JP2019118422A - Ophthalmologic imaging apparatus, control method therefor, program, and recording medium - Google Patents

Abstract

To appropriately set a plurality of fixation positions for acquiring a mosaic image using OCT, regardless of an individual difference in an eyeball.SOLUTION: A control unit of an ophthalmologic imaging apparatus according to the embodiment controls a fixation system and an image acquisition unit such that a front image of an eyeground is repeatedly acquired while fixation marks are moved. A drawing position determination unit analyzes a sequentially acquired front image to determine whether a predetermined site of the eyeground is drawn within a predetermined region of the front image. When it is determined that the predetermined site is drawn within the predetermined region, a fixation position setting unit sets a fixation position on the basis of the position of the fixation mark when the front image was acquired. The control unit controls the fixation system such that the fixation system sequentially presents a plurality of fixation marks corresponding to a plurality of fixation positions including the fixation position, and causes the OCT image acquisition unit to acquire a three-dimensional image of the eyeground while each of the fixation marks is presented. A combine processing unit creates a combined image of a plurality of three-dimensional images corresponding to the plurality of fixation positions.SELECTED DRAWING: Figure 5

Description

  The present invention relates to an ophthalmologic imaging apparatus, a control method thereof, a program, and a recording medium.

  Diagnostic imaging occupies an important position in the field of ophthalmology. In recent years, utilization of optical coherence tomography (OCT) has been advanced. The OCT has come to be used not only for acquiring B-scan images and three-dimensional images of an eye to be examined but also for acquiring front images (en-face images) such as C-scan images and shadowgrams.

  In addition, a modality for acquiring an image in which a specific part of an eye to be examined is emphasized has also been put to practical use. For example, OCT angiography (OCT-Angiography), which forms an image in which retinal blood vessels and choroidal blood vessels are emphasized, has attracted attention (see, for example, Patent Document 1). Generally, the tissue (structure) at the scan site is temporally invariant, but the blood flow part inside the blood vessel temporally changes. In OCT angiography, an image is formed by emphasizing a portion (blood flow signal) in which such temporal change exists. OCT angiography is also referred to as OCT motion contrast imaging or the like. In addition, images obtained by OCT angiography are called angiographic images, angiograms, motion contrast images, and the like.

  In typical conventional OCT angiography, a three-dimensional scan of a predetermined size (eg, 9 mm × 9 mm) is applied to obtain an image representing the three-dimensional distribution of fundus blood vessels. On the other hand, it is desirable to acquire a wider range of angiographic images. Panoramic imaging is known as a technique for acquiring OCT data of a wide range of the fundus (see, for example, Patent Document 2).

  Panoramic imaging is an imaging method in which a three-dimensional scan is respectively applied to a plurality of different areas, and a plurality of three-dimensional images obtained thereby are synthesized to construct a wide area image. Overlapping regions are set in regions adjacent to each other, and relative positions between adjacent images are determined with reference to the overlapping regions. Also, sequential three-dimensional scanning for different regions is typically realized by movement of the fixation position. The wide area image acquired by panoramic imaging is called a panoramic image, a mosaic image or the like.

  By the way, there are individual differences in the size and characteristics of the eyeball, and for example, the axial length and diopter (eye refractive power) differ among individuals. As described above, even in the case of applying a three-dimensional scan of a predetermined size, the range of the fundus actually scanned changes depending on the axial length and diopter.

  For example, as shown in FIG. 1, when the OCT measurement light is incident at the same angle θ to the subject eye E1 having the axial length L1 and the subject eye E2 having the axial length L2 (> L1), the fundus of the subject eye E1 The height Y2 of the projection position of the measurement light on the fundus of the eye to be examined E2 is larger than the height Y1 of the projection position of the measurement light in (Y2> Y1). That is, the height of the projection position of the measurement light on the fundus increases as the axial length increases. On the other hand, the size of the OCT scan is defined by the maximum deflection angle of the measurement light. Therefore, even if the condition of the OCT scan size is the same, the range of the fundus actually scanned changes according to the value of the axial length. The same applies to diopter.

  As such, since the actual scan range is affected by the eye parameter, the size of the overlapping area in panoramic imaging also changes according to the eye parameter. For example, when the axial length of the subject's eye is long, the actual scan range becomes wide, so the overlapping area also becomes wide. If the overlapping area becomes larger than necessary, the area actually drawn out by the mosaic image becomes narrow, and the efficiency of panoramic imaging decreases.

  On the contrary, when the axial length of the subject's eye is short, the actual scan range becomes narrow, so the overlapping area becomes narrow, and in some cases, the overlapping area disappears. If the overlapping area becomes narrow, there is a possibility that relative positions between adjacent images can not be determined with sufficient accuracy. In addition, when there is no overlapping area, the relative position between adjacent images can not be determined, and a mosaic image can not be constructed.

  In addition, there may also be a situation where a notable part (for example, the macula lutea) to be drawn in the central region of the mosaic image is not arranged as such.

JP-A-2015-515894 JP, 2009-183332, A

  An object of the present invention is to provide a technology capable of suitably setting a plurality of fixation positions for acquiring a mosaic image using OCT regardless of individual differences in eye size and characteristics. It is in.

  The first aspect of the embodiment is an ophthalmologic imaging apparatus including a fixation system, an imaging unit, an OCT image acquisition unit, a control unit, a depiction position determination unit, a fixation position setting unit, and an image processing unit. It is. The fixation system presents a fixation target to the subject's eye. The imaging unit captures the fundus of the eye to be examined. The OCT image acquisition unit applies an optical coherence tomography (OCT) to the fundus to acquire an image. The control unit executes fundus imaging control for controlling the fixation system and the imaging unit so as to repeatedly acquire the front image of the fundus while moving the fixation target. The depiction position determination unit analyzes the front image sequentially acquired by the fundus imaging control, and determines whether a predetermined region of the fundus is depicted within a predetermined region of the front image. The fixation position setting unit is based on the position of the fixation target when the corresponding front image is acquired by the imaging unit when the drawing position judgment unit judges that the predetermined part is drawn in the predetermined area. Set one or more fixation positions. The image processing unit processes the image acquired by the OCT image acquisition unit. The control unit controls the fixation system to sequentially present two or more fixation targets corresponding to two or more fixation positions including the set one or more fixation positions to the subject's eye, and The OCT control is performed to control the OCT image acquisition unit so as to acquire a three-dimensional image of the fundus when each of the two or more fixation targets is presented to the eye to be examined. The image processing unit includes a composition processing unit that forms a composite image of two or more three-dimensional images corresponding to two or more fixation positions acquired by OCT control.

  A second aspect of the embodiment is the ophthalmologic imaging apparatus of the first aspect, wherein the control unit starts movement of the fixation target from a preset initial fixation position in the fundus imaging control.

  A third aspect of the embodiment is the ophthalmologic imaging apparatus of the second aspect, wherein the initial fixation position is centered on a position separated by a predetermined distance in a predetermined direction from a predetermined site of the fundus of a standard eye. It is a fixation position for acquiring a front image.

  A fourth aspect of the embodiment is the ophthalmologic imaging apparatus of the second aspect, wherein the control unit is a fixation unit corresponding to a predetermined fixation position for acquiring a front image centering on a predetermined region of the fundus A preliminary control is performed to control the fixation system and the imaging unit so as to obtain a preliminary frontal image of the fundus while presenting a target to the subject's eye. Furthermore, the image processing unit calculates a deviation of the image of the predetermined part of the fundus with respect to the center position of the preliminary frontal image. In addition, the fixation position setting unit sets an initial fixation position based on the calculated deviation.

  A fifth aspect of the embodiment is the ophthalmologic imaging apparatus according to any of the first to fourth aspects, wherein the control unit acquires an OCT image so as to acquire a three-dimensional angiographic image of the fundus in OCT control. Control the department.

  A sixth aspect of the embodiment is a method of controlling an ophthalmologic imaging apparatus capable of applying imaging and optical coherence tomography (OCT) to a fundus of an eye to be examined, comprising: an imaging step; It includes a step, a fixation position setting step, an OCT step, and a combining step. The photographing step repeatedly acquires a front image of the fundus while moving the fixation target. The depiction position determination step analyzes the front image sequentially acquired by the imaging step, and determines whether a predetermined region of the fundus is depicted within a predetermined region of the front image. The fixation position setting step is based on the position of the fixation target when the front image is acquired, when it is determined by the drawing position determination step that a predetermined region of the fundus is drawn in a predetermined region of the front image. Set one or more fixation positions. The OCT step sequentially presents two or more fixation targets corresponding to two or more fixation positions including the set one or more fixation positions to the subject's eye, and each of the two or more fixation targets Acquires the three-dimensional image of the fundus when it is presented to the subject's eye. The combining step forms a combined image of two or more three-dimensional images corresponding to the two or more fixation positions acquired by the OCT step.

  A seventh aspect of the embodiment is a program that causes an ophthalmologic imaging apparatus capable of applying imaging and optical coherence tomography (OCT) to the fundus of a subject's eye to execute the control method of the sixth aspect.

  An eighth aspect of the embodiment is a computer-readable non-transitory recording medium recording the program of the seventh aspect.

  According to the embodiment, setting of a plurality of fixation positions for acquiring a mosaic image using OCT can be suitably performed regardless of individual differences in eyeball size and characteristics.

It is a schematic diagram for explaining background art. It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an exemplary embodiment. It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an exemplary embodiment. It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an exemplary embodiment. It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an exemplary embodiment. It is a schematic diagram for explaining an example of operation of an ophthalmology photographing instrument concerning an exemplary embodiment. It is a schematic diagram for explaining an example of operation of an ophthalmology photographing instrument concerning an exemplary embodiment. It is a schematic diagram for explaining an example of operation of an ophthalmology photographing instrument concerning an exemplary embodiment. It is a schematic diagram for explaining an example of operation of an ophthalmology photographing instrument concerning an exemplary embodiment. It is a flowchart showing an example of operation | movement of the ophthalmologic imaging device which concerns on exemplary embodiment. It is a schematic diagram for explaining an example of operation of an ophthalmology photographing instrument concerning an exemplary embodiment.

  An ophthalmologic photographing apparatus, a control method thereof, a program, and a recording medium according to an exemplary embodiment will be described in detail with reference to the drawings. The ophthalmologic imaging apparatus of the embodiment is an ophthalmologic apparatus having a function of performing optical coherence tomography (OCT). The ophthalmologic imaging apparatus of the embodiment may be capable of performing OCT angiography of the fundus.

  Hereinafter, although the ophthalmologic imaging device which combined the sweep source OCT and the fundus camera is demonstrated, embodiment is not limited to this. The type of OCT is not limited to swept source OCT, and may be, for example, spectral domain OCT.

  Swept source OCT divides the light from the wavelength variable light source (wavelength swept light source) into the measurement light and the reference light, superimposes the return light of the measurement light from the object with the reference light, and generates interference light, This interference light is detected by a balanced photodiode or the like, and the detection data collected according to the sweep of the wavelength and the scan of the measurement light is subjected to Fourier transformation or the like to form an image.

  Spectral domain OCT splits light from a low coherence light source into measurement light and reference light, superimposes return light from measurement light from a test object on reference light, and generates interference light, and the spectrum of this interference light The distribution is detected by a spectroscope, and the detected spectral distribution is subjected to Fourier transform or the like to form an image.

  Thus, the swept source OCT is an OCT method for acquiring a spectral distribution by time division, and the spectral domain OCT is an OCT method for acquiring a spectral distribution by space division. In addition, the OCT method which can be utilized for embodiment is not limited to these, It is also possible to employ | adopt embodiment using the OCT method (for example, time-domain OCT different from them) different from these.

  The ophthalmologic imaging apparatus according to the embodiment has a function of imaging the fundus of an eye to be examined and acquiring a front image. Examples of ophthalmologic modalities that can be used for fundus imaging include a scanning laser ophthalmoscope (SLO), a slit lamp microscope, a surgical microscope, and the like in addition to the fundus camera described below. In addition, the ophthalmology modality which can be utilized for embodiment is not limited to these, Moreover, it is also possible to employ | adopt embodiment using modality other than ophthalmology.

  In the present specification, “image data” and “image” based thereon are not distinguished unless otherwise mentioned. Also, unless otherwise stated, the region or tissue of the eye to be examined and the image representing it are not distinguished.

<Constitution>
The exemplary ophthalmologic imaging apparatus 1 shown in FIG. 2 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200. The fundus camera unit 2 is provided with an optical system and a mechanism for acquiring a front image of the eye to be examined E, and an optical system and a mechanism for executing the OCT. The OCT unit 100 is provided with an optical system or mechanism for performing OCT. The arithmetic and control unit 200 includes one or more processors configured to execute various processes (operations, controls, etc.). In addition to these, any member such as a member for supporting the face of the subject (jaw holder, forehead rest, etc.), or a lens unit for switching the site to which OCT is applied (for example, attachment for anterior segment OCT) Elements or units of the above may be provided in the ophthalmologic imaging apparatus 1.

  In the present specification, the “processor” is, for example, a central processing unit (CPU), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), a programmable logic device (for example, a simple programmable logic device (SPLD), a CPLD (complex). It means a circuit such as a programmable logic device (FPGA), a field programmable gate array (FPGA) or the like. The processor implements the function according to the embodiment by, for example, reading and executing a program stored in a memory circuit or a memory device.

<Fundus camera unit 2>
The fundus camera unit 2 is provided with an optical system for photographing the fundus oculi Ef of the eye to be examined E. The digital image (referred to as a fundus image, a fundus photograph, etc.) of the fundus oculi Ef to be acquired is generally a front image such as an observation image or a photographed image. An observation image is obtained by moving image shooting using near infrared light. The photographed image is a still image using flash light in the visible region.

  The fundus camera unit 2 includes an illumination optical system 10 and an imaging optical system 30. The illumination optical system 10 illuminates the eye E with illumination light. The photographing optical system 30 detects the return light of the illumination light irradiated to the eye to be examined E. The measurement light from the OCT unit 100 is guided to the eye E through an optical path in the fundus camera unit 2. The return light of the measurement light projected onto the eye to be examined E (for example, the fundus oculi Ef) is guided to the OCT unit 100 through the same optical path in the fundus camera unit 2.

  Light (observation illumination light) output from the observation light source 11 of the illumination optical system 10 is reflected by the concave mirror 12, passes through the condenser lens 13, passes through the visible cut filter 14, and becomes near-infrared light. Furthermore, the observation illumination light is once converged in the vicinity of the photographing light source 15 and reflected by the mirror 16, passes through the relay lens system 17, the relay lens 18, the diaphragm 19, and the relay lens system 20 to the apertured mirror 21. Led. Then, the observation illumination light is reflected at the peripheral portion (region around the hole) of the apertured mirror 21, passes through the dichroic mirror 46, is refracted by the objective lens 22, and illuminates the eye E (fundus oculi Ef) Do. The return light of the observation illumination light from the eye E to be examined is refracted by the objective lens 22, transmitted through the dichroic mirror 46, transmitted through the hole formed in the central region of the apertured mirror 21, and transmitted through the dichroic mirror 55. The light beam is reflected by the mirror 32 via the photographing focusing lens 31. Further, this return light passes through the half mirror 33 A, is reflected by the dichroic mirror 33, and is imaged on the light receiving surface of the image sensor 35 by the imaging lens 34. The image sensor 35 detects the return light at a predetermined frame rate. The focus of the photographing optical system 30 is adjusted to coincide with the fundus oculi Ef or the anterior segment.

  The light (shooting illumination light) output from the shooting light source 15 is applied to the fundus oculi Ef through the same path as the observation illumination light. The return light of the photographing illumination light from the eye E to be examined is guided to the dichroic mirror 33 through the same path as the return light of the observation illumination light, passes through the dichroic mirror 33, is reflected by the mirror 36, and is focused by the imaging lens 37. An image is formed on the light receiving surface of the image sensor 38.

  A liquid crystal display (LCD) 39 displays a fixation target (fixation target image). A part of the light beam output from the LCD 39 is reflected by the half mirror 33A, reflected by the mirror 32, passes through the imaging focusing lens 31 and the dichroic mirror 55, and passes through the hole of the apertured mirror 21. The light flux that has passed through the hole of the apertured mirror 21 passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus oculi Ef. Fixation targets are typically used for visual guidance and fixation. The direction in which the line of sight of the subject eye E is guided (and fixed), that is, the direction in which the fixation of the subject eye E is urged is referred to as a fixation position.

  By changing the display position of the fixation target image on the screen of the LCD 39, it is possible to change the fixation position of the eye to be examined E by the fixation target. As an example of the fixation position, a fixation position for acquiring an image centered on the macula, a fixation position for acquiring an image centered on the optic disc, a position between the macula and the optic disc ( There are a fixation position for acquiring an image centered on the ocular fundus) and a fixation position for acquiring an image of a part far from the macula (peripheral part of the fundus).

  A graphical user interface (GUI) or the like may be provided to designate at least one of such typical fixation positions. In addition, a GUI or the like for moving the fixation position (display position of fixation target) manually can be provided. It is also possible to apply a configuration in which the fixation position is automatically set.

  The configuration for presenting a fixation target whose fixation position can be changed to the eye to be examined E is not limited to a display device such as an LCD. For example, a device (fixation matrix) in which a plurality of light emitting units (light emitting diodes or the like) are arranged in a matrix can be employed instead of the display device. In this case, the fixation position of the eye to be examined E by the fixation target can be changed by selectively turning on the plurality of light emitting units. As another example, a device provided with one or more movable light emitters can generate a fixation target whose fixation position can be changed.

  The alignment optical system 50 generates an alignment index used to align the optical system with the eye E. The alignment light output from the light emitting diode (LED) 51 passes through the diaphragm 52, the diaphragm 53, and the relay lens 54, is reflected by the dichroic mirror 55, passes through the hole of the apertured mirror 21, and passes through the dichroic mirror 46. The light is transmitted through the objective lens 22 and projected onto the eye E. The return light (corneal reflection light etc.) from the eye E to be inspected of the alignment light is guided to the image sensor 35 through the same path as the return light of the observation illumination light. Manual alignment and auto alignment can be performed based on the light reception image (alignment index image).

  The focusing optical system 60 generates a split index used for focus adjustment on the eye E. The focusing optical system 60 is moved along the light path (illumination light path) of the illumination optical system 10 in conjunction with the movement of the photographing focusing lens 31 along the light path (shooting light path) of the photographing optical system 30. The reflector bar 67 is inserted into and removed from the illumination light path. When the focus adjustment is performed, the reflection surface of the reflection rod 67 is inclined to the illumination light path. The focus light output from the LED 61 passes through the relay lens 62, is split into two light beams by the split index plate 63, passes through the two-hole aperture 64, is reflected by the mirror 65, and is reflected by the focusing lens 66 The light is once imaged and reflected on the reflective surface of. Further, the focus light passes through the relay lens 20, is reflected by the aperture mirror 21, passes through the dichroic mirror 46, and is projected onto the eye E via the objective lens 22. The return light from the eye E to be examined (e.g., fundus reflected light) of the focus light is guided to the image sensor 35 through the same path as the return light of the alignment light. Manual focusing or auto focusing can be performed based on the light reception image (split index image).

  The diopter correction lenses 70 and 71 can be selectively inserted into the imaging optical path between the aperture mirror 21 and the dichroic mirror 55. The diopter correction lens 70 is a plus lens (convex lens) for correcting intensity hyperopia. The diopter correction lens 71 is a minus lens (concave lens) for correcting the intensity myopia.

  The dichroic mirror 46 combines the fundus imaging light path and the OCT light path (measurement arm). The dichroic mirror 46 reflects light in a wavelength band used for OCT and transmits light for fundus imaging. In the measurement arm, a collimator lens unit 40, a retroreflector 41, a dispersion compensation member 42, an OCT focusing lens 43, an optical scanner 44, and a relay lens 45 are provided in order from the OCT unit 100 side.

  The retroreflector 41 is movable in the direction of the arrow shown in FIG. 2, whereby the length of the measuring arm is changed. The change of the measurement arm length is used, for example, for optical path length correction according to the axial length, adjustment of the interference state, and the like.

  The dispersion compensating member 42 acts to match the dispersion characteristic of the measurement light LS with the dispersion characteristic of the reference light LR, together with the dispersion compensating member 113 (described later) disposed in the reference arm.

  The OCT focusing lens 43 is moved along the measurement arm to perform focus adjustment of the measurement arm. The movement of the imaging focusing lens 31, the movement of the focusing optical system 60, and the movement of the OCT focusing lens 43 can be cooperatively controlled.

  The light scanner 44 is disposed substantially at a position optically conjugate with the pupil of the eye E. The optical scanner 44 deflects the measurement light LS guided by the measurement arm. The optical scanner 44 is, for example, a galvano scanner capable of two-dimensional scanning. Typically, the optical scanner 44 is a one-dimensional scanner (x-scanner) for deflecting the measurement light in the ± x direction, and a one-dimensional scanner (y-scanner) for deflecting the measurement light in the ± y direction. And. In this case, for example, either one of the one-dimensional scanners is disposed at a position optically conjugate with the pupil, or a position optically conjugate with the pupil is disposed between the one-dimensional scanners.

<OCT unit 100>
The exemplary OCT unit 100 shown in FIG. 3 is provided with an optical system for performing the swept source OCT. This optical system includes an interference optical system. This interference optical system divides the light from the wavelength variable light source into the measurement light and the reference light, superimposes the return light of the measurement light projected onto the eye to be examined E and the reference light via the reference light path, and thereby generates interference light. To detect this interference light. The data (detection signal) obtained by the detection of the interference light is a signal representing the spectrum of the interference light, and is sent to the arithmetic control unit 200.

  The light source unit 101 includes, for example, a near-infrared wavelength tunable laser that changes the wavelength of emitted light at high speed. The light L0 output from the light source unit 101 is guided to the polarization controller 103 by the optical fiber 102, and its polarization state is adjusted. Further, the light L0 is guided to the fiber coupler 105 by the optical fiber 104 and split into the measurement light LS and the reference light LR. The optical path of the measurement light LS is called a measurement arm or the like, and the optical path of the reference light LR is called a reference arm or the like.

  The reference light LR generated by the fiber coupler 105 is guided to the collimator 111 by the optical fiber 110 and converted into a parallel light beam, and is guided to the retroreflector 114 via the optical path length correction member 112 and the dispersion compensation member 113. The optical path length correction member 112 acts to match the optical path length of the reference light LR with the optical path length of the measurement light LS. The dispersion compensation member 113 works with the dispersion compensation member 42 disposed in the measurement arm to match the dispersion characteristics between the reference light LR and the measurement light LS. The retroreflector 114 is movable along the optical path of the reference light LR incident thereon, whereby the length of the reference arm is changed. The change of the reference arm length is used, for example, for optical path length correction according to the axial length, adjustment of the interference state, and the like.

  The reference light LR that has passed through the retroreflector 114 passes through the dispersion compensation member 113 and the optical path length correction member 112, is converted from a parallel light beam into a focused light beam by the collimator 116, and enters the optical fiber 117. The reference light LR incident on the optical fiber 117 is guided to the polarization controller 118 to adjust its polarization state, guided to the attenuator 120 through the optical fiber 119 to adjust its light amount, and to the fiber coupler 122 through the optical fiber 121. Led.

  On the other hand, the measurement light LS generated by the fiber coupler 105 is guided to the collimator lens unit 40 through the optical fiber 127 and converted into a parallel light beam, and the retroreflector 41, the dispersion compensation member 42, the OCT focusing lens 43, and the light scanner 44. The light beam is reflected by the dichroic mirror 46 via the relay lens 45, refracted by the objective lens 22, and projected onto the eye E. The measurement light LS is scattered and reflected at various depth positions of the eye E. The return light from the eye E to be examined of the measurement light LS travels the measurement arm in the reverse direction, is guided to the fiber coupler 105, and reaches the fiber coupler 122 via the optical fiber 128.

  The fiber coupler 122 superimposes the measurement light LS incident through the optical fiber 128 and the reference light LR incident through the optical fiber 121 to generate interference light. The fiber coupler 122 splits the generated interference light at a predetermined branching ratio (for example, 1: 1) to generate a pair of interference lights LC. The pair of interference lights LC are guided to the detector 125 through the optical fibers 123 and 124, respectively.

  The detector 125 includes, for example, a balanced photodiode. The balanced photodiode includes a pair of photodetectors that respectively detect the pair of interference lights LC, and outputs the difference between the pair of detection signals obtained by these. The detector 125 sends this output (a detection signal such as a differential signal) to a data acquisition system (DAQ) 130.

  The clock KC is supplied to the data acquisition system 130 from the light source unit 101. The clock KC is generated in the light source unit 101 in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the wavelength tunable light source. For example, the light source unit 101 branches the light L0 of each output wavelength to generate two branched lights, optically delays one of the branched lights, combines the branched lights, and obtains the combined light obtained. A clock KC is generated based on the detection signal. The data acquisition system 130 performs sampling of the detection signal (difference signal) input from the detector 125 based on the clock KC. The data acquisition system 130 sends the data obtained by this sampling to the arithmetic control unit 200.

  In this example, both an element for changing the measurement arm length (for example, retro reflector 41) and an element for changing the reference arm length (for example, retro reflector 114 or reference mirror) are provided. However, only one of these elements may be provided. Also, the element for changing the difference between the measurement arm length and the reference arm length (optical path length difference) is not limited to these, and it is possible to adopt any element (optical member, mechanism, etc.) .

<Operation control unit 200>
The arithmetic control unit 200 controls each part of the fundus camera unit 2, the display device 3 and the OCT unit 100. The arithmetic control unit 200 also executes various arithmetic processes. For example, the arithmetic control unit 200 performs signal processing such as Fourier transform on the spectrum distribution based on the sampling data group obtained by the data acquisition system 130 for each series of wavelength scans (for each A line). Form a reflection intensity profile at the line. Furthermore, the arithmetic control unit 200 forms image data by imaging the reflection intensity profile of each A line. The calculation process for that is similar to the conventional swept source OCT.

  The arithmetic and control unit 200 includes, for example, a processor, a random access memory (RAM), a read only memory (ROM), a hard disk drive, a communication interface, and the like. Various computer programs are stored in a storage device such as a hard disk drive. The arithmetic and control unit 200 may include an operation device, an input device, a display device, and the like.

Control system
The example of a structure of the control system (processing system) of the ophthalmologic imaging device 1 is shown in FIG.4 and FIG.5. The control unit 210, the image forming unit 220, and the data processing unit 230 are provided, for example, in the arithmetic control unit 200.

<Control unit 210>
The control unit 210 includes a processor and controls each unit of the ophthalmologic imaging apparatus 1. Control unit 210 includes a main control unit 211 and a storage unit 212.

<Main control unit 211>
The main control unit 211 includes a processor and controls each element (including the elements shown in FIGS. 2 to 5) of the ophthalmic imaging apparatus 1. The main control unit 211 is realized by the cooperation of hardware including a circuit and control software.

  The imaging focusing lens 31 disposed in the imaging optical path and the focusing optical system 60 disposed in the illumination optical path are moved by an imaging focusing drive unit (not shown) under the control of the main control unit 211. The retroreflector 41 provided on the measurement arm is moved by the retroreflector (RR) drive unit 41A under the control of the main control unit 211. The OCT focusing lens 43 disposed in the measurement arm is moved by the OCT focusing drive unit 43A under the control of the main control unit 211. The light scanner 44 provided in the measurement arm operates under the control of the main control unit 211. The retroreflector 114 disposed in the reference arm is moved by the retroreflector (RR) drive unit 114A under the control of the main control unit 211. Each of these drive units includes an actuator such as a pulse motor that operates under the control of the main control unit 211.

  The moving mechanism 150 three-dimensionally moves at least the fundus camera unit 2, for example. In a typical example, the moving mechanism 150 includes an x-stage movable in the ± x direction (horizontal direction), an x-moving mechanism for moving the x stage, and a y stage movable in the ± y direction (vertical direction) , A y moving mechanism for moving the y stage, a z stage movable in the ± z direction (depth direction), and a z moving mechanism for moving the z stage. Each of these moving mechanisms includes an actuator such as a pulse motor that operates under the control of the main control unit 211.

<Storage unit 212>
The storage unit 212 stores various data. Examples of data stored in the storage unit 212 include image data of an OCT image, image data of a fundus image, and eye information to be examined. The subject's eye information includes subject information such as patient ID and name, identification information of left eye / right eye, electronic medical record information, and the like.

  The storage unit 212 may store positional relationship information indicating a positional relationship between an imaging range (fundus photographing region) in fundus imaging and a range (three-dimensional scanning region) to which a three-dimensional OCT scan is applied. . The fundus imaging region may be defined, for example, by the features (for example, the shape and size) of the region depicted as a front image by the fundus imaging function of the ophthalmologic imaging device 1. In addition, the three-dimensional scan area may be defined by, for example, the features (for example, the shape and size) of the area depicted as a three-dimensional image by the OCT function of the ophthalmologic imaging apparatus 1.

  Here, the feature of the area depicted as a three-dimensional image may be the feature of the area depicted as a rendered image of this three-dimensional image. As a specific example, the feature of the area depicted as a three-dimensional image is the feature of the area depicted as a projection image obtained by projecting the three-dimensional image in the z direction, or a part of the three-dimensional image in the z direction It may be a feature of the area depicted in a shadowgram obtained by projecting onto (eg, two-dimensional shape, area, circumference, diameter).

  The projection image and the shadowgram are frontal images, and can be defined in the same two-dimensional coordinate system (xy coordinate system) as the frontal image obtained by the fundus imaging function. When a three-dimensional image is considered instead of such a two-dimensional image, the definition coordinate system (xy coordinate system) of the front image obtained by the fundus imaging function is set to the definition coordinate system (xyz coordinate system) of the three-dimensional image. It is possible to embed.

  In the present embodiment, as described above, the fundus imaging light path and the OCT light path (measurement arm) are coupled by the dichroic mirror 46. More specifically, the dichroic mirror 46 coaxially couples the fundus imaging light path and the measurement arm. That is, the dichroic mirror 46 couples the fundus imaging optical path and the measurement arm such that the optical axis of the fundus imaging optical path and the optical axis of the measurement arm intersect.

  Furthermore, as mentioned above, the dimensions of the OCT scan are defined by the maximum deflection angle of the measuring light. Therefore, in the present embodiment, the three-dimensional scan area is defined by the maximum deflection angle (maximum deflection angle in the x direction and maximum deflection angle in the y direction) of the measurement light LS by the optical scanner 44.

  Further, in the present embodiment, as in a typical fundus camera, an optical member (shooting field stop) for defining the contour of the fundus imaging region is disposed, or in order to define the contour of the fundus imaging region The digital aperture is set for the image sensors 35 and 38 in FIG.

  An example of the positional relationship between the fundus imaging region and the three-dimensional scan region will be described with reference to FIG. Reference numeral 300 denotes an optical axis (objective optical axis) 300 of the objective lens 22, reference numeral 310 denotes a fundus imaging region (the outline thereof), and reference numeral 320 denotes a three-dimensional scan region (the outline thereof). The fundus imaging region 310 is circular, and the center thereof is disposed on the objective optical axis 300. The three-dimensional scan area 320 is a square, the center of which is disposed on the objective optical axis 300. That is, in this example, the fundus imaging region 310 and the three-dimensional scan region 320 are arranged coaxially with each other. In addition, the fundus imaging region 310 truly includes a three-dimensional scan region 320.

  The shape and / or size of the fundus imaging region 310 may be fixed or variable. The change of the shape and / or size of the fundus imaging region 310 can be realized, for example, by selection of the imaging field stop, control of the aperture size of the imaging field stop, or control of the digital aperture.

  The shape and / or dimensions of the three-dimensional scan area 320 may be fixed or variable. For example, control of the optical scanner 44 (for example, control of the maximum deflection angle, control of the x-scanner, control of the y-scanner, control of the y-scanner, x-scanner and y-scanner) Can be realized by cooperative control with

  The relative position between the fundus imaging region 310 and the three-dimensional scan region 320 may be fixed or variable. The change of the relative position between the fundus imaging region 310 and the three-dimensional scan region 320 can be performed, for example, by one or a combination of two or more of the following controls: the shape of the fundus imaging region 310 And / or change of size; change of position of fundus imaging area 310; change of shape and / or size of three-dimensional scan area 320; change of position of three-dimensional scan area 320. Here, the change of the position of the fundus imaging region 310 can be realized, for example, by selection of the imaging field stop, control of the aperture position of the imaging field stop, or control of the digital aperture. In addition, the change of the position of the three-dimensional scan area 320 can be realized, for example, by the control of the optical scanner 44.

  When the fundus imaging region 310 and the three-dimensional scan region 320 are arranged non-coaxially with each other, for example, relative displacement between the center of the fundus imaging region 310 and the center of the three-dimensional scan region 320 and / or the fundus The relative position between the fundus imaging region 310 and the three-dimensional scan region 320 can be determined in advance or at any time by the relative position between the contour of the imaging region 310 and the contour of the three-dimensional scan region 320 .

  In the present embodiment, the positional relationship between the fundus imaging region 310 and the three-dimensional scan region 320 obtained according to any of the above examples is stored in the storage unit 212 as positional relationship information in advance or as needed. Ru. Such positional relationship information includes, for example, relative position information between the fundus imaging region 310 and the three-dimensional scan region 320 as illustrated in FIG. 6, setting information and / or control information regarding the fundus imaging region 310, and At least one of setting information and / or control information on the three-dimensional scan area 320 may be included.

<Image Forming Unit 220>
The image forming unit 220 forms image data based on the data acquired by the data acquisition system 130. The image forming unit 220 includes a processor. The image forming unit 220 is realized by the cooperation of hardware including a circuit and image forming software.

  The image forming unit 220 forms cross-sectional image data based on the data acquired by the data acquisition system 130. This processing includes signal processing such as noise removal (noise reduction), filter processing, and fast Fourier transform (FFT) as in the case of the conventional swept source OCT.

  The image data formed by the image forming unit 220 is a group of images formed by imaging the reflection intensity profile at a plurality of A lines (scan lines along the z direction) arranged in the area to which the OCT scan is applied. It is a data set including image data (a group of A scan image data).

  The image data formed by the image forming unit 220 is, for example, one or more B-scan image data or stack data formed by embedding a plurality of B-scan image data in a single three-dimensional coordinate system. The image forming unit 220 can also process the stack data into voxels to form volume data (voxel data). Stack data and volume data are typical examples of 3D image data represented by a 3D coordinate system.

  When OCT angiography is performed, the main control unit 211 repeatedly scans the same region of the fundus oculi Ef a predetermined number of times. The image forming unit 220 can form a motion contrast image based on the data set acquired by the data acquisition system 130 in this repetitive scan. The motion contrast image is an angiographic image imaged by emphasizing a temporal change of the interference signal caused by the blood flow of the fundus oculi Ef. Typically, OCT angiography is applied to a three-dimensional area of the fundus oculi Ef, and an image representing a three-dimensional distribution of blood vessels of the fundus oculi Ef is obtained.

  The image forming unit 220 can process three-dimensional image data. For example, the image forming unit 220 can apply rendering to three-dimensional image data to construct new image data. As the rendering method, there are volume rendering, maximum value projection (MIP), minimum value projection (MinIP), surface rendering, multi-section reconstruction (MPR) and the like. Further, the image forming unit 220 can construct projection data by projecting three-dimensional image data in the z direction (A line direction, depth direction). The image forming unit 220 can also construct a shadowgram by projecting a part of three-dimensional image data in the z direction. Note that a part of three-dimensional image data to be projected to construct a shadowgram is set, for example, using segmentation described later.

  When OCT angiography is performed, the image forming unit 220 can construct arbitrary two-dimensional angiographic image data and / or arbitrary pseudo three-dimensional angiographic image data from three-dimensional angiographic image data It is. For example, the image forming unit 220 can construct two-dimensional angiographic image data representing an arbitrary cross section of the fundus oculi Ef by applying multi-sectional reconstruction to the three-dimensional angiographic image data. In addition, it is possible to construct front angiographic image data by projecting three-dimensional angiographic image data or a part thereof in the z direction.

<Data processing unit 230>
The data processing unit 230 executes various data processing. For example, the data processing unit 230 can apply image processing and analysis processing to OCT image data, and can apply image processing and analysis processing to observation image data or captured image data. The data processing unit 230 includes, for example, at least one of a processor and a dedicated circuit board.

  The configuration of an exemplary data processing unit 230 is shown in FIG. The data processing unit 230 of this example includes a rendering position determination unit 231, a fixation position setting unit 232, and an image processing unit 233. The fixation system 250 is configured to present a fixation target to the eye E. The fixation system 250 of this example includes an LCD 39 and an optical system for projecting the light flux output from the LCD 39 onto the fundus oculi Ef. Further, the OCT image acquisition unit 260 is configured to apply an OCT to the fundus oculi Ef of the eye to be examined E to acquire an image. The OCT image acquisition unit 260 of this example includes an element group constituting a measurement arm provided in the fundus camera unit 2, an element group provided in the OCT unit 100, and an image forming part 220. The imaging unit 270 is also configured to image the fundus oculi Ef. The imaging unit 270 of this example includes the illumination optical system 10 and the imaging optical system 30.

<Deposition position determination unit 231>
The depiction position determination unit 231 analyzes the front image acquired by the imaging unit 270, and determines whether a predetermined region of the fundus oculi Ef is depicted in a predetermined region of the front image.

  In the present example, the predetermined site of the fundus oculi Ef may be, for example, the macula (macular center, fovea centralis), the optic nerve head (papillary center), a desired blood vessel position, or a lesion. Typically, the macula is applied.

  Further, in this example, the predetermined area of the front image may be, for example, a one-dimensional partial area or a two-dimensional partial area in a frame (imaging area) of the front image. Typically, two-dimensional subregions are applied. In this example, two-dimensional partial regions in the frame of the front image are set in advance.

  In the first example, the depiction position determination unit 231 first specifies an image area corresponding to a predetermined region (macular, optic nerve head, etc.) of the fundus oculi Ef by analyzing the front image acquired by the imaging unit 270. . The image area specified by this analysis is, for example, an image area corresponding to a predetermined part of the fundus oculi Ef, an image area corresponding to a contour of a predetermined part of the fundus oculi Ef, or a predetermined position of the fundus oculi Ef (macular center, papillary center, etc. It may be a pixel corresponding to. The analysis for specifying such an image area may include, for example, threshold processing on pixel values, edge detection, template matching, and the like. Next, the presentation position determination unit 231 determines whether the image area is included in the predetermined area by comparing the coordinates of the specified image area with the coordinates of the predetermined area.

  A typical example is described. First, the depiction position determination unit 231 analyzes the front image acquired by the imaging unit 270, and specifies an image region (macular region) corresponding to the macula. Next, the depiction position determination unit 231 specifies the coordinates of the center position (macular center) of the macular region. The macular center is specified, for example, as the barycentric position of the macular region, or as the central position of the approximate ellipse (or approximate circle) of the contour of the macular region. Subsequently, the depicting position determination unit 231 compares the coordinates of the identified macular center with the range of the coordinates corresponding to the predetermined area, using the two-dimensional coordinate system in which the front image is defined. In other words, the depiction position determination unit 231 determines whether the coordinates of the macular center are included in the range of coordinates corresponding to the predetermined area. When the coordinates of the macular center are included in the range of the coordinates corresponding to the predetermined area, it is determined that the macular center (predetermined portion) is drawn in the predetermined area of the front image. On the other hand, when the coordinates of the macular center are not included in the range of the coordinates corresponding to the predetermined area, it is determined that the macular center (predetermined portion) is not depicted in the predetermined area of the front image.

  In this typical example, the predetermined site is a single point (macular center), but the embodiment is not limited thereto, and the predetermined site may have a one-dimensional or two-dimensional spread. For example, the predetermined site may be the entire macula or the entire optic disc. When the predetermined part has a spread, for example, the drawing position determination unit 231 may be configured to determine whether at least a part of the predetermined part is drawn in the predetermined area. As another example, the depiction position determination unit 231 may be configured to determine whether the entire predetermined site is depicted in the predetermined area.

  The second example will be described. In the second example, the depiction position determination unit 231 analyzes a predetermined area (or a predetermined area and its vicinity area) in the front image acquired by the imaging unit 270, so that the predetermined region of the fundus oculi Ef is the predetermined area. It is determined whether it is depicted in the area. This analysis may be performed, for example, in the same manner as the first example.

  The processing that can be performed by the imaging position determination unit 231 is not limited to the above example, and it can be determined whether or not a predetermined region of the fundus oculi Ef is visualized in a predetermined area of the front image acquired by the imaging unit 270 May be any process.

  The rendering position determination unit 231 includes an image processing processor and an image analysis processor. The image processing processor is realized by the cooperation of hardware including a circuit and image processing software. Also, an image analysis processor is realized by the cooperation of hardware including a circuit and image analysis software.

<Fixed position setting unit 232>
The fixation position setting unit 232 sets a fixation position for applying the OCT to the fundus oculi Ef. In particular, the fixation position setting unit 232 can set a fixation position for applying panoramic imaging (panoramic OCT) to the fundus oculi Ef based on the front image of the fundus oculi Ef acquired by the imaging unit 270. is there. The processing that can be executed by the fixation position setting unit 232 of this example will be described later.

  The fixation position setting unit 232 includes a processor that sets a fixation position. The processor is realized by the cooperation of hardware including a circuit and software.

<Image processing unit 233>
The image processing unit 233 processes the OCT image acquired by the OCT image acquisition unit 260. For example, the image processing unit 233 can apply segmentation to two-dimensional cross-sectional image data or three-dimensional image data. Segmentation is a process of identifying partial regions in an image. Typically, segmentation is used to identify an image area corresponding to a predetermined tissue of the fundus oculi Ef.

  As described above, the image forming unit 220 can construct the shadowgram (front angiographic image data or the like) by projecting the image region specified by the segmentation in the z direction. As an example of a shadowgram, a shadowgram corresponding to an arbitrary depth region of the fundus oculi Ef (for example, shallow retina, deep retina, choroidal capillary plate, sclera, etc.), arbitrary tissue (for example, inner limiting membrane, Nerve fiber layer, ganglion cell layer, inner plexiform layer, inner granular layer, outer plexiform layer, outer granular layer, outer limiting membrane, retinal pigment epithelium, Bruch's membrane, choroid, choroid-scleral border, sclera, any of these Some of them, such as a combination of at least two or more).

  The image processing unit 233 may be capable of processing an image (an observation image, a photographed image, etc.) acquired by the photographing unit 270 or processing an image acquired by another ophthalmologic photographing apparatus.

  The image processing unit 233 includes an image processing processor and an image analysis processor. The image processing processor is realized by the cooperation of hardware including a circuit and image processing software. Also, an image analysis processor is realized by the cooperation of hardware including a circuit and image analysis software.

  The processing that can be executed by the image processing unit 233 of this example will be described later.

<Composition processing unit 2331>
The image processing unit 233 includes a combination processing unit 2331. The composition processing unit 2331 forms a composite image of two or more three-dimensional images acquired corresponding to two or more different fixation positions in panoramic imaging. The processing that can be executed by the combining processing unit 2331 of this example will be described later.

<User Interface 240>
The user interface 240 includes a display unit 241 and an operation unit 242. The display unit 241 includes the display device 3. The operation unit 242 includes various operation devices and input devices. The user interface 240 may include, for example, a device such as a touch panel in which a display function and an operation function are integrated. It is also possible to construct an embodiment that does not include at least a portion of the user interface 240. For example, the display device may be an external device connected to the ophthalmologic imaging device.

<About panorama shooting>
The panoramic imaging that can be performed in this example will be described. In this example, fundus imaging is preliminarily applied to set a fixation position for panoramic imaging. The preliminary fundus imaging includes, for example, a first preliminary fundus imaging for setting an initial position (initial fixation position) of a fixation target, and a plurality of solid imagings for a plurality of OCT performed in panoramic imaging. And second preliminary fundus imaging to set the viewing position. In the second preliminary fundus imaging, fundus imaging is repeatedly performed while changing the position of fixation.

  The execution of the first preliminary fundus imaging is optional. The second preliminary fundus imaging may be performed without the first preliminary fundus imaging. If the first preliminary fundus imaging is not performed, for example, in the second preliminary fundus imaging, changing the fixation position can be started from the default initial fixation position. Alternatively, if the first preliminary fundus imaging is not performed, the change in the fixation position may be started from the initial fixation position set by the user in the second preliminary fundus imaging.

  On the other hand, when the first preliminary fundus imaging is performed, for example, in the second preliminary fundus imaging, changing the fixation position from the initial fixation position set in the first preliminary fundus imaging It can start. Alternatively, if the first preliminary fundus imaging is performed, the user may correct the initial fixation position set in the first preliminary fundus imaging in the second preliminary fundus imaging, or It may be possible to automatically or manually select one of the initial fixation position set in preliminary fundus imaging and the default initial fixation position.

<About the first preliminary fundus photography etc>
An example of the first preliminary fundus imaging will be described. In the first preliminary fundus imaging, the main control unit 211 presents to the eye E a fixation target corresponding to a first fixation position for acquiring a front image centering on a predetermined region of the fundus oculi Ef. At the same time, the fixation system 250 and the imaging unit 270 are controlled to acquire a front image (referred to as a preliminary front image) of the fundus oculi Ef. In this example, the macula (macular center, fovea centralis) is adopted as a typical example of this predetermined site (that is, the first fixation position), but other sites of the fundus (for example, optic nerve head or fundus center) It may be a site.

  The image processing unit 233 calculates the deviation of the image of the predetermined part of the fundus oculi Ef with respect to the center position of the preliminary front image.

  For example, the image processing unit 233 first analyzes the preliminary front image to obtain the coordinates of the pixel corresponding to the macular center. Subsequently, the image processing unit 233 obtains a difference between the coordinates of the identified macula center and the coordinates of the center position of the preliminary front image. The difference between the coordinates of the macular center and the coordinates of the center position of the preliminary frontal image is the deviation of the actual macular center with respect to the center position of the fundus imaging area (shooting field) applied in the first preliminary fundus imaging. It corresponds to

  The fixation position setting unit 232 can correct the first fixation position based on the deviation obtained by the image processing unit 233. For example, the fixation position setting unit 232 corrects the first fixation position so that the deviation obtained by the image processing unit 233 is canceled (that is, the deviation becomes zero). As a result, the central position of the fundus imaging region (the central position of panoramic imaging) is substantially matched with the portion (the macular center) corresponding to the first fixation position.

  Further, the fixation position setting unit 232 can correct the default initial fixation position. As a specific example, the fixation position setting unit 232 is configured to maintain the relative position between the first fixation position and the second fixation position (predetermined peripheral fixation position). The same amount of correction as that of the visual position can be applied to the second fixation position. That is, the fixation position setting unit 232 can apply the correction amount corresponding to the inverse vector of the deviation (vector) obtained by the image processing unit 233 to the second fixation position. In this example, the fixation position obtained by correcting the default initial fixation position can be applied as the initial fixation position in the second preliminary fundus imaging.

  The process for setting the initial fixation position applied in the second preliminary fundus imaging is not limited to this example. As an example, the initial fixation position can be set based on the fundus imaging region by the imaging unit 270 and the depiction position of the macula in the fundus oculi Ef. For example, the fixation position setting unit 232 may calculate a fixation position such that the macula of the fundus oculi Ef is drawn within a predetermined area of the frame of the preliminary front image acquired in the first preliminary fundus imaging it can. This calculation process can be performed based on the relative position (deviation) between the predetermined area of the frame and the depiction position of the macula.

  As described above, when the initial fixation position is set by the fixation position setting unit 232, it is possible to apply the initial fixation position and execute the second preliminary fundus imaging. Moreover, as described above, it is also possible to correct this initial fixation position.

  The initial fixation position applied to the second preliminary fundus imaging is a fixation position for acquiring a front image centered on a position at a predetermined distance from the macula in a predetermined direction on the fundus of a standard eye It may be.

<About the second preliminary fundus photography etc>
An example of the second preliminary fundus imaging will be described. In the second preliminary fundus imaging, the main control unit 211 first makes an initial fixation position set in the first preliminary fundus imaging (or an initial fixation position obtained by correcting the position or a default initial fixation). The fixation system 250 is controlled to present the fixation target corresponding to the visual position etc. to the eye E to be examined. That is, the main control unit 211 controls the fixation system 250 to display the fixation target at the display position (pixel) of the LCD 39 corresponding to the initial fixation position, for example.

  Furthermore, the main control unit 211 repeats the front image of the fundus oculi Ef while moving the fixation target initially presented to the initial fixation position (that is, changing the fixation position starting from the initial fixation position). The fixation system 250 and the imaging unit 270 are controlled so as to acquire them. The fundus imaging by the imaging unit 270 is, for example, acquisition of an observation image at a predetermined frame rate or acquisition of a photographed image at a predetermined repetition rate. Thereby, a plurality of frontal images corresponding to a plurality of fixation positions are obtained. Further, the main control unit 211 associates, with each front image acquired by the imaging unit 270, information indicating a fixation position when the front image is acquired.

  Here, the movement pattern of the fixation target may be, for example, a predetermined pattern or a pattern determined based on front images sequentially acquired. In the latter case, for example, the data processing unit 230 (the presentation position determination unit 231) first analyzes the front image to determine whether the macula of the fundus oculi Ef is depicted.

  When it is determined that the macula is not depicted in the front image, for example, the data processing unit 230 (the fixation position setting unit 232) determines the relative position between the macula and the initial fixation position and the initial fixation position. Based on the movement content (moving direction, movement amount) to the fixation position, it is possible to determine the next fixation position at which the macula is depicted in the front image to be acquired next. This process can be repeated until the macula is depicted in the frontal image. Alternatively, the main control unit 211 may enlarge the size of the fundus imaging region.

  If it is determined that the macula is rendered in the front image, for example, the rendering position determination unit 231 analyzes this front image to determine whether the macula is rendered in a predetermined region of the front image. This process can be performed as described above.

  When the macula is not depicted in the predetermined area of the front image, for example, the data processing unit 230 (the fixation position setting unit 232) is acquired next based on the relative position between the visualization position of the macula and the predetermined area. The next fixation position can be determined such that the macula is depicted within a predetermined area of the frontal image. This process can be repeated until the macula is visualized in the predetermined area.

  When the macula is drawn in a predetermined area of the front image, the fixation position setting unit 232 determines one or more solid images for panoramic imaging based on the position of the fixation target when the front image is acquired. The viewing position can be set.

  A specific example of such processing will be described. The code Mc shown in FIG. 7 indicates the position of the macula (macular center) of the fundus oculi Ef. Reference numeral 400 indicates the position of the fixation target (the fixation position). Reference numeral 401 denotes a fundus imaging region centered on the fixation position 400. Reference numeral 402 denotes a predetermined area in the fundus imaging area 401.

  In the example shown in FIG. 7, the macula Mc is disposed outside the fundus imaging region 401, and the macula is not depicted in the front image obtained by imaging the fundus imaging region 401. In this case, for example, the fixation position setting unit 232 may fix the fixation target based on the information obtained in the first preliminary fundus imaging and the movement of the fixation target up to the present stage in the second preliminary fundus imaging. A new fixation position closer to the macula Mc than the visual position 400 can be set. While the new fixation position is applied, new fundus imaging is performed to acquire a new front image, and the same processing is performed.

  By repeatedly executing the above-described series of processes until the frontal image in which the macula is drawn is obtained, a frontal image in which the macula Mc is drawn is obtained. An example of such a front image is shown in FIG. The code Mc shown in FIG. 8 indicates the macula lutea similarly to FIG. Reference numeral 410 indicates the position of the fixation target at this time (fixation position). Reference numeral 411 denotes a fundus imaging region centered on the fixation position 410. Reference numeral 412 denotes a predetermined area in the fundus imaging area 411.

  In the example shown in FIG. 8, the macula Mc is depicted outside the predetermined area 412. In this case, for example, the fixation position setting unit 232 sets a new solid such that the macular Mc is drawn in the predetermined area of the front image based on the relative position between the drawing position of the macula Mc and the predetermined area 412. The viewing position can be set. With the new fixation position applied, a new fundus imaging area is executed to acquire a new front image, and the same processing is performed.

  The above-described series of processing is repeatedly performed until a frontal image in which the macula is depicted in the predetermined area is obtained. Thereby, as illustrated in FIG. 9, a front image 421 in which the macula Mc is drawn in the predetermined area 422 is obtained. Reference numeral 420 indicates the fixation position at this time. The fixation position setting unit 232 can set the fixation position 420 as one of a plurality of fixation positions for panoramic imaging.

  The position of the predetermined area in the fundus imaging area is set to the side closer to the macula with respect to the fixation position. Further, the size of the predetermined area is set, for example, in accordance with the size of an overlapping area (margin area) for combining a plurality of images in panoramic imaging. Also, the shape of the predetermined area may be set arbitrarily.

  The fixation position setting unit 232 can set two or more of a plurality of fixation positions for panoramic imaging. For example, when the fixation position 420 illustrated in FIG. 9 is set as a fixation position for panoramic imaging, the fixation position setting unit 232 determines the relative position between the fixation position 420 and the macula Mc. Other fixation positions for panoramic imaging can be set.

  As a typical example, the fixation position setting unit 232 is for panoramic imaging at a position symmetrical to the fixation position 420 with respect to the macula Mc on a first straight line passing through the fixation position 420 and the macula Mc. The fixation position can be set. Further, the fixation position setting unit 232 is separated from the macula Mc by the same distance as the distance between the macula Mc and the fixation position 420 on the second straight line orthogonal to the first straight line at the position of the macula Mc A fixation position for panoramic imaging can be set at at least one of the two positions.

  It is also possible to configure the user to arbitrarily set the fixation position for panoramic imaging.

<Operation>
The operation of the ophthalmologic imaging apparatus 1 according to the present embodiment will be described. An example of the operation of the ophthalmologic imaging apparatus 1 is shown in FIG. It is assumed that general preparation processing for fundus imaging, such as patient information input, alignment, and focus adjustment, has already been completed. In addition, general preparation processing for OCT, such as interference sensitivity adjustment and z position adjustment, is performed at any timing.

(S1: Perform the first preliminary fundus imaging)
First, the ophthalmologic imaging apparatus 1 executes the first preliminary fundus imaging described above. The first preliminary fundus imaging is performed to set an initial position (initial fixation position) of fixation movement applied in the second preliminary fundus imaging. In the first preliminary fundus imaging in this example, the main control unit 211 controls the fixation system 250 so as to present a default macular fixation target for the eye E to be examined, and the solid imaging for the macular fixation is performed. The imaging unit 270 is controlled to capture the fundus oculi Ef of the subject eye E on which the target is presented. Thereby, a preliminary frontal image is obtained.

  Here, the default macular fixation target is a visible bright spot typically displayed at the center position of the display screen of the LCD 39 (that is, the position on the optical axis of the light path branched by the half mirror 33A). It is. However, the default macular fixation target is not limited to this.

(S2: Set initial fixation position)
The main control unit 211 sends the preliminary front image acquired in the first preliminary fundus imaging in step S1 to the data processing unit 230. The image processing unit 233 calculates the displacement of the macular image of the fundus oculi Ef with respect to the center position of the preliminary front image. For example, the image processing unit 233 identifies the position of the pixel corresponding to the macular center by analyzing the preliminary front image, and calculates the displacement of this pixel with respect to the central position of the preliminary front image.

  The fixation position setting unit 232 determines the fixation position corresponding to the default fixation target for macular imaging based on the displacement calculated by the image processing unit 233 (that is, the display position of the visible bright spot on the display screen of the LCD 39). ) To correct. The position (macular) of the fundus oculi Ef corresponding to the corrected macular imaging fixation target substantially coincides with the central position of the panoramic imaging performed in the subsequent stage. That is, by applying the parallel movement of the direction and distance corresponding to the inverse vector of the vector represented by the deviation to the default fixation target for macular photography, the default macular is depicted so that the macular is depicted at the center position of the front image. The position of the fixation target for imaging is corrected.

  Furthermore, the fixation position setting unit 232 performs the same correction on the default peripheral fixation position (second fixation position). For example, the fixation position setting unit 232 corrects the default peripheral fixation position (that is, the display position of the visible bright spot on the display screen of the LCD 39) based on the deviation calculated by the image processing unit 233. That is, the peripheral fixation position is corrected by applying the parallel movement of the direction and distance corresponding to the inverse vector of the vector represented by the deviation to the default peripheral fixation position. The corrected default peripheral fixation position is set to the initial fixation position for the second preliminary fundus imaging.

(S3: Start the second preliminary fundus imaging)
When the setting of the initial fixation position (for example, correction of the peripheral fixation position) is completed, the process proceeds to the second preliminary fundus imaging. The second preliminary fundus imaging is performed to set a plurality of fixation positions for panoramic imaging.

  The main control unit 211 displays the visible bright spot on the position (pixel) of the display screen of the LCD 39 corresponding to the peripheral fixation position corrected in step S2.

(S4: Acquire the front image)
Furthermore, the main control unit 211 controls the imaging unit 270 so as to image the fundus oculi Ef and acquire a front image.

(S5: Is the macula drawn?)
The depiction position determination unit 231 analyzes the front image acquired in step S4 and determines whether the macula of the fundus oculi Ef is depicted in the front image. If it is determined that the macula has not been depicted in the front image (S5: No), the process proceeds to step S6. On the other hand, when it is determined that the macula is depicted in the front image (S5: Yes), the process proceeds to step S7.

(S6: Change fixation position)
If it is determined in step S5 that the macula is not depicted in the front image (S5: No), the fixation position setting unit 232 sets the fixation position so as to render the macula in the front image to be acquired next change.

  A series of processes of steps S4 to S6 are repeatedly executed until it is determined “Yes” in step S5, for example. Here, if the series of processes is repeated a predetermined number of times, or if the series of processes is repeated for a predetermined time, error determination can be performed.

(S7: Is the macula within the given area drawn?)
If it is determined in step S5 that the macula is rendered in the front image (S5: Yes), the rendering position determination unit 231 determines whether the macula is rendered in the predetermined area of the front image. If it is determined that the macula is depicted in the predetermined area of the front image (S7: Yes), the process proceeds to step S8.

  On the other hand, when it is determined that the macula has not been depicted in the predetermined region of the front image (S7: No), the process proceeds to step S6. A series of processes of steps S4 to S7 are repeatedly executed, for example, until "Yes" is determined in step S7. Here, if the series of processes is repeated a predetermined number of times, or if the series of processes is repeated for a predetermined time, error determination can be performed.

(S8: Set multiple fixation positions for panoramic shooting)
If it is determined that the macula is depicted in the predetermined area of the front image (S7: Yes), the processing shifts to setting of a fixation position for panoramic imaging. The fixation position setting unit 232 sets a plurality of fixations for panoramic imaging based on the fixation position when the imaging unit 270 acquires the front image determined that the macula is depicted in the predetermined area. Set the position.

  For example, as shown in FIG. 11, the first peripheral fixation position 501 located at the lower left of the macula 500 (the fixation position for macular photography) is set from the movement of the fixation target starting from the initial fixation position. I suppose. The first peripheral fixation position 501 is set at a distance T away from the macula 500 in the lower left direction. In this case, the fixation position setting unit 232 sets (1) the second peripheral fixation position 502 at a position separated by a distance T in the upper left direction from the macula 500, and (2) the distance T in the upper right direction from the macula 500 The third peripheral fixation position 503 can be set at a position away from the macular 500, and the fourth peripheral fixation position 504 can be set at a position separated by a distance T in the lower right direction from the macula 500 (3).

  The number of peripheral fixation positions is not limited to four, and the arrangement of the peripheral fixation positions is not limited to the arrangement shown in FIG. In general, setting (correcting) a plurality of peripheral fixation positions in accordance with an arrangement of a plurality of peripheral fixation positions set in advance (for example, an arrangement of a default, an arrangement designated by the user or the ophthalmologic imaging apparatus 1) Is possible.

(S9: Perform panoramic shooting and acquire multiple 3D images)
The main control unit 211 controls the fixation system 250 so that the plurality of fixation targets corresponding to the plurality of (peripheral) fixation positions set in step S8 are sequentially presented to the eye to be examined E, and The OCT image acquisition unit 260 is controlled to acquire a three-dimensional image of the fundus oculi Ef when each of the fixation targets is presented to the eye E to be examined. The three-dimensional OCT applied here may be three-dimensional OCT angiography.

  As an example, the case where four peripheral fixation positions 501 to 504 shown in FIG. 11 are applied to panoramic imaging will be described.

  First, the main control unit 211 controls the fixation system 250 to present the first peripheral fixation target corresponding to the first peripheral fixation position 501, and the first peripheral fixation target is further presented. The OCT image acquisition unit 260 is controlled to execute a three-dimensional scan in the above state. Thereby, a first peripheral three-dimensional image corresponding to the first peripheral scan range 511 shown in FIG. 11 is acquired. The dimensions of the first peripheral three-dimensional image (first peripheral scan range 511) are W (mm) in both the length in the x direction and the length in the y direction.

  Next, the main control unit 211 controls the fixation system 250 to present a second peripheral fixation target corresponding to the second peripheral fixation position 502, and further, the second peripheral fixation target is The OCT image acquisition unit 260 is controlled to execute a three-dimensional scan in the presented state. Thereby, a second peripheral three-dimensional image corresponding to the second peripheral scan range 512 shown in FIG. 11 is acquired. The dimensions of the second peripheral three-dimensional image (the second peripheral scan range 512) are W (mm) in both the length in the x direction and the length in the y direction.

  Subsequently, the main control unit 211 controls the fixation system 250 so as to present the third peripheral fixation target corresponding to the third peripheral fixation position 503, and further, the third peripheral fixation target is The OCT image acquisition unit 260 is controlled to execute a three-dimensional scan in the presented state. Thereby, a third peripheral three-dimensional image corresponding to the third peripheral scan range 513 shown in FIG. 11 is acquired. The dimensions of the third peripheral three-dimensional image (third peripheral scan range 513) are W (mm) in both the length in the x direction and the length in the y direction.

  Finally, the main control unit 211 controls the fixation system 250 to present a fourth peripheral fixation target corresponding to the fourth peripheral fixation position 504, and further, the fourth peripheral fixation target is The OCT image acquisition unit 260 is controlled to execute a three-dimensional scan in the presented state. Thereby, a fourth peripheral three-dimensional image corresponding to the fourth peripheral scan range 514 shown in FIG. 11 is acquired. The dimensions of the fourth peripheral three-dimensional image (the fourth peripheral scan range 514) are W (mm) in both the length in the x direction and the length in the y direction.

  Also, two neighboring three-dimensional images adjacent to each other have overlapping regions (margins) of a suitable width for combining them. For example, in the example illustrated in FIG. 11, the first peripheral scan range 511 and the second peripheral scan range 512 have overlapping regions of width ΔW, and the second peripheral scan range 512 and the third peripheral scan range 513 Has an overlapping area of width ΔW, and the third peripheral scan area 513 and the fourth peripheral scan area 514 have an overlapping area of width ΔW, and a fourth peripheral scan area 514 and a first peripheral scan The range 511 has an overlapping area of width ΔW.

(S10: form a composite image)
The composition processing unit 2331 forms a composite image (mosaic image) of the plurality of three-dimensional images acquired in step S9. As an example, in the example illustrated in FIG. 11, the combining processing unit 2331 combines the first to fourth peripheral three-dimensional images to form a single three-dimensional image. In addition, it is also possible to combine two or more arbitrary three-dimensional images of the plurality of three-dimensional images acquired in step S9.

  The process of combining a plurality of three-dimensional images is, for example, as in the conventional image combining technique, matching of overlapping areas using image correlation or the like, positioning of surrounding three-dimensional images using the matching result, and , And combining with these peripheral three-dimensional images.

(S11: Display and save composite image)
The main control unit 211 can cause the display unit 241 to display the composite image formed in step S10. Further, the main control unit 211 stores the composite image in the storage unit 212, performs control for transmitting the composite image to an external device, and performs control for recording the composite image on the recording medium. Is possible.

  In addition, the main control unit 211 causes the display unit 241 to display a part or all of the plurality of three-dimensional images formed in step S9, stores the composite image in the storage unit 212, or combines the images in the external device. It is possible to perform control for transmitting an image, and control for recording a composite image on a recording medium. This is the end of the process according to this example.

<Operation / Effect>
The operation and effects of the ophthalmologic imaging apparatus 1 according to the present embodiment will be described.

  The ophthalmologic imaging apparatus (1) according to the present embodiment includes a fixation system (250), an imaging unit (270), an OCT image acquisition unit (260), a control unit (main control unit 211), and a drawing position determination A unit (231), a fixation position setting unit (232), and an image processing unit (233).

  The fixation system (250) presents a fixation target to the eye to be examined (E). The photographing unit (270) photographs the fundus (Ef) of the eye to be examined (E). The OCT image acquisition unit (260) applies an optical coherence tomography (OCT) to the fundus (Ef) to acquire an image.

  The control unit (211) controls the fixation system (250) and the imaging unit (270) so as to repeatedly acquire a front image of the fundus (Ef) while moving the fixation target. This control is called fundus imaging control.

  The visualization position determination unit (231) analyzes the front image sequentially acquired by the fundus imaging control, and determines whether a predetermined region of the fundus oculi (Ef) is visualized in a predetermined area of the front image.

  The fixation position setting unit (232) determines that the predetermined position of the fundus (Ef) is drawn in the predetermined area of the front image by the drawing position determination unit (231), the front image is taken by the photographing unit ( Based on the position of the fixation target when acquired in 270), one or more fixation positions for panoramic imaging are set. The fixation position setting unit (232) can also set two or more fixation positions for panoramic imaging. For example, the fixation position setting unit (232) may set two or more peripheral fixation positions including the first peripheral fixation position 501 and any one or more of the second to fourth peripheral fixation positions 502 to 504. Can be set. It is also possible to configure so that the user can set at least one of a plurality of fixation positions for panoramic imaging.

  The image processing unit (233) processes the image acquired by the OCT image acquisition unit (260). The image processing unit (233) includes a combination processing unit (2331).

  The control unit (211) performs two or more fixation positions (first to fourth peripheral fixations) including one or more fixation positions set by the fixation position setting unit (232) as panoramic imaging (OCT control). The fixation system (250) is controlled so that two or more fixation targets (first to fourth peripheral fixation targets) corresponding to the visual positions 501 to 504) are sequentially presented to the eye to be examined (E), And, when each of two or more fixation targets (first to fourth peripheral fixation targets) is presented to the eye to be examined (E), an OCT image is acquired so as to acquire a three-dimensional image of the fundus oculi (Ef) The acquisition unit (260) is controlled.

  The composition processing unit (2331) generates two or more three-dimensional images (first to fourth) corresponding to two or more fixation positions (first to fourth peripheral fixation positions 501 to 504) acquired by panoramic imaging. Form a composite image (mosaic image) of the surrounding three-dimensional image).

  According to such an embodiment, a plurality of fixation positions for panoramic imaging can be set by actually performing fundus imaging control (second preliminary fundus imaging). Thereby, regardless of individual differences such as eyeball size information such as eye axial length and eyeball characteristic information such as diopter, preferably, setting of a plurality of fixation positions for acquiring a mosaic image using OCT is suitably performed. Is possible.

  In the present embodiment, the control unit (211) may be configured to start movement of the fixation target from a preset initial fixation position in the fundus imaging control (second preliminary fundus imaging). .

  Furthermore, in the present embodiment, the initial fixation position may be a fixation position for acquiring a front image centered on a position separated by a predetermined distance in a predetermined direction from a predetermined region of a standard eye fundus. .

  Further, in the present embodiment, before the fundus imaging control (second preliminary fundus imaging), the control unit (211) is a default for acquiring a front image centered on a predetermined region of the fundus (Ef). Preliminary control of the fixation system (250) and the imaging unit (270) to obtain a preliminary frontal image of the fundus (Ef) while presenting a fixation target corresponding to the fixation position to the eye to be examined (E) The control (first preliminary fundus imaging) may be configured to be performed. Furthermore, the image processing unit (233) may be configured to calculate deviation of the image of the predetermined part of the fundus (Ef) with respect to the center position of the preliminary front image. In addition, the fixation position setting unit (232) may be configured to set an initial fixation position based on this deviation.

  According to such a configuration, the fundus imaging control (second preparatory fundus) is performed by setting the initial fixation position using the preliminary frontal image obtained by the preliminary control (first preparatory fundus photography). Shooting) can be performed. Thereby, it is possible to set a suitable initial fixation position regardless of individual differences in eye parameters of the eye to be examined. With a suitable initial fixation position, for example, a predetermined region of the fundus of the eye to be examined is depicted within or in the vicinity of a predetermined area in a front image obtained by performing fundus imaging with the initial fixation position applied. Fixation position.

  In the present embodiment, the control unit (211) may control the OCT image acquisition unit (260) to acquire a three-dimensional angiographic image of the fundus oculi (Ef) in OCT control (panoramic imaging).

  According to such a configuration, it is possible to preferably acquire a three-dimensional angiographic image (mosaic image) over a wide range of the fundus.

  A control method of an ophthalmologic imaging apparatus according to the present embodiment controls an ophthalmologic imaging apparatus (1) capable of applying imaging and optical coherence tomography (OCT) to a fundus (Ef) of an eye to be examined (E) The method includes an imaging step, a drawing position determination step, a fixation position setting step, an OCT step, and a combining step.

  The imaging step repeatedly acquires a front image of the fundus (Ef) while moving the fixation target. The imaging step may include any process relating to the second preliminary fundus imaging described in the present embodiment.

  The depiction position determination step analyzes the front image sequentially acquired by the imaging step, and determines whether a predetermined region of the fundus oculi (Ef) is depicted within a predetermined region of the front image. The depiction position determination step may include any process related to the depiction position determination described in the present embodiment.

  In the fixation position setting step, when it is determined by the delineation position determination step that the predetermined region of the fundus (Ef) is delineated in the predetermined area of the front image, the fixation target when the front image is acquired Set one or more fixation positions based on the position. The fixation position setting step may include any process regarding fixation position setting described in the present embodiment.

  The OCT step sequentially presents two or more fixation targets corresponding to two or more fixation positions including the one or more fixation positions set in the fixation position setting step to the eye to be examined (E), and The OCT is performed to acquire a three-dimensional image of the fundus (Ef) when each of the two or more fixation targets is presented to the eye to be examined (E). The OCT step may include any process regarding panoramic imaging described in the present embodiment.

  The combining step forms a combined image (mosaic image) of two or more three-dimensional images corresponding to the two or more fixation positions acquired in the OCT step. The combining step may include any process related to image combining described in the present embodiment.

  To create a program for causing an ophthalmologic imaging apparatus (1) capable of applying such a control method to imaging and optical coherence tomography (OCT) to the fundus (Ef) of an eye (E) to be examined Is possible. Moreover, it is possible to create a computer readable non-transitory recording medium recording such a program. This non-transitory recording medium may be in any form, and examples thereof include magnetic disks, optical disks, magneto-optical disks, semiconductor memories and the like.

  The embodiment described above is merely an example of the present invention. Those who intend to practice the present invention can optionally make modifications (omission, substitution, addition, etc.) within the scope of the present invention.

1 ophthalmologic imaging apparatus 210 control unit 211 main control unit 230 data processing unit 231 depiction position determination unit 232 fixation position setting unit 233 image processing unit 2331 composition processing unit 250 fixation system 260 OCT image acquisition unit 270 imaging unit

Claims (8)

A fixation system for presenting a fixation target to an eye to be examined;
An imaging unit configured to image the fundus of the eye to be examined;
An OCT image acquisition unit that acquires an image by applying optical coherence tomography (OCT) to the fundus;
A control unit that executes fundus imaging control that controls the fixation system and the imaging unit to repeatedly acquire a front image of the fundus while moving the fixation target;
A depiction position determination unit that analyzes a front image sequentially acquired by the fundus imaging control, and determines whether a predetermined region of the fundus is depicted within a predetermined region of the front image;
When it is determined by the depiction position determination unit that the predetermined part is depicted in the predetermined area, one or more of the position of the fixation target when the corresponding front image is acquired by the imaging unit A fixation position setting unit that sets a fixation position of
An image processing unit that processes an image acquired by the OCT image acquisition unit;
The control unit controls the fixation system to sequentially present two or more fixation targets corresponding to two or more fixation positions including the one or more fixation positions to the subject's eye, and Performing OCT control to control the OCT image acquisition unit to acquire a three-dimensional image of the fundus when each of the two or more fixation targets is presented to the eye;
An ophthalmologic imaging apparatus, wherein the image processing unit includes a combination processing unit that forms a combined image of two or more three-dimensional images corresponding to the two or more fixation positions acquired by the OCT control. The ophthalmologic photographing apparatus according to claim 1, wherein the control unit starts movement of the fixation target from a preset initial fixation position in the fundus photographing control. The initial fixation position is a fixation position for acquiring a front image centered on a position separated by a predetermined distance in a predetermined direction from a predetermined region of a standard eye fundus. The ophthalmologic photographing apparatus described in. The control unit is configured to obtain a preliminary front image of the fundus while presenting a fixation target corresponding to a predetermined fixation position for obtaining a front image centered on the predetermined region to the subject's eye. Execute preliminary control to control the fixation system and the imaging unit;
The image processing unit calculates a deviation of the image of the predetermined part of the fundus with respect to the center position of the preliminary front image;
The ophthalmologic photographing apparatus according to claim 2, wherein the fixation position setting unit sets the initial fixation position based on the deviation. The ophthalmologic imaging apparatus according to any one of claims 1 to 4, wherein the control unit controls the OCT image acquisition unit to acquire a three-dimensional angiographic image of the fundus in the OCT control. . A method of controlling an ophthalmologic imaging apparatus capable of applying imaging and optical coherence tomography (OCT) to a fundus of an eye to be examined, comprising:
An imaging step of repeatedly acquiring a front image of the fundus while moving a fixation target;
A depiction position determination step of analyzing a frontal image sequentially acquired in the imaging step to determine whether a predetermined region of the fundus is depicted within a predetermined region of the frontal image;
One or more fixation positions based on the position of the fixation target when the corresponding front image is acquired when it is determined in the delineation position determination step that the predetermined part is delineated in the predetermined area Fixation position setting step to set
Two or more fixation targets corresponding to two or more fixation positions including the one or more fixation positions are sequentially presented to the subject's eye, and each of the two or more fixation targets corresponds to the subject's eye An OCT step of acquiring a three-dimensional image of the fundus when being presented;
A control step of forming a composite image of two or more three-dimensional images corresponding to the two or more fixation positions acquired by the OCT step.   A program that causes an ophthalmologic imaging apparatus capable of applying imaging and optical coherence tomography (OCT) to the fundus of a subject's eye to execute the control method according to claim 6. A non-transitory computer-readable storage medium storing the program according to claim 7.

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