′ of the IOL iris diaphragm 107b-2 has a smaller outer diameter than the ring slit Rs of the healthy eye iris diaphragm 107b-1, the outer diameter of the ring slit image formed on the iris is small. Becomes smaller. Therefore, since the outer diameter of the illumination light incident on the IOL in the eye E is reduced, scattering at the edge portion and the support portion of the lens body of the IOL is suppressed, and flare is prevented. Therefore, according to the fundus camera 1 of the present embodiment, when photographing the fundus of the eye E to which the IOL is attached, it is possible to easily obtain a fundus image without flare only by switching the illumination aperture 107 to the setting for the IOL. Is possible. The operation for that purpose is also as simple as operating the IOL mode setting key 31.

  Further, since the central light-shielding portion Rb ′ of the IOL lens aperture 107c-2 has a smaller diameter than the central light-shielding portion Rb of the normal-eye lens aperture 107c-1, the ring slit of the IOL lens aperture 107c-2 is used. The cross-sectional area of the illumination light that passes through Rs ′ is larger than the cross-sectional area of the illumination light that passes through the ring slit Rs of the lens stop 107c-1 for normal eyes. This means that the amount of transmitted illumination light increases unless the output light amount of the light source is increased. Accordingly, when the IOL iris diaphragm 107b-2 is used, the amount of illumination light applied to the eye E is increased by switching the lens diaphragm 107c to the IOL lens diaphragm 107c-2. An image can be taken.

[Modification]
As shown in FIG. 4A, the iris diaphragm member 107B (outer diameter limiting means) in the above embodiment has a ring slit Rs (translucent portion) for healthy eyes having a relatively large diameter and a relatively small size. A ring slit Rs ′ (translucent portion) having a diameter is provided. The number of light transmitting parts provided in the outer diameter limiting means according to the present invention is not limited to two as described above, and three or more light transmitting parts can be arbitrarily provided. In that case, for example, depending on the size of the lens body of the IOL, a translucent part with various diameters is provided in the outer diameter limiting means, and a plurality of these are controlled by a driving device (outer diameter changing means) such as a solenoid or a pulse motor. The translucent part can be configured to be switched on the optical axis. At this time, the selection of the translucent portion can be performed by a selection key provided on the control panel 3a.

  Similarly, with respect to the central light shielding means according to the present invention, the number of light shielding portions is limited to two (center light shielding portions Rb and Rb ′ in FIG. 4B) as in the lens diaphragm member 107C of the above embodiment. Instead of this, three or more stops having central light shielding portions with different diameters may be provided.

  In addition, although the translucent part of the iris diaphragm 107b in the above embodiment is formed in a ring shape, for example, a circular translucent part may be applied in the ophthalmologic photographing apparatus according to the present invention. In addition, the lens diaphragm 107c and the corneal diaphragm 107a can also be applied with a light shielding plate that acts as a central light shielding portion instead of the ring slit plate as in the above embodiment.

  Furthermore, a transmissive liquid crystal panel or the like can be used as the illumination stop according to the present invention. In this case, the liquid crystal panel is driven by a normal liquid crystal driving device to form a peripheral light shielding portion, a central light shielding portion, and a light transmitting portion.

  In addition, the illumination stop 107 of the above embodiment includes the three stops of the corneal stop 107a, the iris stop 107b, and the crystalline lens stop 107c. However, the illumination stop 107 may have one, two, or four or more stops. . For example, it is also possible to apply a configuration in which a single illumination stop and a drive device that moves it in the optical axis direction are provided so that the illumination stop acts as a stop corresponding to the cornea, iris, crystalline lens, and the like. . In that case, for example, when the illumination diaphragm is arranged substantially conjugate to the iris, the IOL mode is controlled so as to reduce the outer diameter, and when arranged substantially conjugate to the lens, the inner diameter of the ring slit is reduced. It can be configured to control. The same control can be performed when two or more apertures are included.

  When the fundus camera 1 is connected to an electronic medical record management system that manages the patient's electronic medical record, it is described that the IOL is attached to the electronic medical record of the subject. It is also possible to automatically input information indicating that the camera is mounted to the fundus camera 1 from the system and automatically set the illumination stop 107 to the IOL mode.

  In addition, the fundus camera 1 according to the present embodiment may be configured by adding a configuration (correction unit or the like) of a second embodiment or a third embodiment described later. That is, the color balance of the fundus image taken with the outer diameter of the illumination light changed to be small with respect to the eye E to which the intraocular lens is attached is matched with the color balance of the fundus image taken for the normal eye. It can be configured to correct.

<Second Embodiment>
A second embodiment of the ophthalmologic photographing apparatus according to the present invention will be described. When the IOL is attached to the eye to be examined, the ophthalmologic photographing apparatus of the present embodiment reduces the influence of the IOL on the color balance of the photographed image and corrects the color of the photographed image with respect to the eye to be examined of the human eye lens. Acts like

  Here, the “color balance” is a reference color (RGB (red, green, blue), CMY (cyan, magenta, yellow), etc .; referred to as a reference color) constituting the color of the captured image). It means balance. In this embodiment, an image is acquired using an electronic image sensor such as a CCD. In general, a CCD for color photographing is classified into a primary color CCD that separates and detects photographing light into RGB and a complementary color CCD that separates and detects CMY. In this embodiment, a configuration using a primary color CCD is applied, but the same configuration can be applied to a case where a complementary color CCD is used. In general, the primary color CCD is excellent in color reproducibility, and the complementary color CCD is excellent in detection sensitivity.

  The ophthalmologic photographing apparatus (fundus camera) of this embodiment has the same external configuration (see FIG. 1) and optical system (see FIG. 2) as those in the first embodiment. Hereinafter, the same components as those in the first embodiment will be described using the reference numerals shown in FIGS. 1 and 2. In this embodiment, the imaging device 9 and the television camera 10 that use the primary color CCD as the imaging devices 9a and 10a are used. The imaging device 9 and the television camera 10 each constitute “imaging means” according to the present invention.

[Control system configuration]
FIG. 6 shows the configuration of the control system of the fundus camera 200 of this embodiment. The fundus camera 200 includes a control unit 210, a correction information storage unit 220, a color balance correction unit, and a captured image storage unit 240. Further, the control panel 3a is provided with an IOL mode setting key 251, an IOL product name input key 252, and a lens color input key 253.

  The IOL mode setting key 251 of the control panel 3a constitutes the “input unit” of the present invention, and is a key operated when the IOL is attached to the eye to be examined. When the IOL mode setting key 251 is operated, a correction process described later is executed under the control of the control unit 210.

  The IOL product name input key 252 constitutes “type input means” of the present invention, and is operated to input product names of various IOLs. The IOL product name input key 252 is a key for selecting and inputting a desired product name from various IOL product names displayed in a list on the display area of the control panel 3a or the monitor 11 of the fundus camera 200, for example.

  The lens color input key 253 constitutes the “lens color input means” of the present invention, and is operated to input the color of the lens body of the IOL attached to the eye to be examined. For example, “yellow”, “transparent” ”,“ Light blue ”, etc., and various lens color keys.

  As described above, the imaging device 9 and the television camera 10 each include a (primary color) CCD as the imaging elements 9a and 10a, and detects the intensity of each component by decomposing the photographing light into R, G, and B components. By doing so, the color of the photographed image is formed. Image data (captured image data 241) captured by the imaging device 9 or the television camera 10 is stored in a captured image storage unit 240 including an image storage device such as an image memory. The captured image data 241 is stored for each component as R image data 241R which is R component intensity information, G image data 241G which is G component intensity information, and B image data 241B which is B component intensity information.

  Similar to the control unit 30 of the first embodiment, the control unit 210 includes an arithmetic control device such as a CPU, and controls each part of the device by executing a computer program stored in a ROM, a hard disk drive, or the like. I do. In particular, the control unit 210 performs processing for storing a photographed image by the imaging device 9 or the television camera 10, operation control of the color balance correction unit 230, and the like.

  The correction information storage unit 220 includes a nonvolatile storage device such as a ROM or a hard disk drive, and includes IOL spectral characteristic information 221, human eye lens spectral characteristic information 222, and lens color spectral characteristic information 223 as described below. Is stored in advance. Updating or adding information stored in the correction information storage unit 220 can be performed as appropriate. The correction information storage unit 220 constitutes “storage means” of the present invention.

  The IOL spectral characteristic information 221 corresponds to “spectral characteristic information of a plurality of types of intraocular lenses” according to the present invention, and the intensity of each component when the light transmitted through the IOL is decomposed into an R component, a G component, and a B component. This is spectral characteristic information including the ratio. Here, for example, the R component corresponds to a wavelength component of 600 to 700 nm, the G component corresponds to a wavelength component of 500 to 600 nm, and the B component corresponds to a wavelength component of 400 to 500 nm.

  FIG. 7 is a conceptual diagram illustrating an example of the IOL spectral characteristic information 221. As shown in the figure, the IOL spectral characteristic information 221 is formed by the intensity ratio (%) of each component of RGB for various IOL products (product names A to H). For example, the intensity ratio of the R component, G component, and B component of the light transmitted through the IOL of the product name A is 37%: 35%: 28%. In FIG. 7, product names A to C are yellow type colored IOLs, product names D to F are transparent type IOLs, and product names G and H are light blue type IOLs. Of course, the IOL spectral characteristic information 221 may include other types of IOLs, and the number of products is also arbitrary.

  For the spectral characteristic information of each product included in the IOL spectral characteristic information 221, data disclosed by a manufacturer or a seller may be used, or a light source or white light having the same specifications as the xenon lamp 103 of the fundus camera 200 may be used. It can also be obtained by measuring in advance using the above.

  The human eye lens spectral characteristic information 222 is spectral characteristic information including the intensity ratio of each component when the light transmitted through the human eye lens is decomposed into an R component, a G component, and a B component. It is stored in the same format as 221. For example, clinical data is used as the human eye lens spectral characteristic information 222. In general, the crystalline lens absorbs a short wavelength (B component) slightly, so that the light transmitted through it has a yellowish tinge. Here, it is assumed that the human eye lens spectral characteristic information 222 is R: G: B = 35%: 38%: 27%.

  The lens color spectral characteristic information 223 is spectral characteristic information including intensity ratios of representative RGB components in the IOL of various lens colors. FIG. 8 is a conceptual diagram illustrating an example of the lens color spectral characteristic information 223, and includes intensity ratios of representative RGB components of an IOL whose lens colors are yellow, transparent, and light blue. The information can be obtained, for example, as an average value of intensity ratios for a plurality of IOLs of similar colors.

  Here, when obtaining the IOL spectral characteristic information 221, the human eye lens spectral characteristic information 222, and the lens color spectral characteristic information 223, it is preferable to use the same measurement light. Further, as the measurement light, light from the above-mentioned xenon lamp or white light is used. In particular, white light is considered to be suitable for measuring the intensity ratio of RGB for obtaining the information 221 to 223 because the intensity at each wavelength is averaged. Since these information 221 to 223 are formed as intensity ratios in RGB, monochromatic light such as laser light is inappropriate as the measurement light.

  The color balance correction unit 230 includes an arithmetic control device such as a CPU that executes a predetermined computer program, and includes a spectral characteristic information selection unit 231, a correction coefficient calculation unit 232, and an RGB correction processing unit 233. The color balance correction unit 230 constitutes the “correction unit” of the present invention.

  The spectral characteristic information selection unit 231 performs processing for selecting spectral characteristic information corresponding to the product name input by the IOL product name input key 252 of the control panel 3a from the IOL spectral characteristic information 221 of the correction information storage unit 220. Further, the spectral characteristic information selection unit 231 displays a representative spectral in the lens color input from the lens color input key 253 when the spectral characteristic information corresponding to the input product name is not included in the IOL spectral characteristic information 221. The characteristic information is selected from the lens color spectral characteristic information 223.

The correction coefficient calculation unit 232 calculates a correction coefficient in the correction process based on the spectral characteristic information selected by the spectral characteristic selection unit 231 and the human eye lens spectral characteristic information 222. The correction coefficient is a coefficient for correcting the selected spectral characteristic information (intensity ratio of each component of RGB in the IOL in the eye to be examined; see FIG. 7) to match the intensity ratio shown in the human eye lens spectral characteristic information 222. Information. For example, correction factors (K _R , K _G , K _B ) for adjusting the intensity ratio 37%: 35%: 28% in the IOL of the product name A to the intensity ratio 35%: 38%: 27% of the human eye lens are as follows: For example, K _R = 35 / 37≈0.946, K _G = 38 / 35≈1.086, and K _B = 27 / 28≈0.964.

The RGB correction processing unit 233 performs a process of correcting the color balance of the image captured by the imaging device 9 or the TV camera 10 based on the correction coefficients (K _R , K _G , K _B ) obtained by the correction coefficient calculation unit 232. Execute. That is, the RGB correction processing unit 233 corrects the captured image data 241 stored in the captured image storage unit 240 using the correction coefficient. Eg, RGB correction unit 233 multiplies the correction coefficient _{K R} to R image data 241R is a detected intensity of the R component, multiplied by a correction factor _{K G} to G image data 241G is a detected intensity of the G component, B by multiplying the correction coefficient K _B in the detection intensity of the component B image data 241B, performs color balance correction processing of the captured image.

[Mode of operation]
An example of the operation mode of the fundus camera 200 having the above configuration will be described.

  When the IOL is attached to the eye E to be observed and photographed by the fundus camera 200, the examiner operates the IOL mode setting key 251 of the control panel 3a. Upon receiving an input signal from the IOL mode setting key 251, the control unit 210 puts the color balance correction unit 230 into an operating state.

  Further, the examiner inputs the IOL product name in the eye E by operating the IOL product name input key 252. The input product name is recorded in, for example, a RAM (not shown). The product name is input by referring to a medical record, for example.

  When the IOL product name input key 252 does not include the product name of the IOL, the examiner operates the lens color input key 253 to input the lens color of the IOL. The input lens color is recorded in, for example, a RAM.

  The spectral characteristic information selection unit 231 selects spectral characteristic information corresponding to the product name input from the IOL product name input key 252 from the IOL spectral characteristic information 221. If there is no product name of the IOL, the spectral characteristic information selection unit 231 selects representative spectral characteristic information from the lens color spectral characteristic information 223 for the lens color input from the lens color input key 253.

The correction coefficient calculation unit 232 calculates correction coefficients (K _R , K _G , K _B ) based on the spectral characteristic information selected by the spectral characteristic information selection unit 231 and the spectral characteristic information of the human eye lens spectral characteristic information 222. To do. The calculated correction coefficients (K _R , K _G , K _B ) are recorded in, for example, a RAM.

  When the fundus image of the eye E is captured by the imaging device 9 or the television camera 10, the control unit 210 uses the captured image data 241 as image data (R image data 241R, G image data 241G, B image data 241B) is stored in the captured image storage unit 240.

RGB correction processing unit 233 changes the R image data 241R based on the correction coefficient _{K R} to change the G image data 241G based on the correction coefficient _{K G,} modify B image data 241B based on the correction coefficient _{K B} By doing so, the color balance of the photographed fundus image is corrected. The control unit 210 stores the corrected fundus image in the captured image storage unit 240 and displays the corrected fundus image on the monitor 11 or the like in response to a request from the examiner or the like.

[Action, effect]
According to the correction processing of the photographed image as described above, the intensity ratio of each component of RGB in the IOL is matched with the intensity ratio in the human eye lens simply by inputting the product name of the IOL attached to the eye E. Since the captured image is corrected, it is possible to easily acquire a fundus image having a hue close to that of the captured image for a normal eye.

  Even if the product name is not registered in the IOL spectral characteristic information 221, just by inputting the color of the lens body of the IOL, similarly, a fundus image having a hue close to a photographed image for a healthy eye can be obtained. Can be easily obtained.

  Therefore, according to the present embodiment, it is possible to obtain a photographed image close to the human eye lens regardless of the type of IOL. For example, a bleeding site or a lesion in the fundus shown in the fundus image Is clearly visible. Thereby, the state of the fundus of the eye E can be confirmed with high accuracy, and accurate and effective medical care can be performed.

[Modification]
In the second embodiment, a configuration in which a correction coefficient is calculated from the IOL stored in the correction information storage unit 220 and the spectral characteristic information of the human eye lens is applied. For example, it corresponds to various IOLs. A correction coefficient to be calculated is calculated in advance and stored in the correction information storage unit 220, and correction processing corresponding to the IOL product name and lens color input from the control panel 3a at the time of inspection is selected and corrected. It is also possible to configure. Thereby, the time required for the correction process can be shortened.

  The IOL spectral characteristic information 221 is formed by spectral characteristic information for each product. For example, a similar product may be grouped and spectral characteristic information may be given to each group.

  Although the present embodiment is configured to correct the color balance of the fundus image according to the type of IOL (product name), even if correction processing according to the type (identifier) of the IOL other than the product name is performed. Good.

  As an input mode using the IOL product name input key 252 and the lens color input key 253 of the control panel 3a, a configuration in which selection input is performed by using, for example, a pull-down menu can be employed in addition to the above method.

  As a correction coefficient calculation method and a correction method by the RGB correction processing unit 233, any method can be appropriately used.

  Data such as the IOL product name and lens color input at the time of correction may be stored together with the corrected fundus image. In addition, the input data can be displayed on the monitor 11 or the like together with the fundus image. Thereby, the type of the IOL can be confirmed, and the IOL through which the fundus image is captured can be confirmed.

  The correction coefficient used for the correction may be stored together with the captured image data so that it can be confirmed later what kind of correction processing has been performed. It is also possible to reversely convert the captured image data into the original data using the correction coefficient.

  As the image sensors 9a and 10a for detecting the fundus image, for example, an image sensor other than a CCD such as a CMOS sensor may be used.

  When the fundus camera 200 of this embodiment is connected to an electronic medical chart management system, the IOL product name and lens color can be automatically input from the subject's electronic medical chart.

<Third Embodiment>
A third embodiment of the ophthalmologic photographing apparatus (fundus camera) according to the present invention will be described. Similar to the second embodiment described above, the ophthalmic imaging apparatus according to the present embodiment reduces the influence of the IOL on the color balance of the captured image when the IOL is attached to the eye to be examined. It corrects to the hue of the photographed image with respect to the eye to be examined of the crystalline lens.

  In the second embodiment, the color balance of the photographed image is corrected based on the product name and lens color of the IOL input from the control panel 3a or the like. A characteristic is that the IOL image is taken, the spectral characteristics information of the crystalline lens is acquired by analyzing the image, and the captured image is corrected based on the spectral characteristics information.

  The ophthalmologic photographing apparatus of this embodiment has the same external configuration (see FIG. 1) and optical system (see FIG. 2) as those in the first and second embodiments. Hereinafter, components similar to those will be described using the reference numerals shown in FIGS. 1 and 2. In the present embodiment, the imaging device 9 and the television camera 10 using the primary color CCDs as the imaging elements 9a and 10a are used as in the second embodiment. Processing can be executed.

  FIG. 9 is a block diagram showing the configuration of the control system of the fundus camera 300 of this embodiment. The fundus camera 300 includes a control unit 310, an anterior eye image storage unit 320, a color balance correction unit 330, a captured image storage unit 340, and a correction information storage unit 350. In addition, the control panel 3a is provided with an IOL mode setting key 361 that is operated when the IOL is attached to the eye to be examined as an “input unit” of the present invention.

  Each of the imaging device 9 and the television camera 10 includes a primary color CCD as the imaging elements 9a and 10a, and decomposes the photographing light into R, G, and B components and detects the intensity of each component to detect the captured image. Form a color.

  Image data (captured image data 341) of the fundus image of the eye E to be inspected captured by the imaging device 9 or the television camera 10 is stored in a captured image storage unit 340 including an image storage device such as an image memory. The captured image data 341 is stored for each component as R image data 341R which is R component intensity information, G image data 341G which is G component intensity information, and B image data 341B which is B component intensity information.

  In addition, the anterior eye image data (anterior eye image data 321) of the anterior eye image of the eye E taken by the imaging device 9 or the television camera 10 is an anterior eye image storage unit 320 including an image storage device such as an image memory. Saved in. Like the captured image data 341, the anterior segment image data 321 includes R image data 321R that is R component intensity information, G image data 321G that is G component intensity information, and B image data that is B component intensity information. It is stored for each component as 321B. The anterior segment image to be photographed includes an IOL image (IOL image) attached to the eye E. Note that when an anterior segment image is captured, an enlarged image of the IOL may be captured.

  Similar to the control unit 210 of the second embodiment, the control unit 310 includes an arithmetic control device such as a CPU, and controls each part of the device by executing a computer program stored in a ROM, a hard disk drive, or the like. I do.

  The correction information storage unit 350 is composed of a nonvolatile storage device such as a ROM or a hard disk drive, and the intensity ratio of each component when the light produced by the human eye lens is decomposed into an R component, a G component, and a B component. Is stored in advance. The correction information storage unit 350 constitutes “storage means” of the present invention.

  Here, the human eye lens spectral characteristic information 222 in the second embodiment is information relating to light that is “transmitted” through the lens (that is, information related to the spectral transmittance). The crystalline lens characteristic information 351 is information relating to light “reflected” by the crystalline lens (that is, information related to spectral reflectance). Note that information regarding light scattering by the human eye lens may be reflected in the human eye lens spectral characteristic information 351.

  The color balance correction unit 330 is configured by an arithmetic control device such as a CPU that executes a predetermined computer program, and includes an anterior ocular segment image analysis unit 331, a correction coefficient calculation unit 332, and an RGB correction processing unit 333. The color balance correction unit 330 constitutes the “correction unit” of the present invention.

  The anterior ocular segment image analysis unit 331 corresponds to the “analyzing unit” in the present invention, and analyzes the anterior ocular segment image data 321 stored in the anterior ocular segment image storage unit 320 to obtain the anterior segment. Processing for acquiring spectral characteristic information of the IOL included in the image is performed. More specifically, the anterior ocular segment image analyzing unit 331 detects the anterior segment reflected light by the CCD of the imaging device 9 or the like, that is, the R image data 321R, G image data 321G, and B image data of the anterior segment image data 321. Based on the intensity of 321B, the intensity ratio of each component of RGB of the IOL image represented by the anterior segment image data 321 is acquired. Here, the IOL image is an image formed by detecting reflected light of illumination light in the IOL.

Based on the intensity ratio of each component of the IOL image acquired by the anterior segment image analysis unit 31 and the human eye lens spectral characteristic information 351, the correction factor calculation unit 332 has the same correction factor (as in the second embodiment) K _R , K _G , K _B ) are calculated. The correction coefficients K _R , K _G , and K _B are coefficient information that corrects the intensity ratio of the RGB components in the IOL image to match the intensity ratio in the human eye lens.

Similarly to the second embodiment, the RGB correction processing unit 333 performs shooting by the imaging device 9 or the television camera 10 based on the correction coefficients (K _R , K _G , K _B ) calculated by the correction coefficient calculation unit 332. A process for correcting the color balance of the image is executed. Eg, RGB correction unit 333 multiplies the correction coefficient _{K R} to R image data 341R is a detected intensity of the R component, multiplied by a correction factor _{K G} to G image data 341G is a detected intensity of the G component, B by multiplying the correction coefficient K _B in the detection intensity of the component B image data 341B, performs color balance correction processing of the captured image.

[Mode of operation]
An example of the operation mode of the fundus camera 300 having the above configuration will be described.

  When the IOL is mounted on the eye E to be observed and photographed by the fundus camera 300, the examiner operates the IOL mode setting key 361 on the control panel 3a. Upon receiving an input signal from the IOL mode setting key 361, the control unit 310 puts the color balance correction unit 330 into an operating state.

  The examiner operates the fundus camera 300 to capture an anterior eye image of the eye E with the imaging device 9 or the television camera 10. The anterior segment image data (anterior segment image data 321) taken by the control unit 310 is converted into image data for each component such as R image data 321R, G image data 321G, and B image data 321B. The image is stored in the image storage unit 320.

  The anterior segment image analysis unit 331 compares the intensities of the R image data 321R, the G image data 321G, and the B image data 321B of the anterior segment image data 321 stored in the anterior segment image storage unit 320. Then, the intensity ratio of each component of RGB in the IOL image attached to the eye E is calculated.

The correction coefficient calculation unit 232 calculates a correction coefficient (K) based on the intensity ratio of each component of RGB in the IOL image calculated by the anterior ocular segment image analysis unit 331 and the intensity ratio indicated in the human eye lens spectral characteristic information 351. _{R 1} , K _G , K _B ) are calculated. The calculated correction coefficients (K _R , K _G , K _B ) are recorded in, for example, a RAM.

  When the fundus image of the eye E is captured by the imaging device 9 or the television camera 10, the control unit 310 uses the captured image data 341 as image data (R image data 341R, G image data 341G, B image data 341B) is stored in the captured image storage unit 340.

RGB correction processing unit 333 changes the R image data 341R for the captured image data 341 based on the correction coefficient _{K R} to change the G image data 341G based on the correction coefficient _{K G,} based on the correction coefficient _{K B} B The color balance of the photographed fundus image is corrected by changing the image data 341B. The control unit 310 stores the corrected fundus image in the captured image storage unit 340 and displays the corrected fundus image on the monitor 11 or the like in response to a request from the examiner or the like.

[Action, effect]
According to the correction processing of the captured image as described above, the intensity ratio of each component of RGB in the IOL can be determined by simply photographing the anterior segment image (IOL image) of the eye E to which the IOL is mounted. Since the photographed image is corrected so as to match the intensity ratio at, it is possible to easily obtain a fundus image having a hue close to that of the photographed image for a normal eye. Further, since the correction is performed based on the spectral characteristic information of the IOL mounted on the eye E, the correction according to the actually mounted IOL can be performed.

[Variations]
The configuration described in detail in each of the above embodiments is merely an example of an ophthalmologic photographing apparatus according to the present invention, and can be appropriately modified within the scope of the gist of the present invention.

  For example, it can be configured to automatically determine whether or not to perform imaging in the IOL mode by analyzing an actually captured image. Further, an actual captured image is analyzed to determine whether or not an IOL is attached to the eye to be examined. When it is determined that the IOL is attached, image processing such as color correction is automatically performed on the captured image. It can also be configured to be applied.

  Further, when the fundus reflection image by the illumination light of visible light is received and the fundus is observed, it is possible to analyze the hue of the image and automatically switch to the IOL mode. Further, based on the analysis result such as the hue of the image, it is determined whether or not the eye to be inspected is wearing the IOL. The message such as “Please” may be displayed on a monitor or the like, and the examiner may confirm whether or not the IOL mode is necessary.

  Further, when the IOL mode is selected, a message or a mark indicating that may be displayed on a monitor or the like.

  In addition, when observing the fundus using infrared illumination light, visible light is emitted in advance (pre-emission), and the fundus reflection light is received by a separately provided detector, CCD, etc. It can also be configured to determine whether to set to the IOL mode by analysis.

1 is a schematic side view illustrating an example of an external configuration of a first embodiment of an ophthalmologic photographing apparatus according to the present invention. It is a schematic side view showing an example of a structure of the optical system of 1st Embodiment of the ophthalmologic imaging device which concerns on this invention. It is the schematic showing an example of the structure of the ring slit board contained in the illumination stop of the optical system of 1st Embodiment of the ophthalmologic imaging device which concerns on this invention. It is the schematic showing an example of a structure of the illumination stop of the optical system of 1st Embodiment of the ophthalmologic imaging device which concerns on this invention. FIG. 4A shows a configuration example of an iris diaphragm member included in the illumination diaphragm. FIG. 4B shows a configuration example of the lens diaphragm member included in the illumination diaphragm. It is a block diagram showing an example of the composition of the control system of a 1st embodiment of the ophthalmology photographing instrument concerning the present invention. It is a block diagram showing an example of a structure of the control system of 2nd Embodiment of the ophthalmologic imaging device which concerns on this invention. It is a conceptual diagram showing an example of the spectral characteristic information used for the correction process of the picked-up image by 2nd Embodiment of the ophthalmologic imaging device which concerns on this invention. It is a conceptual diagram showing an example of the spectral characteristic information used for the correction process of the picked-up image by 2nd Embodiment of the ophthalmologic imaging device which concerns on this invention. It is a block diagram showing an example of a structure of the control system of 3rd Embodiment of the ophthalmologic imaging device which concerns on this invention.

Explanation of symbols

1 Fundus camera (ophthalmologic imaging device)
3a Control panel 4 Joystick 4a Operation button 9 Imaging device 9a Imaging medium (imaging device)
DESCRIPTION OF SYMBOLS 10 Television camera 10a Image pick-up element 11 Monitor 30 Control part 31 IOL mode setting key 32a, 32b, 32c Pulse motor 33b, 33c Solenoid 100 Illumination optical system 101 Halogen lamp 103 Xenon lamp 107 Illumination diaphragm 107a Corneal diaphragm (ring slit board)
107b Iris diaphragm (ring slit plate)
107B Iris diaphragm member 107b-1 Iris diaphragm for normal eyes 107b-2 IOL iris diaphragm 107c Crystal diaphragm (ring slit plate)
107c-1 Lens stop for normal eye 107c-2 Lens stop for IOL Ra, Ra 'Peripheral shading part Rb, Rb' Center shading part Rs, Rs' Ring slit 120 Imaging optical system 200 Fundus camera 210 Control part 220 Correction information storage part 221 IOL spectral characteristic information 222 Human eye lens spectral characteristic information 223 Lens color spectral characteristic information 230 Color balance correction unit 231 Spectral characteristic information selection unit 232 Correction coefficient calculation unit 233 RGB correction processing unit 240 Captured image storage unit 241 Captured image data 241R R Image data 241G G image data 241B B image data 251 IOL mode setting key 252 IOL product name input key 253 Lens color input key 300 Fundus camera 310 Control unit 320 Anterior eye image storage unit 321 Anterior eye image data 321R R image data 321G G drawing Data 321B B image data 330 Color balance correction unit 331 Anterior eye image analysis unit 332 Correction coefficient calculation unit 333 RGB correction processing unit 340 Captured image storage unit 341 Captured image data 341R R image data 341G G image data 341B B image data 350 Correction Information storage unit 351 Human eye lens spectral characteristic information 361 IOL mode setting key E Eye to be examined Ef Fundus

Claims (17)

A light source that emits illumination light; and an outer diameter restricting unit that is disposed substantially conjugate to a pupil of the eye to be examined and restricts an outer diameter of a cross section of the illumination light, and is configured to receive the illumination light that has passed through the outer diameter restricting unit. An illumination optical system for irradiating the optometry;
A photographing optical system for photographing a fundus image by detecting fundus reflected light from the irradiated illumination light;
An ophthalmologic photographing apparatus comprising:
An outer diameter change for controlling the outer diameter limiting means to make the outer diameter of the illumination light irradiated to the eye to be examined wearing an intraocular lens smaller than the outer diameter of the illumination light for a healthy eye An ophthalmologic photographing apparatus characterized by comprising means. The illumination optical system further includes a central light shielding unit that is arranged substantially conjugate to the crystalline lens of the eye to be examined and shields a central region of the cross section of the illumination light, and is cross-sectionalized via the outer diameter limiting unit and the central light shielding unit. Irradiate the eye with the illumination light in a ring shape,
When the outer diameter of the illumination light having the ring-shaped cross section is changed to be smaller by the outer diameter changing means, the inner diameter of the cross section of the illumination light is made smaller than the inner diameter of the illumination light for healthy eyes. An inner diameter changing means for controlling the central light shielding means,
The ophthalmologic photographing apparatus according to claim 1. The outer diameter limiting means includes a diaphragm member in which a first light-transmitting portion and a second light-transmitting portion having a smaller diameter than the first light-transmitting portion are formed.
The outer diameter changing means is configured to arrange the second light transmitting portion on the optical axis of the illumination optical system when the illumination light is irradiated to the eye to be examined with an intraocular lens. Including drive means for driving
The ophthalmologic photographing apparatus according to claim 1, wherein the ophthalmologic photographing apparatus is provided. The central light shielding means includes a diaphragm member in which a first central light shielding part and a second central light shielding part having a diameter smaller than the first central light shielding part are formed,
The inner diameter changing unit is configured to arrange the second central light-shielding portion on the optical axis of the illumination optical system when the outer diameter of the illumination light is changed by the outer diameter changing unit. Including drive means for driving
The ophthalmologic photographing apparatus according to claim 2. Comprising input means for inputting that an intraocular lens is attached to the eye to be examined;
The outer diameter changing means controls the outer diameter limiting means when the input is made by the input means.
The ophthalmologic photographing apparatus according to any one of claims 1 to 4, wherein the ophthalmologic photographing apparatus is characterized.   When the outer diameter of the illumination light is changed to be smaller by the outer diameter changing means, the color balance of the fundus image taken by the photographing optical system is matched with the color balance of the fundus image taken for the normal eye. The ophthalmologic photographing apparatus according to any one of claims 1 to 5, further comprising correction means for correcting as described above. An ophthalmologic imaging apparatus comprising: an illumination optical system that irradiates illumination light to an eye to be examined; and an imaging optical system that includes an imaging unit that detects fundus reflection light by the illumination light and captures a fundus image;
Correction so that the color balance of the fundus image taken by the imaging means when the intraocular lens is attached to the eye to be examined matches the color balance of the photographed fundus image for the eye to be examined having a human eye lens An ophthalmologic photographing apparatus comprising correction means for performing Comprising input means for inputting that an intraocular lens is attached to the eye to be examined;
The correction means corrects the color balance of the photographed fundus image in response to the input by the input means;
The ophthalmologic photographing apparatus according to claim 7. Storage means for storing spectral characteristic information of a plurality of types of intraocular lenses in advance;
Type input means for inputting the type of intraocular lens;
Further comprising
The correction unit selects the spectral characteristic information corresponding to the input type of intraocular lens from the storage unit, and calculates the color balance of the photographed fundus image based on the selected spectral characteristic information. to correct,
The ophthalmologic photographing apparatus according to claim 7 or 8, characterized by the above. The spectral characteristic information is an intensity ratio of each reference color component when the light transmitted through the intraocular lens is separated into a plurality of reference colors,
The storage means stores in advance the intensity ratio of each reference color component of light transmitted through the human eye lens,
The imaging means includes an imaging device that detects the intensity of each reference color component by decomposing the fundus reflected light into the plurality of reference colors,
The correction means changes the intensity of each reference color component detected by the imaging device based on the intensity ratio of the selected intraocular lens and the intensity ratio of the human eye lens, Correcting the color balance of the photographed fundus image,
The ophthalmologic photographing apparatus according to claim 9. The spectral characteristic information matches the intensity ratio of each reference color component when the light transmitted through the intraocular lens is separated into a plurality of reference colors to the intensity ratio of each reference color component of the light transmitted through the human eye lens. Correction factor for
The imaging means includes an imaging device that detects the intensity of each reference color component by decomposing the fundus reflected light into the plurality of reference colors,
The correction means corrects the color balance of the photographed fundus image by changing the intensity of each reference color component detected by the image sensor with the correction coefficient.
The ophthalmologic photographing apparatus according to claim 9. The storage means stores in advance spectral characteristic information corresponding to the lens color of the intraocular lens,
A lens color input means for inputting the lens color of the intraocular lens;
The correction unit selects spectral characteristic information corresponding to the lens color of the input intraocular lens from the storage unit, and corrects the color balance of the photographed fundus image based on the selected spectral characteristic information. To
The ophthalmologic photographing apparatus according to any one of claims 9 to 11, wherein the ophthalmologic photographing apparatus is characterized.   The ophthalmologic photographing apparatus according to any one of claims 7 to 12, wherein the type of the intraocular lens is a product name of the intraocular lens. The imaging means of the imaging optical system detects an anterior ocular segment reflected light by the illumination light, and captures an image of an intraocular lens attached to the eye to be examined,
The correction unit includes an analysis unit that analyzes the captured image of the intraocular lens and acquires spectral characteristic information of the intraocular lens, and the captured fundus is based on the acquired spectral characteristic information Correct the color balance of the image,
The ophthalmologic photographing apparatus according to claim 7 or 8, characterized by the above. The imaging means includes an imaging device that detects the intensity of each reference color component by separating each of the anterior ocular segment reflected light and the fundus reflected light into a plurality of reference colors,
The analysis means acquires, as the spectral characteristic information, an intensity ratio of each reference color component based on a detection result of the anterior segment reflection light by the imaging device,
Storage means for storing in advance the intensity ratio of each reference color component of light reflected by the human eye lens;
The correction unit is configured to adjust the intensity of each reference color component of the fundus reflected light detected by the imaging device so that the intensity ratio of the acquired intraocular lens matches the intensity ratio of the human eye lens. By correcting the color balance of the photographed fundus image,
The ophthalmologic photographing apparatus according to claim 14.   The ophthalmologic photographing apparatus according to claim 10, wherein the plurality of reference colors are RGB. The ophthalmologic photographing apparatus according to claim 10, wherein the image pickup device of the image pickup unit is a CCD.

Images