JP6701250B2 - Ophthalmic photographing apparatus, control method thereof, and program - Google Patents

Description

  The present invention relates to a technique for acquiring an image of an eye to be inspected.

  Currently, various ophthalmologic apparatuses using optical devices such as an anterior segment imaging apparatus, a fundus camera, and a confocal laser scanning ophthalmoscope (SLO) are used. Among them, an optical tomographic imaging apparatus (hereinafter referred to as an OCT apparatus) by optical coherence tomography (OCT) using multi-wavelength light wave interference can obtain tomographic image data of a sample with high resolution, It is becoming an indispensable ophthalmologic device in the retinal outpatient department.

  Patent Document 1 discloses a technique capable of displaying fundus surface image data showing the surface of the fundus and fundus tomographic image data showing the tomography of the fundus side by side.

JP 2008-154704 A

  Usually, when capturing fundus tomographic image data, the lesion site of the eye to be examined is confirmed by the fundus surface image data, and the lesion region distributed in a narrower range than the imaging range of the fundus surface image is targeted to the fundus tomographic image data. Image. That is, normally, the fundus tomographic image is captured as an image of a photographing range narrower than the photographing range of the fundus surface image (fundus image). However, since the resolution of the OCT device is being increased, the technique disclosed in Patent Document 1 does not consider the display magnification when observing the fundus surface image data. Therefore, when targeting a small lesion site, if the display magnification of the fundus surface image data is fixed, it is difficult to determine the lesion site, and the position of the fundus tomographic image data to be imaged cannot be easily determined. As a result, there is a problem that it takes a long time to image the fundus tomographic image data and it is necessary to re-acquire the fundus tomographic image data, which places a burden on the subject.

  Therefore, one of the objects of the present invention is to enable the setting of the position of the image of the fundus of the eye to be imaged to be easily and accurately executed using the fundus surface image (fundus image).

One of the ophthalmologic imaging apparatus of the present invention is a projection optical system that projects light to each position of the fundus of the eye to be examined, and from a fundus emitted from each position of the fundus with light from the projection optical system. Image pickup optical system having a light-receiving optical system for receiving the above light by a light-receiving element, and a fundus image is generated based on a light-receiving signal from the light-receiving element, and a first moving image including a plurality of continuous fundus images is displayed on the display means. To generate a partial image in which a part of the fundus image is extracted, display a second moving image composed of a plurality of continuous partial images together with the first moving image on the display unit, characterized in that it comprises display control means for displaying on said display means in a state of overlapping a display form indicating a position of the tomographic image indicating the fault before Symbol subfractions image, a.
In addition, one of the other aspects of the ophthalmologic imaging apparatus of the present invention is a projection optical system that projects light to each position of the fundus of the eye to be inspected, and each of the fundus associated with the light from the projection optical system. La an imaging optical system, the corresponding partial image area of interest included in the fundus image image to be photographed by using the photographing optical system having a light receiving optical system, for receiving light from the fundus emitted from the position in the light receiving element as Eve image, to be displayed together with the fundus image on the display means, display control means for displaying on said display means in a state of overlapping the display mode before Symbol subfractions image showing the position of the tomographic image indicating the fault of said fundus , Are provided.

  According to one aspect of the present invention, the setting of the position of the fundus image of the subject's eye to be imaged can be easily and accurately executed using the fundus surface image (fundus image).

It is a figure which shows the structure of the ophthalmologic apparatus which concerns on embodiment of this invention. It is a figure which shows the example of a screen displayed in the ophthalmologic apparatus which concerns on embodiment of this invention. 6 is a flowchart showing a process of capturing fundus tomographic image data by the ophthalmologic apparatus according to the embodiment of the present invention.

  Hereinafter, preferred embodiments to which the present invention is applied will be described in detail with reference to the accompanying drawings.

<Structure of ophthalmic device>
FIG. 1 is a diagram showing a configuration of an ophthalmologic apparatus according to an embodiment of the present invention. That is, FIG. 1A shows the external configuration of the ophthalmologic apparatus according to the present embodiment, and FIG. 1B shows the internal configuration of the optical head and the base portion of the ophthalmologic apparatus according to the present embodiment. There is. The ophthalmologic apparatus shown in FIG. 1 has an exemplary configuration of a control system.

  In FIG. 1A, 100 is an ophthalmologic apparatus. An optical head 1000 is a measurement optical system for capturing anterior ocular segment surface image data showing the surface of the anterior segment of the eye, ocular fundus surface image data showing the surface of the ocular fundus, and ocular fundus tomographic image data showing the ocular fundus. Is. Reference numeral 1002 denotes a stage unit that moves the optical head 1000 in the xyz directions of FIG. 1A using a motor (not shown). Reference numeral 1001 denotes a base unit that incorporates a spectroscope described later.

  A computer 1003 controls the movement processing of the optical head 1000 by the stage unit 1002 and the imaging processing of the fundus tomographic image data. Reference numeral 1004 denotes a hard disk that is built in the computer 1003 and stores a subject information, a program for capturing fundus tomographic image data, and the like. A monitor 1005 is a display unit. An input unit 1006 is used by the examiner to give an instruction to the computer 1003, and specifically includes a keyboard and a mouse. Reference numeral 1007 denotes a chin rest, which is an external fixation lamp for fixing the subject's eye (subject's eye) by fixing the subject's chin and forehead, in order to fix the subject's eye. Used for. The computer 1003 is an example of a control device.

<Configuration of measurement optical system and spectroscope>
Next, the internal configurations of the optical head 1000 and the base portion 1001 will be described with reference to FIG. First, the internal configuration of the optical head 1000 will be described. An objective lens 135-1 is installed so as to face the eye E to be inspected, and the optical path of the OCT optical system is set for each wavelength band by the first dichroic mirror 132-1 and the second dichroic mirror 132-2 on the optical axis thereof. 351, a fundus observation and fixation lamp optical path 352, and an anterior segment observation optical path 353. Here, 135-3 and 135-4 are lenses, and the lens 135-3 is driven by a motor (not shown) for focus adjustment of the fixation lamp 191 and the fundus observation CCD 172.

  A perforated mirror 303 is arranged between the lens 135-4 and the third dichroic mirror 132-3, and the optical path 352 is branched into an optical path 355 and an optical path 354. The optical path 354 forms an illumination optical system that illuminates the fundus of the eye E to be inspected, the LED light source 316 that is an illumination light source for fundus observation used for alignment of the eye E to be inspected, and fundus image data of the eye E to be inspected. The strobe tube 314 used for the image pickup is installed. 313 and 315 are condenser lenses, and 317 is a mirror. The illumination light from the LED light source 316 and the strobe tube 314 becomes a ring-shaped luminous flux by the ring slit 312, is reflected by the perforated mirror 303, and illuminates the retina Er of the eye E to be examined. Here, 309 and 311 are lenses. The LED light source 316 has a central wavelength near 780 nm.

  After the perforated mirror 303 on the optical path 352, the third dichroic mirror 132-3 branches the optical path to the fundus observation CCD 172 and the optical path to the fixation lamp 191 for each wavelength band. The fundus observation CCD 172 has sensitivity in the vicinity of the center wavelength (780 nm) of the LED light source 316 that is the fundus observation illumination light, and is connected to the CCD control unit 102. On the other hand, the fixation lamp 191 generates visible light and promotes fixation of the subject, and is connected to the fixation lamp control unit 103.

  The CCD control unit 102 and the fixation lamp control unit 103 are connected to the calculation unit 104, and data is exchanged between the base unit 1001 and the computer 1003 via the calculation unit 104. In the optical path 353, 135-2 is a lens and 171 is an anterior eye observation CCD. The anterior ocular segment observing CCD 171 has sensitivity in the vicinity of the wavelength (970 nm) of the anterior ocular segment observing illumination light (not shown). An image split prism (not shown) is arranged in the optical path 353, and the distance in the z direction of the optical head 1000 with respect to the eye E can be detected as a split image in the anterior eye observation image.

  The optical path 351 constitutes an OCT optical system and is for imaging fundus tomographic image data of the fundus Er of the eye E to be examined. More specifically, the optical path 351 is for obtaining an interference signal for forming fundus tomographic image data. Reference numeral 134 is an XY scanner for scanning light on the fundus. The XY scanner 134 is shown as a single mirror, but scans in the XY biaxial directions. Reference numerals 135-5 and 135-6 are lenses, and the lens 135-5 of the lenses 135-5 focuses light from the light source 101 emitted from the fiber 131-2 connected to the optical coupler 131 onto the fundus Er. Therefore, it is driven by a motor (not shown). By this focusing adjustment, the light from the fundus 107 is simultaneously imaged and incident on the tip of the fiber 131-2 in a spot shape.

  Next, the configurations of the optical path from the light source 101, the reference optical system, and the spectroscope will be described. In FIG. 1B, 101 is a light source. 132-4 is a mirror. Reference numeral 115 is a dispersion compensating glass. Reference numeral 131 is an optical coupler. Reference numerals 131-1 to 131-4 are single mode optical fibers connected to and integrated with an optical coupler. 135-7 is a lens. Reference numeral 180 is a spectroscope.

  The Michelson interference system is configured by the above configuration. The light emitted from the light source 101 is split into the measurement light on the optical fiber 131-2 side and the reference light of the optical fiber 131-3 through the optical fiber 131-1 and the optical coupler 131. The measurement light irradiates the fundus Er of the eye E to be observed through the above-mentioned optical path of the OCT optical system, and reaches the optical coupler 131 through the same optical path due to reflection and scattering by the retina.

  On the other hand, the reference light reaches and is reflected by the mirror 132-4 via the optical fiber 131-3, the lens 135-7, and the dispersion compensating glass 115 inserted to match the dispersion of the measurement light and the reference light. .. Then, the reflected light returns through the same optical path and reaches the optical coupler 131.

  The measurement light and the reference light are combined by the optical coupler 131 to become interference light. Here, interference occurs when the optical path length of the measurement light and the optical path length of the reference light become substantially the same. The mirror 132-4 is held so as to be adjustable in the optical axis direction by a motor and a drive mechanism (not shown), and the optical path length of the reference light can be matched with the optical path length of the measurement light that changes depending on the eye E to be inspected. The interference light is guided to the spectroscope 180 via the optical fiber 131-4.

  Reference numeral 139-1 is a polarization adjusting unit on the measurement light side provided in the optical fiber 131-2. Reference numeral 139-2 is a reference light side polarization adjusting unit provided in the optical fiber 131-3. These polarization adjusters have several looped portions of the optical fiber, and the loop-shaped portion is rotated around the longitudinal direction of the fiber to add twist to the fiber for measurement. It is possible to adjust and match the polarization states of the light and the reference light, respectively. In this embodiment, the polarization states of the measurement light and the reference light are adjusted and fixed in advance.

  The spectroscope 180 includes a lens 135-8, a lens 135-9, a diffraction grating 181, and a line sensor 182. The interference light emitted from the optical fiber 131-4 becomes substantially parallel light via the lens 135-8, is then dispersed by the diffraction grating 181, and is imaged on the line sensor 182 by the lens 135-9.

  Next, the light source 101 will be described. The light source 101 is an SLD (Super Luminescent Diode) which is a typical low coherent light source. The central wavelength is 855 nm and the wavelength band width is about 100 nm. Here, the bandwidth is an important parameter because it affects the resolution of the obtained tomographic image in the optical axis direction. Although SLD is selected here as the type of light source, ASE (Amplified Spontaneous Emission) or the like may be used as long as low-coherent light can be emitted. The near-infrared light is suitable as the center wavelength in view of measuring the eye. Further, since the central wavelength affects the lateral resolution of the tomographic image obtained, it is desirable that the central wavelength be as short as possible. The center wavelength is set to 855 nm for both reasons.

  Although the Michelson interferometer is used as the interferometer in the present embodiment, a Mach-Zehnder interferometer may be used. It is preferable to use a Mach-Zehnder interferometer when the light amount difference between the measurement light and the reference light is large, and to use a Michelson interferometer when the light amount difference is relatively small.

<Imaging screen>
Next, the imaging screen in the present embodiment will be described with reference to FIG. In FIG. 2A, 2000 is an image pickup screen. The imaging screen 2000 is a screen for performing various settings and adjustments in order to obtain a desired eye image to be inspected, and is a screen displayed on the monitor 1005 before imaging.

  In FIG. 2A, 2400 is a patient information display unit, which displays various information (for example, patient ID, patient name, age, and sex) of the patient currently undergoing the examination. Reference numeral 2101 denotes an anterior segment observation screen for displaying anterior segment surface image data obtained by the anterior segment observation CCD 171. 2201 is a fundus surface observation screen for displaying the fundus surface image data obtained by the fundus observation CCD 172. Reference numeral 2301 is a fundus tomographic confirmation screen for confirming fundus tomographic image data. Reference numeral 2001 is a button for switching the left and right of the eye to be inspected, and when the “L” or “R” button is pressed, the optical head 1000 moves to the initial positions of the left and right eyes.

  Reference numeral 2010 denotes an inspection set selection screen, which displays the selected inspection set. The inspection set is a scan pattern group that stores at least one scan pattern together with its order. The examination set includes, for example, a scan pattern group suitable for macular disease, a scan pattern group suitable for glaucoma, and a scan pattern group suitable for nipple analysis and anterior segment analysis. There is also an examination set called follow-up that has the same scan pattern group as in the past imaging processing. When changing the examination set, the examiner clicks the button 2011 to display a pull-down menu (not shown) and selects the desired examination set. Further, on the scan pattern display screen 2012, an outline of scan patterns performed in the currently selected inspection set, for example, 3D scan, cross scan, etc., is displayed in order.

  Reference numeral 2002 denotes a mouse cursor, and the examiner operates the mouse included in the input unit 929 to move the position of the mouse cursor. The ophthalmologic apparatus 100 is provided with a mouse cursor position detection means, and is configured so that the alignment can be changed according to the position of the mouse cursor. The mouse cursor position detecting means calculates the position from the pixel position of the mouse cursor on the display screen. A range is provided in the measurement screen, and the correspondence between the provided range and the alignment drive is set in advance. Thus, when the mouse cursor is within the set range of pixels, the alignment determined in the set range can be performed. The alignment operation with the mouse is performed by rotating the wheel of the mouse.

  Reference numeral 2004 denotes a start button. By pressing the start button 2004, acquisition of the fundus tomographic image data and the fundus surface image data is started, and the fundus tomographic confirmation screen 2301 and the fundus surface observation screen 2201 each display as a moving image in real time. To be done. At this time, a frame 2202 displayed in the fundus surface observation screen 2201 indicates a range in which fundus tomographic image data is acquired in the fundus surface image data. A cursor 2208 indicated by a horizontal arrow line indicates the position on the subject's eye E and the scan direction of the fundus tomographic image data displayed on the fundus tomographic confirmation screen 2301, and can be moved by the mouse. is there.

  A slider 2103 arranged near the anterior ocular segment surface observation screen 2101 is a slider for adjusting the position of the optical head 1000 in the Z direction with respect to the eye E to be inspected. A slider 2203 arranged near the fundus surface observation screen 2201 is a slider for performing focus adjustment. Similarly, a slider 2205 arranged near the fundus surface observation screen 2201 is a slider for adjusting the magnification of the fundus surface image data. A slider 2303 arranged near the fundus tomographic confirmation screen 2301 is a slider for adjusting the coherence gate.

  The focus adjustment is an adjustment for moving the lenses 135-3 and 135-5 in the direction shown in FIG. 1B in order to adjust the focus on the fundus Er. Further, the coherence gate adjustment is an adjustment for moving the mirror 132-4 in the direction shown by the arrow in FIG. 1B in order to observe the fundus tomographic image data at a desired position on the fundus tomographic confirmation screen 2301. .. Further, these sliders 2103, 2203, 2205, and 2303 are adapted to move in conjunction with the alignment operation by the mouse in the image data displayed on the corresponding screen.

  A magnifying button 2206 is used to magnify the fundus surface image data displayed on the fundus surface observation screen 2201. After the magnifying button 2206 is pressed, the magnification of the fundus surface image data is adjusted by the slider 2205. Reference numeral 2003 denotes an image capturing button, and when various adjustments are completed and the image capturing button 2003 is pressed, image capturing processing of still image data indicating a tomographic image of the fundus of the eye is executed.

  Next, the imaging process of fundus tomographic image data by the ophthalmologic apparatus 100 according to the present embodiment will be described. First, the operator presses the start button 2004 to start acquisition of fundus surface image data, which is moving image data.

  In FIG. 1B, the illumination light from the LED light source 316 passes through the condenser lenses 315 and 313, is reflected by the mirror 317, becomes a ring-shaped light flux by the ring slit 312, and passes through the lenses 311 and 309. The light is reflected by the perforated mirror 303, passes through the lens 135-3, the lens 135-4, the second dichroic mirror 132-2, the first dichroic mirror 132-1 and the objective lens 135-1 and passes through the eye E. Illuminate the retina Er.

  The reflected light from the retina Er of the eye E to be examined passes through the objective lens 135-1, and the first dichroic mirror 132-1, the second dichroic mirror 132-2, the lens 135-3, the lens 135-4, and the hole. The light passes through the hole of the perforated mirror 303, is reflected by the third dichroic mirror 132-3, and is imaged on the CCD 172. The fundus surface image formed on the CCD 172 is read by the CCD control unit 102, amplified and A/D converted, and input to the arithmetic unit 104 as fundus surface image data. The fundus surface image data input to the computing unit 104 is displayed in real time on the fundus surface observation screen 2201 by being captured by the computer 1003 shown in FIG.

  The computer 1003 performs contrast detection processing on the captured fundus surface image data, drives the lens 135-3 to a position where the contrast of the fundus surface image data is best, and focuses the eye E on the fundus Er. .. The ophthalmologic apparatus 100 can capture fundus tomographic image data of a desired portion of the fundus Er of the eye E by controlling the XY scanner 134.

  First, the measurement light is scanned in the x-direction in FIG. 1B, and the line sensor 182 captures information on a predetermined number of images from the imaging range in the x-direction on the fundus Er. The fundus tomographic image data captured by the line sensor 182 is captured by the computer 1003, and the luminance distribution on the line sensor 182 obtained at a certain position in the x direction is FFT processed. The linear luminance distribution obtained by the FFT processing is converted into density or color information in order to show it on the monitor 1005, and is called A-scan image data. Two-dimensional image data in which a plurality of A-scan image data are arranged is referred to as B-scan image data. A plurality of B-scan image data is obtained by capturing a plurality of A-scan image data for constructing one B-scan image data, moving the scan position in the y-direction, and scanning again in the x-direction. ..

  By displaying a plurality of B-scan image data or three-dimensional fundus tomographic image data constructed from a plurality of B-scan image data on the monitor 1005, the examiner can use it for diagnosis of the eye E to be inspected. The acquired fundus tomographic image data of the eye E to be examined is displayed in real time on the fundus tomographic confirmation screen 2301.

  The computer 1003 detects the contrast with respect to the captured fundus tomographic image data, drives the lens 135-3 to a position where the contrast of the fundus tomographic image data is best, and automatically adjusts the focus of the eye E to be examined on the fundus Er. Done in.

<Ocular fundus tomographic image data imaging process>
Next, the processing of the computer 1003 of the ophthalmologic apparatus 100 according to this embodiment will be described with reference to FIG. The process shown in FIG. 3 is a process realized by the CPU in the computer 1003 by reading and executing necessary data and programs from a recording medium such as a ROM.

  In step S1, the computer 1003 displays the imaging screen 2000 on the monitor 1005. In step S2, the computer 1003 selects an inspection set according to the operation of the examiner on the inspection set selection screen 2010. In step S3, the computer 1003 determines whether the follow-up examination has been selected. If the follow-up examination is selected, the process proceeds to step S4. On the other hand, if the follow-up examination is not selected, the process proceeds to step S5.

  In step S4, the computer 1003 reads patient information from the patient information storage unit. The patient information includes a scan pattern group, a scan position, a focus position, the presence or absence and display magnification of the fundus surface magnifying observation screen 2204, and the presence or absence and display magnification of the fundus tomographic magnifying confirmation screen 2302 in the past imaging processing. Etc. By performing the imaging process based on the patient information, the fundus tomographic image data of the eye E to be inspected can be newly acquired under the same condition as the fundus tomographic image data captured in the past which is the comparison target.

  In step S<b>5, the computer 1003 acquires the fundus surface moving image data that is moving image data in response to the start button 2004 being pressed, and displays the fundus surface moving image data on the fundus surface observation screen 2201. The operator moves the cursor 2208 to the position where the fundus tomographic image data is desired to be acquired on the fundus surface moving image data displayed on the fundus surface observation screen 2201. As a result, moving image data that is fundus tomographic image data corresponding to the position of the cursor 2208 is acquired and displayed on the fundus tomographic confirmation screen 2301. Note that step S5 is a processing example of the surface moving image acquisition means, the surface moving image display control means, the tomographic image acquisition means, and the tomographic image display control means.

  In step S6, the computer 1003 determines whether the enlargement button 2206 has been pressed. For example, when the subject's eye E has a small lesion and it is difficult to identify the lesion site from the fundus surface moving image data, the operator presses the enlargement button 2206. If the enlarge button 2206 is pressed, the process proceeds to step S7. On the other hand, if the enlargement button 2206 is not pressed, the process proceeds to step S10.

  In step S7, the computer 1003 enlarges the fundus surface moving image data displayed on the fundus surface observation screen 2201 and displays it on the fundus surface magnification observation screen 2204, as shown in FIG. 2B. The fundus surface moving image data displayed on the fundus surface magnifying observation screen 2204 is image data obtained by enlarging a region surrounded by a dashed line in the fundus surface moving image data displayed on the fundus surface observation screen 2201. ..

  In step S8, the computer 1003 enlarges the fundus tomographic image data displayed on the fundus tomographic confirmation screen 2301 and displays it on the fundus tomographic enlargement confirmation screen 2302 as illustrated in FIG. 2B. The fundus tomographic image data displayed on the fundus tomographic expansion confirmation screen 2302 is image data obtained by enlarging a region surrounded by a two-dot chain line in the fundus tomographic image data displayed on the fundus tomographic confirmation screen 2301. Note that steps S7 and S8 are processing examples of the display magnification control means.

  The display magnification adjusted by the slider 2205 is displayed on the fundus surface display magnification display unit 2207 and the fundus tomographic display magnification display unit 2304. Here, the display magnifications of the fundus surface moving image data and the fundus tomographic image data are interlocked. For example, if the display magnification of the fundus surface moving image data is 2 times, the display magnification of the fundus tomographic image data is also 2 times. become.

  In step S9, the computer 1003 also changes the minimum movement interval and the maximum movement range of the cursor 2208 according to the display magnification. In the present embodiment, the minimum movement interval is 10 um and the maximum movement range is 10 mm when the display magnification is 1 time, and the minimum movement interval is 5 um and the maximum movement range is 5 mm when the display magnification is 2 times. Has been changed to. Further, the computer 1003 aligns the cursor 2208 with the cursor 2208 displayed on the fundus surface observation screen 2201 and the cursor displayed on the fundus surface magnification observation screen 2204 so that the cursor 2208 moves in conjunction with the cursor 2208. The movement of the cursor displayed on the screen 2204 is controlled. As a result, it is possible to improve usability when designating the imaging position of the tomographic image data that is still image data. It should be noted that step S9 is a processing example of the cursor movement distance control means.

  In step S10, the computer 1003 determines whether the imaging button 2003 has been pressed. If the imaging button 2003 is pressed, the process proceeds to step S11. On the other hand, if the imaging button 2003 has not been pressed, the process returns to step S6. Note that step S10 is a processing example of the receiving unit.

  In step S11, the computer 1003 executes an imaging process of fundus tomographic image data. As a result, fundus tomographic image data that is still image data is captured. In step S12, the computer 1003 saves the patient information such as the display magnification, the patient ID, and the imaging position in the patient information storage unit during the imaging process of the fundus tomographic image data this time. Thereby, at the time of the next follow-up imaging, the imaging processing can be executed using the patient information saved this time. Note that step S11 is a processing example of the tomographic image capturing means. Further, step S12 is a processing example of the display magnification storage means.

  As described above, according to the present embodiment, since the fundus surface moving image data and the fundus tomographic image data can be enlarged and displayed, the position of the tomographic image data of the fundus Er of the eye E to be imaged can be easily and easily obtained. It is possible to set accurately.

  In the present embodiment, the ophthalmologic apparatus that captures fundus tomographic image data of the eye to be inspected has been described, but the present invention is not limited to this, and in order to capture tomographic image data of another inspected object such as skin and internal organs. It is also applicable to the above device. Further, in the present embodiment, the optical head 1000 for capturing fundus tomographic image data and the computer 1003 are communicably connected in a wired form, but the optical head 1000 and the computer 1003 can communicate in a wireless form. You may connect.

  The present invention is also realized by executing the following processing. That is, software (program) that realizes the functions of the above-described embodiments is supplied to a system or device via a network or various storage media, and the computer (or CPU, MPU, etc.) of the system or device reads the program. This is the process to be executed.

Claims (19)

A light projecting optical system that projects light to each position of the fundus of the eye to be inspected, and a light receiving optical system that receives light from the fundus emitted from each position of the fundus along with light from the light projecting optical system by a light receiving element. A taking optical system having
A fundus image is generated based on a light reception signal from the light receiving element, a first moving image composed of a plurality of continuous fundus images is displayed on a display unit, and a partial image in which a part of the fundus image is extracted is generated. , the second moving picture made of a plurality of partial images successively, the display means is displayed together with the first moving image, the display form indicating the position of the tomographic image indicating the fault of the fundus prior Symbol subfractions image Display control means for displaying on the display means in an overlapped state,
An ophthalmologic photographing apparatus comprising:   The ophthalmologic imaging apparatus according to claim 1, wherein the display control unit causes the second moving image to be displayed in a larger size than an area corresponding to a part of the fundus image in the first moving image. .   The ophthalmic imaging apparatus according to claim 1, further comprising an extraction range setting unit that sets a part of the fundus image extracted as the partial image based on an instruction from an examiner.   4. The display control means performs, in the first moving image, a display for discriminating between a region corresponding to a part of the fundus image extracted as the partial image and another region. The ophthalmic photographing apparatus according to any one of 1.   The ophthalmologic photography according to any one of claims 1 to 4, wherein the display control unit causes the display unit to display at least one of the first moving image and the second moving image as a live image. apparatus. A light projecting optical system that projects light to each position of the fundus of the eye to be inspected, and a light receiving optical system that receives light from the fundus emitted from each position of the fundus along with light from the light projecting optical system by a light receiving element. A taking optical system having
A partial image corresponding to the target range comprised fundus image image to be photographed by using the photographing optical system as a live image, to be displayed together with the fundus image on the display unit, position of the tomographic image indicating the fault of said fundus display control means for displaying on said display means in an overlapped state before Symbol subfractions image display manner indicating,
An ophthalmologic photographing apparatus comprising:   The ophthalmologic imaging apparatus according to claim 1, wherein the display control unit causes the display unit to display the partial image in a state of being superimposed on a part of the fundus image. Said display control means, said display means to display, the display form indicating the position of the tomographic image, the display in a state superimposed on the fundus image and the partial image the fundus image and the partial image as a live image The ophthalmologic imaging apparatus according to claim 1, wherein the ophthalmologic imaging apparatus displays the image on a device. It said display control means, a display form indicating a pre-Symbol position location, the arrow indicating the scanning direction of the measuring light in acquiring the tomographic image to be displayed on said display means in a state superposed before Symbol subfractions image The ophthalmologic imaging apparatus according to any one of claims 1 to 8, wherein Wherein the display control unit, the so-scanning direction is identifiable, ophthalmologic photographing apparatus according to claim 9, characterized in that to be displayed on said display means in a state of overlapping the arrow before Symbol part images.   The display control means causes the display means to display, as the tomographic image, a first tomographic image corresponding to a display magnification of the fundus image and a second tomographic image corresponding to a display magnification of the partial image. The ophthalmologic imaging apparatus according to any one of claims 1 to 10. The ophthalmologic imaging apparatus according to claim 11 , wherein the display control unit causes the display unit to display the first tomographic image and the second tomographic image as live images . The display control unit is a tomographic image showing a tomographic image of the fundus, and displays a tomographic image corresponding to a display range of the partial image as a live image on the display unit together with the fundus image and the partial image. The ophthalmologic imaging apparatus according to claim 1, wherein the ophthalmologic imaging apparatus is characterized by including: A light projecting optical system that projects light to each position of the fundus of the eye to be inspected, and a light receiving optical system that receives light from the fundus emitted from each position of the fundus along with light from the light projecting optical system by a light receiving element. A method of controlling an ophthalmologic imaging apparatus having an imaging optical system having,
A fundus image is generated based on a light reception signal from the light receiving element, a first moving image composed of a plurality of continuous fundus images is displayed on a display unit, and a partial image in which a part of the fundus image is extracted is generated. , the second moving picture made of a plurality of partial images successively, the display means is displayed together with the first moving image, the display form indicating the position of the tomographic image indicating the fault of the fundus prior Symbol subfractions image A method of controlling an ophthalmologic imaging apparatus, comprising the step of displaying on the display means in an overlapped state. A light projecting optical system that projects light to each position of the fundus of the eye to be inspected, and a light receiving optical system that receives light from the fundus emitted from each position of the fundus along with light from the light projecting optical system by a light receiving element. A method of controlling an ophthalmologic imaging apparatus having an imaging optical system having,
A partial image corresponding to the target range comprised fundus image image to be photographed by using the photographing optical system as a live image, to be displayed together with the fundus image on the display unit, position of the tomographic image indicating the fault of said fundus control method for an ophthalmologic photographing apparatus characterized by comprising a step of displaying on the display unit in an overlapped state before Symbol subfractions image display manner indicating. In the step of displaying, the display unit displays the fundus image and the partial image as live images on the display unit, and a display form indicating the position of the tomographic image is displayed on the fundus image and the partial image in a state of being superimposed. The method for controlling an ophthalmologic imaging apparatus according to claim 14, wherein the control method is displayed on the screen. In the displaying step, as the tomographic image, a first tomographic image corresponding to a display magnification of the fundus image and a second tomographic image corresponding to a display magnification of the partial image are displayed on the display unit. The method for controlling an ophthalmologic imaging apparatus according to claim 14, wherein In the step of displaying, a tomographic image showing a tomographic image of the fundus, a tomographic image corresponding to a display range of the partial image is displayed as a live image on the display unit together with the fundus image and the partial image. The method for controlling an ophthalmologic imaging apparatus according to claim 14, wherein the method is a method for controlling an ophthalmologic imaging apparatus. A computer program that causes a computer to execute each step of the method for controlling the ophthalmologic imaging apparatus according to claim 14 .

Images