JP4889030B2 - Image processing device - Google Patents

Description

  The present invention relates to an image processing device, and more particularly to an image processing device that performs stereo imaging of a subject's eye fundus with a predetermined parallax via a fundus imaging optical system and performs three-dimensional shape measurement processing using the obtained parallax image. .

  2. Description of the Related Art Conventionally, for the purpose of diagnosing glaucoma, an image processing apparatus such as a fundus camera that captures a three-dimensional image of the fundus of the eye to be examined is known in order to grasp the shape of the fundus of the eye to be examined. For example, there is a device that stereo-photographs the fundus of the eye to be examined by moving the diaphragm in a single optical system of the fundus camera to different positions that are decentered from the optical axis to the left and right (or up and down). Known (Patent Document 1 below).

Image processing for three-dimensional measurement of the fundus can be performed as follows. For example, pattern matching is performed on left and right (or top and bottom) images taken in stereo to search for corresponding image points, that is, corresponding points. If the corresponding points can be searched, each of the object points conjugated with the corresponding points using the principle of triangulation along the xy axes (two orthogonal axes parallel to the image plane) and the z axis (one axis parallel to the optical axis). Coordinates can be calculated. If a three-dimensional coordinate value of a sufficient number of object points is obtained, a three-dimensional model of the fundus of the eye to be examined can be created.
JP-A-10-75932 JP 2002-34924 A

  Incidentally, an optical system of a photographing apparatus such as a fundus camera has image distortion. For example, when a grid pattern such as graph paper placed on a plane is captured, an image such as reference numeral 151 in FIG. 5 is captured. This distortion includes distortion that is caused by a manufacturing error that occurs in each optical system, in addition to distortion that is preliminarily designed in the optical system.

  If stereo imaging and three-dimensional measurement image processing as described above are performed with an optical system having such image distortion, the z-axis coordinates obtained on the P-P ′ line, for example, are square patterns placed on a plane. Even if it should be measured linearly as indicated by reference numeral 152, there is a possibility of deformation as indicated by reference numeral 153.

  Generally, in the three-dimensional measurement using a stereo image, it is necessary to correct the image distortion as described above, and there is a possibility that a three-dimensional shape different from the actual condition of the subject may be measured without correction. In view of this point, a configuration is used in which image data is affine transformed using parameters corresponding to the distortion of the optical system estimated in advance. In addition, in the case of fundus photography, there is also known a configuration in which a stereo photographed image is corrected on the assumption that the fundus is an ideal spherical surface in advance (Patent Document 2 described above).

  However, it is difficult to say that such conventional correction processing accurately reflects the characteristics of the optical system actually used for photographing, and there is a high possibility that some error will occur in the three-dimensional measurement result of the fundus. In clinical applications such as fundus retinal shape analysis and optic nerve head shape analysis, depending on the degree of error, there is a risk of misdiagnosis, and image processing that can accurately correct optical distortion from stereo images is required. Yes.

  For example, in the case of a grid pattern placed on the plane of FIG. 5, it is desired that a shape that is distorted and measured as indicated by reference numeral 153 on the P-P ′ line can be accurately corrected as indicated by reference numeral 154.

  In view of the above problems, an object of the present invention is to provide a distortion of an optical system that is actually used for photographing in an image processing apparatus that performs stereo photographing of the fundus of the eye to be examined and performs three-dimensional measurement processing on the obtained photographing image data. Therefore, it is possible to perform accurate three-dimensional measurement processing on the fundus image so that the three-dimensional shape of the fundus to be examined can be accurately evaluated.

In order to solve the above problems, in the present invention, in an image processing apparatus that performs stereo imaging of a subject's eye fundus with a predetermined parallax via a fundus imaging optical system, and performs a three-dimensional shape measurement process using the obtained parallax image Obtained by simulating the shape and optical characteristics of the human eye and taking a stereo image of the model eye having the fundus simulating surface provided with a predetermined shading pattern as a predetermined part with the predetermined parallax through the fundus imaging optical system. and the three-dimensional shape of the predetermined region is measured based on the image data of the parallax image, corresponding to the difference of the actual three-dimensional shape of the predetermined region, the three-dimensional shape of said measured predetermined portion based on the image data and, wherein is represented by the amount of parallax or depth quantity calculated based on the parallax amount of the parallax images to be corrected in the three-dimensional shape measurement process of the fundus, the fundus photographing optical Create a calibration data used for correcting the shape distortion resulting from, subjected to shape distortion correction on the three-dimensional shape data obtained by the stereo imaging of the fundus by using the calibration data, the three-dimensional shape A configuration for performing measurement processing was adopted.

  According to the above configuration, in the image processing apparatus that performs the three-dimensional measurement process on the obtained fundus image data in stereo through the stereo imaging optical system, the optical system actually used for imaging is used. There is an excellent effect that distortion can be corrected, accurate three-dimensional measurement processing can be performed on the fundus image, the three-dimensional shape of the fundus can be accurately evaluated, and problems such as misdiagnosis can be avoided.

  Further, by using a model eye that simulates the shape and optical structure of the eye to be examined, calibration measurement and calculation can be easily performed without changing other imaging conditions and calculation conditions.

  Hereinafter, as an example of the best mode for carrying out the present invention, an implementation relating to a fundus camera that performs a three-dimensional measurement process on the obtained photographed image data by photographing the fundus oculi to be examined in stereo via a stereo photographing optical system. An example will be described.

  In the fundus camera 10 illustrated in FIG. 1 surrounded by a one-dot chain line, an observation lamp 11 that emits infrared light and visible illumination light is disposed at the center of curvature of the spherical mirror 12. The light from the mirror 12 is incident on the total reflection mirror 17 through the condenser lens 14, the strobe 15 that is a photographing light source, and the condenser lens 16.

  The illumination light reflected by the total reflection mirror 17 passes through the relay lens 22 through the illumination diaphragm 19, is reflected by the perforated total reflection mirror 23, and passes through the objective lens 24 to the anterior eye part (pupil) Ep of the eye E to be examined. Incident. The illumination stop 19 is disposed in a position substantially conjugate with the anterior segment Ep (pupil) of the eye to be examined in the illumination optical system.

  The reflected light from the fundus Er illuminated with the illumination light is transmitted through the objective lens 24, the aperture 23a of the perforated total reflection mirror 23, the aperture of the 2 aperture aperture stop (2 aperture aperture) 28, the focusing lens 35, and the imaging lens 36. Then, the light passes through the zoom lens 38a and enters the return mirror 39. At the position where the return mirror 39 is shown, the reflected light from the fundus is incident on a CCD (imaging means) 40 at a position conjugate with the fundus sensitive to infrared light, the fundus is imaged by the CCD 40, and the return mirror 39 Is separated from the optical path, the reflected light from the fundus enters the CCD (imaging means) 41 conjugate with the fundus sensitive to visible light, and the fundus is photographed by the CCD 41.

  The photographing aperture 28 is provided with two rectangular openings 28a and 28b as shown in FIG. The photographing aperture 28 is disposed such that the openings 28a and 28b are decentered with respect to the optical axis 26 and are symmetric with respect to the optical axis 26, and are substantially conjugate with the anterior eye portion (pupil) of the eye to be examined. .

  The positions and sizes of the openings 28a and 28b are set so that the opening 23a of the perforated total reflection mirror 23 includes the entire openings 28a and 28b.

  The apertures 28a and 28b of the photographing aperture 28 are opened or closed by shutter plates 29 and 30 moved along guides 28c and 28d, respectively.

  For this opening and closing, switching means comprising rotary solenoids 31 and 32 is provided. When the rotary solenoids 31 and 32 are not energized, the shutter plates 29 and 30 are at the position of FIG. , 28b are opened.

  On the other hand, when the rotary solenoids 31 and 32 are energized, the rods 31a and 32a of the rotary solenoids 31 and 32 rotate, and the other ends of the rods 31a and 32a are connected to pins 29a and 30a provided on the shutter plates 29 and 30, respectively. Engagement causes the shutter plates 29 and 30 to move inward to close the openings 28a and 28b.

  The fundus image captured by the CCD 40 is input to a control calculation unit 60 constituted by a CPU or the like, and the image is displayed on the monitor 62 as a moving image. The examiner looks at the image displayed on the monitor 62 and can perform operations such as alignment and focus adjustment as will be described later. In addition, a stereo monitor 63 is provided as a stereoscopic display, and the examiner can observe the fundus in a stereoscopic manner by observing the left and right images through the stereo monitor 63.

  Further, the fundus illuminated by the strobe 15 when the shutter switch 66 is operated can be photographed as a still image by the CCD 41. This fundus image is temporarily stored in the high-speed memory 61 and recorded on a recording means realized by a low-speed hard disk (HDD) 64 as an external recording device via the control calculation unit 60, or a monitor 62 and a stereo monitor 63. Is displayed.

  Also, input means such as a keyboard 67 and a mouse 68 are provided, and various data can be input via these input means.

  Further, the fundus camera is provided with a control unit 65 composed of a CPU or the like. The control unit 65 is connected to the control calculation unit 60 and exchanges signals with each other. When the shutter switch 66 is operated, the control unit 65 returns. The mirror 39 is removed from the optical path, and the strobe 15 is caused to emit light with an appropriate amount of light. The control unit 65 controls insertion / removal of the variable magnification lens 38a and the like into the optical path, and controls driving of the rotary solenoids 31 and 32 described above.

  In addition, the fundus camera is provided with an operation unit (operation panel) 69, and the operation unit 69 can select a photographing mode. Further, a left / right eye detection unit 70 that detects whether the subject eye to be photographed is the left eye or the right eye is provided, and information on whether the detected left eye or right eye is detected is input to the control unit 65.

  Here, an outline of stereo imaging of the fundus of the eye to be examined in the above configuration will be described.

  First, at the time of observation, the observation lamp 11 is turned on, and the illumination stop 19 is inserted into the optical path. The rotary solenoids 31 and 32 are driven to the positions shown in FIG. 2A, whereby the two openings 28a and 28b of the photographing aperture 28 are in the open positions. Reflected light from the fundus of the subject's eye irradiated with non-infrared light through the illumination diaphragm 19 is received by the observation CCD 40 through the openings 28a and 28b of the imaging diaphragm 28, and the fundus image is displayed on the monitor 62. The

  In this state, alignment and focusing with the eye to be examined are performed. At this time, alignment and focusing operations of the examiner are supported by a target projection system (not shown).

  When the shutter operation is completed after the alignment and focusing, the examiner presses the shutter switch 66. In response to this operation, the control unit 65 drives the rotary solenoid 31 to move the shutter plate 29 to the right, and closes the opening 28a on the left side of the photographing aperture 28. The strobe 15 emits light in synchronization with the operation of the shutter switch 66, and the return mirror 39 leaves the optical path, so that the light flux from the fundus illuminated by the strobe passes through the opening 28b of the photographing aperture 28 that is open. The light enters the image receiving surface of the CCD 41, and the first fundus image for stereoscopic viewing is captured as a still image by the CCD 41 and stored in the memory 61.

  Subsequently, the rotary solenoids 31 and 32 are controlled to move the shutter plates 29 and 30 to the left, and when the opening 28a is opened and the opening 28b is closed, the strobe 15 is caused to emit light again. At this time, the second fundus image for stereoscopic viewing that has passed through the opening 28 a is captured as a still image by the CCD 41 and stored in the memory 61.

  In this way, two parallax images photographed from two left and right viewpoints in succession by one shutter operation, that is, stereo photography, are the positions of the aperture of the photographing aperture that is open, the left position, and the right position. And the like are added to the HDD 64 from the memory 61. The two parallax images stored in this way are read from the HDD 64 and displayed using the stereo monitor 63, and the examiner observes one corresponding fundus image with the left and right eyes. The fundus can be viewed stereoscopically.

  Here, before describing the calibration process according to the present invention, an outline of a process for three-dimensionally measuring the three-dimensional shape of the fundus of the eye to be examined from the left and right parallax images taken in stereo as described above will be described.

  FIG. 6 shows an outline of this fundus three-dimensional measurement process. In step S161 in FIG. 6, the fundus of the eye to be examined is photographed in stereo as described above.

  Subsequently, a parallax amount calculation process between the left and right parallax images taken in stereo is performed in step S162. This parallax amount calculation processing is as follows.

  First, a region of interest of 15 × 15 pixels is set in the left parallax image with the focus point for obtaining the parallax amount as the center (FIGS. 7A and 7B). Then, a region having the highest correlation with the region of interest (15 × 15 pixels: FIG. 7C) of the left parallax image is searched from the right parallax image (FIG. 7D).

  At this time, since it takes a calculation time to search from the entire image, the search area is limited to 20 × 20 pixels. That is, the search is performed in the range of 20 × 20 pixels in the right parallax image with the point for obtaining the parallax amount of the left parallax image as the center.

  The attention points for obtaining the amount of parallax are all points in the left parallax image, and an area having the highest correlation in the right parallax image is searched for each point, but instead of searching for each pixel, for example, four pixels The search may be performed with a certain interval.

  Then, the position shift of the region in the right parallax image having the highest correlation with the region of interest in the left parallax image is obtained as parallax (number of parallax pixels). In this way, one amount of parallax is calculated for each attention point.

  Through the above processing, it is possible to obtain the number of parallax pixels of a specific pixel or a specific part, that is, how many pixels the specific pixel or the specific part is imaged in the left and right parallax images.

  If the conditions of the magnification (or shooting distance) of the optical system are recorded, the number of parallax pixels on a specific pixel or specific part on the shooting screen is converted into the actual amount of parallax on the retina (fundus) can do.

  If the actual amount of parallax on the retina (fundus) of a specific pixel or a specific part is obtained, the depth of the specific pixel or the specific part (or the coordinate value in the z-axis direction parallel to the optical axis) is obtained. It can be obtained as follows (S163 in FIG. 6).

Here, in specific imaging, the parallax angle determined by the imaging distance and the positions of the stops 28a and 28b is 8 degrees, and the parallax amount on the fundus of a specific site is set to 0. 0 by the above calculation (S162). When calculated as 1 mm, the depth of the specific part (depth or coordinates in the z-axis direction) is calculated from this parallax amount using the principle of triangulation as shown in FIG.
Depth amount = (parallax amount / 2) / tan (parallax angle / 2) (Formula 1)
Is calculated to be 0.715 mm (relative amount from a part having a parallax amount of 0).

  In the case of a fundus camera, since the shooting distance is adjusted to a specific working distance by alignment before shooting, the parallax angle (8 degrees in the above example) determined by the positions of the stops 28a and 28b is assumed to be constant. A three-dimensional measurement process can be performed.

  Now, the imaging optical system of the fundus camera in FIG. 1, that is, the objective lens 24... Variable magnification lens 38a has the image distortion as shown in FIG. to be influenced.

  Therefore, in this embodiment, a subject having a predetermined shape, in particular, a model eye 300 as shown in FIG. 3 is photographed in stereo, and an inherent shape distortion caused by the optical system of the fundus camera is calculated in advance. The image data used for the three-dimensional measurement shown in FIGS. 6 to 8 is corrected.

  The model eye 300 is created in a shape that simulates (simulates) the optical characteristics of the human eye as shown in FIG. For example, the model eye 300 is created by a technique such as cutting and polishing optical glass having a refractive index n = 1.52. The curvature of the cornea simulated surface (incident surface) 302 is a spherical surface of about R7.7 mm, and the curvature of the simulated retina surface 301 corresponding to the retina is a spherical surface of about R15 mm. The distance between these two surfaces is about 22.6 mm, for example.

  In the later-described calibration imaging, a fundus simulating surface that simulates the fundus of the model eye 300 is imaged as a predetermined part for acquiring calibration data. More specifically, this fundus simulating surface is configured as a surface 301 that simulates the retina in the model eye 300 of this embodiment. The surface 301 simulating the retina is processed into a three-sided (semi-transparent) surface, and a certain shade pattern (for example, a square pattern or the like) is given by a technique such as engraving + coloring or printing. It should be noted that when creating calibration data, which will be described later, a specific pattern may be set to a specific color so as to facilitate processing.

  The model eye 300 is attached to and detached from the chin rest 310 of the fundus camera of FIG. 1 through a jig 311 calibrated to a predetermined shape as a mounting member (for example, using a structure such as latch coupling or screwing). It is convenient to configure the optical system so that it is positioned at substantially the same position as the (ideal) position of the eye E when mounted.

  Using the above model eye 300, calibration data for correcting image data used for three-dimensional measurement can be acquired as follows at any timing before or after shipment of the fundus camera of FIG. it can.

  First, the model eye 300 is positioned at substantially the same position as the (ideal) position of the eye E using the jig 311 as described above, and right and left parallax images are captured as described above.

  The photographing distance and the magnification are also controlled so as to be constant values for the calibration process. For this reason, it is convenient to provide a notch in the position of the optical system, the variable magnification ring (dial), etc. so that the photographing distance and magnification for calibration processing can be easily selected.

  In this embodiment, the calibration data can be obtained by photographing the model eye 300 and calculating the three-dimensional shape as described above. When photographing is performed under different photographing magnification conditions by the magnification lens 38a of the fundus camera, calibration data is obtained for each magnification condition.

  As shown in FIG. 10A, the calibration data includes a three-dimensional shape (curve of depth information (z coordinate)) 1002 obtained by photographing the model eye 300, and a shape 1001 of the actual model eye 300. This is equivalent to the difference 1003.

  In FIG. 10A, the three-dimensional shape 1002 obtained by photographing the model eye 300 is affected by image distortion, and the fundus shape of the model eye 300 must be obtained as 1001 originally. . Here, for ease of explanation, the fundus shape 1001 of the model eye 300 is illustrated in a substantially flat shape.

  The calibration data of the present embodiment is recorded with the expression of the difference 1003 in the depth amount (coordinate in the z-axis direction) as shown in FIG. 10A, or by the measurement of the above three-dimensional shape. It can be expressed by the difference in the amount of parallax used (if the amount of parallax is determined, the depth amount is uniquely determined as apparent from the above equation 1).

  The calibration data can be used to correct the three-dimensional shape of the fundus obtained by actually photographing the eye to be examined to obtain the three-dimensional shape of the fundus of the actual eye to be examined.

  For example, as shown in FIG. 10B, when the shape 1004 (depth information (z coordinate) curve) of the fundus of the eye to be examined is measured, the calibration data expressing the difference 1003 is applied to act as shown in FIG. The fundus shape 1005 of the eye to be examined can be corrected as in c) (the fundus shape 1005 of the eye to be examined is shown in a substantially flat shape for the sake of easy explanation).

  The calibration data obtained as described above can be recorded in an HDD or a non-volatile memory in a table format.

  For example, in the case of calibration data representing a depth amount (coordinate in the z-axis direction), since it is applied after obtaining the captured image depth amount (coordinate in the z-axis direction) by the above three-dimensional measurement process, the three-dimensional The shape data is recorded in association with the abscissa (xy coordinate or polar coordinate expression from the image center (optical axis)). Then, if calibration data is read from the table using the abscissa of the predetermined part in the fundus shape data and applied, the corrected depth amount (coordinate in the z-axis direction) of the part can be obtained.

  In addition, when the calibration data is a representation of the amount of parallax used in the measurement of the three-dimensional shape, the parallax amount measurement processing is performed with attention points at specific intervals in the parallax image (about 4 pixels in the above example). Therefore, the calibration data representing the parallax amount may be recorded in a table format for each point of interest. Then, at the stage of the parallax amount calculation process (step S162) in FIG. 6, based on the attention point (point number or pixel address) being processed, the table data is referred to, the calibration data representing the parallax amount expression is read, and the depth amount What is necessary is just to apply to the amount of parallax used for calculation (step S163).

  By using the calibration data having the table configuration as described above, it is possible to perform image distortion correction at a high speed with an extremely small calculation load.

  FIG. 9 shows a flow of the above-described shape distortion correction and actual fundus stereo photography.

  Steps S901 and S902 in FIG. 9 show calibration imaging and calibration data acquisition processing performed at any timing before or after shipment of the fundus camera in FIG.

  In step S901, the model eye 300 is photographed in stereo as described above, and in step S902, calibration data is obtained as described above.

  That is, in step S902, the amount of parallax is calculated for each point of interest from the left and right parallax images of the model eye 300, and the shape data of the model eye 300 (1002 in FIG. 10A) is obtained. Since the fundus shape of the model eye 300 (1001 in FIG. 10A) is known, calibration data can be acquired as the difference between them (representation by the depth or parallax described above). The acquired calibration data is recorded in the HDD or nonvolatile memory as described above.

  Thereafter, in step S161 and subsequent steps, actual fundus stereo photography is performed. Steps S161, S162 ′, and S163 ′ in FIG. 9 are substantially the same as the stereo shooting (S161), parallax pixel number measurement (S162), and depth amount calculation (S163) in FIG. In S162 ′ or S163 ′, correction processing is performed using the calibration data recorded in the table format as described above.

  That is, when the calibration data is expressed by the amount of parallax as described above, correction is performed at the stage of measuring the number of parallax pixels in step S162. Alternatively, when the calibration data is expressed by a depth amount, correction is performed at the depth amount calculation stage in step S163.

  In this way, it is possible to accurately measure the number of parallax pixels and calculate the depth amount in steps S162 and S163 after applying the shape distortion correction inherent to the optical system to the left and right captured images.

  As described above, according to the present embodiment, in the image processing apparatus that performs the three-dimensional measurement processing on the obtained photographed image data by actually photographing the fundus of the eye to be examined through the stereo photographing optical system. It is possible to correct distortion of the optical system used for photographing, perform accurate three-dimensional measurement processing on the fundus image, accurately evaluate the three-dimensional shape of the fundus of the eye to be examined, and avoid problems such as misdiagnosis.

  For example, in the case of the fundus image 141 as shown in FIG. 4, by performing the correction as described above, a three-dimensional shape that accurately reflects the shape of the nipple portion 143 on the line P-P ′ is represented by depth information. (Z-axis coordinate value).

  Note that the subject to be stereo-photographed to obtain the calibration data may theoretically be a subject such as graph paper. However, by using a model eye that simulates the shape and optical structure of the eye to be examined as in the above embodiment, calibration measurement and calculation can be easily performed without changing other imaging conditions and calculation conditions.

  Further, by providing a model eye wearing adapter such as the jig 311 described above, calibration measurement and calculation can be easily performed, and the model eye, the jig 311, the model eye wearing adapter, etc. This product can be supplied and sold to users and maintenance companies as calibration kits and expansion parts.

  The present invention can be implemented in an image processing apparatus such as a fundus camera that performs stereo imaging of the fundus of a subject to be examined through a stereo imaging optical system and performs three-dimensional measurement processing on the obtained captured image data.

It is explanatory drawing which showed the structure of the retinal camera as an image processing apparatus which employ | adopted this invention. It is explanatory drawing which showed the structure around the imaging | photography diaphragm of FIG. It is explanatory drawing which showed the model eye used in the apparatus of FIG. It is explanatory drawing which showed the three-dimensional shape measurement result of the fundus oculi obtained in the apparatus of FIG. It is explanatory drawing which showed the problem of the image distortion in the conventional stereo photography. It is the flowchart figure which showed the stereo imaging | photography process and three-dimensional measurement process in the apparatus of FIG. It is explanatory drawing which showed the mode of the parallax amount measurement process in the apparatus of FIG. It is explanatory drawing which showed the mode of depth amount (z-axis coordinate) measurement in the apparatus of FIG. It is the flowchart figure which showed the calibration and imaging | photography process used in the apparatus of FIG. It is explanatory drawing which showed the calibration process used in the apparatus of FIG.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 Fundus camera 24 Objective lens 28 Imaging stop 28a, 28b Aperture 300 Model eye 301 Retina simulation surface 302 Cornea simulation surface 311 Jig

Claims (4)

In an image processing apparatus that performs stereo imaging of the fundus of a subject's eye with a predetermined parallax via a fundus imaging optical system and performs a three-dimensional shape measurement process using the obtained parallax image.
Obtained by simulating the shape and optical characteristics of the human eye and taking a stereo image of the model eye having the fundus simulating surface provided with a predetermined shading pattern as a predetermined portion with the predetermined parallax through the fundus imaging optical system the three-dimensional shape of the predetermined region is measured based on the image data of the parallax image,
The parallax image corresponding to the difference between the actual three-dimensional shape of the predetermined part and the three-dimensional shape of the predetermined part measured based on the image data, and to be corrected in the three-dimensional shape measurement process of the fundus oculi to be examined A calibration data that is expressed by a parallax amount or a depth amount calculated based on the parallax amount and used to correct a shape distortion caused by the fundus photographing optical system,
An image processing apparatus that performs shape distortion correction on three-dimensional shape data obtained by stereo imaging of the fundus of the eye to be examined using the calibration data, and performs the three-dimensional shape measurement process. The image processing apparatus according to claim 1 , wherein the calibration data is created for each zooming condition of the fundus photographing optical system. The image processing apparatus according to claim 1 , wherein the calibration data is generated in a table format in association with an abscissa of three-dimensional shape data or a specific part in a parallax image that is stereo-photographed by the fundus imaging optical system. An image processing apparatus. The image processing apparatus according to claim 1 , further comprising a mounting member that positions the model eye at a position substantially the same as a position of the eye to be examined with respect to the fundus photographing optical system.

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