JP6531369B2 - Fundus imaging device - Google Patents

Description

The present disclosure relates to a fundus imaging apparatus .

  Conventionally, a scanning laser ophthalmoscope is known as a type of fundus imaging apparatus. In the scanning laser ophthalmoscope, the fundus is scanned with laser light by turning the laser light emitted from the light source about a point near the pupil, and a fundus image is obtained by receiving the fundus reflection light. .

  In the above apparatus, for example, a wide-angle image is acquired by using a wide-angle attachment (see Patent Document 1).

JP, 2009-011381, A

  In this type of device, the resolution of the image captured by the device and the imaging range on the fundus are in a trade-off relationship.

  For example, when imaging a wide area of the fundus using a wide-angle attachment, the imaging magnification is low, so the resolution is relatively poor. That is, the image obtained by wide-range shooting was not suitable for confirmation of the detailed part.

  On the other hand, when photographing the fundus by limiting the photographing range, the photographing magnification is high, so that the resolution is secured. However, the images obtained at high magnification were not suitable for the whole observation.

One object in an embodiment of the present disclosure is to provide a fundus imaging apparatus that allows an examiner to better understand the state of the fundus through an image displayed on a display medium.

The fundus imaging apparatus according to the first aspect of the present disclosure has a light receiving element, projects light to the fundus of the subject's eye through the objective lens optical system, and emits light from each position of the fundus with the projected light. Optical system for receiving the light to be received by the light receiving element, and the photographing angle of view is between a first angle of view of 30.degree. Or more and 75.degree. Or less and a second angle of view wider than the first angle of view. When the switchable photographing optical system, the fundus image photographed when the angle of view of the photographing optical system is the second angle of view, and the angle of view of the photographing optical system is the first angle of view Acquisition means for acquiring a partial image having a resolution higher than that of the fundus image photographed with respect to a part of the fundus image, and combining the partial image with an image area on the fundus image corresponding to the partial image; A display control hand for displaying a composite image of the fundus image and the partial image on a display medium It has a step.

The fundus imaging apparatus according to the second aspect of the present disclosure has a light receiving element, projects light to the fundus of the subject's eye through the objective lens optical system, and emits light from each position of the fundus with the projected light. A photographing optical system for receiving the light to be received by the light receiving element, the photographing angle of view being changed by switching the arrangement of lenses included in the objective lens system or by attaching or detaching a wide-angle lens attachment; A photographing optical system capable of switching between a first angle of view and a second angle of view wider than the first angle of field, and an image obtained when the angle of view of the photographing optical system is the second angle of view An acquisition unit configured to acquire a fundus image, and a partial image having a resolution higher than that of the fundus image captured for a part of the fundus image when the angle of view of the imaging optical system is the first angle of view; An image on the fundus image corresponding to a partial image The partial image synthesizing a, and a display control unit for displaying a composite image of said partial image and the fundus image on the display medium with respect to frequency.

  According to the present disclosure, the examiner can better understand the state of the fundus through the image displayed on the display medium.

It is a schematic block diagram of the optical system which the ophthalmologic imaging device of the 1st Embodiment has. A is a schematic view showing the objective lens optical system in the narrow angle shooting mode, and B is a schematic view showing the objective lens optical system in the wide angle shooting mode. It is a graph which shows typically the relationship between an imaging | photography field angle and the diopter (D) by an objective lens optical system on the conditions which make the position of the turning point with respect to a to-be-tested eye fixed. A table showing design values of an objective lens optical system in which the position of the pivot point with respect to the eye to be examined and the diopter of the photographing optical system are maintained before and after the photographing angle of view switches to the first angle of view and the second angle of view. is there. It is a figure which shows the rotor plate seen from the arrow A direction of FIG. A and B are graphs showing the filtering characteristics of the filter that the rotating plate has. It is a block diagram which shows the electric constitution of an ophthalmologic imaging device. It is a flowchart which shows the imaging | photography display process performed by CPU. It is a schematic diagram which shows an example of the display mode of a fundus oculi image. It is a flow chart which shows photography display processing in a 2nd embodiment. It is a continuation of the flowchart shown in FIG. It is a flow chart which shows the 1st display control processing in a 2nd embodiment. It is a schematic diagram which shows an example of the display mode of the fundus oculi image in 2nd Embodiment. A shows the lens arrangement in the narrow-angle shooting mode of the modified example of the objective lens optical system, and B shows the lens arrangement in the wide-angle shooting mode. It is a figure which shows an example of a diopter correction part.

  Hereinafter, exemplary embodiments of the present disclosure will be described with reference to the drawings. First, the first embodiment will be described with reference to FIGS. 1 to 9.

  FIG. 1 shows an optical system which the ophthalmologic photographing apparatus 1 of the first embodiment has. In the first embodiment, the ophthalmologic imaging apparatus 1 basically has a scanning laser ophthalmoscope (SLO). The ophthalmologic imaging apparatus 1 may be an apparatus integrated with another ophthalmologic apparatus such as an optical coherence tomography (OCT) or a perimeter.

  As an example, the ophthalmologic photographing apparatus 1 mainly includes a photographing optical system 2. Further, a rotary plate unit 30 is provided in the ophthalmologic imaging apparatus 1 of the first embodiment. First, the photographing optical system 2 will be described. The imaging optical system 2 projects light to the fundus Er of the eye E and also receives, with the light receiving element 25, "light emitted from each position of the fundus Er with the projected light". Although the details will be described later, the ophthalmologic imaging apparatus 1 acquires (photographs) a fundus oculi image based on the light reception result of the light receiving element 25. The photographing optical system 2 has a light projecting optical system 3 and a light receiving optical system 4. The photographing optical system 2 is directed in the left-right direction (arrow X direction), the up-down direction (arrow Y direction), and the front-rear direction (arrow Z direction) of the eye E by a drive mechanism 50 (see FIG. 7) described later. Be moved.

  The projection optical system 3 projects light (illumination light or excitation light) to each position in the imaging range of the fundus Er of the eye E to be examined. In the first embodiment, the light projecting optical system 3 includes the laser light emitting unit 11, the apertured mirror 12, the lens 13, the lens 14, the scanning unit 15, and the objective lens optical system 16.

  The laser beam emitting unit 11 is a light source of the photographing optical system 2. The laser beam emitting unit 11 may emit, for example, a laser beam of at least a first wavelength (around 790 nm) and a laser beam of a second wavelength (around 490 nm). Of course, the laser beam emitting unit 11 may emit only monochromatic light. In the first embodiment, the laser beam emitting unit 11 can simultaneously emit two types of laser beams or can emit only one of them.

  The laser light from the laser light emitting unit 11 passes through the opening of “a perforated mirror 12 having an opening at the center”, passes through the lens 13 and the lens 14, and then travels to the scanning unit 15. The light beam reflected by the scanning unit 15 passes through the objective lens optical system 16 and is then collected by the fundus Er of the eye to be examined E. Along with the irradiation of the laser light from the laser light emitting unit 11 to the fundus Er, light is emitted from the fundus Er. For example, laser light is scattered or reflected by the fundus Er. As a result, light scattered or reflected by the fundus Er (hereinafter referred to as fundus reflected light) is emitted from the pupil. The laser light may excite a fluorescent substance present in the fundus Er. As a result, fluorescence emitted from a fluorescent substance present in the fundus Er may be emitted from the pupil.

  In the first embodiment, the lens 13 is configured to be movable in the direction of the optical axis L1 by the drive mechanism 13a. Depending on the position of the lens 13, the diopter of the photographing optical system 2 changes. Therefore, in the first embodiment, the error of the diopter of the subject eye E with respect to the emmetropic eye is corrected (reduced) by "the position of the lens 13 is adjusted". The displacement of the lens 14 may correct the diopter error of the eye E.

  The scanning unit 15 is a unit that changes the traveling direction of the “laser light guided from the laser light emitting unit 11 to scan the fundus with the laser light” (deflects the laser light). In the first embodiment, the scanning unit 15 has a resonant scanner 15a and a galvano mirror 15b.

  Note that, as the scanning unit 15, for example, an acousto-optic element (AOM) or the like that changes the traveling (deflection) direction of light may be used other than a reflection mirror (galvano mirror, polygon mirror, resonant scanner).

  In the first embodiment, the resonant scanner 15a deflects the laser light projected onto the fundus of the eye to be examined E in a predetermined direction. As shown in FIG. 1, the light passing through the resonant scanner 15a is directed to the galvano mirror 15b. In the first embodiment, as the resonant scanner 15a is rotated by the motor 15c (see FIG. 7), the irradiation position (scan position) of the laser light on the fundus Er is in the horizontal direction (that is, the X direction). Move to

  In the first embodiment, the galvano mirror 15b further deflects the laser beam having passed through the resonant scanner 15a in a direction different from that of the resonant scanner 15a. As shown in FIG. 1, the light having passed through the galvano mirror 15 b travels to the objective lens optical system 16. In the first embodiment, “the galvano mirror 15 b is rotated by the motor 15 d (see FIG. 7)” moves the irradiation position of the laser light on the fundus Er in the vertical direction (that is, the Y direction). As described above, the scanning unit 15 of the first embodiment two-dimensionally scans the fundus Er with laser light by scanning the fundus Er in the X direction with the resonant scanner 15a and scanning with the galvano mirror 15b in the Y direction. Do.

  The objective lens optical system 16 guides the laser light having passed through the scanning unit 15 so as to pass through the pupil position. In the first embodiment, the objective lens optical system 16 has a first convex lens 16 a and a second convex lens 16 b. As shown in FIG. 1, in the objective lens optical system 16, these lenses are arranged in series. The number of lenses of the objective lens optical system 16 is not limited to the above configuration. The objective lens optical system 16 may be an objective lens system including three or more lenses. Further, each lens of the objective lens optical system 16 may be a “aspheric lens and a compound lens composed of a plurality of lenses” or the like, as necessary for aberration correction.

  Among the lenses of the objective lens optical system 16, the first convex lens 16a is disposed closest to the eye to be examined. The second convex lens 16 b is disposed closer to the scanning unit 15 than the first convex lens 16 a. As shown in FIG. 1, in the first embodiment, a plano-convex lens is used as the first convex lens 16a, the convex surface of which is directed to the scanning unit 15 side. A biconvex lens is used as the second convex lens 16b. However, these lens shapes are merely illustrative, and each may have positive power.

  In the first embodiment, the laser light that has passed through the objective lens optical system 16 is irradiated onto the fundus Er via a point on the optical axis L3 of the objective lens optical system 16 (hereinafter referred to as “pivot point”). . In the first embodiment, the position of the turning point is “a position optically conjugate with the scanning unit 15 (for example, an intermediate point between the resonant scanner 15 a and the galvano mirror 15 b) via the objective lens optical system 16” Become. Therefore, the principal ray of the laser light that has passed through the objective lens optical system 16 is pivoted around the pivot point with the operation of the scanning unit 15. As a result, the fundus Er is two-dimensionally scanned by the laser beam. The vignetting at the iris is suppressed by “preventing the turning point of the laser light and the pupil position of the subject eye E in advance”, so that the laser light is well guided to the fundus. As a result, the fundus image is captured well.

  The ophthalmologic photographing apparatus 1 according to the first embodiment has a lens moving mechanism (field angle switching mechanism, photographing field angle adjusting mechanism) 17 for moving each lens of the objective lens optical system 16. The lens moving mechanism 17 can move each lens of the objective lens optical system 16 by an arbitrary moving amount. For convenience of explanation, in the first embodiment, the lens moving mechanism 17 is described as a single device. However, the configuration of the lens moving mechanism 17 is not limited to this. For example, as the lens moving mechanism 17, "a plurality of devices each moving a single lens" may be used.

  In the first embodiment, “the arrangement of each lens in the objective lens optical system 16 is changed by the lens moving mechanism 17”, “the irradiation range of the laser light projected from the light projecting optical system 3, ie, The photographing angle of view in the ophthalmologic photographing apparatus 1 (or the photographing optical system 2) is changed. The ophthalmologic photographing apparatus 1 according to the first embodiment can switch the photographing angle of view between at least two types of “first angle of view and second angle of view wider than the first angle of view”. “Arrangement of the respective lenses 16 a and 16 b when the shooting angle of view is the first angle of view in the first embodiment” is shown in FIG. 2A. FIG. 2B shows the “arrangement of the lenses 16 a and 16 b when the shooting angle of view is the second angle of view” in the first embodiment. Hereinafter, the “state of the ophthalmologic imaging apparatus 1 when the imaging angle of view is the first angle of view” will be referred to as a narrow angle imaging mode. The “state of the ophthalmologic imaging apparatus 1 when the imaging angle of view is the second angle of view” is referred to as a wide-angle imaging mode.

  As shown in FIGS. 2A and 2B, in the first embodiment, a control unit, which will be described later, is configured to maintain the position of the turning point and the like with respect to the ophthalmologic imaging apparatus 1 even if the irradiation range of the laser light is changed. Each lens of the objective lens optical system 16 is arranged by 90. In the first embodiment, as an example, “the first convex lens 16a and the second convex lens 16b are displaced in the same direction along the optical axis L3”, so that the photographing angle of view is the first angle of view. And “when changing to the second angle of view mutually” (see FIGS. 2A and 2B).

  For example, in the first embodiment, when the shooting angle of view is increased from the first angle of view to the second angle of view, each of the two convex lenses 16a and 16b can be brought closer to the eye E side along the optical axis L3. (FIG. 2A → FIG. 2B). In the first embodiment, the second convex lens 16b is moved larger than the first convex lens 16a. That is, the two convex lenses 16a and 16b move so that "when the shooting angle of view is the second angle of view, the distance between the lenses is smaller than when the shooting angle of view is the first angle of view". Be done. As a result, when the shooting angle of view is the second angle of view, the incident height of the “laser light incident on each convex lens 16 a and 16 b” is higher than that when “the shooting angle of view is the first angle of view”. . As a result, when the shooting angle of view is the second angle of view, the convergence action of the two convex lenses 16a and 16b is larger than when the shooting angle of view is the first angle of view, and the shooting angle of view Extends as compared to the first angle of view. In the first embodiment, the pivot point is “captured by moving the first convex lens 16 a with a displacement smaller than that of the second convex lens 16 b in order to set the shooting angle of view to the second angle of view”. It is closer to the first convex lens 16 a than in the case where the angle of view is the first angle of view. As a result, in the present apparatus, the position of the pivot point with respect to the eye to be examined is maintained before and after the imaging angle of view switches from the first angle of view to the second angle of view.

  On the other hand, in the first embodiment, when the shooting angle of view is narrowed from the second angle of view to the first angle of view, each lens of the objective lens optical system 16 is moved in the opposite direction to the case of widening the shooting angle of view. (FIG. 2B → FIG. 2A). As a result, when the shooting angle of view is the first angle of view, the incident heights of the laser beams entering the two convex lenses 16a and 16b are lower than in the case where the shooting angle of view is the second angle of view. Thereby, when the shooting angle of view is the first angle of view, the converging action of each of the convex lenses 16a and 16b is smaller than in the case where the shooting angle of view is the second angle of view, and the shooting angle of view is the first. It is narrowed compared to the two angles of view. Further, at this time, the pivot point is obtained by “moving the first convex lens 16 a toward the scanning unit 15 with a smaller displacement amount than the second convex lens 16 b in order to set the shooting angle of view to the first angle of view”. However, as compared with “when the shooting angle of view is the second angle of view”, the lens moves away from the first convex lens 16 a. As a result, in the present apparatus, the position of the pivot point with respect to the eye to be examined is maintained before and after the shooting angle of view switches from the second angle of view to the first angle of view.

  As described above, in the ophthalmologic photographing apparatus 1 according to the first embodiment, “the position of the turning point of the laser light with respect to the eye to be examined” when the photographing angle of view is the first angle of view and the second angle of view. Is maintained. For this reason, when changing the shooting angle of view, the need to "re-adjust the positional relationship between the apparatus and the eye E so that the pivot point is located near the pupil of the eye E" becomes smaller. . That is, the ophthalmologic photographing apparatus 1 according to the first embodiment can photograph the fundus oculi images different in photographing angle of view with a constant positional relationship between the eye E and the apparatus. Therefore, the ophthalmologic photographing apparatus 1 of the first embodiment can satisfactorily photograph fundus images different in photographing angle of view.

  By the way, under the condition that “the position of the turning point with respect to the subject's eye is kept constant”, the diopter of the photographing optical system 2 changes with the photographing angle of view of the objective lens optical system 16. The “diopter (D) corresponding to each photographing angle of view when the position of the turning point is constant” is schematically shown in the graph of FIG. That is, in the graph in which the vertical axis represents diopter (D) and the horizontal axis represents imaging angle of view, the diopter (D) corresponding to each imaging angle of view has “a negative value (D) as the minimum value, "Convex curve". As shown in FIG. 3, the objective lens optical system 16 including the two convex lenses 16a and 16b has the same diopter (D) at two photographing angle of view different from each other. For example, the diopter of the objective lens optical system 16 is 0 (D) when the shooting angle of view is θ1 and when θ2 (θ1 <θ2).

  Therefore, for example, in the ophthalmologic photographing apparatus 1, the diopter of “in narrow angle photographing mode (that is, when the photographing angle of view is the first angle of When the angle is the second angle of view, the first angle of view and the second angle of view are set such that the diopter of FIG. 2B becomes a constant value (for example, 0 (D)). It is good. In this case, in the ophthalmologic photographing apparatus (ophthalmologic apparatus) 1, when the photographing angle of view is switched between the first angle of view and the second angle of view, “the position of the pivot point with respect to the subject eye Two convex lenses 16a and 16b are arranged by the lens moving mechanism 17 so that the power is maintained.

  In FIG. 4, it is possible to maintain the diopter and the position of the pivot point when "switching the shooting angle of view between the first angle of view of about 50 ° and the second angle of view of about 110 °". The focal lengths of the convex lenses 16a and 16b and the arrangement of the convex lenses 16a and 16b are shown as an example. In the example shown in FIG. 4, the focal length of the first convex lens 16a is 42.6 mm, and the focal length of the second convex lens 16b is 70.5 mm.

  When the shooting angle of view is the first angle of view (about 50 °), the second convex lens 16b is 115.3 mm from the scanning unit 15 (in the first embodiment, the midpoint between the resonant scanner 15a and the galvano mirror 15b). , And is arranged at the side of the eye E to be examined. In addition, the first convex lens 16a is disposed further away from the second convex lens 16b toward the subject's eye E by 66.5 mm. As a result, the position of the turning point is 31.1 mm away from the first convex lens 16 a toward the eye E. That is, “the distance from the scanning unit 15 to the turning point when the shooting angle of view is 50 °” is 212.9 mm. Further, the diopter of the objective lens optical system 16 is 0 (D).

  On the other hand, when the shooting angle of view is the second angle of view (about 110 °), the second convex lens 16b is disposed away from the scanning unit 15 by 177.1 mm toward the eye E. In addition, the first convex lens 16a is disposed further to the 4.8 mm eye E side from the second convex lens 16b. As a result, the position of the turning point is 30.9 mm away from the first convex lens 16 a toward the subject's eye E. That is, “the distance from the scanning unit 15 to the turning point when the shooting angle of view is 110 °” is 212.8 mm.

  As described above, in the example of FIG. 4, the “scanning unit is used for the case where the shooting angle of view is the first angle of view (approximately 50 °) and the case where the shooting angle of view is the second angle of view (approximately 110 °). The distance from 15 to the turning point is substantially the same. When the convex lenses 16a and 16b are arranged as described above so that the shooting angle of view becomes the second angle of view (about 110 °), the diopter of the objective lens optical system 16 is 0 (D). Become. Therefore, in the example of FIG. 4, the case where the shooting angle of view is the first angle of view (approximately 50 °) and the case where the shooting angle of view is the second angle of view (approximately 110 °) Diopter is maintained. The diopter maintained when the shooting angle of view is changed may not be 0 (D). For example, each parameter shown in FIG. 4 can also be set such that “diopter at the first angle of view and the second angle of view becomes −2D”. Also, the focal lengths and specific positions of the respective lenses 16a and 16b are not limited to those illustrated in FIG. The focal lengths and specific positions of the respective lenses 16a and 16b can be determined as appropriate according to the set photographing angle of view and the like.

  As described above, the diopter of the photographing optical system 2 is maintained together with the position of the turning point with respect to the subject eye before and after the photographing angle of view switches between the first angle of view and the second angle of view. This reduces the need to adjust the diopter after switching the shooting angle of view. Therefore, fundus images with different imaging angle of view can be acquired more favorably.

  The ophthalmologic photographing apparatus 1 may be configured such that “the diopter of the photographing optical system 2 is not maintained when the photographing angle of view switches between the first angle of view and the second angle of view”. In this case, the ophthalmologic photographing apparatus 1 may use, for example, a diopter correction mechanism provided in the photographing optical system 2. More specifically, the change in diopter associated with "the shooting angle of view switches between the first angle of view and the second angle of view" Of the at least one lens (e.g., the lens 13) "on the common light path of. When the change in diopter is corrected by displacing the lens 13, the lens 13 and the drive mechanism 13a function as a diopter correction mechanism.

  In the first embodiment, the shooting angle of view in the shooting optical system 2 is switched by moving each lens of the objective lens optical system 16 by the lens moving mechanism 17. Instead of this, for example, the ophthalmologic photographing apparatus 1 “a plurality of objective lens optical systems for setting the photographing optical system 2 different from each other in the photographing optical system 2” and “a plurality of objective lens optical systems” An angle of view switching mechanism for selectively arranging the light on the optical path of light. However, it is included in “one optical system as in the first embodiment” rather than “a device that switches the imaging angle of view by switching the objective lens optical system disposed in front of the eye E”. The apparatus for moving the position of the lens (in the first embodiment, each lens of the objective lens optical system 16) is more compact in size.

  Next, the light receiving optical system 4 will be described. The light receiving optical system 4 is "a light from the fundus Er (that is, a reflected light from the fundus at the time of normal photographing, a fluorescence generated at the fundus Er at the time of fluorescence photographing) in accordance with the projection of the laser light from the projection optical system 3" Receive light. The light receiving optical system 4 of the first embodiment projects “each member from the perforated mirror 12 to the objective lens optical system 16 disposed on the optical axis (optical path) L1 of the light projecting optical system 3” It is shared with the optical system 3. The light receiving optical system 4 of the first embodiment includes the lens 22, the pinhole plate 23, the lens 24, and the light receiving element 25.

  When the fundus of the eye to be examined E is irradiated with laser light, light reflected or emitted from the fundus Er based on the laser light is traced back to the projection optical system 3 described above and reflected by the perforated mirror 12 It is led to the lens 22. The pupil position of the eye E to be examined and the opening of the perforated mirror 12 are in an optically conjugate relationship. On the downstream side of the lens 22, the light from the fundus Er is focused at the pinhole of the pinhole plate 23, and is received by the light receiving element 25 through the lens 24. In the first embodiment, an APD (avalanche photodiode) having sensitivity in the visible region and the infrared region is used as the light receiving element 25.

  The rotating plate unit 30 selects the wavelength of the “light received by the light receiving element 25”. The rotating plate unit 30 includes a rotating plate 31, a pulse motor 32, and a sensor 33.

  The rotary plate 31 has “a plurality of types of barrier filters for observing the fluorescence generated in the fundus Er”. The rotary plate 31 is placed such that the plate surface of the rotary plate 31 is orthogonal to the optical axis L2. Further, the optical axis L2 of the light receiving optical system 4 passes through a part of the rotary plate 31 separated from the rotation axis. The rotary plate 31 is rotated by the pulse motor 32. Here, as shown in FIG. 5, the rotary plate 31 is provided with a filter 31 b, a filter 32 c, and an opening 31 d. The filter 31b, the filter 32c, and the opening 31d are all disposed on a "trajectory through which the imaging region Lz of the light receiving optical system 4 passes when the rotary plate 31 is rotated." Therefore, when the rotary plate 31 rotates, any one of the filter 31b, the filter 32c, and the opening 31d is set in the imaging region Lz of the light receiving optical system 4. In addition, on the basis of the rotation angle detected by the sensor 33, the "type of filter to be set" or the like is adjusted.

  The filter 31 b is a barrier filter for infrared fluorescence imaging. The filter 31 b has the spectral characteristics shown in FIG. 6A. The filter 31 b can be used, for example, for indocyanine-green-fundus-angiography (ICG) which is one of infrared fluorescence imaging. The ICG imaging is fluorescence imaging using indocyanine green as a fluorescent fundus contrast agent. In the ophthalmologic photographing apparatus 1 of the first embodiment, photographing is performed by irradiating the first light (around the wavelength of 790 nm) from the laser light emitting unit 11. The ICG imaging is mainly used for observation of choroidal blood vessels.

  The filter 31 c is a barrier filter for visible fluorescence imaging. The filter 31c has the spectral characteristics shown in FIG. 6B. The filter 31 c can be used, for example, in “FA (fundus-auto-fluorescence: spontaneous fluorescence) imaging in which laser light of a second wavelength (laser light in the visible region) is irradiated to the fundus”. In addition, the spontaneous fluorescence photography illustrated here utilizes the principle that "the lipofuscin of the retinal pigment epithelium exhibits spontaneous fluorescence (about 500 nm wavelength to about 750 nm wavelength) when the second light (about 490 nm wavelength) is irradiated". ing. Note that by providing “a light source and a filter in accordance with the fluorescence characteristics of a fluorescent substance to be emitted”, it is possible to excite a fluorescent substance other than those exemplified to photograph the fundus.

  The opening 31 d is placed on the imaging region Lz, for example, “at the time of alignment of the eye E to the apparatus and at the time of normal fundus observation”. At this time, the opening 31 d passes substantially all the light from the fundus Er to the light receiving element 25. In the first embodiment, the size of the opening 31 d is designed to substantially match the size of the imaging area Lz of the light receiving optical system 4.

  FIG. 7 is a block diagram showing a control system of the ophthalmologic photographing apparatus 1 in the first embodiment. The main control of the ophthalmologic imaging apparatus 1 is performed by the control unit 90. The control unit 90 is a processing apparatus (image processing apparatus for ophthalmology) having “an electronic circuit that performs control processing of each part of the ophthalmologic imaging apparatus 1 and calculation processing of measurement results”.

  In the first embodiment, the control unit 90 includes an HDD (hard disk) 95, an image processing IC 96, a laser beam emitting unit 11, a drive mechanism 13a, a resonant scanner drive motor 15c, a galvano mirror drive motor 15d, and a lens moving mechanism 17 The light receiving element 25, the pulse motor 32, the drive mechanism 50, the operation unit 60, and the monitor (display medium, display device) 70 or the like are connected.

  The control unit 90 also includes a CPU (display control unit, photographing angle adjustment mechanism) 91, a ROM 92, and a RAM (storage unit) 93. The CPU 91 is a processing device for executing “various processes related to the ophthalmologic imaging apparatus 1”. The ROM 92 is a non-volatile storage device in which a control program, fixed data, and the like are stored. The RAM 93 is a rewritable volatile storage device. The RAM 93 stores, for example, “temporary data used for photographing and measuring the eye E to be examined by the ophthalmologic photographing apparatus 1”.

  The HDD 95 is a rewritable non-volatile storage device. The HDD 95 stores at least “a program for causing the control unit 90 to execute shooting and display processing described later.” Further, in the HDD 95, a fundus oculi image (fundus oculi captured image) captured by the ophthalmologic imaging apparatus 1 is stored.

  The image processing IC 96 is a processing device that generates “image data of“ fundus oculi image photographed using the photographing optical system 2 ”” based on the light reception signal from the light reception element 25. Here, “when the fundus oculi Er is two-dimensionally scanned by laser light with driving of the scanning unit 15”, the light receiving element 25 is a fundus reflection corresponding to “a scanning position of the laser light at the fundus oculi Er”. Light is received sequentially. As a result, the light reception signal from the light reception element 25 is sequentially output to the image processing IC 96. In the image processing IC 96 of the first embodiment, the input light reception signal is converted into image data, and the image data is stored in a buffer (not shown). Therefore, when a light reception signal of one frame (one fundus image) is input to the image processing IC 96, image data of one frame is accumulated in the buffer of the image processing IC 96.

  In the operation unit 60, “an input device such as a switch or the like operated by an examiner” is disposed. In the first embodiment, a joystick 60a, an imaging switch 60b, an imaging angle switch 60c, and various switches such as an imaging mode switch 60d are prepared as input devices.

  The joystick 60 a is an input device operated to “specify an imaging range of the fundus Er” by the examiner. The control unit 90 drives the drive mechanism 50 in accordance with the operation of the joystick 60 a to move the ophthalmologic imaging apparatus 1 with respect to the eye E. As described above, the position adjustment of the photographing optical system 2 may be performed by “the control unit 90 drives the drive mechanism 50”. Instead of this, the ophthalmologic imaging apparatus 1 may include, for example, a drive mechanism that receives the manual input of the examiner. That is, this drive mechanism is a mechanism for “the examiner manually moves the position of the imaging optical system 2 to adjust the position of the imaging optical system 2”.

  The imaging switch 60 b is a switch operated to capture (capture) a fundus oculi image.

  The shooting angle of view switching switch 60 c is a switch operated to “switch the shooting angle of view (shooting range) of the shooting optical system 2”. In the first embodiment, the size of the imaging range is selected by the examiner from at least two types of ranges (the first angle of view and the second angle of view) through the imaging angle of view switching switch 60c. The control unit 90 arranges each lens included in the objective lens optical system 16 in accordance with the operation to the photographing angle switch 60c. In the first embodiment, when the first angle of view is selected, the control unit 90 controls the lens moving mechanism 17 so that each lens of the objective lens optical system 16 is set to the arrangement shown in FIG. 2A. Drive. On the other hand, when the second angle of view is selected, the control unit 90 drives the lens moving mechanism 17 so that “each lens of the objective lens optical system 16 is set to the arrangement shown in FIG. 2B”. Thus, in the first embodiment, the objective lens optical system 16 is maintained so that the position of the pivot point is maintained when the shooting angle of view is the first angle of view and the second angle of view. Lenses 16a to 16c are disposed.

  The photographing mode switching switch 60d is a switch for "switching the photographing mode of the ophthalmologic photographing apparatus 1 executed by the control unit 90 among the manual photographing mode, the FAF photographing mode, and the IGC photographing mode". Although the details will be described later, the manual mode is a mode in which the fundus oculi is observed with the fundus oculi reflection light of infrared light. The FAF imaging mode is a mode for observing the spontaneous fluorescence emitted from the fundus Er. The IGC imaging mode is a mode for observing "fluorescence from a fluorescent contrast agent administered to the fundus Er". When the photographing mode changeover switch 60d is operated, "the wavelength of the light output from the laser light emitting part 11 and the barrier filter set in the passing area of the optical axis" are selected according to the newly set photographing mode. Switch.

  The monitor 70 is a display device having “a display for displaying“ an image of the subject's eye E photographed by the ophthalmologic photographing apparatus 1 and various measurement results ”.

  Next, the operation of the ophthalmologic imaging apparatus 1 having the above-described configuration will be described.

  First, the examiner operates the photographing mode switching switch 60d to select the manual photographing mode. Thus, the control unit 90 drives the pulse motor 32 to adjust the rotation angle of the rotary plate 31 such that “the opening 31 d of the rotary plate 31 is positioned on the optical axis L 2”. In addition, when the manual imaging mode is selected, the control unit 90 causes the imaging optical system 2 to be in the lighting state that “the laser beam (infrared light) of the first wavelength is emitted from the laser beam emitting unit 11”. Set Thereby, the examiner can perform the alignment of the imaging optical system 2 performed later while viewing the “image captured by the fundus reflected light”. When an image captured by the fundus reflected light is used, the imaging state can be more easily grasped as compared to a fluorescently captured image, and thus the examiner can easily perform alignment.

  Next, the examiner aligns the photographing optical system 2 and photographs a photographed image using the ophthalmologic photographing apparatus 1. Although illustration is omitted, in the first embodiment, at least "during alignment processing is performed and imaging of the photographed image is completed", the scanning unit 15 is continuously driven by the control unit 90. . That is, the fundus Er is continuously scanned in a predetermined procedure by the laser light.

  Next, the examiner observes a “live image (fundus oculi observation image) photographed using fundus oculi reflected light” and causes the apparatus to acquire a photographed image. The operation of the ophthalmologic imaging apparatus 1 at this time will be described with reference to the flowchart of FIG. Here, the live image mentioned here includes not only “a fundus image displayed simultaneously with the timing of imaging (that is, in real time)” but also “a slight lag (for example, several milliseconds, several seconds) from the timing of imaging. The fundus image displayed through is also included.

  In the ophthalmologic photographing apparatus 1 of the first embodiment, photographing and display of a fundus oculi image are performed by photographing display processing. In the photographing display process, first, the processes of S11 and S12 are executed by the CPU 91. As a result, the fundus oculi image taken by the ophthalmologic imaging apparatus 1 is displayed on the display area D of the monitor 70.

  In the process of S11, the CPU 91 acquires image data of a fundus oculi image for one frame from the image processing IC 96 (S11). For example, in the first embodiment, the image data is acquired by “transferring the image data stored in the buffer of the image processing IC 96 to the RAM 93”. Note that this process is on standby until "one frame of image data is stored in the buffer of the image processing IC 96".

  Next, the CPU 91 executes a first display control process (S12). In the first display control process (S12), the CPU 96 displays "one frame of fundus image newly acquired by the ophthalmologic imaging apparatus 1" in the first display area D1 (see FIG. 9). As described later, the present process is repeatedly performed until imaging of the fundus oculi photographed image is completed. As a result, in the first display region D1, live images (observation images, first live images) including continuous fundus images are sequentially displayed by the first display control process (S12). Therefore, the examiner adjusts the position of the photographing optical system 2 so that a desired photographed image can be obtained by “operating the joystick 60 a while confirming the display content of the first display area D1”. Can. In the first embodiment, “the movement processing of the photographing optical system 2 (the drive control of the drive mechanism 50) performed in response to the operation of the joystick 60a” is performed in parallel with the photographing display processing by the control unit 90. It may be done. Alternatively, the “moving process of the photographing optical system 2” may be “a process not shown which is appropriately executed in the control unit 90 during a standby time when acquiring image data from the image processing IC 96”.

  Even when the number of pixels (so-called number of image pixels) of the “fundus image obtained by the process of S11” is larger than “the number of pixels of the first display area D1 in the monitor 70 (the number of so-called device pixels)”. Conceivable. In this case, in the first display process (S12), for example, the process of “compressing (reducing) the fundus image according to the number of pixels in the first display area D1” may be performed by the CPU 91.

  Next, the CPU 91 performs processing for “displaying a part (second partial image) of the fundus image displayed in the first display area D1 in an area different from the first display area D1” (S13 to S13). S17).

  First, the CPU 91 determines "whether or not the setting operation of the attention range C has been received" (S13). The attention range C is “a range in which image processing is performed in the fundus oculi image displayed in the first display region D1 (or in the region of the fundus oculi Er indicated by the fundus oculi image). The setting operation of the range of interest C may be performed, for example, by the examiner designating the position on the fundus image to which the range of interest C is desired to be set using a pointing device such as a mouse. In the first embodiment, in addition to providing a new focused range C for setting the focused range C, moving the set position of the focused range C and changing the vertical and horizontal sizes of the focused range C Also includes doing.

  In the first embodiment, it is determined that "until the examiner sets the attention range C for the first time" in S13, "the setting operation of the attention range C is not received" (S13: No) . In this case, the CPU 91 executes the processing of S15 without setting the attention range C.

  On the other hand, when it is determined that the setting operation of the attention range C is received in the process of S13 (S13: Yes), the CPU 91 sets the attention range C in the range designated by the examiner by the setting operation (S14) . For example, in the first embodiment, the CPU 91 stores, in the RAM 93, position information indicating “the position occupied by the attention range C in the photographing range of the fundus image”. Next, the CPU 91 executes the process of S15.

  As described above, in the first embodiment, the attention range C is described as being provided when an instruction from the examiner is given. However, the setting of the attention range C is not limited to this. For example, regardless of the instruction from the examiner, the CPU 91 may set the attention range C in a predetermined range of the fundus image. Further, in the first embodiment, the CPU 91 sets not only whether to provide the attention range C but also the position and size of the attention range C in accordance with an instruction from the examiner. However, the setting of the attention range C is not limited to this. For example, the ophthalmologic imaging apparatus 1 (or the CPU 91) may be configured such that “the attention range C is always set at a constant position (for example, the central region of the fundus image) with respect to the fundus image”.

  In the process of S15, the CPU 91 determines "whether or not the attention range C is provided" (S15). As described above, when the setting operation of the attention range C is performed at least once, the attention range C is already provided. In this case, the CPU 91 executes the process of S16 (S15: Yes).

  In the process of S16, the CPU 91 acquires image data of the second partial image (S16). In the first embodiment, the image data of the second partial image is generated and acquired by “the CPU 91 extracts data indicating the attention range from the image data indicating the entire fundus image”. In the first embodiment, the CPU 91 generates image data of the second partial image from the image data indicating the entire fundus image based on “the position information of the attention range C acquired in advance in the process of S14”. It can be extracted.

  Next, the CPU 91 executes a second display control process (S17). In the second display control process (S17), the CPU 91 displays "a second partial image whose image data has been acquired by the process of S16" in the second display area D2 (see FIG. 9). Similar to the first display control process (S12), the second display control process is repeatedly executed until the photographing of the fundus oculi photographing image is completed. Therefore, the second display control process (S17) displays the second live image including the continuous second partial image in the second display area D2.

  That is, the CPU 91 displays the first live image and the second live image side by side on the monitor 70.

  In the first embodiment, the second live image is described as being displayed in synchronization with the first live image. However, the display mode is not limited to this. The display mode may be, for example, a mode in which “one of the first live image and the second live image continues to be displayed, and the other display and non-display are switched at intervals of several seconds”. Also, the first live image and the second live image may be displayed alternately.

  That is, the CPU 91 may be configured to display at least one of the first live image and the second live image on the monitor 70.

  Further, in the second display control process (S17) of the first embodiment, the CPU 91 displays the "second live image expanded more than the attention range C on the first live image". For example, in the first embodiment, the second live image is displayed in the second display area D2 having the same size as the “first display area D1 in which the fundus image is displayed” (see FIG. 9). Thereby, the examiner can perform observation of the attention range C more easily using the second live image.

  In addition, as described above, the number of pixels (the number of image pixels) of the “fundus image obtained by the ophthalmologic imaging apparatus 1” is larger than the number of pixels of the first display area D1 (the number of device pixels). The compressed image of the fundus oculi image acquired by the imaging device 1 may be displayed as a first live image. In such a case, in the second display control process (S17), the second live image may be displayed at a higher resolution than the first live image. Note that the resolution in the first embodiment is correlated with the resolution of the fundus tissue in the image. In this case, the attention range C in the fundus image is displayed in more detail in the second display region D2 than in the first display region D1. Therefore, the examiner can perform the detailed observation of the attention range C well.

  Next, the CPU 91 executes a discrimination display process (S18). By executing the process of S18, when the second live image is displayed in the second display area D2, the discrimination display of the attention range C and the other areas is performed on the first live image. The determination display may be any display that helps “determine between the attention range C and the other area by the examiner”. In the first embodiment, the attention range C is surrounded by a line on the first display area D1 (on the first live image) as an example of the determination display (see FIG. 9). Other modes of the discrimination display are, for example, a mode in which "the range of interest C is displayed darker or thinner than the surrounding area" and a mode in which "the range of interest C is shaded". Is also included.

  Next, the CPU 91 determines "whether or not the photographing operation of the photographed image (the operation of the photographing switch 60b in the first embodiment) is received" (S19). If the photographing operation has not been received (S19: No), the CPU 91 repeatedly executes the processing from S11 to S19. On the other hand, when the imaging operation from the examiner is received by the process of S19 (S19: Yes), the CPU 91 executes the imaging process of S20. The CPU 91 acquires a fundus oculi photographed image by the photographing process (S20). The imaging process may be, for example, a process of “the CPU 91 newly acquires a fundus image from the image processing IC 96 and stores the acquired fundus image as a fundus image in the HDD 95 or the like”. A plurality of fundus images may be acquired from the image processing IC. Alternatively, the fundus photographed image may be an added average image of “a plurality of continuously photographed fundus images” or the like. In the first embodiment, after the shooting process (S20), the shooting display process ends.

  Here, it returns to the process of S15 and continues description. If the setting operation of the attention range C has not been performed even once, the CPU 91 determines that “the attention range C is not set” in the process of S15. In this case, the CPU 91 skips the processing of S16 to S18 and performs the processing of S19 and thereafter. Therefore, the second live image is not displayed in the display area D until the setting operation of the attention range C is performed by the examiner.

  In the above description, the case where the “captured image captured using the fundus reflected light” is acquired has been described. Instead of this, it is also possible to acquire “a photographed image photographed using fluorescence from the fundus”. In this case, for example, the examiner may have performed alignment of the imaging optical system 2 while looking at “observed images (first live image and second live image) captured using the fundus reflected light”. The photographing mode is switched to “mode photographed using fluorescence from the fundus (FAF photographing mode, IGG photographing mode)” by operating the photographing mode switching switch 60d. Thereafter, the examiner operates the photographing switch 60b.

  As described above, according to the ophthalmologic photographing apparatus 1 of the first embodiment, the first live image including a plurality of consecutive fundus images is displayed on the monitor 70 by the first display control process (S12) which is sequentially executed. Is displayed on. Thereby, for example, “confirmation omission by the examiner on a characteristic site (for example, a nipple, a macula, a lesion, a blood vessel, and the like) present in the imaging range of the fundus image is suppressed. Further, according to the ophthalmologic photographing apparatus 1 of the first embodiment, the second display control process (S17) is performed as "the setting operation of the attention range C with respect to the fundus image is performed in advance by the examiner". A “second partial image extracted as a range of interest from the fundus image” is generated. A second live image including a plurality of consecutive second partial images is also displayed on the monitor 70. As a result, the examiner can easily observe in detail the characteristic site present in “a part of the fundus image (in the first embodiment, the attention range C) displayed as the second live image”. it can. Therefore, in the ophthalmologic imaging apparatus 1, the examiner can easily observe in detail the imaging range of the fundus image without omission using the live image of the fundus image.

  In addition, for example, when the position of the turning point of the laser light is shifted from the pupil position of the eye to be examined E, a part of the light from the device may be blocked (eclipsed) by the iris. In this case, the outer edge portion or the like of the fundus image may be affected by the vignetting light. This may not be confirmed by the examiner if only the second live image containing a portion of the fundus image is displayed. Therefore, there is a possibility that "the fundus image in which it is difficult to observe the outer edge portion and the like" may be obtained as "the examiner confirms only the second live image and acquires the photographed image of the entire fundus image". On the other hand, in the ophthalmologic photographing apparatus 1 of the first embodiment, the first live image including the fundus image is displayed together with the second live image. Therefore, the examiner can easily confirm "whether or not the outer edge portion or the like of the fundus image is affected by vignetted light". For this reason, the examiner executes acquisition of the photographed image to the apparatus in the “state where the photographing optical system 2 is aligned so that the desired photographed image can be obtained” while confirming the first and second live images. It can be done. Therefore, in the ophthalmologic photographing apparatus 1 of the first embodiment, it is possible to take a good image of the fundus oculi.

  In the ophthalmologic photographing apparatus 1 according to the first embodiment, “the attention range C of the fundus image from which the second partial image is extracted” is set based on an instruction from the examiner (S14). The “desired range in the fundus image” can be displayed as a second live image. As a result, observation of the fundus by the examiner is likely to be performed better.

  Further, in the ophthalmologic photographing apparatus 1 of the first embodiment, when the second live image is displayed in the second display area D2, the attention range C and the other areas are displayed on the first live image of the first display area D1. And the discrimination display of (S18). Thus, the examiner can easily understand the correspondence between the fundus image and the second partial image.

  In the first embodiment, the “case where the attention range C is set at a fixed position with respect to the display range (or the imaging range) of the fundus oculi image” has been described. For example, in the ophthalmologic photographing apparatus 1 according to the first embodiment, the position of the attention range C on the first display area D1 before and after “the imaging range of the optical system in the fundus Er is changed by the alignment operation”. Does not change. However, the attention range C may not be set at a fixed position with respect to the display range of the fundus oculi image. For example, the attention range C may be set at “a fixed position of the fundus oculi Er indicated by the fundus oculi image”. In this case, for example, "the imaging range on the fundus Er is moved by the involuntary eye movement of the eye E to be examined E", and the focused range C on the first display area D1 tracks a fixed position on the fundus Er. As an example, the following modified example of the first embodiment is shown. In this modification, the CPU 91 may perform the process of setting the range of interest C (S14) by “obtaining a template image from a part of the fundus image”. As the template image, an image extracted from “a fundus image acquired in advance by the ophthalmologic imaging apparatus 1” is used.

  Further, the CPU 91 specifies “an image area having a high correlation with the template image” from “the fundus oculi image displayed in the first display area D1 at each timing”. Thus, the movement of the “image area extracted as the second display area D2” is detected. The CPU 91 may correct the “region extracted as the second partial image from the fundus image” according to the detection result, and perform the second display control process (S17) on the corrected region. Thus, even in the case where the imaging range on the fundus Er is moved by the involuntary eye movement of the eye E to be examined or the like, the “fixed region included in the template image” is displayed in the second display region D2.

  Next, a second embodiment of the present disclosure will be described with reference to FIGS. 10 to 13. As described above, the ophthalmologic photographing apparatus 1 according to the first embodiment displays a plurality of continuous live images in the first display area D1 of the monitor 70. In addition, the ophthalmologic imaging apparatus 1 displays a second live image including a second partial image of the “fundus image displayed in the first display area D1” in the second display area D2 of the monitor 70.

  On the other hand, the ophthalmologic imaging apparatus 100 according to the second embodiment acquires “the first fundus image and the second fundus image having different“ resolutions of the image ”,” to obtain the first fundus image and the second fundus image. The composite image of the image is displayed on the monitor 70. In the second embodiment, the first fundus oculi image is a fundus oculi image captured with the imaging angle of view of the imaging optical system 2 set to the second angle of view (ie, in the wide-angle imaging mode). The second fundus oculi image (first partial image) is an image captured with respect to a part of the first fundus oculi image with the imaging angle of view of the imaging optical system 2 set as the first angle of field (in the narrow angle imaging mode).

  As described above, the first fundus image and the second fundus image are formed based on light reception signals from the same light receiving element (in the present embodiment, the light receiving element 25). In the second embodiment, the wide-angle first fundus image may be an image captured at an imaging angle of view of 100 ° or more and 180 ° or less (more preferably, 120 ° or less). In addition, the second fundus image at an included angle may be an image captured at an imaging angle of view of 30 ° or more and 75 ° or less (preferably, 40 ° or more and 55 ° or less). In the second embodiment, the second fundus oculi image has a high resolution, as the imaging angle of view is narrower than the first fundus oculi image. In the following description, the observation image and the photographed image of the first fundus image are respectively referred to as an observation image (wide) and a photographed image (wide), and the observation image and the photographed image of the second fundus image are respectively observed It is described as an image (narrow) and a photographed image (narrow).

  The ophthalmologic photographing apparatus 100 of the second embodiment has, for example, the same optical system as the ophthalmologic photographing apparatus 1 of the first embodiment. In addition, the ophthalmologic imaging apparatus 100 has, for example, “a control system that is approximately the same as the control system of the ophthalmologic imaging apparatus 1 according to the first embodiment”. However, in the ophthalmologic imaging apparatus 100, at least "a control program that defines" a process to be executed at the time of imaging of a fundus image "" is different from the ophthalmologic imaging apparatus 1 of the first embodiment.

  Hereinafter, “the operation of the ophthalmologic photographing apparatus 100 at the time of photographing of a fundus oculi image” will be described with reference to flowcharts of FIGS.

  First, the CPU 91 determines "whether the photographing angle of view (photographing magnification) of the photographing optical system 2 is the first angle of view or the second angle of view wider than the first angle of view" (S21). For example, in the second embodiment, the CPU 91 carries out this determination based on “a shooting angle of view (shooting magnification, optical magnification) preset in accordance with the operation of the shooting angle of view switching switch 60 c”. .

  When it is determined that the shooting angle of view is the second angle of view (S21: second angle of view), the CPU 91 executes "processing in wide-angle shooting mode after S22". By the process of S22, the CPU 91 determines "whether or not a photographing operation has been received" (S22). When the CPU 91 determines that the photographing operation has been received (S22: Yes), the image processing IC 96 acquires image data for one frame (S23). Thus, image data of "a fundus oculi image of a wide angle of view (a second angle of view in the second embodiment)" is acquired. This image data is displayed on the monitor 70 as a photographed image (wide) by the subsequent processing. In the second embodiment, the “image data of the captured image (wide)” acquired by the process of S23 is temporarily stored in the RAM 93 until the new captured image (wide) is captured. . Note that the CPU 91 can also save “image data of a captured image” acquired by the process of S23 in a non-volatile storage device (for example, the HDD 95). After the process of S23, the CPU 91 executes a first display control process (S25).

  On the other hand, when it is determined that the photographing operation has not been received (S21: No), the CPU 91 acquires image data for one frame from the image processing IC 96 (S24). This image data is displayed on the monitor 70 as an observation image (wide) by the subsequent processing (S24). In the second embodiment, the “image data of the observation image (wide)” acquired by the process of S24 is temporarily stored in the RAM 93 until the imaging of the observation image (wide) is newly performed. . After the process of S23, the CPU 91 executes a first display control process (S25).

  In the wide-angle shooting mode, display control of the monitor 70 is performed in the first display control process (S25). In the first display control process (S25), the CPU 91 controls the display of the monitor 70 using the image data acquired in the process of S23 or the process of S24 (S25). Here, the first display control processing (S25) in the wide-angle shooting mode will be described with reference to FIG. In the first display control process (S25), first, the CPU 91 determines "whether or not to display a photographed image (wide)" (S31). In the second embodiment, if the captured image (wide) is acquired in advance by the process of S23, the CPU 91 determines to display the captured image (wide) (S31: Yes). On the other hand, if the photographed image (wide) is not obtained in advance, the CPU 91 determines that the photographed image (wide) is not displayed (S31: No). When it is determined that the captured image (wide) is not displayed by the process of S31 (S31: No), the monitor 70 uses the “image data of the observation image (wide) acquired by the process of S24 immediately before”. Is displayed. That is, in this case, display of a live image including an observation image (wide) is performed. Here, in the second embodiment, the CPU 91 determines whether “the captured image (narrow) is captured (acquired) in advance in the narrow-angle capturing mode” (S32).

  If the photographed image (narrow) is not obtained in advance (S32: No), the CPU 91 displays the observation image (wide) on the display area D of the monitor 70 (S33).

  On the other hand, if the captured image (narrow) is acquired in advance (S32: Yes), the CPU 91 aligns the observation image (wide) with the captured image (narrow) (S34). In the second embodiment, the CPU 91 determines the positions of the “first fundus image (observed image (wide) or photographed image (wide)) and the second fundus image (observed image (small) or a photographed image (small)). The “matching (matching process)” can be performed, for example, using the correlation between the two images (for example, pattern matching). Thereby, even in the case where the positional relationship between the first fundus image and the second fundus image is not constant due to the involuntary eye movement or the like, image processing of both images described later can be properly performed. . In addition, “when the second fundus image is included in a fixed position of the first fundus image”, based on the information indicating “the imaging range of the second fundus image (that is, the attention range C) in the first fundus image”. The CPU 91 can also align the image.

  That is, the CPU 91 can match the “image area corresponding to the second fundus image on the fundus image” with the second fundus image by image processing to correct the positional deviation between the images.

  In the second embodiment, the first fundus image and the second fundus image are captured with the same number of pixels although the imaging angle of view is different from each other. Therefore, in the second embodiment, when the first fundus image and the second fundus image are aligned, the enlargement / reduction magnification of each of the first fundus image and the second fundus image is adjusted by the CPU 91. For example, in the second embodiment, alignment of the second fundus image is performed with respect to the enlarged image of the first fundus image such as “the attention range C in the first fundus image matches the size of the second fundus image”. Is done. In addition, the enlargement / reduction magnification of each of the first fundus image and the second fundus image is, for example, the photographing angle of view (or photographing magnification) of the first fundus image and the photographing angle of view (or photographing magnification) of the second fundus image It can be determined from

  After completion of the alignment processing of S34, the CPU 91 executes composite image display processing (S35). In the composite image display process (S35), the CPU 91 displays on the monitor 70 a composite image obtained by "combining the first fundus image and the second fundus image registered in advance by image processing". Do. In the second embodiment, the CPU 91 displays on the monitor 70 a composite image of “the enlarged image of the first fundus image used for alignment and the second fundus image”. Various image processing methods can be used as image processing for combining the first fundus image and the second fundus image. For example, “a method of acquiring a composite image by adding the first fundus image and the second fundus image” can be used. Also, “a method of replacing the attention range C of the first fundus image with the second fundus image” can be used.

  It returns to the process of S31 and demonstrates. In the second embodiment, even when it is determined that “captured image (wide) is displayed” (S 31: Yes), the CPU 91 determines “whether or not the captured image (narrow) is acquired in advance”. (S36). If the photographed image (narrow) is not obtained in advance (S36: No), the photographed image (wide) stored in the RAM 93 is displayed by the CPU 91 in the display area D of the monitor 70 (S38). On the other hand, if the captured image (narrow) is acquired in advance (S31: Yes), the CPU 91 aligns the captured image (wide) with the captured image (narrow) (S38). And the photographed image (narrow) are displayed in the display area D (S35). As described above, in the second embodiment, “when the captured image (wide) is stored in advance in the RAM 93”, the captured image (wide) in the RAM 93 is used for the first image portion of the composite image. As described above, in the second embodiment, “when the photographed image of the first fundus image is obtained in advance using the photographing optical system 2”, the photographed image continues in the first fundus image portion in the composite image. Is displayed.

  The CPU 91 displays the composite image of the photographed image (wide) and the photographed image (small) not only on the monitor 70 but also on a print medium by printing on a print medium using a printer or the like. May be

  In the process of S26, the CPU 91 determines whether or not the process is to be ended (S26). For example, when the CPU 91 receives an instruction to end the process from the examiner, the process ends (S30: Yes). On the other hand, when it is determined that the process is not ended (S30: No), the CPU 91 repeats the process from S21.

  Return to S21 and continue the explanation. When it is determined that the shooting angle of view is the first angle of view (S21: first angle of view), the CPU 91 executes the processing (S27 to S29, S40) in the narrow angle shooting mode.

  First, the CPU 91 executes the processing of S27 to S29 to acquire a second fundus image (observed image (narrow) or photographed image (narrow)). First, the CPU 91 determines "whether or not a photographing operation has been received" (S27). When it is determined by the CPU 91 that the photographing operation has been received (S27: Yes), the CPU 91 acquires image data of one frame as image data of a photographed image (narrow) from the image processing IC 96 (S28). The image data of the photographed image (narrow) is temporarily stored in the RAM 93 until the photographing of the photographed image (narrow) is newly performed. After the process of S28, the CPU 91 executes a second display control process (S40).

  On the other hand, when it is determined by the CPU 91 that the photographing operation has not been received (S27: No), the CPU 91 acquires image data of one frame as image data of a photographed image (narrow) from the image processing IC 96 (S29). ). Thereby, the image data of "the fundus oculi image of the narrow angle of view (the first angle of view in the second embodiment)" is acquired. The image data of the observation image (narrow) is temporarily stored in the RAM 93 until the new observation image (narrow) is taken. After the process of S23, the CPU 91 executes a second display control process (S40).

  In the narrow-angle shooting mode, display control of the monitor 70 is performed by the second display control process (S40). In the second display control process (S40), the display of the monitor 70 is controlled using "the image data of the second fundus image obtained in the process of S28 or the process of S29". In the second control process (S40) of the second embodiment, a process according to each process of the first display control process (S25) is performed. Specifically, in each step of the flowchart shown in FIG. 12, “observation image (wide) and observation image (narrow) are mutually read” along with “read the photographed image (wide) and the photographed image (narrow) mutually”. The read-out process "" is executed in the second control process (S40). After execution of the second control process (S40), returning to FIG. 10, the CPU 91 executes the process of S26.

  According to the ophthalmologic imaging apparatus 100 of the second embodiment, “one of the first fundus image (fundus image) and the second fundus image (first partial image) is obtained (captured) in advance. When the other image is newly obtained (captured), the CPU 91 displays “a composite image of the first fundus image and the second fundus image” on the display area D of the monitor 70. Here, the second fundus image is synthesized by image processing in “the image area of the first fundus image corresponding to the second fundus image (the attention area C in the second embodiment) corresponding to the second fundus image”. It is In the second embodiment, the composite image has the same imaging angle of view as the first fundus image. Therefore, the examiner can observe the wide area of the fundus through the composite image. Also, the second fundus image has a higher resolution of the image than the first fundus image. Therefore, the composite image is displayed on the monitor 70 in a state where the resolution of the image of the “second fundus image part in the composite image” is higher than the resolution of the image of the first fundus image part. Thus, the examiner can observe the fundus Er in detail through the “region where the second fundus image is synthesized in the synthesized image”. Further, in the composite image, the second fundus image is composited in “the image area of the first fundus image corresponding to the second fundus image”. Therefore, the examiner can easily observe. Therefore, according to the image processing apparatus of claim 1, the examiner can grasp the state of the fundus oculi Er well through the composite image displayed on the monitor 70.

  In the second embodiment, when the "image resolution of the second fundus image portion is higher than the" image resolution "of the first fundus image portion", the entire composite image is displayed. , And may be displayed on the monitor 70 at the default display magnification. In addition, the above display may be performed when “the entire composite image is displayed at a higher magnification than the default display magnification”. For example, “when the number of device pixels in the display area D is larger than the number of pixels in the image of at least the first fundus image portion”, the second fundus image portion in the entire display of the entire composite image is larger than the first fundus image portion. Can also be displayed in high resolution.

  Moreover, the display in the state in which the "image resolution" of the second fundus image portion is higher than the "image resolution of the first fundus image portion" is "default for part or all of the composite image". When the image is displayed on the monitor 70 at a higher magnification than the display magnification, the process may be performed. In this case, the CPU 91 displays the composite image with at least two types of display magnifications of the first display magnification and the second display magnification that is larger than the first display magnification.

  Further, the CPU 91 sets the second fundus oculi image portion of the composite image to “the display magnification from the first display magnification to“ the second display magnification larger than the first display magnification ””, Display with higher resolution than the display magnification of 1. In this case, the CPU 91 may set the display area with the first display magnification and the display area with the second display magnification on the same screen. In this case, for example, the CPU 91 can arrange and display the composite image of the first display magnification and the second fundus image at the second display magnification on the same screen.

  Further, the CPU 91 may be configured to “switch and display a composite image at a plurality of display magnifications in one display area”. In this case, the CPU 91 “when the“ region where the second fundus image in the combined image is combined ”is displayed at the second display magnification”, “the second fundus image in the combined image is combined. The composite image (or “the second fundus image in the composite image is higher in resolution than in the case where the peripheral region (that is, the region of the first fundus image)” is displayed at the second display magnification ”). Display the synthesized area ").

  Further, according to the ophthalmologic photographing apparatus 100 of the second embodiment, “when a composite image is generated in the first display control process (S25) or the second display control process (S40)”, the first fundus image and Alignment (matching) with the second fundus image is performed. As a result, the ophthalmologic imaging apparatus 100 can obtain an appropriate composite image.

  In addition, according to the ophthalmologic imaging apparatus 100 of the second embodiment, “an enlarged image of the first fundus image in which“ the attention range C in the first fundus image matches the size of the second fundus image ””. The second fundus image is synthesized by image processing. As a result, it is possible to display each part of the fundus on the composite image while suppressing that "each part of the fundus included in the imaging range of the fundus image" is hidden by the second fundus image. Therefore, the examiner can observe the characteristic site in the fundus without omission through the composite image.

  Further, according to the ophthalmologic imaging apparatus 100, the CPU 91 sets “the imaging angle of view (optical magnification) of the imaging optical system 2 set by the CPU 91 or the lens moving mechanism 17 out of the first fundus image and the second fundus image. One of the images according to "is displayed as a live image."

  Further, according to the ophthalmologic imaging apparatus 100, when an observation image of "one of the first fundus image and the second fundus image according to the imaging angle of view of the imaging optical system 2" is captured, the other image When the captured image of the image is acquired in advance, the captured image and the live image including one of the images are synthesized by the CPU 91 and displayed on the monitor 70. Thereby, the examiner can observe the first fundus image and the second fundus image in substantially real time through the composite image.

  That is, the CPU 91 sets an imaging angle of view different from “the imaging angle of view (optical magnification) of the imaging optical system 2 set by the CPU 91 or the lens moving mechanism 17 out of the first fundus image and the second fundus image And the live image of the one image are combined and displayed.

  In the case of the ophthalmologic photographing apparatus 100 according to the second embodiment, "when both the first fundus image and the second fundus image forming the composite image are images taken using the fundus reflection light from the fundus" explained. Instead of this, at least one of the first fundus image and the second fundus image may be a fluorescence image captured using fluorescence from the fundus.

  In the second embodiment, the case where two types of fundus oculi images (first and second fundus oculi images) having different angles of view are captured by switching the arrangement of the objective lens optical system 16 has been described. However, the method of acquiring two types of fundus oculi images different in angle of view is not limited to this. For example, two fundus images with different angles of view can be captured by adjusting the deflection angle of the scanning unit 15 of the imaging optical system 2 (in the above embodiments, the resonant scanner 15a and the galvano mirror 15b in the above embodiments). it can. At this time, for example, the scanning speed of the scanning member when capturing the second fundus image may be slower than when capturing the first fundus image. As a result, at the time of capturing the second fundus image, the number of pixels acquired in the “scan per unit length of the fundus Er” becomes larger than at the time of capturing the first fundus image. For this reason, in such an apparatus, the same effect as that of the second embodiment can be obtained. Further, in the second embodiment, switching of the shooting angle of view is not performed by “switching of the lens arrangement of the objective lens optical system 16” but by “mounting of wide angle lens attachment for widening the shooting angle of view of the apparatus” It may be

  In the second embodiment, the case where the ophthalmologic imaging apparatus 1 generates a composite image of the first fundus image and the second fundus image (first partial image) has been described. The method of generating a composite image is not necessarily limited to this. For example, the composite image may be generated by a general-purpose computer (for example, a personal computer). In this case, for example, “an analysis program that causes the processor of the computer to execute“ the processing of S34 and S35 of the photographing display processing performed by the ophthalmologic photographing apparatus 1 according to the above embodiment ”” is prepared Memory). Also in this case, a composite image of the first fundus image and the second fundus image (first partial image) can be generated as in the ophthalmologic imaging apparatus 1 of the above embodiment.

  Further, in each of the above embodiments, “when photographing a fundus oculi image using reflected light from the fundus oculi Er” and “when photographing a fundus oculi image using fluorescence generated in the fundus oculi Er” are common. The case of using the light receiving element 25 has been described. Instead of this, "a different light receiving element 25 can be used depending on each case". For example, the light path of the light receiving optical system 4 can be branched using a half mirror or the like, light receiving elements can be provided at the end of each light path, and imaging can be performed simultaneously using each light receiving element. By disposing “elements having different light receiving characteristics as each light receiving element”, imaging with a plurality of wavelengths can be performed simultaneously.

  Further, in each of the above embodiments, the control unit 90 has been described as performing position control of “each lens of the objective lens optical system 16”. However, the setting method of the position of each lens is not limited to this. For example, the lens moving mechanism 17 configured to “colocate the arrangement of the lenses of the objective lens optical system 16 with one another” maintains the turning point of the laser light when changing the photographing angle of view in the photographing optical system 2 May be

  Further, in the above embodiment, “the case where the objective lens optical system 16 is configured by two lenses (the first convex lens 16 a and the second convex lens 16 b)” has been described. However, the objective lens optical system 16 may be configured by three or more lenses. As an example in which the objective lens optical system 16 is configured by three lenses, in addition to the first convex lens 16 a and the second convex lens 16 b described above, a lens having negative power scans more than the second convex lens 16 b It may be provided on the part 15 side. For example, as shown in FIGS. 14A and 14B, a concave lens 16c may be provided as a lens having negative power.

  In the example of FIGS. 14A and 14B, the concave lens 16c is disposed with the concave surface facing the scanning unit 15 side. In the examples of FIGS. 14A and 14B, a plano-concave lens is used as the concave lens 16c. However, the concave lens 16c is not limited to this. The concave lens 16c may be, for example, a biconcave lens, a concave meniscus lens, an aspheric lens, or a compound lens.

  The “laser light from the scanning unit 15 side that passes through other than the center of the concave lens 16c” is refracted in the direction away from the optical axis L3 by the concave lens 16c that directs the concave surface to the scanning unit side than when the concave lens 16c is not present. Ru. Therefore, the height of the laser beam can be set to a required height at a position closer to the scanning unit 15 than when the concave lens 16c is not present. That is, when a fixed imaging angle of view can be obtained, each of the two convex lenses 16a and 16b can be arranged at a position closer to the scanning unit 15 side than in the case without the concave lens 16c. Therefore, in the examples of FIGS. 14A and 14B, the total length of the objective lens optical system 16 can be shortened as compared with the case without the concave lens 16c. Therefore, the ophthalmologic imaging apparatus 100 can be easily configured compactly.

  In the examples of FIGS. 14A and 14B, two convex lenses are used when the shooting angle of view of the shooting optical system 2 is the first angle of view (see FIG. 14A) and the second angle of view (see FIG. 14B). 16a and 16b are displaced by the lens moving mechanism 17 in the same manner as the example shown in FIGS. 2A and 2B. At this time, the concave lens 16c may be displaced together with the two convex lenses 16a and 16b. For example, the two convex lenses 16 a and 16 b may be arranged such that “diopter is maintained together with the position of the turning point with respect to the subject's eye when the shooting angle of view is the first angle of view and the second angle of view.” , And the concave lens 16 c may be disposed by the lens moving mechanism 17.

  As described above, when the objective lens optical system 16 includes the two convex lenses 16a and 16b, the shooting angle of view is cut between “a specific angle of view according to the design value of the two convex lenses 16a and 16b”. Except when changing (see, for example, FIG. 4), the position of the pivot point with respect to the eye to be examined and the diopter are not maintained before and after the switching of the imaging angle of view. On the other hand, in the example of FIGS. 14A and 14B, the change in diopter caused by the displacement of the two convex lenses 16a and 16b can be canceled out by the displacement (movement) of the concave lens 16c. Therefore, in the examples of FIGS. 2A and 2B, even when the imaging angle of view is switched between specific angles of view, a good fundus image is easily captured. The position of the concave lens 16c can be appropriately determined based on "the focal length of each of the lenses 16a to 16c, the required photographing angle of view", and the like. In addition, the concave lens 16c may be fixedly disposed on the optical axis L3.

  In the configuration of the above embodiment, the diopter correction unit is provided on the common optical path of the light projecting optical system 3 and the light receiving optical system 4 (for example, between the scanning unit 15 and the laser beam emitting unit 11). It is also good. The diopter correction unit has a function of correcting “a change in diopter due to the objective lens optical system 16 according to a photographing angle of view” or a function of correcting “an error in the diopter of the eye E to be examined with respect to the emmetropic eye”. As a specific example, the diopter correction unit 18 will be described with reference to FIG. The diopter correction unit 18 performs diopter correction by “adjusting the optical path length of the imaging optical system 2 between the scanning unit 15 and the laser beam emitting unit 11”. The diopter correction unit 18 may have, for example, two mirrors 18 a and 18 b and a drive unit (not shown). The drive unit moves the two mirrors 18a and 18b in the direction of the arrow s while maintaining the positional relationship between the two mirrors 18a and 18b. As a result, the optical path length of "the common part of the light projecting optical system 3 and the light receiving optical system 4" is changed.

  Also, in the above embodiment, in order to change the shooting angle of view so that the position of the pivot point with respect to the subject's eye is maintained, the first convex lens 16a and the second convex lens 16b are mutually arranged along the optical axis L3. The case of displacement in the same direction has been described. However, the displacement of the first convex lens 16a and the second convex lens 16b is not limited to this. "When switching the shooting angle of view while maintaining the position of the turning point with respect to the subject's eye", at least the second convex lens 16b is displaced in the direction corresponding to "enlargement or reduction of the shooting angle of view" along the optical axis L3. It may be done. More specifically, when the imaging angle of view expands, at least the second convex lens 16b may be displaced in the “direction from the scanning unit 15 toward the eye E”. In addition, when the imaging angle of view is narrowed, at least the second convex lens 16b may be displaced in the “direction from the eye E to be scanned” to the scanning unit 15. In this case, the first convex lens 16a is in the same direction as the second convex lens 16b depending on the design value of the objective lens optical system 16 and the required photographing angle of view (the first photographing angle of view and the second photographing angle of view). Not only when displaced, but also when displaced in the opposite direction to the second convex lens 16b.

  In the above embodiment, the case where the shooting angle of view in the shooting optical system 2 is switched to “two steps of the first angle of view and the second angle of view wider than the first angle of view” has been described. However, the shooting angle of view in the shooting optical system 2 may be switched to more than two steps. Further, the shooting angle of view may be switched not continuously but continuously. In these cases, when the shooting angle of view is changed between any two values, the technology of the above embodiment can be applied.

  Further, in the above embodiment, the ophthalmologic imaging apparatus 1 has been described as "an SLO apparatus that two-dimensionally scans the fundus with laser light". However, the configuration of the ophthalmologic imaging apparatus 1 is not limited to this. For example, the ophthalmologic imaging apparatus (fundus imaging apparatus) 1 may be a so-called line scan SLO. In this case, based on the operation of the scanning unit 15, the linear laser light flux is scanned one-dimensionally on the fundus. The ophthalmologic imaging apparatus 1 may be a fundus camera.

  The present disclosure can also be said to relate to a scanning laser ophthalmoscope for imaging the fundus of an eye to be examined.

  The ophthalmologic image processing apparatus of the present embodiment can also be expressed as the following apparatus.

  That is, the first ophthalmologic image processing apparatus projects imaging light onto the fundus of an eye to be examined and receives light from the fundus along with the projected light by the light receiving element to capture an image of the fundus image. The display control unit generates a fundus oculi image and a second partial image from which a part of the fundus oculi image is extracted based on a light reception signal from the light receiving element, and a plurality of consecutive fundus oculi images are generated. And a second live image composed of a plurality of continuous second partial images are displayed side by side on the display device.

  The second ophthalmic image processing apparatus is the first ophthalmic image processing apparatus, wherein the display control unit is configured to set the second live image to a region corresponding to a part of the fundus image in the first live image. Also show enlarged.

  The third ophthalmic image processing apparatus is the first ophthalmic image processing apparatus, wherein the display control unit displays a range defined based on an instruction from the examiner in the fundus image as the second partial image. Do.

  The fourth ophthalmologic image processing apparatus according to the present invention is the first ophthalmologic image processing apparatus, wherein the display control unit includes an area corresponding to a part of a fundus image extracted as the second partial image, and another area. Is displayed on the first live image.

  The fifth ophthalmic image processing apparatus is an imaging optical system that captures a fundus image by projecting light onto the fundus of the subject's eye and receiving light from the fundus along with the projected light with a light receiving element. The display control unit causes the display device to display a second partial image in which a focused range included in the fundus image is captured along with the fundus image captured using the imaging optical system; At least one of the second partial images is displayed as a live image.

  A sixth ophthalmic image processing apparatus includes: a fundus oculi image; and a partial image captured with respect to a part of the fundus oculi image, wherein a first partial image higher in resolution than the fundus oculi image is stored A display control unit configured to combine the first partial image with an image area on the fundus image corresponding to the first partial image, and to display a composite image of the fundus image and the first partial image on a display medium And.

  A seventh ophthalmologic image processing apparatus according to the present invention is the first ophthalmologic image processing apparatus, wherein the display control unit performs the first display magnification and the combined image at a second display magnification that is larger than the first display magnification. When a first partial image area in which the first partial image is combined in the combined image can be displayed at the second display magnification, the first or second combined image may be displayed. The display in high resolution is performed as compared with the case where the peripheral region where the partial image is not synthesized is displayed at the second display magnification.

1, 100 ophthalmologic photographing apparatus 2 photographing optical system 3 projection optical system 4 light receiving optical system 16 objective lens optical system 17 lens moving mechanism 25 light receiving element 70 monitor 90 control unit

Claims (5)

A photographing optical system which has a light receiving element, projects light to the fundus of an eye to be examined through an objective lens optical system, and receives, by the light receiving element, light emitted from each position of the fundus along with the projected light. There,
An imaging optical system capable of switching an imaging angle of view between a first angle of view of 30 ° or more and 75 ° or less and a second angle of view wider than the first angle of view;
A fundus image captured when the angle of view of the imaging optical system is the second angle of view, and a portion of the fundus image captured when the angle of view of the imaging optical system is the first angle of view Acquisition means for acquiring a partial image of higher resolution than the captured fundus image;
Display control means for combining the partial image with an image area on the fundus image corresponding to the partial image and displaying a composite image of the fundus image and the partial image on a display medium A fundus imaging apparatus characterized by The imaging optical system is configured such that the imaging angle of view corresponds to the first angle of view, the second angle of view, and the second angle of view by switching the arrangement of lenses included in the objective lens system or by attaching and detaching a wide-angle lens attachment. The fundus imaging apparatus according to claim 1, which is switched between the angle of view. The display control means can display a part or all of the composite image at each of a first display magnification and a second display magnification larger than the first display magnification.
The display control unit is configured to, when the partial image area in which the partial image in the composite image is synthesized is displayed at the second display magnification, a peripheral area in which the partial image is not synthesized in the synthetic image. The fundus imaging apparatus according to claim 1 or 2 , wherein the composite image is displayed at a high resolution as compared with the case where the second display magnification is displayed. The fundus imaging apparatus according to any one of claims 1 to 3, wherein the fundus image and the partial image are images generated based on signals from the same light receiving element. A photographing optical system which has a light receiving element, projects light to the fundus of an eye to be examined through an objective lens optical system, and receives, by the light receiving element, light emitted from each position of the fundus along with the projected light. There,
By changing the arrangement of lenses included in the objective lens system, or by attaching or detaching a wide-angle lens attachment, the shooting angle of view may be a first angle of view and a second angle of view larger than the first angle of view. An imaging optical system switchable between the angle of view and
A fundus image captured when the angle of view of the imaging optical system is the second angle of view, and a portion of the fundus image captured when the angle of view of the imaging optical system is the first angle of view Acquisition means for acquiring a partial image of higher resolution than the captured fundus image;
Display control means for combining the partial image with an image area on the fundus image corresponding to the partial image and displaying a composite image of the fundus image and the partial image on a display medium A fundus imaging apparatus characterized by

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