JP6625251B2 - Ophthalmic imaging equipment - Google Patents

Description

  The present invention relates to an ophthalmologic photographing apparatus.

  2. Description of the Related Art Conventionally, an ophthalmologic photographing apparatus for photographing an eye to be examined is known. For example, an ophthalmologic imaging apparatus includes an illumination optical system that irradiates an illumination light beam to an eye to be inspected, and an imaging optical system that guides reflected light from the fundus to an imaging device. In such an ophthalmologic photographing apparatus, two split optotypes are projected on the fundus of the eye to be inspected, and the focusing lens is moved based on the positional relationship between the two split optotype images obtained by the return light for photographing. Some have an autofocus function for changing the focus position of the optical system.

  In an ophthalmologic photographing apparatus having an autofocus function, the focusable range by moving the focusing lens is set to a range in which the average diopter correction of the subject's eye can be performed. Therefore, even if the focusing lens is moved with respect to the subject's eye with high myopia or high hyperopia, it may not be possible to determine the focus position of the imaging optical system. Therefore, a diopter correction lens is inserted into the optical path of the photographing optical system in order to enable the focusing lens to focus on a strong myopic or strong hyperopic eye.

  However, when a diopter correction lens is inserted into the optical path of the imaging optical system, the optical relationship between the imaging optical system and the focus optical system that projects the split optotype on the fundus changes, and the split optotype is changed by the imaging optical system. The image cannot be acquired. As a result, not only the automatic focusing by the autofocus function but also the manual focusing using the split optotype becomes impossible.

  For example, in Patent Document 1, when the diopter correction lens is inserted in the optical path by moving the focusing lens at a higher moving speed than in the retracted state when the diopter correction lens is inserted. However, a method has been proposed in which manual focusing is performed smoothly.

JP 2011-189063 A

  However, in the ophthalmologic photographing apparatus disclosed in Patent Literature 1, when a diopter correction lens is inserted in the optical path of the photographing optical system, focusing cannot be performed automatically, and a person unfamiliar with the apparatus cannot adjust the focus position. It takes time for adjustment, and it is difficult to perform focusing with high accuracy.

  The present invention has been made in order to solve such a problem, and an object thereof is to automatically focus even when a diopter correction lens is inserted in an optical path and to photograph an eye to be inspected. An object of the present invention is to provide a possible ophthalmologic photographing apparatus.

  The ophthalmologic photographing apparatus according to the embodiment includes a first optical system, a second optical system, and a first focusing control unit. The first optical system includes a first focusing lens disposed in the first optical path, and a diopter correction lens that can be inserted into and removed from the first optical path, and guides light from the subject's eye to the first light receiving element. . The second optical system includes a second focusing lens disposed on the second optical path. The first focus control unit focuses on the first focus lens based on a focus state of the second optical system by the second focus lens when the diopter correction lens is inserted in the first optical path. Execute control.

  According to the present invention, it is possible to provide an ophthalmologic photographing apparatus capable of automatically focusing and photographing an eye to be inspected even when a diopter correction lens is inserted in an optical path.

FIG. 1 is a schematic diagram illustrating an example of a configuration of an optical system of an ophthalmologic imaging apparatus according to an embodiment. FIG. 1 is a schematic diagram illustrating an example of a configuration of an optical system of an ophthalmologic imaging apparatus according to an embodiment. FIG. 2 is a schematic diagram illustrating an example of a configuration of a control system of the ophthalmologic imaging apparatus according to the embodiment. FIG. 2 is a schematic diagram illustrating an example of a configuration of a control system of the ophthalmologic imaging apparatus according to the embodiment. FIG. 2 is a schematic diagram illustrating an example of a configuration of a control system of the ophthalmologic imaging apparatus according to the embodiment. FIG. 6 is a flowchart of an operation example of the ophthalmologic photographing apparatus according to the comparative example of the embodiment. FIG. 5 is a flowchart of an operation example of the ophthalmologic imaging apparatus according to the embodiment. FIG. 8 is a schematic diagram illustrating an example of a configuration of a control system of an ophthalmologic imaging apparatus according to a first modification of the embodiment. FIG. 11 is a schematic diagram illustrating an example of a configuration of a control system of an ophthalmologic imaging apparatus according to a second modification of the embodiment. FIG. 13 is a flowchart of an operation example of the ophthalmologic imaging apparatus according to the second modification of the embodiment.

  An example of an embodiment of the present invention will be described in detail with reference to the drawings. The ophthalmologic imaging apparatus according to the embodiment has a first optical system for changing the focus position and performing imaging of the eye to be inspected, and a focus position that can be changed separately from the first optical system to observe the eye to be inspected. Or a second optical system for photographing. The first optical system includes a diopter correction lens that can be inserted into and removed from the optical path. The first optical system in which the diopter correction lens is inserted in the optical path can change the focus position based on the control content of the focusing control performed on the subject's eye by the second optical system. is there.

  Hereinafter, it is assumed that the ophthalmologic photographing apparatus according to the embodiment includes two optical systems each capable of photographing the eye to be inspected. As a specific example, the ophthalmologic imaging apparatus according to the embodiment has a function of a fundus imaging apparatus and a function of an optical coherence tomography, and performs fundus imaging and optical coherence tomography (Optical Coherence Tomography: hereinafter) on the subject's eye. OCT). The OCT is performed on an arbitrary part of the subject's eye, such as the fundus or the anterior segment.

  In the following embodiment, an ophthalmologic imaging apparatus capable of performing Fourier domain type OCT will be described. In particular, the ophthalmologic imaging apparatus according to the embodiment is applicable to a swept-source OCT technique. The configuration according to the present invention can be applied to an ophthalmologic imaging apparatus that can execute OCT of a type other than the swept source type, for example, a spectral domain type. In the following embodiments, a device in which a fundus camera having a fundus imaging function and an OCT device are combined will be described. However, it is also possible to combine a fundus camera having the configuration according to the embodiment with a modality other than the OCT apparatus, for example, an SLO (Scanning Laser Ophthalmoscope), a slit lamp, a microscope for ophthalmic surgery, a photocoagulation apparatus, and the like.

  In this specification, an image acquired by OCT may be collectively referred to as an OCT image. Further, the contents described in the documents cited in this specification can be used as the contents of the following embodiments.

[Constitution]
As shown in FIG. 1, the ophthalmologic photographing apparatus 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200. The retinal camera unit 2 has almost the same optical system as a conventional retinal camera. The OCT unit 100 is provided with an optical system for performing OCT. The arithmetic and control unit 200 includes a computer that executes various arithmetic and control processes.

[Fundus camera unit]
The fundus camera unit 2 shown in FIG. 1 is provided with an optical system for acquiring a two-dimensional image (fundus image) representing the surface morphology of the fundus oculi Ef of the eye E. The fundus image includes an observation image, a captured image, and the like. The observation image is, for example, a monochrome moving image formed at a predetermined frame rate using near-infrared light. The captured image may be, for example, a color image obtained by flashing visible light, or a monochrome still image using near-infrared light or visible light as illumination light. The fundus camera unit 2 may be configured to be able to acquire images other than these, for example, a fluorescein fluorescent image, an indocyanine green fluorescent image, a spontaneous fluorescent image, and the like.

  The retinal camera unit 2 is provided with a chin rest and a forehead support for supporting the face of the subject. Further, the fundus camera unit 2 is provided with an illumination optical system 10 and a photographing optical system 30. The illumination optical system 10 irradiates the fundus oculi Ef with illumination light. The imaging optical system 30 guides the fundus reflection light of the illumination light to imaging devices (CCD image sensors (sometimes simply referred to as CCDs) 35 and 38). The imaging optical system 30 guides the measurement light from the OCT unit 100 to the eye E and guides the measurement light that has passed through the eye E to the OCT unit 100.

  The observation light source 11 of the illumination optical system 10 is constituted by, for example, a halogen lamp or an LED (Light Emitting Diode). Light (observation illumination light) output from the observation light source 11 is reflected by a reflection mirror 12 having a curved reflection surface, passes through a condenser lens 13, passes through a visible cut filter 14, and is converted into near-infrared light. Become. Further, the observation illumination light once converges in the vicinity of the imaging light source 15, is reflected by the mirror 16, and passes through the relay lenses 17 and 18, the stop 19 and the relay lens 20. Then, the observation illumination light is reflected at the periphery of the perforated mirror 21 (the area around the perforated portion), passes through the dichroic mirror 46, is refracted by the objective lens 22, and illuminates the fundus Ef.

  The fundus reflection light of the observation illumination light is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through the hole formed in the center area of the aperture mirror 21, passes through the dichroic mirror 55, and focuses on imaging. The light is reflected by the mirror 32 via the lens 31. Further, the fundus reflection light passes through the half mirror 33A, is reflected by the dichroic mirror 33, and forms an image on the light receiving surface of the CCD image sensor 35 by the condenser lens. The CCD image sensor 35 detects fundus reflection light at a predetermined frame rate, for example. The display device 3 displays an image (observation image) based on the fundus reflection light detected by the CCD image sensor 35. When the focus of the imaging optical system 30 is adjusted to the anterior segment, an observation image of the anterior segment of the eye E is displayed.

  The imaging light source 15 is configured by, for example, a xenon lamp or an LED. Light (photographing illumination light) output from the photographing light source 15 is applied to the fundus oculi Ef through the same path as the observation illumination light. The fundus reflection light of the photographing illumination light is guided to the dichroic mirror 33 through the same path as that of the observation illumination light, passes through the dichroic mirror 33, is reflected by the mirror 36, and is reflected by the condenser lens 37 to the CCD image sensor 38. An image is formed on the light receiving surface. The display device 3 displays an image (captured image) based on the fundus reflection light detected by the CCD image sensor 38. Note that the display device 3 for displaying the observation image and the display device 3 for displaying the captured image may be the same or different. In the case where the subject's eye E is illuminated with infrared light and the same imaging is performed, an infrared captured image is displayed. Further, it is also possible to use an LED as a photographing light source.

  An LCD (Liquid Crystal Display) 39 displays a fixation target and a visual acuity measurement index. The fixation target is an index for fixing the eye E to be examined, and is used at the time of fundus photographing, OCT measurement, and the like.

  A part of the light output from the LCD 39 is reflected by the half mirror 33A, reflected by the mirror 32, passes through the imaging focusing lens 31 and the dichroic mirror 55, and passes through the hole of the perforated mirror 21. The light that has passed through the aperture of the apertured mirror 21 passes through the dichroic mirror 46, is refracted by the objective lens 22, and irradiates the fundus Ef. By changing the display position of the fixation target on the screen of the LCD 39, the fixation position of the eye E can be changed.

  Further, the retinal camera unit 2 is provided with an alignment optical system 50 and a focus optical system 60 as in the conventional retinal camera. The alignment optical system 50 generates an index (alignment index) for performing alignment (alignment) of the apparatus optical system with respect to the eye E to be inspected. The focus optical system 60 generates an index (split index) for focusing on the eye E to be inspected.

  Light (alignment light) output from the LED 51 of the alignment optical system 50 is reflected by the dichroic mirror 55 via the stops 52 and 53 and the relay lens 54 and passes through the hole of the perforated mirror 21. The light that has passed through the aperture of the apertured mirror 21 passes through the dichroic mirror 46 and is irradiated on the cornea of the eye E by the objective lens 22.

  The corneal reflected light of the alignment light passes through the objective lens 22, the dichroic mirror 46, and the above-mentioned hole, and a part of the light passes through the dichroic mirror 55 and passes through the imaging focusing lens 31. The corneal reflected light passing through the imaging focusing lens 31 is reflected by the mirror 32, passes through the half mirror 33A, is reflected by the dichroic mirror 33, and is projected on the light receiving surface of the CCD image sensor 35 by the condenser lens. The received light image (alignment index) by the CCD image sensor 35 is displayed on the display device 3 together with the observation image. The user performs the alignment by performing the same operation as the conventional fundus camera. Alternatively, the arithmetic and control unit 200 may perform the alignment by analyzing the position of the alignment index and moving the optical system (automatic alignment function).

  The focus optical system 60 moves the optical path of the illumination optical system 10 (hereinafter, referred to as the “optical path”) in conjunction with the movement of the imaging focusing lens 31 along the optical path of the imaging optical system 30 (hereinafter, sometimes referred to as “imaging optical path”). (May be referred to as “illumination light path”). The reflecting rod 67 of the focusing optical system 60 can be inserted into and removed from the illumination optical path.

  When performing focus adjustment, the reflecting surface of the reflecting bar 67 is inclined on the illumination optical path. Light (focus light) output from the LED 61 of the focus optical system 60 passes through the relay lens 62, is split into two light beams by the split target plate 63, and passes through the two-hole stop 64. The light that has passed through the two-hole stop 64 is reflected by the mirror 65, and is once imaged and reflected by the condenser lens 66 on the reflection surface of the reflection rod 67. Further, the focus light passes through the relay lens 20, is reflected by the aperture mirror 21, passes through the dichroic mirror 46, is refracted by the objective lens 22, and irradiates the fundus Ef.

  The fundus reflection light of the focus light is detected by the CCD image sensor 35 through the same path as the corneal reflection light of the alignment light. The received light image (split index image) by the CCD image sensor 35 is displayed on the display device 3 together with the observation image. The arithmetic and control unit 200 analyzes the position of the split index image and moves the focusing lens 31 and the focusing optical system 60 to perform focusing (autofocus function) as in the related art. The focus may be manually adjusted while visually recognizing the split index image.

  The reflection bar 67 is inserted at a position on the illumination optical path that is optically substantially conjugate with the fundus oculi Ef of the eye E. The position of the reflection surface of the reflection rod 67 inserted into the illumination light path is a position optically substantially conjugate to the split optotype plate 63. As described above, the split target light beam is split into two by the action of the two-hole stop 64 or the like. When the fundus oculi Ef of the subject's eye E and the reflecting surface of the reflecting rod 67 are not conjugate, the split optotype image acquired by the CCD image sensor 35 is split into two in the left-right direction and displayed on the display device 3, for example. Is done. When the fundus oculi Ef of the eye E to be examined and the reflecting surface of the reflecting rod 67 are substantially conjugate, the split optotype image acquired by the CCD image sensor 35 is displayed on the display device 3 in the vertical direction, for example. . The focus optical system 60 is moved along the illumination optical path in conjunction with the photographing focusing lens 31 so that the fundus oculi Ef and the split optotype plate 63 are always optically conjugate. When the fundus oculi Ef and the split optotype plate 63 are not conjugate, the split optotype image is separated into two, so that the focus optical system 60 is moved so that the two split optotype images coincide with each other in the vertical direction. By doing so, the position of the focusing lens 31 is obtained. In this embodiment, a case has been described in which two split optotype images are acquired, but three or more split optotype images may be obtained.

  The imaging optical system 30 includes diopter correction lenses 70 and 71 that can be inserted into and removed from the imaging optical path between the aperture mirror 21 and the dichroic mirror 55. The diopter correction lens 70 is a plus (+) lens used to correct strong hyperopia. As the diopter correction lens 70, for example, a + 20D (diopter) convex lens is used. The diopter correction lens 71 is a minus (-) lens used to correct strong myopia. As the diopter correction lens 71, for example, a -20D (diopter) concave lens is used. For example, diopter correction lenses 70 and 71 are provided on the turret plate along the circumferential direction. A hole is formed in the circumferential direction of the turret plate. The turret plate is rotated by a stepping motor (driving unit) or the like around a rotation axis provided at a position eccentric from the optical axis of the imaging optical system 30. By rotating the turret plate around the rotation axis by the stepping motor, the diopter correction lens 70 or the diopter correction lens 71 is disposed in the imaging optical path, or the diopter correction lens 70 and the diopter correction The lens 71 can be retracted.

  The dichroic mirror 46 branches an optical path for OCT from an optical path for fundus imaging. The dichroic mirror 46 reflects light in the wavelength band used for OCT and transmits light for fundus imaging. In the OCT optical path, a collimator lens unit 40, an optical path length changing unit 41, an optical scanner 42, an OCT focusing lens 43, a mirror 44, and a relay lens 45 are provided in this order from the OCT unit 100 side. Have been.

  The optical path length changing unit 41 is movable in the direction of the arrow shown in FIG. 1 and changes the optical path length of the optical path for OCT. The change in the optical path length is used for correcting the optical path length according to the axial length of the eye E, adjusting the interference state, and the like. The optical path length changing unit 41 includes, for example, a corner cube and a mechanism for moving the corner cube.

  The optical scanner 42 is disposed at a position optically conjugate with the pupil of the eye E to be examined. The optical scanner 42 changes the traveling direction of light (measuring light LS) passing through the OCT optical path. Thus, the eye E can be scanned with the measurement light LS. The optical scanner 42 includes, for example, a galvanomirror that scans the measurement light LS in the x direction, a galvanomirror that scans in the y direction, and a mechanism that independently drives these. Thus, the measurement light LS can be scanned in any direction on the xy plane.

[OCT unit]
An example of the configuration of the OCT unit 100 is shown in FIG. The OCT unit 100 is provided with an optical system for acquiring an OCT image of the eye E to be inspected. This optical system has a configuration similar to that of a conventional swept-source OCT apparatus. That is, this optical system divides light from a wavelength-swept (wavelength-scanning) light source into measurement light and reference light, and converts return light of measurement light from the eye E to be examined and reference light that has passed through a reference optical path. An interference optical system that generates interference light by causing interference and detects the interference light. The detection result (detection signal) of the interference light by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the arithmetic and control unit 200.

  The light source unit 101 is configured to include a wavelength-swept (wavelength-scanning) light source capable of sweeping (scanning) the wavelength of emitted light, similarly to a general swept-source OCT apparatus. The wavelength-swept light source includes a laser light source including a resonator. The light source unit 101 temporally changes the output wavelength in a near-infrared wavelength band that cannot be visually recognized by human eyes.

  The light L0 output from the light source unit 101 is guided to a polarization controller 103 by an optical fiber 102, and its polarization state is adjusted. The polarization controller 103 adjusts the polarization state of the light L0 guided through the optical fiber 102 by, for example, externally applying a stress to the looped optical fiber 102.

  The light L0 whose polarization state has been adjusted by the polarization controller 103 is guided to a fiber coupler 105 by an optical fiber 104 and split into a measurement light LS and a reference light LR.

  The reference light LR is guided to the collimator 111 by the optical fiber 110 and becomes a parallel light beam. The reference light LR that has become a parallel light beam is guided to the corner cube 114 via the optical path length correction member 112 and the dispersion compensation member 113. The optical path length correction member 112 functions as delay means for adjusting the optical path length (optical distance) of the reference light LR and the optical path length of the measurement light LS. The dispersion compensating member 113 functions as a dispersion compensating unit for matching the dispersion characteristics between the reference light LR and the measurement light LS.

  The corner cube 114 turns the traveling direction of the reference light LR converted into a parallel light beam by the collimator 111 in the opposite direction. The optical path of the reference light LR entering the corner cube 114 and the optical path of the reference light LR exiting from the corner cube 114 are parallel. The corner cube 114 is movable in a direction along the incident light path and the output light path of the reference light LR. This movement changes the length of the optical path of the reference light LR.

  In the configuration shown in FIGS. 1 and 2, the optical path length changing unit 41 for changing the length of the optical path (measurement optical path, measurement arm) of the measurement light LS, and the optical path (reference optical path, reference Both corner cubes 114 for changing the length of the arm) are provided. However, one of the optical path length changing unit 41 and the corner cube 114 may be provided. It is also possible to change the difference between the measurement optical path length and the reference optical path length by using other optical members.

  The reference light LR passing through the corner cube 114 passes through the dispersion compensating member 113 and the optical path length correcting member 112, is converted from a parallel light beam into a converged light beam by the collimator 116, and is incident on the optical fiber 117. The reference light LR that has entered the optical fiber 117 is guided to the polarization controller 118, and its polarization state is adjusted.

  The polarization controller 118 has, for example, a configuration similar to that of the polarization controller 103. The reference light LR whose polarization state has been adjusted by the polarization controller 118 is guided to the attenuator 120 by the optical fiber 119, and the light amount is adjusted under the control of the arithmetic and control unit 200. The reference light LR whose light amount has been adjusted by the attenuator 120 is guided to the fiber coupler 122 by the optical fiber 121.

  On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber 127 and is converted into a parallel light beam by the collimator lens unit 40. The measurement light LS converted into a parallel light beam reaches a dichroic mirror 46 via an optical path length changing unit 41, an optical scanner 42, an OCT focusing lens 43, a mirror 44, and a relay lens 45. Then, the measurement light LS is reflected by the dichroic mirror 46, refracted by the objective lens 22, and radiated to the eye E. The measurement light LS is scattered (including reflection) at various depth positions of the eye E. 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 105, and reaches the fiber coupler 122 via the optical fiber 128.

  The fiber coupler 122 combines (measures) the measurement light LS incident via the optical fiber 128 and the reference light LR incident via the optical fiber 121 to generate interference light. The fiber coupler 122 generates a pair of interference lights LC by splitting the interference light between the measurement light LS and the reference light LR at a predetermined split ratio (for example, 1: 1). The pair of interference lights LC emitted from the fiber coupler 122 is guided to the detector 125 by the optical fibers 123 and 124, respectively.

  The detector 125 is, for example, a balanced photodiode (Balanced Photo Diode) that has a pair of photodetectors that respectively detect a pair of interference lights LC, and outputs a difference between detection results obtained by the pair of photodetectors. The detector 125 sends the detection result (detection signal) to a DAQ (Data Acquisition System) 130. The DAQ 130 is supplied with a clock KC from the light source unit 101. The clock KC is generated in the light source unit 101 in synchronization with the output timing of each wavelength swept (scanned) within a predetermined wavelength range by the wavelength sweep type light source. The light source unit 101, for example, optically delays one of the two split lights obtained by splitting the light L0 of each output wavelength, and then generates the clock KC based on the result of detecting the combined light. Generate. The DAQ 130 samples the detection result of the detector 125 based on the clock KC. The DAQ 130 sends the sampled detection result of the detector 125 to the arithmetic and control unit 200. The arithmetic and control unit 200 performs a Fourier transform or the like on the spectral distribution based on the detection result obtained by the detector 125 for each series of wavelength scans (for each A line), thereby obtaining a reflection intensity profile in each A line. Form. Further, the arithmetic and control unit 200 forms image data by imaging the reflection intensity profile of each A line.

[Operation control unit]
The configuration of the arithmetic and control unit 200 will be described. The arithmetic and control unit 200 analyzes the detection signal input from the detector 125 and forms an OCT image of the eye E to be inspected. The arithmetic processing for that is the same as in a conventional swept-source OCT apparatus.

  The arithmetic and control unit 200 controls each unit of the fundus camera unit 2, the display device 3, and the OCT unit 100. For example, the arithmetic and control unit 200 causes the display device 3 to display the OCT image of the eye E to be inspected.

  The arithmetic and control unit 200 includes, for example, a microprocessor, a random access memory (RAM), a read only memory (ROM), a hard disk drive, a communication interface, and the like, similarly to a conventional computer. A storage device such as a hard disk drive stores a computer program for controlling the ophthalmologic photographing apparatus 1. The arithmetic and control unit 200 may include various circuit boards, for example, a circuit board for forming an OCT image. Further, the arithmetic and control unit 200 may include an operation device (input device) such as a keyboard and a mouse, and a display device such as an LCD.

(Control system)
The configuration of the control system of the ophthalmologic photographing apparatus 1 will be described with reference to FIG. In FIG. 3, some components of the ophthalmologic photographing apparatus 1 are omitted, and components particularly necessary for describing this embodiment are selectively shown.

(Control unit)
The control system of the ophthalmologic imaging apparatus 1 is mainly configured with the control unit 210. The control unit 210 includes, for example, a microprocessor, a RAM, a ROM, a hard disk drive, a communication interface, and the like. The control unit 210 includes a main control unit 211 and a storage unit 212.

(Main control unit)
The main control unit 211 performs the various controls described above. In particular, as shown in FIG. 3, the main control unit 211 controls the imaging / focusing drive unit 31A, the CCD image sensors 35 and 38, the LCD 39, the optical path length changing unit 41, and the optical scanner 42 of the fundus camera unit 2. The main control unit 211 controls the OCT focusing drive unit 43A, the focus optical system drive unit 60A, the reflection bar drive unit 67A, and the like. Further, the main control unit 211 controls the light source unit 101, the reference drive unit 114A, the detector 125, the DAQ 130, and the like of the OCT unit 100.

  The imaging focusing drive unit 31A moves the imaging focusing lens 31 along the optical axis of the imaging optical path. Thereby, the focus position of the photographing optical system 30 is changed. The main control unit 211 can control an optical system driving unit (not shown) to move the optical system provided in the fundus camera unit 2 three-dimensionally. This control is used in alignment and tracking. The tracking is to move the apparatus optical system in accordance with the movement of the eye E. When performing tracking, alignment and focusing are performed in advance. In tracking, the apparatus optical system is moved in real time in accordance with the position and orientation of the subject's eye E based on an image obtained by capturing a moving image of the subject's eye E, thereby maintaining a suitable positional relationship with alignment and focus. Function.

  The OCT focusing drive unit 43A moves the OCT focusing lens 43 along the optical axis of the measurement optical path. Thereby, the focus position of the measurement light LS is changed. The focus position of the measurement light LS corresponds to the depth position (z position) of the beam waist of the measurement light LS.

  The focus optical system driving unit 60A moves the focus optical system 60 along the optical axis of the illumination light path. The focusing optical system driving unit 60A moves the focusing optical system 60 in conjunction with the movement of the imaging focusing lens 31 by the imaging focusing driving unit 31A.

  The reflection rod driving section 67A arranges the reflection rod 67 in the illumination light path, or retracts the reflection rod 67 from the illumination light path. By disposing the reflection bar 67 in the illumination optical path, two split optotype images are displayed on the display device 3. As described above, the photographing optical system 30 can be focused by analyzing the positions of the two split optotype images.

  The reference drive unit 114A moves the corner cube 114 provided on the reference optical path. Thereby, the length of the reference light path is changed. As described above, a configuration in which only the optical path length changing unit 41 and any one of the corner cube 114 and the reference driving unit 114A may be provided.

  The main control unit 211 includes an imaging focus control unit 211a, an OCT focus control unit 211b, and an intensity detection unit 211c.

(Shooting focus control unit)
The imaging and focusing control unit 211a controls the imaging and focusing driving unit 31A so as to focus the imaging optical system 30. Since the imaging focusing drive unit 31A and the focusing optical system driving unit 60A are interlocked, the control on the imaging focusing driving unit 31A can be regarded as the same as the control on the focusing optical system driving unit 60A. The imaging focus control unit 211a is configured to reciprocate between the diopter correction lenses 70 and 71 from the imaging optical path and the insertion state where the diopter correction lens 70 or the diopter correction lens 71 is inserted into the imaging optical path. A different focusing control is performed on the photographing focusing drive unit 31A.

<Evacuation state>
In the retracted state, the imaging and focusing control unit 211a determines the position of the imaging and focusing lens 31 by controlling the focusing optical system driving unit 60A so that the positional relationship between the two split optotype images becomes the reference positional relationship. I do. The two split optotype images are acquired by the CCD 35 based on the return light from the eye E to which the two split optotypes are projected by the focus optical system 60. The imaging and focusing control unit 211a analyzes the image acquired by the CCD 35 and controls the imaging and focusing driving unit 31A so that the positional relationship between the two split optotype images depicted in the image coincides with the vertical direction. . The imaging focus control unit 211a determines the position of the imaging focusing lens 31 on the imaging optical path when the two split optotype images coincide in the up-down direction as the in-focus position. The imaging focusing control unit 211a controls the imaging focusing driving unit 31A to move the imaging focusing lens 31 to the determined position. The shooting / focusing control unit 211a refers to shooting / focusing control information 212a, which will be described later, which is stored in the storage unit 212 in advance corresponding to the position of the focus optical system 60 where the two split optotype images coincide vertically. It is possible to determine the position of the photographing focusing lens 31 by using

<Inserted state>
As described above, the split optotype image cannot be acquired by the imaging optical system 30 in the inserted state. In the inserted state, the imaging focusing control unit 211a determines the position of the imaging focusing lens 31 based on the position of the OCT focusing lens 43 determined by the OCT focusing control unit 211b described below. As will be described later, the OCT focusing control unit 211b determines the position of the OCT focusing lens 43 based on the interference light LC detected by the interference optical system. It is possible to determine the position of the photographing focusing lens 31 based on this. The imaging and focusing control unit 211a can determine the position of the imaging and focusing lens 31 so that the intensity of the interference light LC detected by the intensity detection unit 211c described below is maximized. Further, the imaging focusing control unit 211a may determine the position of the imaging focusing lens 31 based on the control content (control history) of the OCT focusing driving unit 43A by the OCT focusing control unit 211b. The imaging focusing control unit 211a controls the imaging focusing driving unit 31A to move the imaging focusing lens 31 to the determined position. The imaging focusing control unit 211a can determine the position of the imaging focusing lens 31 by referring to OCT focusing control information 212b, which will be described later, stored in the storage unit 212 in advance.

(OCT focus control unit)
The OCT focus control section 211b controls the OCT focus drive section 43A so as to focus the interference optical system. As described above, the OCT focusing control unit 211b determines the position of the OCT focusing lens 43 based on the interference light LC detected by the interference optical system. As a specific example, the OCT focusing control unit 211b determines the position of the OCT focusing lens 43 so that the intensity of the interference light LC detected by the intensity detecting unit 211c is maximized. The OCT focusing control unit 211b controls the OCT focusing driving unit 43A to move the OCT focusing lens 43 to the determined focusing position.

(Intensity detector)
The intensity detector 211c detects the intensity of the interference light detected by the interference optical system. The intensity detector 211c detects the intensity of the interference light based on the detection signal detected by the detector 125. The intensity detector 211c can detect the maximum value of the intensity of the interference light. The OCT focus control unit 211b determines the focus position of the OCT focus lens 43 so that the intensity of the interference light is maximized by the intensity detection unit 211c in a preset scan range or scan position of the eye E.

(Storage unit)
The storage unit 212 stores various data. The data stored in the storage unit 212 includes, for example, image data of an OCT image, image data of a fundus image, eye information to be examined, and the like. The subject's eye information includes information about the subject, such as a patient ID and a name, and information about the subject's eye, such as left / right eye identification information. Further, the storage unit 212 stores various programs and data for operating the ophthalmologic photographing apparatus 1.

  The storage unit 212 stores imaging focusing control information 212a and OCT focusing control information 212b in advance.

  As shown in FIG. 4, the shooting focus control information 212a includes the positions F1, F2,... Of the focus optical system 60 where the positional relationship between the two split optotype images is the aforementioned reference positional relationship, and the shooting focus lens. 31 are the control information associated with the positions D1, D2,... According to the diopter of the eye E, the position of the focus optical system 60 in which the positional relationship between the two split optotype images on the illumination optical path is the reference positional relationship is determined. Further, the position on the imaging optical path of the imaging focusing lens 31 for focusing the imaging optical system 30 is determined according to the diopter of the eye E to be inspected. Accordingly, the diopter of the eye E to be inspected can be obtained from the position of the focus optical system 60, and the position of the imaging focusing lens 31 can be obtained from the obtained diopter of the eye E. The information 212a can be generated in advance. The imaging and focusing control unit 211a specifies the position of the imaging and focusing lens 31 from the position of the focusing optical system 60 based on the imaging and focusing control information 212a. At this time, the shooting and focusing control unit 211a performs an interpolation process using control information stored in advance as the shooting and focusing control information 212a, and performs the shooting and focusing lens 31 based on the new control information obtained by the interpolation process. Can be specified.

  As shown in FIG. 5, the OCT focusing control information 212b associates the positions C1, C2,... Of the OCT focusing lens 43 with the positions d1, 2,. This is control information. The position on the measurement optical path of the OCT focusing lens 43 for focusing the interference optical system is determined according to the diopter of the eye E. Further, as described above, the position on the imaging optical path of the imaging focusing lens 31 for focusing the imaging optical system 30 is determined according to the diopter of the eye E to be inspected. Therefore, the diopter of the eye E to be inspected can be obtained from the position of the OCT focusing lens 43, and the position of the imaging focusing lens 31 can be obtained from the obtained diopter of the eye E. Therefore, the OCT focusing shown in FIG. The control information 212b can be generated in advance. The imaging focusing control unit 211a specifies the position of the imaging focusing lens 31 from the position of the OCT focusing lens 43 based on the OCT focusing control information 212b. At this time, the imaging focusing control unit 211a performs an interpolation process using control information stored in advance as the OCT focusing control information 212b, and performs the imaging focusing lens 31 based on new control information obtained by the interpolation process. Can be specified.

(Image forming unit)
The image forming section 220 forms image data of a cross-sectional image of the fundus oculi Ef based on a detection signal from the detector 125 (DAQ130). That is, the image forming unit 220 forms image data of the eye E based on the detection result of the interference light LC by the interference optical system. This processing includes processing such as noise removal (noise reduction), filter processing, and FFT (Fast Fourier Transform), similarly to the conventional swept-source OCT. The image data obtained in this manner is a data set including a group of image data formed by imaging the reflection intensity profiles in a plurality of A lines (the paths of the respective measurement lights LS in the eye E). is there.

  In order to improve the image quality, a plurality of data sets acquired by repeating scanning with the same pattern a plurality of times can be superimposed (averaged).

  Further, the image forming unit 220 generates two or more split optotype images from the image signals detected by the CCD 35 based on the return light of the two or more split optotypes from the eye E passing through the imaging focusing lens 31. Form the rendered image. The formation of the image in which the two or more split optotype images are drawn may be performed by the main control unit 211.

  The image forming unit 220 includes, for example, the above-described circuit board. In this specification, “image data” and “image” based on the image data may be identified. In addition, the part of the eye E to be examined may be identified with the image thereof.

(Data processing unit)
The data processing section 230 performs various data processing (image processing) and analysis processing on the image formed by the image forming section 220. For example, the data processing unit 230 executes correction processing such as luminance correction and dispersion correction of the image. Further, the data processing unit 230 performs various image processing and analysis processing on the image (fundus image, anterior eye image, etc.) obtained by the fundus camera unit 2.

  The data processing unit 230 can form volume data (voxel data) of the eye E by performing known image processing such as interpolation processing for interpolating pixels between cross-sectional images. When displaying an image based on the volume data, the data processing unit 230 performs a rendering process on the volume data to form a pseudo three-dimensional image when viewed from a specific viewing direction.

  The data processing unit 230 can perform positioning between the fundus image and the OCT image. When the fundus image and the OCT image are acquired in parallel, since the two optical systems are coaxial, the fundus image and the OCT image acquired (almost) at the same time are combined with the optical axis of the photographing optical system 30. Can be aligned on the basis of. In addition, regardless of the acquisition timing of the fundus image and the OCT image, alignment between the fundus image and the front image obtained by projecting at least a part of the image area corresponding to the fundus oculi Ef in the OCT image on the xy plane is performed. By doing so, it is possible to align the OCT image with the fundus image. This positioning method is applicable even when the optical system for obtaining a fundus image and the optical system for OCT are not coaxial. Even when both optical systems are not coaxial, if the relative positional relationship between the two optical systems is known, the same alignment as in the case of coaxial is performed with reference to this relative positional relationship. It is possible.

  The data processing unit 230 that functions as described above includes, for example, a microprocessor, a RAM, a ROM, a hard disk drive, a circuit board, and the like. In a storage device such as a hard disk drive, a computer program for causing the microprocessor to execute the above functions is stored in advance.

(User interface)
The user interface 240 includes a display unit 241 and an operation unit 242. The display unit 241 includes the display device and the display device 3 of the arithmetic and control unit 200 described above. The operation unit 242 includes the operation device of the arithmetic and control unit 200 described above. The operation unit 242 may include various buttons and keys provided on the housing of the ophthalmologic imaging apparatus 1 or outside. In addition, the display unit 241 may include various display devices such as a touch panel provided on the housing of the fundus camera unit 2.

  The display unit 241 and the operation unit 242 do not need to be configured as separate devices. For example, a device in which a display function and an operation function are integrated, such as a touch panel, can be used. In that case, the operation unit 242 is configured to include the touch panel and the computer program. The content of the operation performed on the operation unit 242 is input to the control unit 210 as an electric signal. Further, operations and information input may be performed using a graphical user interface (GUI) displayed on the display unit 241 and the operation unit 242.

  The imaging optical system 30 is an example of the “first optical system” according to the embodiment. The imaging optical path, which is the optical path of the imaging optical system 30, is an example of the “first optical path” according to the embodiment. The shooting focusing lens 31 is an example of the “first focusing lens” according to the embodiment. The CCD 35 is an example of the “first light receiving element” according to the embodiment. The shooting and focusing drive unit 31A is an example of the “first drive unit” according to the embodiment. The shooting focus control unit 211a is an example of the “first focus control unit” according to the embodiment.

  The OCT unit 100, the collimator lens unit 40, the optical path length changing unit 41, the optical scanner 42, the OCT focusing lens 43, the mirror 44, and the relay lens 45 correspond to the “second optical system” or the “interference optical system” according to the embodiment. This is an example. The measurement light path that is the light path of the measurement light LS and the return light thereof is an example of the “second light path” according to the embodiment. The OCT focusing lens 43 is an example of the “second focusing lens” according to the embodiment. The detector 125 is an example of the “second light receiving element” according to the embodiment. The OCT focus driving unit 43A is an example of the “second driving unit” according to the embodiment. The OCT focus control unit 211b is an example of the “second focus control unit” according to the embodiment.

  The illumination optical path that is the optical path of the illumination optical system 10 is an example of the “third optical path” according to the embodiment. The focus optical system 60 is an example of the “focused target projection optical system” according to the embodiment. The two split targets are examples of the “focus target” according to the embodiment. The focus optical system driving unit 60A is an example of the “third driving unit” according to the embodiment. The shooting focusing control information 212a is an example of “second control information” according to the embodiment. The OCT focusing control information 212b is an example of “first control information” according to the embodiment.

[Operation example]
The operation of the ophthalmologic photographing apparatus 1 will be described. The ophthalmologic imaging apparatus 1 according to the embodiment obtains an image of the fundus oculi Ef of the eye E by the fundus camera unit 2 and obtains a cross-sectional image of the fundus oculi Ef by the OCT unit 100 and the like. The operation of the ophthalmologic photographing apparatus 1 for acquiring a sectional image of the fundus oculi Ef by the OCT unit 100 or the like is known. Hereinafter, an operation example when the fundus camera unit 2 acquires an image of the fundus oculi Ef of the eye E to be inspected will be described.

  Before describing an operation example of the ophthalmologic imaging apparatus 1 according to the embodiment, an operation example of the ophthalmologic imaging apparatus according to the comparative example will be described.

  FIG. 6 is a flowchart illustrating an operation example of the ophthalmologic imaging apparatus according to the comparative example. In this operation example, it is assumed that alignment for photographing (auto-alignment) has already been executed and tracking has already started.

(S21)
When the diopter correction lens is inserted in the imaging optical path (S21: Y), the operation of the ophthalmologic imaging apparatus according to the comparative example shifts to S27. When the diopter correction lens is retracted from the imaging optical path (S21: N), the operation of the ophthalmologic imaging apparatus according to the comparative example shifts to S22.

(S22)
When the diopter correction lens is retracted from the photographing optical path (S21: N), the control unit that controls the ophthalmologic photographing apparatus according to the comparative example inserts a reflecting rod into the illumination optical path, and moves the split optotype image vertically. The focus optical system is moved to a matching position (a split bright line matching position).

(S23)
When the focus optical system is moved to a position where the split optotype image coincides in the vertical direction, the control unit causes the storage unit to store the moved position of the focus optical system after the movement.

(S24)
Control information in which the movement position of the focus optical system is associated with the diopter of the eye E is stored in the storage unit in advance. The control unit obtains the diopter of the eye E from the moving position of the focus optical system stored in S23 by referring to the control information stored in the storage unit.

(S25)
The diopter of the eye E and the position of the focusing lens for changing the focus position of the imaging optical system are associated in advance. The control unit obtains the position of the imaging focusing lens from the diopter of the eye E obtained in S24.

(S26)
The control unit moves the imaging focusing lens to the position determined in S25. After the imaging focusing lens is moved to the in-focus position, the ophthalmologic imaging apparatus according to the comparative example executes imaging on the fundus oculi Ef. Thus, the operation of the ophthalmologic imaging apparatus according to the comparative example ends (end).

(S27)
When the diopter correction lens is inserted in the imaging optical path (S21: Y), the ophthalmologic imaging apparatus according to the comparative example performs focus adjustment manually in response to a user operation on an operation unit (not shown). That is, the photographing focusing lens is manually moved. After the position of the imaging focusing lens is manually adjusted, the ophthalmologic imaging apparatus according to the comparative example executes imaging on the fundus oculi Ef. Thus, the operation of the ophthalmologic imaging apparatus according to the comparative example ends (end).

  As described above, in the ophthalmologic photographing apparatus according to the comparative example, when the diopter correction lens is inserted into the photographing optical path, the focusing control using the split optotype image becomes impossible. Adjustments need to be made.

  FIG. 7 is a flowchart illustrating an operation example of the ophthalmologic imaging apparatus 1 according to the embodiment. In this operation example, it is assumed that alignment for photographing (auto-alignment) has already been executed and tracking has already been started.

(S1)
First, the main control unit 211 determines whether or not the diopter correction lenses 70 and 71 are inserted in the imaging optical path. The main control unit 211 inserts the diopter correction lenses 70 and 71 into the imaging optical path from the state of the operation knob (operation unit 242) that inserts or retracts the diopter correction lens 70 or the diopter correction lens 71 into the imaging optical path. It is possible to determine whether or not. Further, the main control unit 211 determines whether or not the diopter correction lenses 70 and 71 are inserted in the photographing optical path based on the detection result of the sensor provided in the moving mechanism that moves the diopter correction lenses 70 and 71. Is possible. When the main control unit 211 determines that the diopter correction lens 70 or the diopter correction lens 71 is inserted in the imaging optical path (S1: Y), the operation of the ophthalmologic imaging apparatus 1 proceeds to S7. When the main control unit 211 determines that the diopter correction lens 70 and the diopter correction lens 71 are retracted from the imaging optical path (S1: N), the operation of the ophthalmologic imaging apparatus 1 proceeds to S2.

(S2)
When the main control unit 211 determines that the diopter correction lens 70 and the diopter correction lens 71 are retracted from the imaging optical path (S1: N), the imaging focus control unit 211a controls the reflection rod driving unit 67A. Is performed, the reflecting rod 67 is inserted into the illumination optical path. Subsequently, the imaging focus control unit 211a controls the focus optical system driving unit 60A to move the focus optical system 60 to a position where the split optotype image coincides vertically (a split bright line coincidence position).

(S3)
When the focus optical system 60 is moved to a position where the split optotype image coincides with the vertical direction, the main control unit 211 (imaging and focusing control unit 211a) stores the moved position of the focus optical system 60 after the movement in the storage unit 212. To memorize.

(S4)
The photographing and focusing control unit 211a obtains the position of the photographing and focusing lens 31 from the moving position of the focusing optical system 60 stored in S3 by referring to the photographing and focusing control information 212a stored in the storage unit 212.

(S5)
The shooting and focusing control unit 211a moves the shooting and focusing lens 31 to the position determined in S4 by controlling the shooting and focusing driving unit 31A. After the imaging focusing lens 31 is moved to the in-focus position, the ophthalmologic imaging apparatus 1 performs imaging on the fundus oculi Ef. Thus, the operation of the ophthalmologic photographing apparatus 1 according to the embodiment ends (end).

(S7)
When the main control unit 211 determines that the diopter correction lens 70 or the diopter correction lens 71 is inserted in the photographing optical path (S1: Y), the OCT focusing control unit 211b executes the OCT measurement, and The detection of the interference light LC is started by the detection unit 211c. The OCT focus control unit 211b controls the OCT focus drive unit 43A to move the OCT focus lens 43 to a position where the intensity of the interference light LC detected by the intensity detection unit 211c is maximized.

(S8)
When the OCT focusing lens 43 is moved to a position where the intensity of the interference light LC is maximized, the main control unit 211 (OCT focusing control unit 211b) stores the moved position of the OCT focusing lens 43 after the movement. 212 is stored.

(S9)
The photographing focusing control unit 211a refers to the OCT focusing control information 212b stored in the storage unit 212 to determine the position of the photographing focusing lens 31 from the moving position of the OCT focusing lens 43 stored in S8. . Thereafter, the operation of the ophthalmologic photographing apparatus 1 proceeds to S5.

  As described above, when the diopter correction lens is inserted into the photographing optical path, it is necessary to manually perform the focusing adjustment in the comparative example, whereas the ophthalmologic imaging apparatus 1 according to the embodiment automatically performs the focusing. It becomes possible.

  Note that, in this embodiment, the case where the “second optical system” according to the embodiment is an optical system that captures the eye E using OCT has been described. An observation system that guides light from the optometry E to the eyepiece may be used.

[effect]
Effects of the ophthalmologic photographing apparatus according to the embodiment will be described.

  The ophthalmologic photographing apparatus (for example, the ophthalmologic photographing apparatus 1) of the embodiment includes a first optical system (for example, the photographing optical system 30), a first driving unit (for example, the photographing focusing driving unit 31A), and a first focusing. And a control unit (for example, a shooting and focusing control unit 211a). The first optical system includes a first focusing lens (for example, the photographing focusing lens 31) and a diopter correction lens (for example, diopter correction lenses 70 and 71), and the subject's eye (for example, the subject's eye E). Is guided to the first light receiving element (for example, the CCD 35). The first focusing lens is movable along an optical axis of a first optical path (for example, a photographing optical path). The diopter correction lens can be inserted into and removed from the first optical path. The first driving unit moves the first focusing lens. The first focus control unit performs first driving different focus control between a retracted state in which the diopter correction lens is retracted from the first optical path and an insertion state in which the diopter correction lens is inserted in the first optical path. Perform on the department.

  According to such a configuration, the focus control different from the focus control performed in the retracted state is performed in the insertion state. Therefore, even when the optical relationship changes due to the insertion of the diopter correction lens, the focus control is automatically performed. Can be focused. In other words, even if the diopter correction lens is inserted in the first optical path or the diopter correction lens is retracted from the first optical path, the first optical system is controlled by the so-called autofocus function. It becomes possible to focus.

  The ophthalmologic imaging apparatus according to the embodiment includes a second optical system (for example, the interference optical system includes an OCT unit 100, a collimator lens unit 40, an optical path length changing unit 41, an optical scanner 42, an OCT focusing lens 43, and a mirror 44). And a relay lens 45), a second drive unit (for example, the OCT focus drive unit 43A), and a second focus control unit (for example, the OCT focus control unit 211b). The second optical system includes a second focusing lens (for example, the OCT focusing lens 43), and guides light from the subject's eye to the second light receiving element (for example, the detector 125) or the eyepiece. The second focusing lens is movable along an optical axis of a second optical path (for example, the optical path of the measurement light or its return light). The second driving unit moves the second focusing lens. The second focus control unit determines the position of the second focus lens by executing focus control on the second drive unit, and moves the second focus lens to the determined focus position. The first focus control unit determines the position of the first focus lens based on the position of the second focus lens determined by the second focus control unit in the inserted state, and sets the position of the first focus lens to the determined focus position. The first focusing lens is moved.

  According to such a configuration, the focus control for the first drive unit is reflected in the focus control for the second drive unit in the insertion state. Accurate focusing control can be automatically executed.

  In the ophthalmologic imaging apparatus according to the embodiment, the second optical system includes an interference optical system. The interference optical system splits light (for example, light L0) from a light source (for example, light source unit 101) into measurement light (for example, measurement light LS) and reference light (for example, reference light LR), and splits the measurement light. The second light receiving element detects the interference light (for example, the interference light LC) between the return light of the measurement light from the eye to be examined and the reference light. The second focusing lens is arranged on the optical path of the measurement light and the return light. The second focusing control unit determines the position of the second focusing lens based on the interference light detected by the interference optical system.

  According to such a configuration, the first optical system is focused on the basis of the interference light generated by the interference optical system. The control can be automatically executed.

  Further, the ophthalmologic imaging apparatus according to the embodiment includes an intensity detection unit (for example, the intensity detection unit 211c). The intensity detector detects the intensity of the interference light detected by the interference optical system. The second focus control unit determines the position of the second focus lens such that the intensity of the interference light detected by the intensity detection unit is maximized.

  According to such a configuration, since the first optical system is focused based on the intensity of the interference light, it is possible to automatically execute highly accurate focusing control with simple control in the inserted state. become.

  Further, the ophthalmologic imaging apparatus according to the embodiment includes a storage unit (for example, the storage unit 212). The storage unit stores in advance first control information (for example, OCT focusing control information 212b) in which the position of the second focusing lens and the position of the first focusing lens are associated with each other. In the inserted state, the first focus control unit determines the position of the first focus lens based on the position of the second focus lens determined by the second focus control unit and the first control information.

  According to such a configuration, since the first optical system is focused based on the first control information, it is possible to simplify and speed up the focusing control in the inserted state.

  Further, the ophthalmologic photographing apparatus according to the embodiment includes an illumination optical system (for example, the illumination optical system 10), a focused optotype projection optical system (for example, the focus optical system 60), and a third drive unit (for example, the focus optical system). System drive unit 60A). The illumination optical system irradiates the subject's eye with the illumination light beam via a third optical path (for example, an illumination optical path) that is combined with the first optical path between the subject's eye and the diopter correction lens. The focusing target projection optical system projects a focusing target (for example, a split target) to the eye to be examined via the third optical path. The third drive unit moves the focused optotype projection optical system along the optical axis of the third optical path. The first light receiving element receives the return light of the in-focus target from the eye to be examined that has passed through the first in-focus lens. The first focusing control unit determines the position of the first focusing lens by controlling the third driving unit based on the position of the in-focus target image acquired by the first light receiving element in the retracted state. Then, the first focusing lens is moved to the determined focusing position.

  According to such a configuration, in addition to the above-described effects, in the retracted state, it is possible to automatically execute high-precision focusing control based on the position of the in-focus target image obtained by the focusing optical system. Will be possible.

[First Modification]
The imaging focus control unit 211a according to the embodiment is not limited to the one that obtains the focusing position of the imaging focusing lens 31 based on the OCT focusing control information 212b shown in FIG.

  The configuration and operation of the ophthalmologic imaging apparatus according to the first modification are substantially the same as the configuration and operation of the ophthalmologic imaging apparatus 1 according to the embodiment. Hereinafter, the ophthalmologic imaging apparatus according to the first modified example will be described focusing on differences from the present embodiment.

  FIG. 8 shows an example of a block diagram of a control system of the ophthalmologic imaging apparatus according to the first modification. 8, the same components as those in FIG. 3 are denoted by the same reference numerals, and the description will be omitted as appropriate. The main difference between the configuration of the control system of the ophthalmologic imaging apparatus according to the first modification and the configuration of the control system of the ophthalmologic imaging apparatus 1 according to the embodiment is that correction information 212c is stored in the storage unit instead of the OCT focusing control information 212b. 312.

  In the ophthalmologic imaging apparatus according to the first modification, a control unit 310 is provided instead of the control unit 210. Control unit 310 includes a main control unit 311 and a storage unit 312. The main control unit 311 includes an imaging focusing control unit 211d, an OCT focusing control unit 211b, and an intensity detection unit 211c. The storage unit 312 stores the shooting focus control information 212a and the correction information 212c.

  The correction information 212c is control information for correcting the imaging focus control information 212a to determine the position of the imaging focusing lens 31 from the position of the OCT focusing lens 43. The correction information 212c may be, for example, control information in which the position of the OCT focusing lens 43 and the correction value are associated. The correction information 212c may include a correction value corresponding to each of the positions D1, D2,... Of the photographing focusing lens 31, or a plurality of correction positions among the focusing positions D1, D2,. Information to which one correction value is assigned may be used.

  When the diopter correction lens 70 or the diopter correction lens 71 is inserted in the imaging optical path, the imaging focus controller 211d determines the position of the imaging focus lens obtained from the imaging focus control information 212a as the correction information 212c. Is corrected based on. Thereby, the shooting / focusing control unit 211d newly determines the position of the shooting / focusing lens 31. The shooting focus control unit 211d controls the shooting focus driving unit 31A to move the shooting focus lens 31 to the newly determined focus position.

[effect]
The ophthalmologic imaging apparatus according to the embodiment includes a storage unit (for example, storage unit 312). The storage unit stores in advance the second control information (for example, the shooting and focusing control information 212a) and the correction information (for example, the correction information 212c). The second control information is information in which the position of the focus target projection optical system at which the position of the image of the focus target is a predetermined position is associated with the position of the first focus lens. The correction information is information for correcting the second control information. The first focus control unit (for example, the shooting focus control unit 211d) determines the position of the first focus lens based on the second control information in the retracted state, and sets the first focus lens to the determined focus position. Move the focus lens. In the inserted state, the first focus control unit determines a new position of the first focus lens by correcting the position of the first focus lens stored in the storage unit based on the correction information, and determines a new position of the first focus lens. The first focusing lens is moved to a focusing position.

  According to such a configuration, in the retracted state, the first optical system is focused on the basis of the second control information, and in the inserted state, the first optical system is focused on the basis of the second control information and the correction information. Therefore, the focus control using the diopter correction lens can be simplified and speeded up.

[Second Modification]
In the ophthalmologic imaging apparatus 1 according to the embodiment, a case has been described in which different focusing controls are executed in accordance with the determination result as to whether or not the diopter correction lenses 70 and 71 are inserted in the imaging optical path. The operation of the ophthalmologic photographing apparatus 1 is not limited to this.

  The configuration and operation of the ophthalmologic imaging apparatus according to the second modification are substantially the same as the configuration and operation of the ophthalmologic imaging apparatus 1 according to the embodiment. Hereinafter, an ophthalmologic imaging apparatus according to a second modification will be described focusing on differences from the present embodiment.

  FIG. 9 shows an example of a block diagram of a control system of an ophthalmologic imaging apparatus according to the second modification. In FIG. 9, the same portions as those in FIG. 3 are denoted by the same reference numerals, and the description will be appropriately omitted. The main difference between the configuration of the control system of the ophthalmologic imaging apparatus according to the second modification and the configuration of the control system of the ophthalmologic imaging apparatus 1 according to the embodiment is that a fundus camera unit 2a is provided instead of the fundus camera unit 2. And a control unit 410 is provided instead of the control unit 210.

  The configuration of the retinal camera unit 2a differs from the configuration of the retinal camera unit 2 in that a correction lens driving unit 70A is provided. The correction lens driving unit 70A moves the diopter correction lenses 70 and 71. The correction lens driving unit 70A receives control from a later-described diopter correction control unit 211f, and causes the diopter correction lens 70 or the diopter correction lens 71 to be inserted into and removed from the imaging optical path.

  Control unit 410 differs from control unit 210 in that main control unit 411 is provided instead of main control unit 211. The main control unit 411 includes a shooting focus control unit 211a, an OCT focus control unit 211b, an intensity detection unit 211c, a determination unit 211e, and a diopter correction control unit 211f.

  The shooting and focusing control unit 211a determines the position of the shooting and focusing lens 31 by controlling the shooting and focusing driving unit 31A within a predetermined focusable range. The determination unit 211e determines whether or not the photographic optical system 30 is focused by the photographic focusing lens 31 within a predetermined focusable range while the diopter correction lenses 70 and 71 are retracted from the photographic optical path. The determination unit 211e determines that the imaging optical system 30 has been focused by the imaging focusing lens 31, for example, when the split optotype images vertically coincide with each other in the focusable range described above. The determining unit 211e determines that the imaging optical system 30 has not been focused by the imaging focusing lens 31 when, for example, the split optotype images do not coincide vertically in the focusable range described above.

  The diopter correction control unit 211f controls the correction lens driving unit 70A based on the determination result by the determination unit 211e. When the determination unit 211e determines that the imaging optical system 30 is not focused by the imaging focusing lens 31, the diopter correction control unit 211f sends the diopter correction lens 70 or diopter to the correction lens driving unit 70A in the imaging optical path. The correction lens 71 is inserted.

  FIG. 10 is a flowchart illustrating an operation example of the ophthalmologic imaging apparatus according to the second modification of the embodiment. In this operation example, it is assumed that alignment for photographing (auto-alignment) has already been executed and tracking has already been started. In this operation example, a case where the diopter correction lens 70 is inserted will be described.

(S11)
First, the imaging focusing control unit 211a controls the reflection rod driving unit 67A to insert the reflection rod 67 into the illumination light path. Subsequently, by controlling the focus optical system drive unit 60A, the imaging focus control unit 211a moves the focus optical system 60 within a predetermined focusable range, and positions the split optotype images in the vertical direction ( Search for split emission line coincidence position).

(S12)
The determination unit 211e determines whether or not a position where the split optotype image matches in the up-down direction has been searched in S11. When it is determined that the position where the split optotype image coincides with the vertical direction has been searched (S12: Y), the operation of the ophthalmologic imaging apparatus according to the second modified example shifts to S13. When it is determined that the position where the split optotype image coincides with the vertical direction has not been searched (S12: N), the operation of the ophthalmologic imaging apparatus according to the second modification proceeds to S16.

(S13)
When it is determined that the position where the split optotype image coincides in the up-down direction has been searched (S12: Y), the main control unit 411 (imaging focusing control unit 211a) determines the moving position of the focus optical system 60 after the movement. It is stored in the storage unit 212.

(S14)
The photographing and focusing control unit 211a refers to the photographing and focusing control information 212a stored in the storage unit 212 to determine the position of the photographing and focusing lens 31 from the moving position of the focusing optical system 60 stored in S13.

(S15)
The imaging focusing control unit 211a controls the imaging focusing driving unit 31A to move the imaging focusing lens 31 to the position determined in S14. After the imaging focusing lens 31 is moved to the in-focus position, the ophthalmologic imaging apparatus according to the second modification performs imaging on the fundus oculi Ef. Thus, the operation of the ophthalmologic photographing apparatus according to the second modification is completed (end).

(S16)
When it is determined that the position where the split optotype image coincides in the vertical direction is not searched (S12: N), the diopter correction control unit 211f controls the correction lens driving unit 70A to correct the diopter in the photographing optical path. The lens 70 is inserted.

(S17)
The OCT focus control unit 211b causes the OCT measurement to be performed, and causes the intensity detection unit 211c to start detecting the interference light LC. The OCT focus control unit 211b controls the OCT focus drive unit 43A to move the OCT focus lens 43 to a position where the intensity of the interference light LC detected by the intensity detection unit 211c is maximized.

(S18)
When the OCT focusing lens 43 is moved to a position where the intensity of the interference light LC is maximized, the main control unit 411 (OCT focusing control unit 211b) stores the moved position of the OCT focusing lens 43 after the movement. 212 is stored.

(S19)
The imaging focusing control unit 211a refers to the OCT focusing control information 212b stored in the storage unit 212, and obtains the position of the imaging focusing lens 31 from the moving position of the OCT focusing lens 43 stored in S18. . Thereafter, the operation of the ophthalmologic photographing apparatus according to the second modification proceeds to S15.

  Although FIG. 10 illustrates the case where the diopter correction lens 70 is automatically inserted, the same applies to the case where the diopter correction lens 71 is automatically inserted. In addition, it is determined whether or not the diopter correction by the diopter correction lens 70 is good in a state where the diopter correction lens 70 is automatically inserted into the photographing optical path, and when it is determined that the diopter correction is not good, The diopter correction lens 71 may be automatically inserted into the photographing optical path. For example, when the intensity of the interference light detected by the intensity detecting unit 211c while the diopter correction lens is inserted is equal to or higher than a predetermined threshold intensity, it is possible to determine that the diopter correction is good. .

[effect]
The ophthalmologic imaging apparatus according to the embodiment includes a correction lens driving unit (for example, a correction lens driving unit 70A), a determination unit (for example, a determination unit 211e), and a diopter correction control unit (for example, a diopter correction control unit 211f). And The correction lens driving unit moves the diopter correction lens. The determining unit determines whether the first optical system is focused by the first focusing lens within a predetermined focusable range in the retracted state. The diopter correction control unit causes the correction lens driving unit to insert the diopter correction lens into the first optical path when the determination unit determines that the first optical system is not focused.

  According to such a configuration, the diopter correction lens is automatically inserted into the first optical path, and the above-described focusing control is executed in the inserted state. In addition, it becomes possible to automatically execute the focusing control using the diopter correction lens.

(Other modifications)
The configuration described above is merely an example for suitably implementing the present invention. Therefore, arbitrary modifications (omission, substitution, addition, etc.) within the scope of the gist of the present invention can be appropriately made. The applied configuration is selected, for example, according to the purpose. Further, depending on the configuration to be applied, the effects and advantages obvious to those skilled in the art and the advantages and effects described in this specification can be obtained.

Reference Signs List 1 ophthalmic imaging apparatus 2, 2a fundus camera unit 3 display apparatus 10 illumination optical system 30 imaging optical system 31 imaging focusing lens 43 OCT focusing lens 60 focusing optical system 100 OCT unit 200 arithmetic control units 210, 310, 410 control unit 211 , 311, 411 Main control units 211a, 211d Imaging focus control unit 211b OCT focus control unit 211c Intensity detection unit 211e Judgment unit 211f Diopter correction control unit 212, 312 Storage unit 212a Imaging focus control information 212b OCT focus control Information 212c Correction information 220 Image forming unit 230 Data processing unit 240 User interface 241 Display unit 242 Operation unit E Eye to be examined

Claims (5)

A first optical system that includes a first focusing lens disposed in a first optical path, and a diopter correction lens that can be inserted into and removed from the first optical path, and guides light from the eye to be inspected to a first light receiving element; ,
A second optical system including a second focusing lens disposed in the second optical path;
When the diopter correction lens is inserted in the first optical path, focus control is performed on the first focus lens based on a focus state of the second optical system by the second focus lens. A first focusing control unit,
Ophthalmological imaging apparatus including: A first driving unit that drives the first focusing lens;
The ophthalmologic imaging apparatus according to claim 1, wherein the first focus control unit performs focus control on a first drive unit. A second driving unit that drives the second focusing lens;
A second focus control unit that performs focus control on the second drive unit;
Including
The ophthalmologic imaging apparatus according to claim 1, wherein the second optical system guides light from the eye to be inspected to a second light receiving element or an eyepiece. The second optical system divides light from a light source into measurement light and reference light, causes the measurement light to enter the subject's eye, and includes a return light of the measurement light from the subject's eye and the reference light. An interference optical system that detects interference light with the second light receiving element,
The second focusing lens is disposed in an optical path of the measurement light and the return light,
The ophthalmologic imaging according to claim 3, wherein the second focus control unit performs focus control on the second drive unit based on the interference light detected by the interference optical system. apparatus. When the diopter correction lens is retracted from the first optical path, the first focusing control unit focuses on the first focusing lens based on a detection result obtained by the first light receiving element. The ophthalmologic imaging apparatus according to any one of claims 1 to 4, wherein focus control is performed.

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