JP2018089480A - Ophthalmic photographing system, method for controlling the same and program - Google Patents

Abstract

PROBLEM TO BE SOLVED: To readily and correctly execute positioning of an image of a fundus of a subject eye to image using an ocular fundus surface image (fundus image).SOLUTION: An ophthalmic photographing system displays a dynamic image of a fundus surface image obtained by a fundus observation CCD on a fundus surface observation screen 2201 on an imaging screen 2000 and displays a dynamic image of a partial image extracting part of the fundus surface image that is displayed on the fundus surface observation screen 2201 on a fundus surface expansion observation screen 2204.SELECTED DRAWING: Figure 2

Description

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

  At present, various devices such as an anterior ocular segment imaging device, a fundus camera, and a confocal laser scanning ophthalmoscope (SLO) are used as an ophthalmologic apparatus using an optical device. Among them, an optical tomographic imaging apparatus (hereinafter referred to as an OCT apparatus) by optical coherence tomography (OCT: Optical Coherence Tomography) using multiwavelength lightwave interference can obtain tomographic image data of a sample with high resolution, It is becoming an indispensable ophthalmic device for specialized retina outpatients.

  Patent Document 1 discloses a technique that can display fundus surface image data indicating a fundus surface and fundus tomographic image data indicating a fundus tomogram 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 with the fundus surface image data, and the fundus tomographic image data is aimed at a lesion site distributed in a range narrower than the imaging range of the fundus surface image. Image. That is, normally, the fundus tomographic image is captured as an image in an imaging range narrower than the imaging range of the fundus surface image (fundus image). However, since the resolution of the OCT apparatus is increasing, the technique disclosed in Patent Document 1 does not consider the display magnification when observing the fundus surface image data. Therefore, when a small lesion site is targeted, 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 captured cannot be easily determined. As a result, there has been a problem that it takes time for the subject to take time to capture the fundus tomographic image data or to reacquire the fundus tomographic image data.

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

One of the ophthalmologic photographing apparatuses 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 a fundus that is emitted from each position of the fundus with the light from the projection optical system. A photographing optical system having a light receiving optical system for receiving the light of the light from the light receiving element, and generating a fundus image based on a light receiving signal from the light receiving element, and displaying a first moving image including a plurality of continuous fundus images Display control means for generating a partial image from which a part of the fundus image is extracted and displaying a second moving image composed of a plurality of continuous partial images together with the first moving image on the display means It is characterized by providing.
Another aspect of the ophthalmologic photographing apparatus according to the present invention is a projection optical system that projects light to each position of the fundus of the eye to be examined, and each of the fundus according to the light from the projection optical system. A photographing optical system having a light receiving optical system that receives light from the fundus radiated from a position by a light receiving element, and a fundus image photographed using the photographing optical system, together with a range of interest included in the fundus image And a display control unit that displays a partial image on a display unit and displays at least one of the fundus image and the partial image as a live image on the display unit.

  According to one aspect of the present invention, it is possible to easily and accurately execute the setting of the position of the fundus image of the eye to be imaged 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. It is a flowchart which shows the imaging process of the fundus tomographic image data by the ophthalmologic apparatus according to the embodiment of the present invention.

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

<Configuration of ophthalmic apparatus>
FIG. 1 is a diagram illustrating a configuration of an ophthalmologic apparatus according to an embodiment of the present invention. 1A shows the external configuration of the ophthalmologic apparatus according to this embodiment, and FIG. 1B shows the internal configuration of the optical head and base portion of the ophthalmic apparatus according to this embodiment. Yes. The ophthalmologic apparatus shown in FIG. 1 is a configuration that is an example of a control system.

  In FIG. 1A, reference numeral 100 denotes an ophthalmologic apparatus. Reference numeral 1000 denotes an optical head which is a measurement optical system for capturing anterior ocular surface image data indicating the anterior ocular surface, fundus surface image data indicating the ocular fundus surface, and fundus tomographic image data indicating a fundus tomographic image. It is. Reference numeral 1002 denotes a stage unit that moves the optical head 1000 in the xyz direction in FIG. 1A using a motor (not shown). Reference numeral 1001 denotes a base unit incorporating a spectroscope described later.

  Reference numeral 1003 denotes a computer that controls the movement process of the optical head 1000 by the stage unit 1002 and the imaging process of fundus tomographic image data. Reference numeral 1004 denotes a hard disk that is built in the computer 1003 and stores a program and the like for imaging subject information and fundus tomographic image data. Reference numeral 1005 denotes a monitor as a display unit. Reference numeral 1006 denotes an input unit for 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 urging the subject's eyes (the subject's eyes) to be fixed by fixing the subject's chin and forehead to fixate the subject's eyes. Used for. Note that the computer 1003 has a configuration as an example of a control device.

<Configuration of measurement optical system and spectrometer>
Next, the internal configuration of the optical head 1000 and the base unit 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 facing the eye E, and an optical path of the OCT optical system is provided for each wavelength band by the first dichroic mirror 132-1 and the second dichroic mirror 132-2 on the optical axis. 351, the fundus observation and fixation lamp optical path 352, and the anterior segment observation optical path 353 are branched. Here, reference numerals 135-3 and 135-4 denote lenses, and the lens 135-3 is driven by a motor (not shown) for adjusting the focus of the fixation lamp 191 and the fundus observation CCD 172.

  A perforated mirror 303 is disposed 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, and an LED light source 316 that is a fundus observation illumination light source used for alignment of the eye E and fundus image data of the eye E A strobe tube 314 used for imaging is provided. Reference numerals 313 and 315 denote condenser lenses, and 317 denotes a mirror. Illumination light from the LED light source 316 and the strobe tube 314 becomes a ring-shaped light flux by the ring slit 312 and is reflected by the perforated mirror 303 to illuminate the retina Er of the eye E to be examined. Here, reference numerals 309 and 311 denote lenses. The LED light source 316 has a central wavelength around 780 nm.

  After the holed 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 oculi observation CCD 172 has sensitivity near the center wavelength (780 nm) of the LED light source 316 that is illumination light for fundus oculi observation, and is connected to the CCD controller 102. On the other hand, the fixation lamp 191 generates visible light to promote 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 a CCD for anterior eye observation. The anterior ocular segment observation CCD 171 has sensitivity near the wavelength (970 nm) of illumination light for anterior ocular observation (not shown). In addition, an image split prism (not shown) is disposed 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 forms an OCT optical system, and is used to capture fundus tomographic image data of the fundus Er of the eye E to be examined. More specifically, the optical path 351 obtains an interference signal for forming fundus tomographic image data. An XY scanner 134 scans light on the fundus. The XY scanner 134 is illustrated as a single mirror, but performs scanning in the XY biaxial directions. Reference numerals 135-5 and 135-6 denote lenses, and the lens 135-5 adjusts the focus of light from the light source 101 emitted from the fiber 131-2 connected to the optical coupler 131 on 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.

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

  With the above configuration, a Michelson interference system is configured. The light emitted from the light source 101 is split into measurement light on the optical fiber 131-2 side and reference light on the optical fiber 131-3 via the optical coupler 131 through the optical fiber 131-1. The measurement light is applied to the fundus Er of the eye E to be observed through the OCT optical system optical path described above, 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 the mirror 132-4 and reflects through the optical fiber 131-3, the lens 135-7, and the dispersion compensation glass 115 inserted in order to match the dispersion of the measurement light and the reference light. . Then, the reflected light returns on 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 are substantially the same. The mirror 132-4 is held so as to be adjustable in the optical axis direction by a motor and a driving mechanism (not shown), and the optical path length of the reference light can be adjusted to the optical path length of the measurement light that changes depending on the eye E. The interference light is guided to the spectroscope 180 through the optical fiber 131-4.

  Reference numeral 139-1 denotes a measurement light side polarization adjusting unit provided in the optical fiber 131-2. Reference numeral 139-2 denotes a reference light side polarization adjusting unit provided in the optical fiber 131-3. These polarization adjustment units have several parts where the optical fiber is routed in a loop shape. By rotating the loop-shaped part around the longitudinal direction of the fiber, twisting is applied to the fiber. It is possible to adjust and match the polarization states of the light and the reference light. In this embodiment, it is assumed that 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) that is a typical low-coherent light source. The center wavelength is 855 nm and the wavelength bandwidth 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. In addition, although the SLD is selected here as the type of light source, it is sufficient that low-coherent light can be emitted, and ASE (Amplified Spontaneous Emission) or the like can also be used. In view of measuring the eye, the center wavelength is preferably near infrared light. In addition, since the center wavelength affects the lateral resolution of the obtained tomographic image, it is desirable that the center wavelength be as short as possible. For both reasons, the center wavelength was set to 855 nm.

  In this embodiment, a Michelson interferometer is used as an interferometer, but 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, reference numeral 2000 denotes an imaging screen. The imaging screen 2000 is a screen for performing various settings and adjustments in order to obtain a desired eye image, and is a screen displayed on the monitor 1005 before imaging.

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

  2010 is an inspection set selection screen for displaying the selected inspection set. An inspection set is a group of scan patterns that stores at least one scan pattern along with its order. The test 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 papillary analysis and anterior segment analysis. There is also an inspection set called follow-up having the same scan pattern group as in the past imaging process. When changing the examination set, the examiner clicks a button 2011 to display a pull-down menu (not shown) and selects a desired examination set. On the scan pattern display screen 2012, an overview of scan patterns performed in the currently selected inspection set, for example, 3D scan, cross scan, and the like are displayed in order.

  Reference numeral 2002 denotes a mouse cursor, and the examiner moves the position of the mouse cursor by operating the mouse included in the input unit 929. The ophthalmologic apparatus 100 includes a mouse cursor position detecting unit, 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 on the display screen of the mouse cursor. A range is provided in the measurement screen, and the correspondence between the provided range and the alignment drive is set in advance. As a result, when the mouse cursor is in a pixel in the set range, alignment defined in the set range can be performed. In addition, the alignment operation with the mouse is performed by rotating the mouse wheel.

  Reference numeral 2004 denotes a start button. When the start button 2004 is pressed, acquisition of fundus tomographic image data and fundus surface image data is started, and each is displayed as a moving image in real time on the fundus tomography confirmation screen 2301 and fundus surface observation screen 2201. Is 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 from the fundus surface image data. A cursor 2208 indicated by a horizontal arrow line indicates the position on the eye E and the scan direction of the fundus tomographic image data displayed on the fundus tomography confirmation screen 2301, and can be moved by the mouse. is there.

  A slider 2103 arranged in the vicinity of the anterior eye 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. A slider 2203 disposed near the fundus surface observation screen 2201 is a slider for performing focus adjustment. Similarly, a slider 2205 arranged in the vicinity of the fundus surface observation screen 2201 is a slider for adjusting the magnification of the fundus surface image data. A slider 2303 disposed in the vicinity of the fundus tomography confirmation screen 2301 is a slider for performing coherence gate adjustment.

  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. The coherence gate adjustment is an adjustment for moving the mirror 132-4 in the direction indicated by the arrow in FIG. 1B in order to observe the fundus tomographic image data at a desired position on the fundus tomography confirmation screen 2301. . The sliders 2103, 2203, 2205, and 2303 are also moved in conjunction with an alignment operation using a mouse in image data displayed on the corresponding screen.

  Reference numeral 2206 denotes an enlargement button for enlarging the fundus surface image data displayed on the fundus surface observation screen 2201. After the enlargement button 2206 is pressed, the magnification of the fundus surface image data is adjusted by the slider 2205. Reference numeral 2003 denotes an imaging button. When various adjustments are completed and the imaging button 2003 is pressed, imaging processing of still image data indicating a fundus tomogram is executed.

  Next, imaging processing of fundus tomographic image data by the ophthalmologic apparatus 100 according to the present embodiment will be described. First, the operator presses a start button 2004 to start acquisition of fundus surface image data that 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 beam by the ring slit 312, passes through the lens 311 and the lens 309, 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 the eye E Illuminates the retina Er.

  The reflected light from the retina Er of the eye E 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 portion of the perforated mirror 303, reflects off the third dichroic mirror 132-3, and forms an image 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 calculation unit 104 as fundus surface image data. The fundus surface image data input to the calculation unit 104 is displayed on the fundus surface observation screen 2201 in real time by being captured by the computer 1003 shown in FIG.

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

  First, scanning of the measurement light is performed in the x direction in FIG. 1B, and information on a predetermined number of images is captured by the line sensor 182 from the imaging range of the fundus Er in the x direction. 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 subjected to FFT processing. Data obtained by converting the linear luminance distribution obtained by the FFT processing into density or color information so as to be displayed on the monitor 1005 is referred to as A-scan image data. The two-dimensional image data in which the plurality of A-scan image data are arranged is referred to as B-scan image data. After imaging a plurality of A scan image data for constructing one B scan image data, a plurality of B scan image data can be obtained by moving the scan position in the y direction and performing the scan in the x direction again. .

  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. The acquired fundus tomographic image data of the eye E to be examined is displayed on the fundus tomography confirmation screen 2301 in real time.

  The computer 1003 detects the contrast of the acquired fundus tomographic image data, drives the lens 135-3 to a position where the contrast of the fundus tomographic image data is the best, and automatically focuses the eye E on the fundus Er. To do.

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

  In step S <b> 1, the computer 1003 displays the imaging screen 2000 on the monitor 1005. In step S <b> 2, the computer 1003 selects an examination set in accordance with an examiner's operation on the examination set selection screen 2010. In step S3, the computer 1003 determines whether or not a follow-up examination is selected. If the follow-up inspection is selected, the process proceeds to step S4. On the other hand, when the follow-up inspection is not selected, the process proceeds to step S5.

  In step S4, the computer 1003 reads patient information from the patient information storage unit. Patient information includes scan pattern groups, scan positions, focus positions, presence / absence and display magnification of the fundus surface enlargement observation screen 2204, and presence / absence and display magnification of the fundus tomography enlargement confirmation screen 2302 in the past imaging processing. Etc. By performing the imaging process based on the patient information, fundus tomographic image data of the eye E can be newly acquired under the same conditions as the fundus tomographic image data captured in the past to be compared.

  In step S <b> 5, the computer 1003 acquires 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 a 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 tomography confirmation screen 2301. Step S5 is a processing example of the surface moving image acquisition unit, the surface moving image display control unit, the tomographic image acquisition unit, and the tomographic image display control unit.

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

  In step S <b> 7, 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 enlargement observation screen 2204 as shown in FIG. 2B. The fundus surface moving image data displayed on the fundus surface enlargement observation screen 2204 is image data obtained by enlarging a region surrounded by a one-dot chain 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 shown in FIG. Note that the fundus tomographic image data displayed on the fundus tomography enlargement confirmation screen 2302 is image data obtained by enlarging an area surrounded by a two-dot chain line in the fundus tomography image data displayed on the fundus tomography confirmation screen 2301. Steps S7 and S8 are processing examples of the display magnification control means.

  In the fundus surface display magnification display unit 2207 and the fundus tomography display magnification display unit 2304, the display magnification adjusted by the slider 2205 is displayed. Here, the display magnifications of the fundus surface moving image data and the fundus tomographic image data are linked. For example, if the display magnification of the fundus surface moving image data is double, the display magnification of the fundus tomographic image data is also doubled. become.

  In step S9, the computer 1003 also changes the minimum movement interval and maximum movement range of the cursor 2208 according to the display magnification. In the present embodiment, when the display magnification is 1 ×, the minimum movement interval is 10 μm and the maximum movement range is 10 mm. When the display magnification is doubled, the minimum movement interval is 5 μm and the maximum movement range is 5 mm. Has been changed. Further, the computer 1003 aligns the fundus surface with the cursor 2208 so that the cursor 2208 displayed on the fundus surface observation screen 2201 and the cursor displayed on the fundus surface enlargement observation screen 2204 move in conjunction with each other. Controls the movement of the cursor displayed on the screen 2204. Thereby, it is possible to improve usability when designating the imaging position of tomographic image data which is still image data. 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. Step S10 is a processing example of the accepting unit.

  In step S11, the computer 1003 executes imaging processing of fundus tomographic image data. Thereby, fundus tomographic image data which is still image data is captured. In step S12, the computer 1003 stores the patient information such as the display magnification, the patient ID, and the imaging position in the patient information storage unit at the time of the imaging process of the fundus tomographic image data this time. Thereby, at the time of next follow-up imaging, imaging processing can be executed using the patient information stored this time. Step S11 is a processing example of the tomographic image capturing means. Step S12 is a processing example of the display magnification storage unit.

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

  In the present embodiment, the ophthalmologic apparatus that captures fundus tomographic image data of the eye to be examined has been described. However, the present invention is not limited to this, and tomographic image data of other inspected objects such as skin and internal organs is captured. It can be applied to other devices. In this embodiment, the optical head 1000 for capturing fundus tomographic image data and the computer 1003 are communicably connected in a wired format, but the optical head 1000 and the computer 1003 can communicate in a wireless format. You may connect.

  The present invention can also be 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 apparatus via a network or various storage media, and a computer (or CPU, MPU, or the like) of the system or apparatus reads the program. It is a process to be executed.

Claims (13)

A light projecting optical system that projects light to each position of the fundus of the eye to be examined, and a light receiving optical system that receives light from the fundus emitted from each position of the fundus with the light from the light projecting optical system. A photographing optical system having
A fundus image is generated based on a light reception signal from the light receiving element, a first moving image including 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. Display control means for causing the display means to display a second moving image comprising a plurality of continuous partial images together with the first moving image;
An ophthalmologic photographing apparatus comprising:   2. The ophthalmologic photographing apparatus according to claim 1, wherein the display control unit displays the second moving image in an enlarged manner from an area corresponding to a part of the fundus image in the first moving image. .   The ophthalmologic photographing 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.   The said display control means performs the discrimination | determination display of the area | region corresponding to a part of fundus image extracted as the said partial image, and another area | region in the said 1st moving image, It is characterized by the above-mentioned. The ophthalmologic photographing apparatus according to any one of the above.   5. The ophthalmologic photographing according to claim 1, 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. 6. apparatus. A light projecting optical system that projects light to each position of the fundus of the eye to be examined, and a light receiving optical system that receives light from the fundus emitted from each position of the fundus with the light from the light projecting optical system. A photographing optical system having
A display unit displays a partial image corresponding to a range of interest included in the fundus image together with a fundus image captured using the imaging optical system, and at least one of the fundus image and the partial image is displayed as a live image. Display control means for displaying on the display means;
An ophthalmologic photographing apparatus comprising:   The ophthalmologic photographing apparatus according to claim 1, wherein the display control unit displays the partial image on the display unit in a state where the partial image is superimposed on a part of the fundus image.   The display control means causes the display means to display a display form showing a tomographic image acquisition position, which is a moving image showing a fundus tomogram, overlaid on the fundus image and the partial image. The ophthalmologic photographing apparatus according to any one of claims 1 to 7.   The display control means displays, on the display means, an arrow indicating the scanning direction of the measurement light when acquiring the tomographic image in a state of being superimposed on the fundus image and the partial image as a display form indicating the acquisition position. The ophthalmologic photographing apparatus according to claim 8, wherein:   The ophthalmologic imaging according to claim 9, wherein the display control unit displays the arrow on the fundus image and the partial image in a state where the arrow is superimposed on the display unit so that the scanning direction can be identified. apparatus. A light projecting optical system that projects light to each position of the fundus of the eye to be examined, and a light receiving optical system that receives light from the fundus emitted from each position of the fundus with the light from the light projecting optical system. A method for controlling an ophthalmologic photographing apparatus including a photographing optical system having
A fundus image is generated based on a light reception signal from the light receiving element, a first moving image including 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. A method for controlling an ophthalmologic photographing apparatus, comprising: displaying a second moving image including a plurality of continuous partial images together with the first moving image on the display unit. A light projecting optical system that projects light to each position of the fundus of the eye to be examined, and a light receiving optical system that receives light from the fundus emitted from each position of the fundus with the light from the light projecting optical system. A method for controlling an ophthalmologic photographing apparatus including a photographing optical system having
A display unit displays a partial image corresponding to a range of interest included in the fundus image together with a fundus image captured using the imaging optical system, and at least one of the fundus image and the partial image is displayed as a live image. A method for controlling an ophthalmologic photographing apparatus, comprising: displaying on a display unit.   13. A program for causing a computer to execute each step of the method for controlling an ophthalmologic photographing apparatus according to claim 11 or 12.

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