JP6756498B2 - Ophthalmologic imaging equipment - Google Patents

Description

The present invention relates to an ophthalmologic imaging apparatus.

There is a demand for an ophthalmologic imaging device for screening for eye diseases and the like, which can easily image the fundus of the eye to be examined in a wide field of view. As such an ophthalmologic imaging apparatus, a scanning laser ophthalmoscope (hereinafter referred to as SLO) is known. The SLO is a device that forms an image of the fundus by scanning the fundus with light and detecting the return light with a light receiving device.

For example, Patent Document 1 discloses an SLO that includes three optical scanners and can perform scanning in a wide area and scanning that enlarges a part of the scanning area by controlling them.

Japanese Unexamined Patent Publication No. 2015-229023

However, it is known that ghosts (noise) caused by surface reflection of the objective lens and the cornea of the eye to be inspected are drawn in the central portion of the image acquired by an ophthalmologic imaging device such as SLO. The size and amount of light of the ghost increase as the angle of view increases. In many cases, the region of interest is placed in the central part of the acquired image, and if a ghost is drawn in the central part, the diagnosis may be hindered.

The present invention has been made in view of such circumstances, and an object of the present invention is to provide an ophthalmologic imaging apparatus capable of acquiring a wide-angle image in which ghost depiction is suppressed.

The ophthalmologic imaging apparatus according to the embodiment includes an objective optical system, a scanning system, an image forming unit, and an image synthesizing unit . The scanning system is used to scan the fundus with a luminous flux via the objective optical system. The image forming unit forms an image based on the data collected by the scanning system. The objective optical system includes an optical unit including a first optical member and a second optical member arranged closer to the eye to be inspected than the first optical member, and one or more arranged between the scanning system and the optical unit. The light beam that is oblique to the optical axis of the scanning system and has passed through the region near the optical axis of the first optical member is reflected at least twice and passed through the region near the optical axis of the second optical member. Irradiate the fundus of the eye. The optical unit is removable with respect to the optical path of the above luminous flux. The image synthesizing unit includes the first image formed by the image forming unit based on the data collected by the scanning system with the optical unit inserted in the optical path, and the optical unit retracted from the optical path. Based on the data collected by the scanning system, the second image formed by the image forming unit is combined to form a composite image.

According to the present invention, it is possible to provide an ophthalmologic imaging apparatus capable of acquiring a wide-angle image in which ghost depiction is suppressed.

It is the schematic which shows an example of the structure of the optical system of the ophthalmologic imaging apparatus which concerns on embodiment. It is the schematic which shows an example of the structure of the optical system of the ophthalmologic imaging apparatus which concerns on embodiment. It is the schematic which shows an example of the structure of the optical system of the ophthalmologic imaging apparatus which concerns on embodiment. It is the schematic which shows an example of the structure of the processing system of the ophthalmologic imaging apparatus which concerns on embodiment. It is a flow chart of the 1st operation example of the ophthalmologic imaging apparatus which concerns on embodiment. It is operation explanatory drawing of the ophthalmologic imaging apparatus which concerns on embodiment. It is operation explanatory drawing of the ophthalmologic imaging apparatus which concerns on embodiment. It is operation explanatory drawing of the ophthalmologic imaging apparatus which concerns on embodiment. It is operation explanatory drawing of the ophthalmologic imaging apparatus which concerns on embodiment. It is operation explanatory drawing of the ophthalmologic imaging apparatus which concerns on embodiment. It is a flow chart of the 2nd operation example of the ophthalmologic imaging apparatus which concerns on embodiment. It is a flow chart of the 3rd operation example of the ophthalmologic imaging apparatus which concerns on embodiment. It is the schematic which shows an example of the structure of the optical system of the ophthalmologic imaging apparatus which concerns on 1st modification of embodiment. It is the schematic which shows an example of the structure of the optical system of the ophthalmologic imaging apparatus which concerns on the 2nd modification of embodiment.

An example of an embodiment of the ophthalmologic imaging apparatus according to the present invention will be described in detail with reference to the drawings. It should be noted that the description contents of the documents cited in this specification and arbitrary known techniques can be incorporated into the following embodiments.

The ophthalmologic imaging apparatus according to the embodiment deflects the light from the light source by using an optical scanner, and irradiates the polarized light on the eye to be inspected (target eye, patient's eye) to receive light through the pupil of the eye to be inspected. It is a device that can irradiate a wide range of the posterior segment of the eye (fundus, vitreous body, etc.) after optometry. Such a configuration can be applied to any ophthalmologic imaging apparatus capable of irradiating the posterior segment of light with light. Ophthalmologic imaging devices capable of irradiating the back of the eye include a laser treatment device for irradiating the treatment site on the fundus with laser light, and moving the optotype while the eye to be inspected is fixed. It includes a perimeter and the like for measuring the visual field based on the response of the subject (patient).

Further, the ophthalmologic imaging apparatus according to the embodiment forms a distribution of predetermined data (image, layer thickness distribution, lesion distribution, etc.) in the posterior eye portion by receiving the return light from the posterior segment of the eye to be inspected. Is possible. Such a configuration can be applied to any ophthalmologic imaging apparatus capable of acquiring data by scanning the posterior segment of the eye with light. Ophthalmic imaging devices that can acquire data by scanning the back of the eye with light include SLO, which obtains a frontal image of the fundus by laser scanning using a confocal optical system, and Optical Coherence Tomography (hereinafter referred to as “Optical Coherence Tomography”). There are optical coherence tomography that obtains a tomographic image of the fundus using OCT), and a composite machine that combines the functions of an SLO and an optical coherence tomography. Hereinafter, a case where the ophthalmologic imaging apparatus according to the embodiment has the function of SLO and the function of an optical interference tomogram will be described.

Hereinafter, the left-right direction as seen from the subject is the X direction, the vertical direction is the Y direction, and the depth direction of the optical system as seen from the subject is the Z direction.

[Optical system]
1 to 3 show a configuration example of the optical system of the ophthalmologic imaging apparatus according to the embodiment. The ophthalmologic imaging apparatus according to the embodiment can acquire an image of the eye to be inspected in a range corresponding to the imaging mode. In the ophthalmologic imaging apparatus, the objective optical unit corresponding to the imaging mode can be selectively arranged on the optical axis of the optical system.

FIG. 1 shows a configuration example of the optical system of the ophthalmologic imaging apparatus when the high magnification (narrow angle (narrow angle of view)) imaging mode is set. FIG. 2 shows a configuration example of the objective optical system according to the embodiment that can be changed according to the photographing mode. In FIG. 2, the same parts as those in FIG. 1 are designated by the same reference numerals, and the description thereof will be omitted as appropriate. FIG. 3 shows a configuration example of the optical system of the ophthalmologic imaging apparatus when the wide-angle (wide-angle) imaging mode is set. In FIG. 3, the same parts as those in FIGS. 1 or 2 are designated by the same reference numerals, and the description thereof will be omitted as appropriate. In FIGS. 1 and 3, the position optically conjugated with the fundus Ef of the eye E to be examined is illustrated as the fundus conjugate position P, and the position optically conjugated with the pupil (pupil) of the eye E to be examined is defined as the pupil conjugate position Q. It is illustrated.

The optical system 100 includes a projection system that projects light onto the eye to be inspected via the objective optical system 110 and a light receiving system that receives the return light of the light projected on the eye E to be inspected by the projection system via the objective optical system 110. including. The ophthalmologic imaging apparatus forms an image based on the result of light reception by the light receiving system. The ophthalmologic imaging apparatus according to the embodiment can form SLO images and OCT images. That is, the optical system 100 includes an SLO optical system 130 and an OCT optical system 140. The SLO optical system 130 includes an SLO projection system and an SLO light receiving system. The OCT optical system 140 includes an OCT projection system and an OCT light receiving system.

The ophthalmologic imaging apparatus is provided with an anterior segment imaging system (anterior segment observation system) 120 for photographing the anterior segment of the eye to be inspected. The optical system 100 can move in the X direction, the Y direction, and the Z direction by a moving mechanism (moving mechanism 100D described later) (not shown) together with the objective optical system 110 and the anterior segment imaging system 120. The ophthalmologic imaging apparatus moves the optical system 100 or the like by a moving mechanism based on the anterior segment image of the eye to be inspected E obtained by the anterior ocular segment imaging system 120, thereby locating the optical system 100 with respect to the eye to be inspected E. It is possible to perform alignment for alignment. Hereinafter, the case where the optical system 100 includes the objective optical system 110 and the anterior segment imaging system 120 will be described, but the optical system 100 may not include these.

(Objective optical system)
The ophthalmologic imaging apparatus can selectively arrange the objective optical unit on the optical axis O of the optical system 100 according to the imaging mode. In this embodiment, the photographing modes include a high-magnification photographing mode in which the eye E to be examined is photographed in the first range (for example, an angle of view of 50 degrees) and a second range (for example, an angle of view of 105 degrees) wider than the first range. There is a wide-angle shooting mode for shooting the eye E to be inspected. In the high magnification imaging mode, a high magnification (narrow angle) image (SLO image or OCT image) representing the first range of the eye E to be inspected is acquired. In the wide-angle photographing mode, a wide-angle image (SLO image or OCT image) representing a second range wider than the first range of the eye E to be inspected is acquired. Hereinafter, the image acquired in the high-magnification shooting mode may be referred to as a "narrow-angle image"("standardimage"), and the image acquired in the wide-angle shooting mode may be referred to as a "wide-angle image".

The objective optical system 110 includes objective optical units 110A and 110B (see FIG. 2). The objective optical system 110 is provided with an angle of view changing mechanism 116 for changing the angle of view. The angle of view changing mechanism 116 includes, for example, a known rotation mechanism or slide mechanism. In this embodiment, the objective optical unit 110B can be inserted into and removed from the optical axis O (optical path of light from the optical system 100) of the optical system 100 by the angle of view changing mechanism 116. That is, the angle of view can be changed by selectively arranging the objective optical unit 110B between the objective optical unit 110A and the eye E to be inspected by the angle of view changing mechanism 116 according to the photographing mode. In the high-magnification photographing mode, the objective optical unit 110A is arranged so that the optical axis of the optical system 100 coincides with the optical axis (FIG. 1). In the wide-angle shooting mode, the objective optical units 110A and 110B are arranged between the objective optical unit 110A and the eye E to be inspected so that the optical axis coincides with the optical axis O (FIG. 3). For example, by providing the objective optical system 110 with a detection unit for detecting whether or not the objective optical unit 110B is arranged on the optical axis O, the control unit 200 described later can arrange the objective optical unit 110B on the optical axis O. It is possible to specify the type of shooting mode from the detection result of presence / absence. The angle of view changing mechanism 116 may automatically and selectively arrange the objective optical unit 110B on the optical axis O under the control of the control unit 200 described later. For example, the objective optical unit 110B may include a lens group corresponding to the objective optical unit 110A, and the objective optical unit 110A and the objective optical unit 110B may be selectively arranged according to the photographing mode.

The objective optical unit 110A includes two or more lenses. A dichroic mirror DM1 is provided between the two or more lenses. For example, the objective optical unit 110A may be a lens unit (nuggler type) including convex lenses 111A and 112A and a concave lens 113A. The convex lenses 111A, 112A, and the concave lens 113A are arranged in this order from the side of the eye E to be inspected. A dichroic mirror DM1 is arranged between the convex lens 112A and the concave lens 113A. The dichroic mirror DM1 is an optical path coupling member that connects the optical path of the anterior segment imaging system 120 to both the optical path of the SLO optical system 130 and the optical path of the OCT optical system 140. A position (fundus conjugate position) P optically conjugated with the fundus (retina) or its vicinity is arranged between the dichroic mirror DM1 and the concave lens 113A. The objective optical unit 110A may include a dichroic mirror DM1.

The dichroic mirror DM1 emits light from the SLO optical system 130 (SLO light), return light from the eye E to be inspected, light from the OCT optical system 140 (OCT light, measurement light), and return light from the eye E to be inspected. Make it transparent. The dichroic mirror DM1 reflects the light from the anterior segment imaging system 120 toward the eye to be inspected E, and reflects the return light from the eye to be inspected E toward the anterior segment imaging system 120.

The objective optical unit 110B includes a first spherical mirror 111B and a second spherical mirror 112B as optical elements of the reflection optical system. The first spherical mirror 111B is arranged closer to the eye E to be inspected than the second spherical mirror 112B. An opening is formed in the region near the optical axis O of the first spherical mirror 111B (the central portion of the first spherical mirror 111B). The surface of the first spherical mirror 111B on the side of the optical system 100 is provided with a reflecting surface that reflects the irradiated light toward the optical system 100. An opening is formed in the region near the optical axis O of the second spherical mirror 112B (the central portion of the second spherical mirror 112B). The surface of the second spherical mirror 112B on the side of the eye E to be inspected is provided with a reflective surface that reflects the irradiated light toward the eye E to be inspected. The reflecting surface of at least one of the first spherical mirror 111B and the second spherical mirror 112B may be an ellipsoidal surface or a free curved surface instead of a spherical surface. Further, a translucent portion may be provided in a region near the optical axis O in at least one of the first spherical mirror 111B and the second spherical mirror 112B.

The light (SLO light, OCT light) that has passed through the objective optical unit 110A, is oblique to the optical axis O, and has passed through the opening (region near the optical axis O) formed in the second spherical mirror 112B is the first. It is reflected by the spherical mirror 111B toward the reflecting surface of the second spherical mirror 112B. The light reflected by the first spherical mirror 111B is applied to the fundus of the eye E to be inspected through the opening (region near the optical axis O) formed in the first spherical mirror 111B by the second spherical mirror 112B. That is, the objective optical unit 110B reflects light that is oblique to the optical axis O and has passed through the region near the optical axis O in the second spherical mirror 112B at least twice, and is near the optical axis O in the first spherical mirror 111B. Irradiate the fundus through the area. The return light of the light emitted to the fundus of the eye E to be inspected is guided to the optical system 100 through the same path.

Hereinafter, a case where only the objective optical unit 110A is arranged on the optical axis O as the objective optical system 110 will be described.

(Anterior segment imaging system)
The anterior segment imaging system 120 includes an anterior segment illumination light source 121, a collimating lens 122, an anterior segment imaging camera 123, an imaging lens 124, and a beam splitter BS1. The beam splitter BS1 is an optical path coupling member that couples the optical path of the return light to the optical path of the illumination light for illuminating the anterior segment of the eye E to be inspected.

The anterior segment illumination light source 121 is a light source for illuminating the anterior segment of the eye E to be inspected. The anterior segment photographing camera 123 includes an imaging element for detecting the reflected light (return light) from the anterior segment of the eye to be inspected E illuminated by the anterior segment illumination light source 121. As the anterior segment illumination light source 121, for example, an LED that emits light having a center wavelength of 950 nm is used. The light emitted by the anterior segment illumination light source 121 is converted into a parallel luminous flux by the collimating lens 122. The illumination light as a parallel luminous flux is reflected by the beam splitter BS1 toward the dichroic mirror DM1. The illumination light reflected by the beam splitter BS1 is deflected toward the eye E to be inspected by the dichroic mirror DM1. The return light of the illumination light from the eye E to be inspected is reflected by the dichroic mirror DM1 and passes through the beam splitter BS1. The return light transmitted through the beam splitter BS1 is focused by the imaging lens 124 on the detection surface of the image sensor in the anterior segment imaging camera 123. The detection surface of the image sensor is arranged at or near the pupil conjugate position (anterior segment conjugate position) Q. The image sensor is composed of, for example, a CCD or CMOS image sensor. The detection result of the return light from the anterior segment of the eye E to be inspected by the image sensor is used for forming an image of the anterior segment.

(SLO optical system)
The optical path of the SLO optical system 130 and the optical path of the OCT optical system 140 are coupled by the dichroic mirror DM2. At least a part of the SLO optical system 130 is formed as a telecentric optical system. Similarly, at least a part of the OCT optical system 140 is formed as a telecentric optical system. The dichroic mirror DM2 combines an optical path formed by the telecentric optical system of the SLO optical system 130 with an optical path formed by the telecentric optical system of the OCT optical system 140. As a result, even when the focal position of the optical system 100 is changed by moving the objective optical system 110, the aberration of the pupil (for example, the exit pupil by the objective optical system 110) is reduced, so that the focusing state can be easily adjusted.

The SLO optical system 130 includes an SLO light source 131, a collimating lens 132, a beam splitter BS2, a condensing lens 133, a confocal diaphragm 134, a detector 135, an optical scanner 136, and a lens 137. The beam splitter BS2 is an optical path coupling member that couples the optical path of the return light to the optical path of the SLO light projected on the eye E to be inspected.

As the SLO light source 131, for example, one that emits light having a center wavelength of 840 nm is used. Examples of the SLO light source 131 include a laser diode (hereinafter, LD), a super luminescent diode (SLD), and a laser driven light source (LDLS). The SLO light source 131 is arranged at or near a position (fundus conjugate position) P optically conjugated with the fundus (retina).

The light emitted from the SLO light source 131 is converted into a parallel luminous flux by the collimating lens 132. The light as a parallel luminous flux passes through the beam splitter BS2. The light transmitted through the beam splitter BS2 is deflected by the optical scanner 136. The optical scanner 136 is used to scan the fundus Ef of the eye E to be inspected with the light from the SLO light source 131. The optical scanner 136 includes an optical scanner 136X that deflects light in the X direction and an optical scanner 136Y that deflects light in the Y direction. The optical scanner 136X is a mirror whose inclination can be changed, and the inclination of the reflecting surface is controlled by the control unit 200 described later. The optical scanner 136 is used, for example, for horizontal scanning within the fundus. An optical scanner 136Y is arranged on the side of the eye E to be inspected of the optical scanner 136X. The optical scanner 136Y is a mirror whose inclination can be changed, and the inclination of the reflecting surface is controlled by the control unit 200. The optical scanner 136Y is used, for example, for vertical scanning in the fundus that is orthogonal to the horizontal direction. One of the optical scanner 136X and the optical scanner 136Y is a low-speed scanner such as a galvano mirror, and the other is a high-speed scanner such as a resonant mirror, a polygon mirror, or a MEMS (Micro Electro Mechanical Systems: hereinafter, MEMS) mirror. You can. The reflective surface of the optical scanner 136Y is arranged at or near a position (pupil conjugate position) Q that is optically conjugated to the pupil of the eye E to be inspected. A lens 137 and a dichroic mirror DM2 are arranged on the side of the eye E to be inspected of the optical scanner 136Y. The light from the SLO light source 131 deflected by the optical scanner 136 passes through the lens 137 and the dichroic mirror DM2 and is projected onto the eye E to be inspected via the objective optical system 110.

The return light of the light from the SLO light source 131 projected on the eye E to be inspected is reflected toward the detector 135 by the beam splitter BS2 via the same optical path. A confocal lens 133 and a confocal diaphragm 134 are arranged between the beam splitter BS2 and the detector 135. The condensing lens 133 condenses the light reflected by the beam splitter BS2. The light collected by the condensing lens 133 passes through the aperture formed in the confocal diaphragm 134 and is incident on the detection surface of the detector 135. The opening formed in the confocal diaphragm 134 is arranged at or near the position (fundus conjugate position) P optically conjugated with the fundus (retina). The detector 135 is composed of, for example, an avalanche photodiode (APD) or a photomultiplier tube (PMT).

(OCT optical system)
The OCT optical system 140 includes a focusing lens 141, an optical scanner 142, a collimating lens 143, and an interference optical system 150. The interference optical system 150 includes an OCT light source 151, fiber couplers 152 and 153, a prism 154, and a detector 155.

The focusing lens 141 can be moved along the optical axis (optical path) of the OCT optical system 140 by a moving mechanism (moving mechanism 141D described later) (not shown). As a result, the focal position of the OCT optical system 140 can be changed independently of the SLO optical system 130. Therefore, for example, after the focusing state of the SLO optical system 130 and the OCT optical system 140 is adjusted by moving the objective optical system 110, the focusing state of the OCT optical system 140 is finely adjusted by moving the focusing lens 141. Can be done.

The optical scanner 142 is used to scan the fundus Ef of the eye E to be inspected with the measurement light based on the light from the OCT light source 151. The optical scanner 142 includes an optical scanner 142X that deflects light in the X direction and an optical scanner 142Y that deflects light in the Y direction. The optical scanner 142X is a mirror whose inclination can be changed, and the inclination of the reflecting surface is controlled by the control unit 200. The optical scanner 142 is used, for example, for horizontal scanning within the fundus. An optical scanner 142Y is arranged on the side of the eye E to be inspected of the optical scanner 142X. The optical scanner 142Y is a mirror whose inclination can be changed, and the inclination of the reflecting surface is controlled by the control unit 200. The optical scanner 142Y is used, for example, for vertical scanning in the fundus that is orthogonal to the horizontal direction. One of the optical scanner 142X and the optical scanner 142Y may be a low-speed scanner such as a low-speed galvano mirror, and the other may be a high-speed scanner such as a high-speed galvano mirror. The intermediate positions of the optical scanners 142X and 142Y are arranged at or near the position (pupil conjugate position) Q that is optically conjugated with the pupil of the eye E to be inspected. A collimating lens 143 is arranged on the side of the OCT light source 151 of the optical scanner 142Y.

The interference optical system 150 is provided with an optical system for acquiring an OCT image of the eye E to be inspected. This optical system has the same configuration as a conventional Swept source type OCT device. That is, this optical system divides the light from the wavelength sweep type (wavelength scanning type) light source into the measurement light and the reference light, and separates the return light of the measurement light from the eye E to be examined and the reference light via the reference optical path. It is an interference optical system that causes interference to generate interference light and detects this interference light. The detection result (detection signal) of the interference light by the interference optical system is a signal showing the spectrum of the interference light. The interference optical system 150 may have the same configuration as the conventional spectral domain type OCT device, instead of the Swept source type OCT device.

The OCT light source 151 is a wavelength sweep type (wavelength scanning type) light source capable of sweeping (scanning) the wavelength of OCT light (emitted light). As the wavelength sweep type light source, for example, a laser light source including a resonator and emitting light having a center wavelength of 1050 nm is used. The OCT light source 151 changes the output wavelength with time in a near-infrared wavelength band that is invisible to the human eye.

The light L0 output from the OCT light source 151 is guided by the optical fiber f1 to the fiber coupler 152 and divided into the measurement light LS and the reference light LR.

The reference light LR is guided to the fiber exit end c1 by the optical fiber f2 and is irradiated to the collimating lens 156 from the fiber exit end c1. The reference light LR emitted from the fiber exit end c1 is converted into a parallel luminous flux by the collimating lens 156. The reference light LR, which is a parallel luminous flux, is guided to the prism 154. The prism 154 turns back the traveling direction of the reference light LR, which is made into a parallel luminous flux by the collimated lens 156, in the opposite direction. The optical path of the reference light LR incident on the prism 154 and the optical path of the reference light LR emitted from the prism 154 are parallel to each other. The prism 154 can be moved in the direction along the incident optical path and the outgoing optical path of the reference light LR by a moving mechanism (moving mechanism 154D described later) (not shown). In this case, an actuator for generating a driving force for moving the moving mechanism and a transmission mechanism for transmitting the driving force are provided. The actuator is composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears and a rack and pinion. As a result, the length of the optical path of the reference light LR is changed.

The reference light LR that has passed through the prism 154 is converted from a parallel light flux to a focused light flux by the collimated lens 157, is incident on the fiber incident end c2, and is guided to the fiber coupler 153 by the optical fiber f3. An optical path length correction member or a dispersion compensation member may be arranged between the collimating lenses 156 and 157 and the prism 154. The optical path length correction member acts as a delay means for matching the optical path length (optical distance) of the reference light LR with the optical path length of the measurement light LS. The dispersion compensating member acts as a dispersion compensating means for matching the dispersion characteristics between the reference light LR and the measurement light LS.

On the other hand, the measurement optical LS generated by the fiber coupler 152 is guided to the fiber end c3 by the optical fiber f4. The measurement light LS guided to the fiber end c3 is applied to the collimating lens 143. The fiber end c3 is arranged at or near the position (fundus conjugate position) P optically conjugated with the fundus (retina). The measurement light LS emitted from the fiber end c3 is converted into a parallel luminous flux by the collimating lens 143. The measurement light LS converted into a parallel luminous flux reaches the dichroic mirror DM2 via the optical scanner 142 and the focusing lens 141. The measurement light LS is reflected by the dichroic mirror DM2, refracted by the objective optical system 110, and irradiated to the eye E to be inspected. The measurement light LS is scattered (including reflection) at various depth positions of the eye E to be inspected. The return light of the measurement light LS including such backscattered light travels in the same path as the outward path in the opposite direction, is guided to the fiber coupler 152, and reaches the fiber coupler 153 via the optical fiber f5.

The fiber coupler 153 combines (interferes with) the measurement light LS incidented through the optical fiber f5 and the reference light LR incidented via the optical fiber f3 to generate interference light. The fiber coupler 153 generates a pair of interference light LCs by branching the interference light between the measurement light LS and the reference light LR at a predetermined branching ratio (for example, 1: 1). The pair of interference light LCs emitted from the fiber coupler 153 are guided to the detector 155.

The detector 155 is, for example, a balanced photodiode (Balanced Photo Diode) that has a pair of photodetectors that detect each pair of interference light LCs and outputs the difference between the detection results by these. The detector 155 sends the detection result (detection signal) to a DATA (Data Acquisition System) (not shown). A clock is supplied to the DAC from the OCT light source 151. This clock is generated in the OCT light source 151 in synchronization with the output timing of each wavelength swept (scanned) within a predetermined wavelength range by the wavelength sweep type light source. Based on this clock, the DAQ samples the detection result of the detector 155 and sends it to an image forming unit or the like described later. The image forming unit forms a reflection intensity profile in each A line by, for example, performing a Fourier transform or the like on the spectral distribution based on the detection result obtained by the detector 155 for each series of wavelength scans (for each A line). To do. Further, the image forming unit forms image data by imaging the reflection intensity profile of each A line.

[Processing system]
FIG. 4 shows a configuration example of the processing system of the ophthalmologic imaging apparatus according to the embodiment. In FIG. 4, the same parts as those in FIGS. 1 and 3 are designated by the same reference numerals, and the description thereof will be omitted as appropriate.

(Control unit)
The processing system of the ophthalmologic imaging apparatus according to the embodiment is mainly composed of the control unit 200. The control unit 200 controls each part of the ophthalmologic imaging apparatus. The control unit 200 includes a main control unit 201 and a storage unit 202. The function of the main control unit 201 is realized by, for example, a microprocessor. A computer program for controlling the ophthalmologic imaging apparatus is stored in the storage unit 202 in advance. This computer program includes various light source control programs, optical scanner control programs, various detector control programs, image formation programs, data processing programs, user interface programs, and the like. When the main control unit 201 operates according to such a computer program, the control unit 200 executes the control process.

Controls for the objective optical system 110 include control for the moving mechanism 110D for moving the objective optical system 110 along the optical axis O. For example, the moving mechanism 110D is provided with an actuator that generates a driving force for moving the moving mechanism 110D and a transmission mechanism that transmits the driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears and a rack and pinion. The main control unit 201 controls the moving mechanism 110D by sending a control signal to the actuator.

Controls for the SLO optical system 130 include control of the SLO light source 131, control of the optical scanner 136, control of the detector 135, and the like. Control of the SLO light source 131 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. The control of the optical scanner 136 includes control of the scanning position and scanning range by the optical scanner 136X, control of the scanning position and scanning range by the optical scanner 136Y, and the like. Control of the detector 135 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element.

Controls for the OCT optical system 140 include control of the OCT light source 151, control of the optical scanner 142, control of the moving mechanism 141D and moving mechanism 154D, and control of the detector 155. Control of the OCT light source 151 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. The control of the optical scanner 142 includes the control of the scanning position and the scanning range by the optical scanner 142X, the control of the scanning position and the scanning range by the optical scanner 142Y, and the like. The moving mechanism 141D moves the focusing lens 141 along the optical path of the OCT optical system 140. For example, the moving mechanism 141D is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears and a rack and pinion. The main control unit 201 controls the moving mechanism 141D by sending a control signal to the actuator. The moving mechanism 154D moves the prism 154 in the direction along the incident optical path and the outgoing optical path of the reference light LR. For example, the moving mechanism 154D is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears and a rack and pinion. The main control unit 201 controls the moving mechanism 154D by sending a control signal to the actuator. Control of the detector 155 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element.

Controls for the anterior segment imaging system 120 include control of the anterior segment illumination light source 121 and control of the anterior segment imaging camera 123. Control of the anterior segment illumination light source 121 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. Control of the anterior segment imaging camera 123 includes exposure adjustment, gain adjustment, and imaging rate adjustment of the image sensor.

Controls for the optical system 100 include control of a moving mechanism 100D that moves the optical system 100 (including the dichroic mirror DM1 and the anterior segment imaging system 120) in the X, Y, and Z directions. For example, the moving mechanism 100D is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears and a rack and pinion. The main control unit 201 controls the moving mechanism 100D by sending a control signal to the actuator.

The main control unit 201 includes an alignment control unit 201A, a tracking control unit 201B, and a display control unit 201C.

The alignment control unit 201A controls the execution of alignment for aligning the optical system 100 with respect to the eye E to be inspected. The alignment control unit 201A controls the movement mechanisms 100D and 110D based on the anterior segment image of the eye E to be inspected obtained by the anterior segment imaging system 120. The alignment control unit 201A specifies, for example, a feature portion in the anterior segment image of the eye E to be inspected obtained by the anterior segment imaging system 120, and the amount of deviation between the position of the specified feature portion and the predetermined target position. The amount of movement of the optical system 100 or the like is obtained so that The alignment control unit 201A aligns the optical system 100 with respect to the eye E to be inspected by controlling the movement mechanism 100D based on the obtained movement amount (XY directions). The target position may be a predetermined position or a position in the anterior segment image designated by using the UI unit 230.

The alignment control unit 201A specifies, for example, the in-focus state (blurring state) of the anterior segment image of the eye E to be inspected obtained by the anterior segment imaging system 120, and the specified in-focus state is the desired in-focus state. It is possible to obtain the amount of movement of the optical system 100 in the Z direction so as to be. The alignment control unit 201A aligns the optical system 100 with respect to the eye E to be inspected (Z direction) by controlling the movement mechanism 100D based on the obtained movement amount. It should be noted that two or more cameras are used to photograph the anterior segment from different directions, and the focused state is three-dimensionally specified from the two or more images provided with parallax, and the specified focused state is desired. The amount of movement of the optical system 100 in the Z direction may be determined so as to be in the focused state.

The alignment control unit 201A may align the objective optical system 110 with respect to the eye E to be inspected (Z direction) by controlling the movement mechanism 110D based on the SLO image obtained by the SLO optical system 130. In this case, the alignment control unit 201A identifies the in-focus state (blurring degree) of the acquired SLO image, and makes the specified in-focus state a desired in-focus state in the Z direction of the objective optical system 110. Find the amount of movement. The alignment control unit 201A controls the movement mechanism 110D based on the obtained movement amount.

The tracking control unit 201B controls tracking of the SLO image of the eye E to be inspected obtained by the SLO optical system 130. The tracking control unit 201B specifies, for example, a feature portion in the SLO image at a predetermined timing, and when the position of the specified feature portion changes, the movement amount is obtained so that the deviation amount of the position is canceled. The tracking control unit 201B controls tracking for the SLO image based on the obtained movement amount.

Further, the tracking control unit 201B controls tracking of the OCT image of the eye E to be inspected obtained by the OCT optical system 140 based on the SLO image. The tracking control unit 201B specifies, for example, a feature portion in the SLO image at a predetermined timing, and when the position of the specified feature portion changes, the movement amount is obtained so that the deviation amount of the position is canceled. The tracking control unit 201B controls tracking for the OCT image based on the obtained movement amount. The tracking control unit 201B may be provided in the data processing unit 220.

The display control unit 201C causes various information to be displayed on the UI unit 230, which will be described later. The information displayed on the UI unit 230 includes information generated by the control unit 200, an image formed by the image forming unit 210, and information after data processing by the data processing unit 220.

The display control unit 201C causes the UI unit 230 to display the composite image obtained by synthesizing the wide-angle image and the narrow-angle image by the image synthesis unit 220C described later. The wide-angle image is an image (SLO image, OCT image) acquired in the wide-angle shooting mode as described above. The narrow-angle image is an image (SLO image, OCT image) acquired in the high-magnification shooting mode as described above.

The display control unit 201C can display the composite image as a still image on the UI unit 230, or repeatedly display the composite image as a moving image on the UI unit 230. The composite image as a moving image includes an image in which only the narrow-angle image in the composite image is updated and an image in which only the wide-angle image in the composite image is updated. For example, when a narrow-angle image is repeatedly acquired after a wide-angle image is acquired using the SLO optical system 130 or the OCT optical system 140, the narrow-angle image in the composite image is updated to the newly acquired narrow-angle image. To. Alternatively, when the wide-angle image is repeatedly acquired after the narrow-angle image is acquired using the SLO optical system 130 or the OCT optical system 140, the wide-angle image in the composite image is updated to the newly acquired wide-angle image.

(Image forming part)
The image forming unit 210 includes an SLO image forming unit 210A and an OCT image forming unit 210B. The SLO image forming unit 210A forms the image data of the SLO image based on the detection signal input from the detector 135 and the pixel position signal input from the control unit 200. The OCT image forming unit 210B forms image data of an OCT image (tomographic image of the fundus Ef) based on the detection signal input from the detector 155 and the pixel position signal input from the control unit 200. Further, the image forming unit 210 forms an anterior segment image based on the detection result of the reflected light from the anterior segment of the eye E to be inspected by the image sensor of the anterior segment photographing camera 123. Various images (image data) formed by the image forming unit 210 are stored in, for example, a storage unit 202.

(Data processing unit)
The data processing unit 220 executes various data processing. As an example of data processing, there is processing on image data formed by the image forming unit 210 or another device. Examples of this processing include various image processing, analysis processing for images, and diagnostic support processing such as image evaluation based on image data.

The data processing unit 220 includes an alignment unit 220A, a scale adjustment unit 220B, and an image composition unit 220C.

The alignment unit 220A aligns the wide-angle image of the eye E to be inspected acquired in the wide-angle imaging mode with the narrow-angle image of the eye E to be inspected including the central portion of the wide-angle image acquired in the high-magnification imaging mode. The central portion of the wide-angle image is a portion including a position on the optical axis O. The wide-angle image is formed by the wide-angle (second range) SLO image or OCT image forming unit 210B formed by the SLO image forming unit 210A in the wide-angle photographing mode (state in which the objective optical unit 110B is inserted in the optical axis O). It is a wide-angle OCT image. The narrow-angle image is a narrow-angle (first range) SLO image or OCT image forming unit 210B formed by the SLO image forming unit 210A in the high-magnification photographing mode (state in which the objective optical unit 110B is retracted from the optical axis O). It is a narrow-angle OCT image formed by.

The alignment unit 220A specifies, for example, the corresponding region of the wide-angle image corresponding to the central region including the central portion of the narrow-angle image. The alignment unit 220A can specify the corresponding region based on the respective angles of view of the wide-angle image and the narrow-angle image and the position of the central region including the central portion of the wide-angle image. The alignment unit 220A aligns the corresponding region in the wide-angle image with the narrow-angle image. Further, the alignment unit 220A identifies a characteristic portion (characteristic portion such as the papilla, blood vessel, etc.) of the fundus Ef that is commonly depicted in the wide-angle image and the narrow-angle image, and uses the identified characteristic portion as an index to wide-angle. It is also possible to align the image with the narrow-angle image.

The scale adjustment unit 220B combines a wide-angle image and a narrow-angle image that have been aligned by the alignment unit 220A based on the angle of view set in the wide-angle shooting mode and the angle of view set in the high-magnification shooting mode. Performs the process of matching the scales.

The image synthesizing unit 220C forms a composite image by synthesizing a wide-angle image and a narrow-angle image whose scale has been adjusted by the scale adjusting unit 220B. The image synthesizing unit 220C sets the central region (region including the central portion, partial region) of the wide-angle image including the position on the optical axis O of the optical system 100 in at least a part of the narrow-angle image corresponding to the central region. It is possible to form a composite image by substituting. For example, the image synthesizing unit 220C forms a composite image by cutting out a corresponding region in the wide-angle image specified as described above and arranging at least a part of the narrow-angle image in the corresponding region. That is, the region including the central portion of the wide-angle image is replaced with at least a part of the narrow-angle image corresponding to the region. A wide-angle image is an image of a peripheral portion that is a peripheral region of the central portion because the central portion is not imaged. Therefore, by replacing the region including the central portion of the wide-angle image with at least a part of the narrow-angle image corresponding to the region, it is possible to acquire a wide-angle image in which ghost is suppressed. In addition, the resolution of the central portion of the wide-angle image is improved.

Further, the image synthesizing unit 220C forms a composite image by superimposing at least a part of the narrow-angle image corresponding to the central region on the central region of the wide-angle image including the position on the optical axis O of the optical system 100. It is possible to do. For example, the image synthesizing unit 220C forms a composite image by superimposing at least a part of the narrow-angle image on the corresponding region in the wide-angle image specified as described above. That is, at least a part of the narrow-angle image corresponding to the region is superimposed on the region including the central portion of the wide-angle image. In this case as well, it is possible to acquire a wide-angle image in which ghosts are suppressed. In addition, the resolution of the central portion of the wide-angle image is improved.

That is, the image synthesizing unit 220C is a composite image in which the central portion of the wide-angle SLO image is replaced with a narrow-angle SLO image, a composite image in which a narrow-angle SLO image is superimposed on the central portion of the wide-angle SLO image, and a wide-angle image. A composite image in which the central portion of the OCT image is replaced with a narrow-angle OCT image or a composite image in which a narrow-angle OCT image is superimposed on the central portion of the wide-angle OCT image is formed. Further, the image compositing unit 220C includes a composite image in which the central portion of the wide-angle SLO image is replaced with a narrow-angle OCT image, a composite image in which a narrow-angle OCT image is superimposed on the central portion of the wide-angle SLO image, and a wide-angle image. A composite image in which the central portion of the OCT image is replaced with a narrow-angle SLO image, or a composite image in which a narrow-angle SLO image is superimposed on the central portion of the wide-angle OCT image may be formed.

The alignment unit 220A aligns the wide-angle image and the narrow-angle image adjusted so that the scales match, and the image composition unit 220C aligns the aligned wide-angle image and the narrow-angle image. A composite image in which the ghost in the central portion is removed may be formed by compositing.

As described above, the image synthesizing unit 220C has the wide-angle image formed by the image forming unit 210 based on the data collected by the optical system 100 with the objective optical unit 110B inserted in the optical axis O, and the optical axis O. A composite image is formed by synthesizing a narrow-angle image formed by the image forming unit 210 based on the data collected by the optical system 100 with the objective optical unit 110B retracted from the above. The image composition unit 220C can form a composite image in which the narrow-angle image is arranged in the central portion and the wide-angle image is arranged in the peripheral portion.

(UI part)
The UI (User Interface) unit 230 has a function for exchanging information between the user and the ophthalmologic imaging apparatus. The UI unit 230 includes a display device and an operation device (input device). The display device may include a display unit, and may include other display devices. Operating devices include various hardware keys and / or software keys. The control unit 200 can receive the operation content for the operation device and output a control signal corresponding to the operation content to each unit. It is possible to integrally configure at least a part of the operating device and at least a part of the display device. The touch panel display is an example.

The optical system 100 is an example of the "scan system" according to the embodiment. The objective optical unit 110B is an example of the "optical unit" according to the embodiment. The second spherical mirror 112B is an example of the "first optical member" according to the embodiment. The first spherical mirror 111B is an example of the "second optical member" according to the embodiment. The wide-angle image obtained by photographing the eye E to be inspected when the wide-angle photographing mode is set is an example of the "first image" according to the embodiment. The narrow-angle image obtained by photographing the eye E to be inspected when the high-magnification photographing mode is set is an example of the "second image" according to the embodiment.

[motion]
The operation of the ophthalmologic imaging apparatus according to the embodiment will be described.

"First operation example]
5 and 6A to 6E show a first operation example of the ophthalmologic imaging apparatus according to the embodiment. FIG. 5 shows a flow chart of an operation example of the ophthalmologic imaging apparatus when acquiring an SLO image. 6A to 6E show operation explanatory views of the ophthalmologic imaging apparatus according to the embodiment of FIG.

(S1)
First, the angle of view changing mechanism 116 inserts the objective optical unit 110B, which is an objective lens for wide-angle photographing, into the optical axis O. For example, a user such as an examiner, a subject, a doctor, or a patient manually inserts the objective optical unit 110B into the optical axis O. The ophthalmologic imaging apparatus can shift to the next operation based on the operation performed by the user on the UI unit 230. Further, the ophthalmologic imaging apparatus detects the presence or absence of the objective optical unit 110B on the optical axis O, and when it is determined that the objective optical unit 110B is arranged on the optical axis O based on the detection result, the following operation is performed. You may want to move to.

When the objective optical unit 110B is inserted into the optical axis O, the control unit 200 acquires an anterior segment image by photographing the anterior segment of the eye E to be inspected by the anterior segment imaging system 120. The alignment control unit 201A aligns the optical system 100 and the objective optical system 110 with respect to the eye E to be inspected by controlling the movement mechanism 100D based on the acquired anterior eye portion image (X direction, Y direction and Z). direction). The control unit 200 moves the optical scanner 136 to a predetermined initial position. In S1, the tracking control unit 201B may start tracking control for the SLO image.

(S2)
The control unit 200 turns on the SLO light source 131 and controls the optical scanner 136 to start scanning the fundus Ef of the eye E to be inspected with the light from the SLO light source 131. The SLO image forming unit 210A forms an SLO image of the fundus Ef based on the detection result of the fundus reflected light by the detector 135. The SLO image obtained in S2 is a wide-angle image as shown in FIG. 6A. The fundus Ef is not visualized in the central portion G of this wide-angle image (it is difficult to observe the fundus Ef).

(S3)
Next, the objective optical unit 110B is retracted from the optical axis O by the angle of view changing mechanism 116. For example, a user such as an examiner, a subject, a doctor, or a patient manually retracts the objective optical unit 110B from the optical axis O. When the objective optical unit 110B is retracted from the optical axis O, the control unit 200 performs alignment and moves the optical scanner 136 to a predetermined initial position, as in S1.

(S4)
When only the objective optical unit 110A is arranged on the optical axis O, the control unit 200 again aligns and controls the optical scanner 136 in the same manner as S2, so that the eye is examined by the light from the SLO light source 131. The scan of the fundus Ef of E is started. At this time, the area including the central portion of the SLO image acquired in S2 is set to be scanned. The SLO image forming unit 210A forms an SLO image of the fundus Ef based on the detection result of the fundus reflected light by the detector 135. The SLO image obtained in S4 is a narrow-angle image as shown in FIG. 6B. No ghost is drawn in the center of this narrow-angle image (or the ghost is barely noticeable).

(S5)
Subsequently, as shown in FIG. 6C, the alignment unit 220A converts the SLO image (wide-angle image) of the eye E to be inspected acquired in S2 into the SLO image (narrow-angle image) of the eye E to be inspected acquired in S4. The corresponding area (corresponding area) C1 is specified. As described above, the alignment unit 220A aligns the SLO image (wide-angle image) of the eye E to be inspected acquired in S2 and the SLO image (narrow-angle image) of the eye E to be inspected acquired in S4. ..

The scale adjustment unit 220B combines a wide-angle image and a narrow-angle image that have been aligned by the alignment unit 220A based on the angle of view set in the wide-angle shooting mode and the angle of view set in the high-magnification shooting mode. Match the scales. In FIG. 6D, the scale of the narrow-angle image acquired in S4 is adjusted so as to match the scale of the wide-angle image acquired in S2. At this time, the scale adjusting unit 220B (data processing unit 220) can perform known distortion correction processing and color correction processing on at least one of the wide-angle image and the narrow-angle image. As shown in FIG. 6E, the image composition unit 220C combines a wide-angle image and a narrow-angle image whose scale has been adjusted by the scale adjustment unit 220B to remove (or suppress) the ghost in the central portion. To form. For example, the image synthesizing unit 220C forms a composite image by replacing the central region of the wide-angle image with at least a part of the narrow-angle image corresponding to the central region.

(S6)
The display control unit 201C causes the UI unit 230 to display the composite image formed in S5.

(S7)
The control unit 200 determines whether or not the user can diagnose the eye E to be inspected based on the composite image displayed in S6. The user confirms the composite image displayed on the UI unit 230, and instructs the UI unit 230 whether or not the diagnosis is possible. The control unit 200 can determine whether or not the diagnosis is possible based on the operation content of the user with respect to the UI unit 230. When it is determined that the diagnosis is possible (S7: Y), the operation of the ophthalmologic imaging apparatus ends (end). When it is determined that the diagnosis is not possible (S7: N), the operation of the ophthalmologic imaging apparatus shifts to S8.

(S8)
When it is determined that the diagnosis is not possible (S7: N), the display control unit 201C receives the user's predetermined operation on the UI unit 230, and the display control unit 201C receives the SLO image (narrow angle image) of the eye E to be inspected acquired in S4. Is enlarged and displayed on the UI unit 230. After that, the operation of the ophthalmologic imaging device ends (end).

"Second operation example]
5 and 6A to 6E have described the case where the wide-angle SLO image and the narrow-angle SLO image are combined, but the same applies to the case where the wide-angle OCT image and the narrow-angle OCT image are combined.

FIG. 7 shows an example of the second operation of the ophthalmologic imaging apparatus according to the embodiment. FIG. 7 shows a flow chart of an operation example of the ophthalmologic imaging apparatus when acquiring an OCT image.

(S11)
First, similarly to S1, the objective optical unit 110B, which is an objective lens for wide-angle photographing, is inserted into the optical axis O by the angle of view changing mechanism 116. For example, a user such as an examiner, a subject, a doctor, or a patient manually inserts the objective optical unit 110B into the optical axis O.

When the objective optical unit 110B is inserted into the optical axis O, the control unit 200 acquires an anterior segment image by photographing the anterior segment of the eye E to be inspected by the anterior segment imaging system 120. The alignment control unit 201A aligns the optical system 100 and the objective optical system 110 with respect to the eye E to be inspected by controlling the movement mechanism 100D based on the acquired anterior eye portion image (X direction, Y direction and Z). direction). The control unit 200 moves the optical scanner 142 to a predetermined initial position.

Next, the alignment control unit 201A aligns the focus direction of the retina from the anterior segment image obtained by the anterior segment imaging system 120 or the SLO image separately obtained. As a result, the position of the objective optical system 110 in the direction of the optical axis O can be finely adjusted.

Subsequently, the main control unit 201 changes the focal position of the OCT optical system 140 based on the detection signal of the interference light obtained by the OCT optical system 140. The main control unit 201 changes the focal position of the OCT optical system 140 by controlling the moving mechanism 141D so that the amplitude of the detection signal of the predetermined interference light is maximized, for example.

In S11, the tracking control unit 201B may start tracking control for the OCT image.

(S12)
The control unit 200 turns on the OCT light source 151 and controls the optical scanner 142 to start scanning the fundus Ef of the eye E to be inspected with the measurement light LS based on the light from the OCT light source 151. The OCT image forming unit 210B forms an OCT image of the fundus Ef based on the detection result of the interference light by the detector 155. The OCT image obtained in S12 is a wide-angle image. The fundus Ef is not visualized in the central part of this wide-angle image (it is difficult to observe the fundus Ef).

(S13)
Next, the objective optical unit 110B is retracted from the optical axis O by the angle of view changing mechanism 116. For example, a user such as an examiner, a subject, a doctor, or a patient manually retracts the objective optical unit 110B from the optical axis O. When the objective optical unit 110B is retracted from the optical axis O, the control unit 200 performs alignment and moves the optical scanner 142 to a predetermined initial position in the same manner as in S11.

(S14)
When only the objective optical unit 110A is arranged on the optical axis O, the control unit 200 again aligns and controls the optical scanner 142 in the same manner as in S12 to use the measurement light LS to measure the fundus of the eye E. Start scanning Ef. The OCT image forming unit 210B forms an OCT image of the fundus Ef based on the detection result of the interference light by the detector 155. This OCT image is a narrow angle image. No ghost is drawn in the center of this narrow-angle image (or the ghost is barely noticeable).

(S15)
Subsequently, the alignment unit 220A is a region (corresponding area) corresponding to the OCT image (narrow angle image) of the eye E to be inspected acquired in S14 in the OCT image (wide-angle image) of the eye E to be inspected acquired in S12. To identify. As described above, the alignment unit 220A aligns the OCT image (wide-angle image) of the eye E to be inspected acquired in S12 and the OCT image (narrow-angle image) of the eye E to be inspected acquired in S14. ..

The scale adjustment unit 220B combines a wide-angle image and a narrow-angle image that have been aligned by the alignment unit 220A based on the angle of view set in the wide-angle shooting mode and the angle of view set in the high-magnification shooting mode. Match the scales. At this time, the scale adjusting unit 220B (data processing unit 220) can perform known distortion correction processing and color correction processing on at least one of the wide-angle image and the narrow-angle image. The image synthesizing unit 220C forms a composite image in which the ghost in the central portion is removed (or suppressed) by synthesizing the wide-angle image and the narrow-angle image whose scale has been adjusted by the scale adjusting unit 220B. For example, the image synthesizing unit 220C forms a composite image by replacing the central region of the wide-angle image with at least a part of the narrow-angle image corresponding to the central region.

(S16)
The display control unit 201C causes the UI unit 230 to display the composite image formed in S15.

(S17)
Similar to S7, the control unit 200 determines whether or not the user can diagnose the eye E to be inspected based on the composite image displayed in S16. When it is determined that the diagnosis is possible (S17: Y), the operation of the ophthalmologic imaging apparatus ends (end). When it is determined that the diagnosis is not possible (S17: N), the operation of the ophthalmologic imaging apparatus shifts to S18.

(S18)
When it is determined that the diagnosis is not possible (S17: N), the display control unit 201C receives the user's predetermined operation on the UI unit 230, and the display control unit 201C receives the OCT image (narrow angle image) of the eye E to be inspected acquired in S14. Is enlarged and displayed on the UI unit 230. After that, the operation of the ophthalmologic imaging device ends (end).

FIG. 5 describes a case where a wide-angle SLO image and a narrow-angle SLO image are combined, and FIG. 7 describes a case where a wide-angle OCT image and a narrow-angle OCT image are combined, but one is an SLO image. If the other is an OCT image, these may be combined.

"Third operation example]

FIG. 8 shows a third operation example of the ophthalmologic imaging apparatus according to the embodiment. FIG. 8 shows a flow chart of an operation example of the ophthalmologic imaging apparatus when a wide-angle SLO image and a narrow-angle SLO image are combined and only the narrow-angle SLO image is updated.

(S21)
First, similarly to S1, the objective optical unit 110B is inserted into the optical axis O by the angle of view changing mechanism 116. For example, a user such as an examiner, a subject, a doctor, or a patient manually inserts the objective optical unit 110B into the optical axis O.

When the objective optical unit 110B is inserted into the optical axis O, the control unit 200 acquires an anterior segment image by photographing the anterior segment of the eye E to be inspected by the anterior segment imaging system 120. The alignment control unit 201A aligns the optical system 100 and the objective optical system 110 with respect to the eye E to be inspected by controlling the movement mechanism 100D based on the acquired anterior eye portion image (X direction, Y direction and Z). direction). The control unit 200 moves the optical scanner 136 to a predetermined initial position. In S21, the tracking control unit 201B may start tracking control for the SLO image.

(S22)
The control unit 200 turns on the SLO light source 131 and controls the optical scanner 136 to start scanning the fundus Ef of the eye E to be inspected with the light from the SLO light source 131. The SLO image forming unit 210A forms an SLO image of the fundus Ef based on the detection result of the fundus reflected light by the detector 135. The SLO image obtained in S22 is a wide-angle image.

(S23)
Next, the objective optical unit 110B is retracted from the optical axis O by the angle of view changing mechanism 116. For example, a user such as an examiner, a subject, a doctor, or a patient manually retracts the objective optical unit 110B from the optical axis O. When the objective optical unit 110B is retracted from the optical axis O, the control unit 200 performs alignment and moves the optical scanner 136 to a predetermined initial position, as in S1.

(S24)
Similar to S22, the control unit 200 starts scanning the fundus Ef of the eye E to be inspected with the measurement light LS based on the light from the OCT light source 151 by controlling the optical scanner 142. At this time, the area including the central portion of the SLO image acquired in S22 is set to be scanned. The SLO image forming unit 210A forms an SLO image of the fundus Ef based on the detection result of the fundus reflected light by the detector 135. The SLO image obtained in S24 is a narrow-angle image.

(S25)
Subsequently, the alignment unit 220A is a region (corresponding area) corresponding to the SLO image (narrow-angle image) of the eye E to be inspected acquired in S24 in the SLO image (wide-angle image) of the eye E to be inspected acquired in S22. To identify. As described above, the alignment unit 220A aligns the SLO image (wide-angle image) of the eye E to be inspected acquired in S22 with the SLO image (narrow-angle image) of the eye E to be inspected acquired in S24. ..

The scale adjustment unit 220B combines a wide-angle image and a narrow-angle image that have been aligned by the alignment unit 220A based on the angle of view set in the wide-angle shooting mode and the angle of view set in the high-magnification shooting mode. Match the scales. At this time, the scale adjusting unit 220B (data processing unit 220) can perform known distortion correction processing and color correction processing on at least one of the wide-angle image and the narrow-angle image. The image synthesizing unit 220C forms a composite image in which the ghost in the central portion is removed (or suppressed) by synthesizing the wide-angle image and the narrow-angle image whose scale has been adjusted by the scale adjusting unit 220B. For example, the image synthesizing unit 220C forms a composite image by replacing the central region of the wide-angle image with at least a part of the narrow-angle image corresponding to the central region.

(S26)
The display control unit 201C causes the UI unit 230 to display the composite image formed in S25.

(S27)
Similar to S7, the control unit 200 determines whether or not the user can diagnose the eye E to be inspected based on the composite image displayed in S26. When it is determined that the diagnosis is possible (S27: Y), the operation of the ophthalmologic imaging apparatus shifts to S24. As a result, in S24, a new narrow-angle SLO image is acquired, and in S25, the narrow-angle SLO image in the composite image is updated with the narrow-angle SLO image newly acquired in S24. In this case, every time a narrow-angle SLO image is acquired, the narrow-angle SLO image in the composite image is updated with a new narrow-angle SLO image.

When it is determined in S27 that the diagnosis is not possible (S27: N), the operation of the ophthalmologic imaging apparatus shifts to S28.

(S28)
When it is determined that the diagnosis is not possible (S27: N), the display control unit 201C receives the user's predetermined operation on the UI unit 230, and the display control unit 201C receives the SLO image (narrow angle image) of the eye E to be inspected acquired in S24. Is enlarged and displayed on the UI unit 230. After that, the operation of the ophthalmologic imaging device ends (end).

Although FIG. 8 describes a case where the wide-angle SLO image and the narrow-angle SLO image are combined and only the narrow-angle SLO image is updated, the wide-angle OCT image and the narrow-angle OCT image are combined. The same applies when updating only the narrow-angle OCT image. In addition, the wide-angle SLO image and the narrow-angle OCT image are combined to update only the wide-angle SLO image or the narrow-angle OCT image, or the wide-angle OCT image and the narrow-angle SLO image are combined to form the wide-angle SLO image. Only the OCT image or the narrow-angle SLO image may be updated.

<Modification example>
The configuration of the objective optical unit 110B according to the embodiment is not limited to that shown in FIGS. 2 and 3.

(First modification)
FIG. 9A shows a configuration example of the objective optical unit 110B according to the first modification of the embodiment. In FIG. 9A, the same parts as those in FIG. 2 are designated by the same reference numerals, and the description thereof will be omitted as appropriate.

The objective optical unit 110B according to the first modification includes one or more aberration correction lenses (aberration correction elements) in addition to the first spherical mirror 111B and the second spherical mirror 112B. At least one of the one or more aberration correction lenses may be arranged between the first spherical mirror 111B and the second spherical mirror 112B. For example, the objective optical unit 110B includes aberration correction lenses 113B and 114B in addition to the first spherical mirror 111B and the second spherical mirror 112B. The aberration correction lens 113B is arranged between the first spherical mirror 111B and the second spherical mirror 112B. The aberration correction lens 114B is arranged between the second spherical mirror 112B and the objective optical unit 110A (convex lens 111A).

According to the first modification, as compared with the embodiment, it is possible to perform high-precision aberration correction at the time of wide-angle shooting with a simple configuration.

(Second modification)
FIG. 9B shows a configuration example of the objective optical unit 110B according to the second modification of the embodiment. In FIG. 9B, the same parts as those in FIG. 2 are designated by the same reference numerals, and the description thereof will be omitted as appropriate.

The objective optical unit 110B according to the second modification includes an objective lens 115B arranged to face the eye E to be inspected as an optical element of the catadioptric system. A first translucent region 115a is provided in the vicinity of the optical axis O on the first lens surface on the side of the optical system 100 of the objective lens 115B. A first internal reflection region 115b is provided in at least a part of a region other than the first light transmission region 115a on the first lens surface of the objective lens 115B. A second translucent region 115c is provided in the vicinity of the optical axis O on the second lens surface of the objective lens 115B on the side of the eye to be inspected E. A second internal reflection region 115d is provided at least in a part of the second lens surface of the objective lens 115B other than the second translucent region 115c.

The first translucent region 115a and the second translucent region 115c are regions through which light passes. The first internal reflection region 115b and the second internal reflection region 115d are regions that reflect the light guided in the objective lens 115B toward the inside of the objective lens 115B. For example, the first internal reflection region 115b is formed by applying a known coating treatment to a region other than the first translucent region 115a on the first lens surface. Similarly, a second internal reflection region 115d is formed by applying a known coating treatment to a region other than the second translucent region 115c on the second lens surface.

The objective optical unit 110B passes the light passing through the objective optical unit 110A, obliquely with respect to the optical axis O, and passing through the first translucent region 115a into the second internal reflection region 115d and the first internal reflection region 115b. Is reflected and irradiates the fundus through the second translucent region 115c. The return light of the light emitted to the fundus of the eye E to be inspected is guided to the optical system 100 through the same path.

According to the second modification, the number of optical elements constituting the objective optical unit 110B can be significantly reduced as compared with the embodiment.

(Other variants)
In the embodiment, the case where the angle of view is changed by selectively arranging the objective optical unit corresponding to the photographing mode has been described, but the configuration according to the embodiment is not limited to this. For example, the optical system 100 may include a zoom optical system. In this case, the zoom optical system is an objective optical system including two or more lenses whose at least one can move along the optical axis O of the optical system 100, or one or more optical elements that can be inserted into and removed from the optical axis O. Includes (lenses, prisms, flat glass, etc.). One or more optical elements can be inserted between the dichroic mirror DM2 and the objective optical unit.

The control unit 200 according to the embodiment moves at least the objective optical system 110 (optical system 100) so that the working distance (working distance) in the wide-angle shooting mode is shorter than the working distance in the high-magnification shooting mode. May be good.

In the above-described embodiment, the case where the configuration of the optical system 100 is the configuration shown in FIGS. 1 and 3 has been described, but the configuration of the optical system according to the embodiment is not limited to this. The optical system according to the embodiment may include an optical system for irradiating a treatment site on the fundus with laser light, an optical system for moving an optotype while the eye to be inspected is fixed.

In the above-described embodiment, the case where the configuration of the objective optical system 110 is the configuration shown in FIGS. 1 to 3 has been described, but the configuration of the objective optical system according to the embodiment is not limited to this.

The anterior segment imaging system according to the embodiment may include two or more cameras for photographing the anterior segment of the eye E to be examined from two or more directions different from each other. In this case, the alignment control unit 201A according to the embodiment executes the alignment in the Z direction from the parallax obtained based on the captured images of the anterior segment from two or more different directions acquired by using these cameras. It is possible.

In the above-described embodiment, the case where the alignment is performed using the anterior segment image acquired by using the anterior segment imaging system 120 has been described, but the acquired anterior segment image is displayed on the UI unit 230. It may be displayed on the device. Moreover, it is not necessary to use the acquired anterior segment image for alignment.

[effect]
The effect of the ophthalmologic imaging apparatus according to the embodiment will be described.

The ophthalmologic imaging apparatus according to the embodiment includes an objective optical system (objective optical system 110) and a scanning system (optical system 100). The scanning system is used to scan the fundus (fundus Ef) with a luminous flux via the objective optical system. The objective optical system includes an optical member (second spherical mirror 112B) and a second optical member (first spherical mirror 111B) arranged closer to the eye to be inspected (eye to be inspected E) than the first optical member. A second optical member that includes a unit (objective optical unit 110B), is oblique to the optical axis (optical axis O) of the scanning system, and reflects light rays that have passed through a region near the optical axis in the first optical member at least twice. The fundus of the eye is irradiated through a region near the optical axis of the optical member.

According to such a configuration, the objective optical system is scanned by the scanning system using the first optical member and the second optical member which are the optical members of the reflective optical system, so that the objective lens and the eye to be inspected can be scanned. It is possible to acquire a wide-angle image in which the depiction of ghosts (noise) caused by the surface reflection of the optics is suppressed. Further, the number of optical elements constituting the objective optical system can be reduced, and the configuration can be simplified.

Further, in the ophthalmologic imaging apparatus according to the embodiment, the objective optical system may include one or more aberration correction elements (aberration correction lenses 113B, 114B).

According to such a configuration, it is possible to perform highly accurate aberration correction with a simple configuration while significantly reducing the number of optical elements.

Further, in the ophthalmologic imaging apparatus according to the embodiment, at least one of one or more aberration correction elements (aberration correction lens 113B) may be arranged between the first optical member and the second optical member.

According to such a configuration, it becomes possible to perform highly accurate aberration correction with a simple configuration.

Further, in the ophthalmologic imaging apparatus according to the embodiment, each of the surface of the first optical member on the side to be inspected and the surface of the second optical member on the scan system side may reflect the luminous flux.

According to such a configuration, in the objective optical system arranged between the scan system and the eye to be inspected, the luminous flux is generated on the surface of the first optical member on the side to be inspected and the surface of the second optical member on the scan system side. Since the reflection is made, the size of the objective optical system can be reduced. As a result, the ophthalmologic imaging device can be miniaturized.

Further, in the ophthalmologic imaging apparatus according to the embodiment, the vicinity region may be formed as an opening or a translucent portion.

According to such a configuration, it is possible to acquire an image in which the depiction of ghost (noise) caused by the surface reflection of the objective lens or the cornea of the eye to be inspected is suppressed with a simple configuration.

The ophthalmologic imaging apparatus according to the embodiment includes an objective optical system (objective optical system 110) and a scanning system (optical system 100). The scanning system is used to scan the fundus (fundus Ef) with a luminous flux via the objective optical system. The objective optical system includes an optical unit (objective optical unit 110B) including an objective lens (objective lens 115B) arranged to face the eye to be inspected (eye to be inspected E), and the objective lens is a first lens on the scan system side. The first translucent region formed in the vicinity of the optical axis (optical axis O) of the scanning system on the surface and the first internal reflection formed in at least a part of the region other than the first translucent region on the first lens surface. A second translucent region formed in the vicinity of the optical axis on the second lens surface on the side to be inspected, and a second transmissive region formed in at least a part of a region other than the second transmissive region on the second lens surface. It is provided with an internal reflection region, and the light beam that has passed through the first light transmission region obliquely with respect to the optical axis is reflected in the first internal reflection region and the second internal reflection region and is reflected to the fundus through the second light transmission region. Irradiate.

According to such a configuration, the objective optical system is used as an optical member of the catadioptric system, a first light-transmitting region and a first internal reflection region are formed on the first lens surface, and a second light-transmitting region is formed on the second lens surface. Since the fundus of the eye is scanned by a scanning system using an objective lens in which a region and a second internal reflection region are formed, ghost (noise) visualization caused by surface reflection of the objective lens and the cornea of the eye to be inspected is suppressed. Wide-angle images can be acquired. Further, the number of optical elements constituting the objective optical system can be reduced, and the configuration can be simplified.

Further, in the ophthalmologic imaging apparatus according to the embodiment, the objective optical system includes one or more lenses (convex lenses 111A, 112A, concave lenses 113A) arranged between the scanning system and the optical unit, and the optical unit is a luminous flux. It may be removable with respect to the optical path.

According to such a configuration, it is possible to provide an ophthalmologic imaging apparatus capable of acquiring a wide-angle image in which ghosts are suppressed while easily changing the angle of view by inserting and removing the optical unit in the objective optical system. it can.

Further, the ophthalmologic imaging apparatus according to the embodiment has an image forming unit (image forming unit 210) that forms an image based on the data collected by the scanning system and a scanning system with an optical unit inserted in the optical path. A first image (wide-angle image) formed by the image forming unit based on the obtained data, and a second image formed by the image forming unit based on the data collected by the scanning system with the optical unit retracted from the optical path. An image compositing unit (image compositing unit 220C) that synthesizes (narrow-angle image) to form a composite image may be included.

According to such a configuration, a wide-angle first image in which the ghost caused by the surface reflection of the objective lens and the corneum of the eye to be inspected is not drawn in the central part but the fundus is not drawn in the central part, and the ghost is drawn in the central part. Although it is not done, since the second narrow-angle image in which the fundus of the eye with high magnification is drawn is combined with the central portion, it is possible to acquire a wide-angle image in which the drawing of ghosts is suppressed.

Further, in the ophthalmologic imaging apparatus according to the embodiment, the image synthesizing unit may form a composite image in which the second image is arranged in the central portion and the first image is arranged in the peripheral portion.

According to such a configuration, the second image with a narrow angle of the fundus is arranged in the central portion, and the first image with a wide angle of the fundus is arranged in the peripheral portion to form a composite image. It is possible to acquire a wide-angle image in which is suppressed.

The embodiments shown above are merely examples for carrying out the present invention. A person who intends to carry out the present invention can make arbitrary modifications, omissions, additions, etc. within the scope of the gist of the present invention.

100 Optical system 110 Objective optical system 110A, 110B Objective optical unit 111B First spherical mirror 112B Second spherical mirror 116 Angle of view changing mechanism 120 Anterior eye imaging system 130 SLO optical system 140 OCT optical system 150 Interference optical system 200 Control unit 210 Image formation Part 220 Data processing part 220C Image synthesis part 230 UI part DM1 Dycroic mirror E Eye to be inspected Ef Eye bottom

Claims (5)

With the objective optical system
A scanning system for scanning the fundus with a luminous flux via the objective optical system,
An image forming unit that forms an image based on the data collected by the scanning system,
Including the image composition part
The objective optical system is
An optical unit including a first optical member and a second optical member arranged closer to the eye to be inspected than the first optical member .
One or more lenses arranged between the scanning system and the optical unit,
Including
The luminous flux that is oblique to the optical axis of the scanning system and passes through the region near the optical axis in the first optical member is reflected at least twice and passed through the region near the optical axis in the second optical member. irradiating the fundus,
The optical unit is removable with respect to the optical path of the luminous flux.
In the image synthesizing unit, the first image formed by the image forming unit based on the data collected by the scanning system with the optical unit inserted in the optical path and the optical unit are retracted from the optical path. An ophthalmologic photographing apparatus characterized in that a composite image is formed by synthesizing a second image formed by the image forming unit based on the data collected by the scanning system in the state of being in the state . With the objective optical system
A scanning system for scanning the fundus with a luminous flux via the objective optical system,
Including
The objective optical system includes an optical unit including an objective lens arranged to face the eye to be inspected.
The objective lens is
A first translucent region formed in the vicinity of the optical axis of the scan system on the first lens surface on the scan system side, and
A first internal reflection region formed in at least a part of a region other than the first translucent region on the first lens surface,
A second translucent region formed in the vicinity of the optical axis on the second lens surface on the side to be inspected, and
A second internal reflection region formed in at least a part of a region other than the second translucent region on the second lens surface,
With
The luminous flux that has passed through the first translucent region obliquely with respect to the optical axis is reflected in the first internal reflection region and the second internal reflection region, and the fundus is irradiated through the second translucent region. An ophthalmologic imaging device characterized by The objective optical system includes one or more lenses arranged between the scanning system and the optical unit.
The ophthalmologic imaging apparatus according to claim 2 , wherein the optical unit is removable with respect to the optical path of the luminous flux. An image forming unit that forms an image based on the data collected by the scanning system,
The first image formed by the image forming unit based on the data collected by the scanning system with the optical unit inserted in the optical path, and the scanning system with the optical unit retracted from the optical path. To form a composite image by synthesizing the second image formed by the image forming unit based on the data collected by
The ophthalmologic imaging apparatus according to claim 1 or 3 , wherein the ophthalmologic imaging apparatus includes. The ophthalmology according to claim 1 or 4 , wherein the image synthesizing unit forms the composite image in which the second image is arranged in a central portion and the first image is arranged in a peripheral portion. Shooting device.

Images