JP6421919B2 - Ophthalmic imaging equipment - Google Patents

Description

  The present disclosure relates to an ophthalmologic photographing apparatus for photographing a fundus of a subject's eye.

  An optical tomography (OCT) using low-coherent light is known as an optical tomography apparatus that captures a tomogram of a subject's eye (see Patent Document 1).

  In such an apparatus, the examiner has focused the tomographic image of the eye to be examined using a focus state acquired by a front observation system such as an SLO optical system or a fundus camera optical system (Patent Document 1). reference). There is also known an apparatus that adjusts the focus state of an OCT optical system using the focus state of a front image and then adjusts the focus using the OCT optical system (see Patent Document 2).

JP 2012-213489 A JP 2009-291252 A

  However, when adjusting the focus of the OCT optical system using the front image, the focus state may not be detected properly due to the effects of the subject's blink, cataract turbidity, small pupil eye, etc., and autofocus may not be performed. It was. In this case, the front observation system and the OCT optics are shifted from the fundus.

  On the other hand, when the focus is adjusted using the OCT optical system, it takes a relatively long time, which may be a burden on the eye to be examined.

  An object of the present invention is to provide an ophthalmologic photographing apparatus that can solve at least one of the conventional techniques.

  In order to solve the above problems, the present disclosure is characterized by having the following configuration.

A first focus optical member that is moved in the optical axis direction by a first drive unit; and a light receiving element that receives reflected light from the fundus via the first focus optical member, and the light receiving element. A front imaging optical system for acquiring a front image of the fundus oculi based on an output signal from the eye, and a second focus optical member that is moved in the optical axis direction by the second drive unit, and measuring light on the fundus oculi to be examined And a detection signal including an interference signal between the measurement light guided to the eye to be examined via the measurement optical path and the reference light from the reference optical path. For detecting a tomographic image of the fundus oculi based on an output signal from the detector, and focusing position information on the fundus of the front imaging optical system. Before 1 in-focus position information First autofocus control acquired based on a light reception signal output from the light receiving element and moving the first focus optical member and the second focus optical member to a focus position, and alignment of the OCT optical system to the fundus Second autofocus control that acquires second focus position information, which is focus position information, based on an output signal from the detector and moves the second focus optical member to the focus position can be executed. Control means, and the control means includes a determination means for determining whether or not the first autofocus control is successful , and executes the first autofocus control first and succeeds in the determination result of the determination means. When it is determined that the second autofocus control is not executed, the second autofocus control is not executed.

1 is an external view of an ophthalmologic photographing apparatus according to an embodiment. It is a figure which shows the optical system and control system of the ophthalmologic imaging device which concerns on a present Example. It is a figure which shows an example of the infrared fundus image displayed on the display part. It is a figure which shows an example of the anterior ocular segment observation image displayed on the display part. It is a flowchart which shows the flow of operation | movement of this apparatus. It is a figure explaining optimization control. It is a figure which shows the image displayed on the screen of a display part. It is a figure which shows the change of the luminance distribution in the depth direction of an image. It is a figure explaining the optimization control of 2nd Example. It is a figure for demonstrating the manual focus adjustment of 2nd Example.

<First Embodiment>
Hereinafter, the outline | summary about 1st Embodiment of an ophthalmologic imaging device is demonstrated based on drawing. An ophthalmic imaging apparatus (see FIG. 1) 1 according to the first embodiment includes, for example, a front imaging optical system (for example, imaging optical system 30), an OCT optical system (for example, OCT optical system 200), and a control unit (for example, A control unit 70) (see FIG. 2). The front imaging optical system includes, for example, a first focusing optical member (for example, a focusing lens 32) and a light receiving element (for example, an imaging element 35 and an observation imaging element 38). The first focusing optical member is moved in the optical axis direction by, for example, a first driving unit (for example, the driving unit 49). For example, the light receiving element receives reflected light from the fundus via the first focusing optical member. For example, the front imaging optical system acquires a front image of the fundus of the eye to be examined based on an output signal from the light receiving element.

  The OCT optical system includes, for example, a second focus optical member (for example, focusing lens 124), a measurement optical path, a reference optical path, and a detector (for example, detector 120). The second focusing optical member is moved in the optical axis direction by, for example, a second driving unit (for example, the driving unit 124a). The measurement optical path includes a second focus optical member and guides the measurement light to the fundus of the eye to be examined. The reference light path generates reference light, for example. The detector detects a detection signal including an interference signal between the measurement light guided to the eye to be examined through the measurement optical path and the reference from the reference optical path. The OCT optical system acquires a tomographic image of the fundus oculi based on an output signal from the detector.

  The control unit can execute, for example, first autofocus control and second autofocus control. In the first autofocus control, for example, the control unit acquires first in-focus position information based on a light reception signal output from the light receiving element. The first focus position information is, for example, focus position information with respect to the fundus of the front imaging optical system. Then, the control unit moves the first focus optical member and the second focus optical member obtained from the first focus position information to the focus position. The control unit may obtain the in-focus position of the first focus optical member and the in-focus position of the second focus optical member from the first focus position information.

  In the second autofocus control, for example, the control unit acquires second focus position information based on an output signal from the detector. The second focus position information is, for example, a focus position with respect to the fundus of the OCT optical system. Then, the control unit moves the second focus optical member to the in-focus position.

  The control unit includes a determination unit (for example, the control unit 70 may also be used). For example, the determination unit determines whether the first autofocus control is successful. For example, the control unit may execute the first autofocus control first, and may execute the second autofocus control according to the test result of the determination unit.

  As described above, the focus adjustment of the OCT optical system can be smoothly performed by using the front photographing optical system, and when the focus fails, the focus adjustment is surely performed by using the output signal of the OCT optical system. Can be done.

  If the determination unit determines that the first autofocus control is successful, the second autofocus control is not executed. If the first autofocus is determined to be unsuccessful, the second autofocus control is executed. Good.

  In the second autofocus control, the control unit may move the second focus optical member to a plurality of positions and acquire second focus position information based on the light reception signals at each position.

  The front imaging optical system may be, for example, an IR imaging system (infrared imaging optical system) or an SLO imaging system (such as a scanning laser ophthalmoscope).

  The front imaging optical system may be provided with an index projection optical system for projecting a focus index on the fundus of the eye to be examined. In this case, the control unit may acquire the first focus position information based on the focus index received by the light receiving element in the first autofocus control.

  Note that the control unit may acquire the first in-focus position information based on, for example, a front image captured by the front imaging optical system. In this case, an evaluation value for detecting the focus state of the eye to be inspected with respect to the front imaging optical system is calculated based on the front image, and the focus of the first focus optical member and the second focus optical member is calculated from the evaluation value. The position may be obtained. Note that the evaluation value may be at least one of a histogram, a peak position, a luminance distribution, and the like (see, for example, JP 2009-291252 A).

  Note that, when evaluating the light reception signal output from the detector, the control unit may acquire the second in-focus position information based on at least one of a tomographic image, an interference signal, or the like, for example. In this case, an evaluation value for detecting the focus state of the eye to be examined with respect to the OCT optical system is calculated based on at least one of the tomographic image and the interference signal, and the focus position of the second focusing optical member is calculated from the evaluation value. You may ask for. Note that the evaluation value may be at least one of a histogram, a peak position, a luminance distribution, and the like (see, for example, JP 2009-291252 A and JP 2012-213489 A).

  Note that the control unit may control whether to execute the second autofocus control, for example, according to the determination result of the determination unit. Furthermore, the control unit performs only fine adjustment when the determination unit determines that the first autofocus control is successful, and performs rough adjustment using the OCT signal when it is determined that the control has failed. Good.

  Note that the control unit may execute the second autofocus control when it is determined as failure without executing the second autofocus control when it is determined as successful in the determination result of the determination unit. As a result, when it is determined to be successful, the second autofocus control can be skipped, so the time can be shortened. On the other hand, when it is determined that the failure has occurred, the second autofocus control can be executed, so that reliable focusing can be performed.

  The front imaging optical system may be provided with an index projection optical system (for example, the focus index projection optical system 40) for projecting a focus index on the fundus of the eye to be examined. In this case, the control unit may acquire the first focus position information based on the focus index received by the light receiving element in the first autofocus control. Thus, the first autofocus control can be performed in a short time by focus detection using the focus index.

  Note that the determination unit may determine that the first autofocus control is successful when the position of the focus index can be detected. Furthermore, the determination unit may determine that the first autofocus control has failed when the position of the focus index cannot be detected.

  In the second autofocus control, the control unit may further move the first focus optical member to the in-focus position. As a result, the focus of the front photographing optical system is adjusted using the signal from the front photographing optical system, and when the focus fails, the focus of the front photographing optical system is adjusted using the interference signal from the detector of the OCT optical system. It can be carried out.

  Furthermore, the ophthalmologic photographing apparatus may include, for example, an instruction receiving unit (for example, the operation unit 74). The instruction receiving unit receives, for example, an instruction from an examiner for moving the first focus optical member in the optical axis direction. In this case, the control unit may drive the first drive unit independently of the second drive unit based on the instruction signal from the instruction receiving hand unit. As a result, when the first autofocus control fails, the position of the first focus optical member can be manually adjusted independently, so that reliable focus adjustment can be performed.

  The ophthalmologic photographing apparatus may include, for example, an optical member for adjusting an optical path length (for example, the reference mirror 131). The optical member for adjusting the optical path length is disposed, for example, in the measurement optical path or the reference optical path in order to adjust the optical path length difference between the measurement light and the reference light. Furthermore, the optical member for adjusting the optical path length is moved by, for example, a third drive unit (for example, the drive unit 150). In this case, the control unit determines the position of the optical path length adjusting optical member from which the tomographic image of the fundus of the eye to be examined is acquired before the second focusing optical member is moved by the first autofocus control or the second autofocus control. The search may be performed based on the output signal from the detector.

  For example, after the second focusing optical member is moved to the in-focus position by the second autofocus control, the control unit re-adjusts the position of the optical path length adjusting optical member based on the output signal from the detector. You may adjust.

  The control unit may display the first in-focus position information and the second in-focus position information independently on the display unit.

Second Embodiment
Hereinafter, an outline of the second embodiment of the ophthalmologic photographing apparatus will be described. An ophthalmic imaging apparatus (see FIG. 1) 1 according to the second embodiment includes, for example, a front imaging optical system (for example, imaging optical system 30), an OCT optical system (for example, OCT optical system 200), and a control unit (for example, A control unit 70) is mainly provided. The front imaging optical system and the OCT optical system can use the same configuration as in the first embodiment. For example, the control unit can independently execute the first autofocus control and the second autofocus control described in the first embodiment. As a result, the auto-focusing of the front photographing optical system and the auto-focusing of the OCT optical system are executed independently, so that each optical system can be optimized smoothly.

  Note that as the independent control, the control unit does not depend on the output signal from the light receiving element of the front imaging optical system, including rough adjustment (first optical path length adjustment) in the position control of the second focus optical member. There may be.

  In the second autofocus control, coarse adjustment and fine adjustment of the second focus optical member may be performed based on an output signal from the detector.

  The control unit may execute the first autofocus control and the second autofocus control in parallel. Thereby, each optical member can be smoothly moved to the in-focus position.

  In the second autofocus control, the control unit may perform rough adjustment and fine adjustment of the second focus optical member based on the output signal from the detector.

  The front imaging optical system may be provided with an index projection optical system for projecting a focus index on the fundus of the eye to be examined. In this case, the control unit may acquire the first focus position information based on the focus index received by the light receiving element in the first autofocus control.

  Note that the ophthalmologic photographing apparatus may include an instruction receiving unit (for example, the operation unit 74). The instruction receiving unit receives, for example, an instruction from an examiner for moving the first focus optical member and the second focus optical member in the optical axis direction. In this case, the control unit may drive the first driving unit (for example, the driving unit 49) and the second driving unit (for example, the driving unit 124a) in conjunction with each other based on the instruction signal from the instruction receiving unit. Thus, after each optical member is moved to the in-focus position by the first autofocus control and the second autofocus control, in the manual adjustment, each optical member is moved in conjunction with each other so that the focus is finely adjusted. Adjustment can be performed smoothly.

  The control unit may drive the first driving unit and the second driving unit independently based on an instruction signal from the instruction receiving unit.

  The control unit may switch between interlocking control and independent control. The interlock control is, for example, control for driving the first drive unit and the second drive unit in conjunction with each other based on an instruction signal from the instruction receiving unit. Independent control is control which drives a 1st drive part and a 2nd drive part independently, for example based on an instruction signal from an instruction reception part. By switching between interlocking control and independent control, manual independent control and manual interlocking control can be used properly according to circumstances.

  Note that the control unit may include a determination unit (for example, the control unit 70 may also be used). The determination unit may determine whether the first autofocus control is successful. In this case, if it is determined that the first autofocus control has failed, the control unit may move the first focus optical member to the focus position based on the second focus position information. Thereby, even if the first autofocus control is unsuccessful, reliable focus adjustment can be performed by using the OCT signal.

  The determination unit may determine whether the second autofocus control is successful. In this case, when it is determined that the second autofocus control has failed, the second focus optical member may be moved to the focus position based on the first focus position information. Thereby, even if the second autofocus control is unsuccessful, reliable focus adjustment can be performed by using the output signal of the front photographing optical system.

<Example>
Embodiments according to the present invention will be described below with reference to the drawings. 1 to 10 are diagrams illustrating the configuration of the ophthalmologic photographing apparatus according to the present embodiment. In the present embodiment, the axial direction of the subject's eye (eye E) will be described as the Z direction, the horizontal direction as the X direction, and the vertical direction as the Y direction. The surface direction of the fundus may be considered as the XY direction.

  As shown in FIG. 1, the ophthalmologic photographing apparatus 1 according to the present embodiment mainly includes, for example, a base 4, a photographing unit 3, a face support unit 5, and an operation unit 74. The photographing unit 3 may house an optical system described later. The imaging unit 3 may be provided so as to be movable in a three-dimensional direction (XYZ) with respect to the eye E. The face support unit 5 may be fixed to the base 4 in order to support the subject's face.

  The imaging unit 3 may be moved relative to the eye E in the left-right direction, the up-down direction (Y direction), and the front-rear direction by the XYZ drive unit 6.

  The joystick 74a is used as an operation member operated by the examiner to move the photographing unit 3 with respect to the eye E. Of course, it is not limited to the joystick 74a, and may be another operation member (for example, a touch panel, a trackball, etc.).

  For example, the operation unit once transmits an operation signal from the examiner to the control unit 70. In this case, the control unit 70 may send an operation signal to the personal computer 90 described later. For example, the personal computer 90 sends a control signal corresponding to the operation signal to the control unit 70. For example, when the control unit 70 receives the control signal, the control unit 70 may perform various controls based on the control signal.

  For example, the movable table 2 is moved relative to the eye to be examined by operating the joystick 74a. Further, by rotating the rotary knob 74b, the XYZ driving unit 6 is driven and the photographing unit 3 is moved in the Y direction.

  The imaging unit 3 may be provided with a display unit 75 (for example, the examiner side). The display unit 75 may display, for example, a fundus observation image, a fundus photographing image, and an anterior eye observation image. The display unit 75 may include a touch panel that also serves as the operation unit 74.

  The apparatus main body 1 of this embodiment is connected to a personal computer (hereinafter, PC) 90. For example, a display unit 95, an operation unit (keyboard, mouse, etc.) 96, a control unit 70, and the like may be connected to the PC 90.

<Optical system>
As shown in FIG. 2, the optical system of the present embodiment mainly includes an illumination optical system 10, an imaging optical system (front imaging optical system) 30, and an interference optical system (hereinafter also referred to as OCT optical system) 200. The photographing optical system 30 is used as a fundus camera optical system for obtaining an infrared fundus image, a color fundus image, and the like by photographing the fundus with visible light (for example, a non-mydriatic state). The OCT optical system 200 obtains a tomographic image of the fundus of the eye to be examined non-invasively using an optical interference technique. Further, the optical system may include a focus index projection optical system 40, an alignment index projection optical system 50, and an anterior ocular segment observation optical system 60.

<Illumination optics>
The illumination optical system 10 includes, for example, an observation illumination optical system and a photographing illumination optical system. The photographing illumination optical system mainly includes a light source 14, a condenser lens 15, a ring slit 17, a relay lens 18, a mirror 19, a black spot plate 20, a relay lens 21, a perforated mirror 22, and an objective lens 25. The photographing light source 14 may be a flash lamp or the like. The black spot plate 20 has a black spot at the center.

  The observation illumination optical system mainly includes an optical system from the light source 11, the infrared filter 12, the condenser lens 13, the dichroic mirror 16, and the ring slit 17 to the objective lens 25. The light source 11 may be, for example, a halogen lamp. For example, the infrared filter 12 transmits near infrared light having a wavelength of 750 nm or more. The dichroic mirror 16 is disposed, for example, between the condenser lens 13 and the ring slit 17. Further, the dichroic mirror 16 has a characteristic of reflecting light from the light source 11 and transmitting light from the photographing light source 14, for example.

<Photographing optical system>
The photographing optical system (front photographing optical system) 30 mainly includes, for example, an objective lens 25, a photographing diaphragm 31, a focusing lens 32, an imaging lens 33, and an image sensor 35. The photographing aperture 31 is located in the vicinity of the aperture of the perforated mirror 22. The focusing lens 32 is movable in the optical axis direction. The image sensor 35 can be used for imaging having sensitivity in the visible range, for example. For example, the photographing aperture 31 is disposed at a position substantially conjugate with the pupil of the eye E with respect to the objective lens 25. The focusing lens 32 is moved in the optical axis direction by a moving mechanism 49 including a motor, for example.

  A dichroic mirror 37 having a characteristic of reflecting part of infrared light and visible light and transmitting most of visible light is disposed between the imaging lens 33 and the image sensor 35. In the reflection direction of the dichroic mirror 37, an imaging device for observation 38 having sensitivity in the infrared region is disposed. Instead of the dichroic mirror 37, a flip-up mirror may be used. For example, the flip-up mirror is inserted into the optical path during fundus observation, and is retracted from the optical path during fundus imaging.

  In addition, between the objective lens 25 and the perforated mirror 22, for example, an insertable / detachable dichroic mirror (wavelength selective mirror) 24 as an optical path branching member is provided obliquely. The dichroic mirror 24 reflects, for example, the wavelength light of the OCT measurement light and the wavelength light (center wavelength 940 nm) of the alignment index projection optical system 50 and the anterior ocular segment illumination light source 58.

  The dichroic mirror 24 has a characteristic of transmitting a wavelength of 900 nm or less including the light source wavelength (center wavelength 880 nm) of the wavelength light of the fundus observation illumination, for example. When photographing is performed by the photographing optical system 30, the dichroic mirror 24 is flipped up by the insertion / removal mechanism 66 and retracted out of the optical path. The insertion / removal mechanism 66 can be composed of a solenoid and a cam.

  Further, the optical path correction glass 28 is disposed on the image pickup element 35 side of the dichroic mirror 24 so as to be able to be flipped up by driving the insertion / removal mechanism 66. When the optical path is inserted, the optical path correction glass 28 has a role of correcting the position of the optical axis L1 shifted by the dichroic mirror 24.

  The light beam emitted from the observation light source 11 is converted into an infrared light beam by the infrared filter 12 and reflected by the condenser lens 13 and the dichroic mirror 16 to illuminate the ring slit 17. The light transmitted through the ring slit 17 reaches the perforated mirror 22 through the relay lens 18, the mirror 19, the black spot plate 20, and the relay lens 21. The light reflected by the perforated mirror 22 passes through the correction glass 28 and the dichroic mirror 24, and once converges near the pupil of the eye E to be examined by the objective lens 25, and then diffuses to illuminate the fundus of the eye to be examined.

  Reflected light from the fundus is obtained through an imaging element 38 via an objective lens 25, a dichroic mirror 24, a correction glass 28, an aperture of a perforated mirror 22, an imaging aperture 31, a focusing lens 32, an imaging lens 33, and a dichroic mirror 37. To form an image. The output of the image sensor 38 is input to the control unit 70, and the control unit 70 displays a fundus observation image of the eye to be inspected imaged by the image sensor 38 on the display unit 75 (see FIG. 3).

  Further, the light beam emitted from the photographing light source 14 passes through the dichroic mirror 16 via the condenser lens 15. Thereafter, the fundus is illuminated with visible light through the same optical path as the illumination light for fundus observation. Then, the reflected light from the fundus is imaged on the image sensor 35 through the objective lens 25, the opening of the perforated mirror 22, the imaging aperture 31, the focusing lens 32, and the imaging lens 33.

<Focus index projection optical system>
The focus index projection optical system 40 mainly includes an infrared light source 41, a slit index plate 42, two declination prisms 43, a projection lens 47, and a spot mirror 44 obliquely provided in the optical path of the illumination optical system 10. The two declination prisms 43 are attached to the slit target plate 42. The spot mirror 44 is provided obliquely in the optical path of the illumination optical system 10. The spot mirror 44 is fixed to the tip of the lever 45. The spot mirror 44 is normally inclined to the optical axis, but is retracted out of the optical path by rotation of the rotary solenoid 46 at a predetermined timing before photographing.

  The spot mirror 44 is arranged at a position conjugate with the fundus of the eye E. The light source 41, the slit indicator plate 42, the deflection prism 43, the projection lens 47, the spot mirror 44 and the lever 45 are moved in the optical axis direction by the moving mechanism 49 in conjunction with the focusing lens 32. Further, the light flux of the slit index plate 42 of the focus index projection optical system 40 is reflected by the spot mirror 44 via the deflection prism 43 and the projection lens 47, and then the relay lens 21, the perforated mirror 22, the dichroic mirror 24, The light is projected onto the fundus of the eye E through the objective lens 25. When the fundus is out of focus, the focus index images (hereinafter sometimes abbreviated as index images) S1 and S2 are projected onto the fundus in a state of being separated according to the shift direction and shift amount (see FIG. 3 (a)). On the other hand, when the focus is achieved, the index images S1 and S2 are projected onto the fundus in a matched state (see FIG. 3B). The index images S1 and S2 are taken together with the fundus image by the image sensor 38.

<Alignment index projection optical system>
The alignment index projection optical system 50 projects an alignment index beam onto the eye E. In the alignment index projection optical system 50, as shown in the diagram in the lower left dotted line in FIG. 2, a plurality of infrared light sources are arranged at 45 degree intervals on a concentric circle with the photographing optical axis L1 as the center. The ophthalmologic photographing apparatus in the present embodiment mainly includes a first target projection optical system (0 degrees and 180) and a second target projection optical system.

  The first target projection optical system has an infrared light source 51 and a collimating lens 52. The second target projection optical system is arranged at a position different from the first index projection optical system and has six infrared light sources 53. The infrared light sources 51 are arranged symmetrically with respect to a vertical plane passing through the photographing optical axis L1.

  In this case, the first index projection optical system projects an index at infinity on the cornea of the eye E from the left-right direction. The second index projection optical system is configured to project a finite index on the cornea of the eye E from the vertical direction or the oblique direction. In FIG. 2, for convenience, the first index projection optical system (0 degrees and 180 degrees) and only a part of the second index projection optical system (45 degrees and 135 degrees) are shown. .

<Anterior segment observation optical system>
An anterior ocular segment observation (imaging) optical system 60 that images the anterior segment of the eye E to be examined is provided on the reflection side of the dichroic mirror 24 with a dichroic mirror 61, a diaphragm 63, a relay lens 64, and a two-dimensional imaging element (light receiving element: , Which may be abbreviated as “image sensor 65”). The image sensor 65 has infrared sensitivity. The imaging element 65 also serves as an imaging means for detecting the alignment index, and the anterior segment illuminated by the anterior segment illumination light source 58 that emits infrared light and the alignment index are imaged. The anterior segment illuminated by the anterior segment illumination light source 58 is received by the image sensor 65 from the objective lens 25, the dichroic mirror 24, and the dichroic mirror 61 through the optical system of the relay lens 64. Further, the alignment light beam emitted from the light source of the alignment index projection optical system 50 is projected onto the eye cornea to be examined. The cornea reflection image is received (projected) on the image sensor 65 through the objective lens 25 to the relay lens 64.

  The output of the two-dimensional image sensor 65 is input to the control unit 70, and the anterior segment image captured by the two-dimensional image sensor 65 is displayed on the display unit 75 as shown in FIG. The anterior ocular segment observation optical system 60 also serves as a detection optical system for detecting the alignment state of the apparatus main body with respect to the eye to be examined.

<OCT optical system>
Returning to FIG. The OCT optical system 200 has a device configuration of a so-called ophthalmic optical coherence tomography (OCT) and takes a tomographic image of the eye E. The OCT optical system 200 divides light emitted from the measurement light source 102 into measurement light and reference light by a coupler (light splitter) 104. The OCT optical system 200 guides the measurement light to the fundus oculi Ef of the eye E, and guides the reference light to the reference optical system 110. The measurement light reaches the scanning unit 108 via the collimator lens 123 and the focus lens 124, and the reflection direction is changed by driving two galvanometer mirrors, for example. Then, the measurement light reflected by the scanning unit 108 is reflected by the dichroic mirror 24 via the relay lens 109 and then condensed on the eye fundus via the objective lens 25. Thereafter, the detector (light receiving element) 120 receives the interference light obtained by combining the measurement light reflected by the fundus oculi Ef and the reference light.

  The detector 120 detects an interference state between the measurement light and the reference light. In the case of Fourier domain OCT, the spectral intensity of the interference light is detected by the detector 120, and a depth profile (A scan signal) in a predetermined range is obtained by Fourier transform on the spectral intensity data. Examples include Spectral-domain OCT (SD-OCT) and Swept-source OCT (SS-OCT). In the case of Spectral-domain OCT (SD-OCT), for example, a broadband light source is used as the light source 102, and a spectrometer (spectrometer) is used as the detector 120. In the case of Swept-source OCT, for example, a variable wavelength light source is used as the light source 102, and a single photodiode is used as the detector 120 (balance detection may be performed). Moreover, Time-domain OCT (TD-OCT) may be used.

  The scanning unit 108 scans light emitted from the measurement light source on the fundus of the eye to be examined. For example, the scanning unit 108 scans the measurement light two-dimensionally (XY direction (transverse direction)) on the fundus. The scanning unit 108 is disposed at a position substantially conjugate with the pupil. The scanning unit 108 is, for example, two galvanometer mirrors, and the reflection angle thereof is arbitrarily adjusted by the driving unit 151.

  Thereby, the reflection (advance) direction of the light beam emitted from the light source 102 is changed and scanned in an arbitrary direction on the fundus. As a result, the imaging position on the fundus oculi Ef is changed. The scanning unit 108 may be configured to deflect light. For example, in addition to a reflective mirror (galvano mirror, polygon mirror, resonant scanner), an acousto-optic device (AOM) that changes the traveling (deflection) direction of light is used.

  The reference optical system 110 generates reference light that is combined with reflected light acquired by reflection of measurement light at the fundus oculi Ef. The reference optical system 110 may be a Michelson type or a Mach-Zehnder type.

  The reference optical system 110 may change the optical path length difference between the measurement light and the reference light by moving the optical member in the reference light path. For example, the reference mirror is moved in the optical axis direction. The configuration for changing the optical path length difference may be arranged in the measurement optical path of the measurement optical system.

  More specifically, the reference optical system 110 mainly includes, for example, a collimator lens 129, a reference mirror 131, and a reference mirror driving unit 150. The reference mirror driving unit 150 is disposed in the reference optical path and is configured to be movable in the optical axis direction so as to change the optical path length of the reference light. The light is reflected by the reference mirror 131 and returned to the coupler 104 again and guided to the detector 120. As another example, the reference optical system 110 is formed by a transmission optical system (for example, an optical fiber), and guides the light from the coupler 104 to the detector 120 by transmitting the light without returning.

<Control unit>
Next, the control system of this embodiment will be described. The control unit 70 of the present embodiment includes an imaging device 65 for observing the anterior segment, an imaging device 38 for observing the infrared fundus, a display unit 75, an operation unit 74, each light source, and various driving units. The image sensor 35 and the PC 90 are connected. In order to avoid complication, in FIG. 2, the lines indicating the connection between the image sensor 65, each light source, various driving units, and the control unit 70 are omitted.

  The control unit 70 displays the anterior ocular segment observation image captured by the imaging element 65 and the infrared fundus observation image captured by the imaging element 38 on the display unit 75 of the main body.

  The PC 90 includes a CPU as a processor, a memory (nonvolatile memory) as a storage unit, and the like. The PC 90 is connected to an operation unit (for example, a mouse, a keyboard, etc.) 96, a display unit 95, and the like. The PC 90 may transmit a control signal for controlling the ophthalmologic photographing apparatus 1 to the control unit 70. The memory of the PC 90 is a non-transitory storage medium that can retain stored contents even when power supply is interrupted. For example, a hard disk drive, a flash ROM, a USB memory detachably attached to the PC 90, an external server, or the like can be used as the memory. The memory stores an imaging control program for controlling imaging of front images and tomographic images by the ophthalmologic imaging apparatus 1.

  The PC 90 (more specifically, the processor (for example, CPU) of the PC 90 may acquire the light reception signal from the detector 120 via the control unit 70. Then, the PC 90 receives the light reception signal from the detector 120). A tomographic image may be generated by arithmetic processing.

  For example, in the case of Fourier domain OCT, the PC 90 processes a spectrum signal including an interference signal at each wavelength output from the detector 120. The PC 90 processes the spectrum signal to obtain internal information of the eye to be examined (for example, data of the eye to be examined (depth information) regarding the depth direction). More specifically, the spectrum signal (spectrum data) is converted into a function I (k) that is equally spaced with respect to the wave number k (= 2π / λ). The PC 90 obtains a signal distribution in the depth (Z) region by Fourier-transforming the spectrum signal in the wave number k space.

<Control action>
The control operation of the apparatus having the above configuration will be described. Here, the control unit 70 drives and controls the OCT optical system 200 and the imaging optical system 30 to acquire the OCT image and the infrared fundus image for each frame. The control unit 70 controls the display of the monitor 75 and updates the OCT image and the infrared fundus image on the monitor 75 as needed. Note that, for example, a scanning position (for example, the X direction) based on the center position of the infrared fundus image is set as the acquisition position of the first OCT image that is not set by the examiner.

  FIG. 5 is a flowchart showing the flow of operations in the present apparatus. The examiner instructs the subject to watch the fixation target of the fixation target projection unit (not shown), and then looks at the anterior eye portion observation image photographed by the imaging element 65 on the monitor 75 while viewing the eye of the subject eye. An alignment operation is performed by using the operation unit 74 so that the measurement optical axis comes to the center of the pupil. When the alignment with respect to the eye E is thus completed, a front image (infrared fundus image) of the fundus of the eye to be inspected by the imaging optical system 30 is acquired, and the infrared fundus image is displayed on the display unit 75. appear.

  Next, by optimizing the imaging conditions, the OCT optical system 200 enables the fundus site desired by the examiner to be observed with high sensitivity and high resolution. In the present embodiment, the optimization control of the OCT optical system 200 is control of optical path length adjustment, focus adjustment, and polarization state adjustment (polarizer adjustment).

  The examiner presses an optimization start switch (Optimize switch) 74 c arranged on the operation unit 74. When an operation signal is issued from the optimization start switch 74c, the control unit 70 issues a trigger signal for starting optimization control, and starts optimization.

  When the examination switch (not shown) is pushed by the examiner after the optimization is completed, a fundus tomographic image is taken and stored in the memory.

<Optimization control>
FIG. 6 is a diagram illustrating an example of optimization control according to the present embodiment. Generally, the control unit 70 sets the positions of the reference mirror 131 and the focusing lens 124 to the initial positions as initialization control. After the initialization is completed, the control unit 70 moves the reference mirror 131 in one direction from the set initial position in a predetermined step to perform the first optical path length adjustment (first automatic optical path length adjustment). If a fundus tomographic image has already been acquired, the initialization, the first optical path length adjustment, and the like need not be performed.

  Further, in parallel with the first optical path length adjustment, the control unit 70 adjusts the focus of the imaging optical system 30 with respect to the eye to be inspected (first) based on the infrared fundus image acquired by the light reception signal output from the image sensor 38. 1 focus adjustment).

  When the focus adjustment of the photographing optical system 30 based on the infrared fundus image is successful, the control unit 70 performs the focus adjustment (second focus adjustment) of the OCT optical system 200 based on the focus information of the photographing optical system 30.

  On the other hand, when the focus adjustment of the imaging optical system 30 based on the infrared fundus image fails, the control unit 70 adjusts the focus of the OCT optical system 200 with respect to the eye to be examined (first) based on the OCT signal detected by the detector 120. 3 focus adjustment).

  Note that the in-focus position may be a position where the contrast of the tomographic image acceptable as the observation image can be acquired, and is not necessarily the optimum position in the focus state.

  Then, after the focus adjustment is completed, the control unit 70 moves the reference mirror 131 again in the optical axis direction, and performs the second optical path length adjustment for readjustment of the optical path length (fine adjustment of the optical path length). After completing the second optical path length adjustment, the control unit 70 drives the polarizer 133 for adjusting the polarization state of the reference light, and adjusts the polarization state of the measurement light.

  Hereinafter, an example of optimization control will be described in detail.

<Evaluation value>
In the present embodiment, the first automatic optical path length adjustment and the polarizer adjustment are performed by detecting the signal intensity of the tomographic image. In the following description, a predetermined evaluation value B is used as an index indicating the signal strength.

  The evaluation value B is obtained from the equation B = ((average maximum luminance value of the image) − (average luminance value of the background area of the image)) / (standard deviation of the luminance value of the background area). The control unit 70 acquires the luminance distribution data of the tomographic image based on the output signal from the detector 120. For example, FIG. 7 is a diagram illustrating an image displayed on the screen of the display unit 75 when the reference mirror 131, the focusing lens 124, and the polarizer 133 are disposed at predetermined positions.

  First, the control unit 70 sets a plurality of scanning lines to be scanned in the depth direction (A scanning direction), and obtains luminance distribution data on each scanning line. In FIG. 7, the image is divided into ten, and ten dividing lines are used as scanning lines. FIG. 8 is a diagram illustrating a change in luminance distribution in the depth direction of an image.

  Here, the control unit 70 calculates the maximum luminance value (hereinafter, abbreviated as the maximum luminance value) from the luminance distribution corresponding to each scanning line. And the control part 70 calculates the average value of the maximum luminance value in each scanning line as the maximum luminance value in a fundus tomographic image. And the control part 70 calculates the average value of the luminance value of the background area | region in each scanning line as an average luminance value of the background area | region in a fundus tomographic image.

  Thus, the calculated evaluation value B is used in the first automatic optical path length adjustment and the polarizer adjustment. In this case, it is preferable to calculate the evaluation value B in the tomographic image in the image data G1.

<Initialization>
First, the control unit 70 controls initialization. In the initialization control, the positions of the reference mirror 131 and the focusing lens 124 are moved to the initial position (movement start position).

  When the initialization control is started, the control unit 70 selects, for example, either the movement limit position K1 or the movement limit position K2 illustrated in FIG. 2 as the initial position of the reference mirror 131. The initial position is determined by selecting a position closer to the movement limit position K1 or the movement limit position K2 from the position of the reference mirror 131 before the initialization control is started. Then, the control unit 70 moves the reference mirror 131 to the initial position of the movement limit position K1 or the movement limit position K2. Of course, the moving direction for setting the initial position may be determined based on different criteria. Note that the initial position (movement start position) may be set based on an eye axis length input in advance.

  Further, the control unit 70 moves the focusing lens 124 to an initial position (a position corresponding to 0D in the present embodiment).

  When the reference mirror 131 and the focusing lens 124 are moved to the initial positions, the control unit 70 starts the first optical path length adjustment and the focus adjustment. Hereinafter, the control operation of each adjustment will be described.

<First automatic optical path length adjustment (coarse adjustment)>
The first automatic optical path length adjustment (automatic coarse optical path length adjustment) will be described. The control unit 70 controls the drive of the drive mechanism 150 to move the reference mirror 131 and acquires a fundus tomographic image based on output signals output from the detector 120 at each position of the reference mirror 131. The reference mirror 131 is moved to the position.

  Specifically, after acquiring the tomographic image at the initial position, the control unit 70 moves the reference mirror 131 toward the movement limit position opposite to the initial position. For example, when the limit position K1 is selected (set) as the initial position of the reference mirror 131, the reference mirror 131 is moved in the direction toward the limit position K2.

  Here, the control unit 70 moves the reference mirror 131 in predetermined steps (for example, a 2 mm step as an imaging range), sequentially acquires tomographic images at each moving position, and determines the position at which the fundus tomographic image is acquired. I will explore.

  In this case, the control unit 70 acquires a tomographic image every time the reference mirror 131 is stopped at the moving positions of the reference mirror 131 set discretely. Then, the control unit 70 analyzes the tomographic image acquired at each position. For example, the control unit 70 calculates the evaluation value B of the tomographic image acquired at each position. Then, the control unit 70 stores the position of the reference mirror 131 and the evaluation value B of the tomographic image in a memory in association with each other.

  Here, the control unit 70 detects the peak of the evaluation value B from the obtained calculation result of the evaluation value B for each position of the reference mirror 131. Then, the control unit 70 stores the position of the reference mirror 131 corresponding to the peak detection position in the memory. Then, the control unit 70 moves the reference mirror 131 to a position corresponding to the peak of the evaluation value B.

  When the optical path length is roughly adjusted as described above, at least a part of the fundus tomographic image is displayed at any position on the monitor 72.

<First focus control>
In parallel with the first automatic optical path length adjustment (automatic coarse optical path length adjustment), the control unit 70 detects the in-focus position and moves the lens 32 based on the detection result. The control unit 70 issues a trigger signal for starting control of focus adjustment, and starts focus adjustment of the photographing optical system 30.

  FIG. 3 is an example of an infrared fundus image captured by the image sensor 38, and focus index images S1 and S2 by the focus target projection optical system 40 are projected at the center of the fundus image. Here, the focus index images S1 and S2 are separated when the focus is not achieved (see FIG. 3A), and are projected in conformity when the focus is achieved (see FIG. 3B). The control unit 70 detects the index images S1 and S2 by image processing and obtains separation information thereof. Then, the control unit 70 controls the driving of the moving mechanism 49 based on the separation information of the index images S1 and S2, and moves the lens 32 so that the fundus is in focus.

  Next, the control unit 70 moves the focusing lens 124 of the OCT optical system 200 based on the focus position information of the imaging optical system 30 based on the output signal from the image sensor 38. In this case, the control unit 70 may start the movement of the focusing lens 124 after the movement of the focusing lens 32 to the in-focus position is completed in the first focus control. Alternatively, the control unit 70 starts the movement of the focusing lens 124 with the timing at which the focusing position information of the photographing optical system 30 is detected before the movement of the focusing lens 32 to the focusing position is completed. May be.

  More specifically, the control unit 70 acquires the focus position information of the OCT optical system 200 based on the focus position information of the imaging optical system 30, and moves the focusing lens 124 to the focus position (automatic operation for the OCT image). focus). Here, for example, the control unit 70 acquires the moving position of the focusing lens 32 as focusing position information of the OCT optical system 200, and controls the driving mechanism 124a based on the focusing position information to control the focusing lens 124. Move to the in-focus position.

  For example, if the focus position of the photographic optical system 30 is a position corresponding to −3D, the focus position of the OCT optical system 200 is similarly controlled to be a position corresponding to −3D. In this case, the diopter conversion is performed between the moving position of the focusing lens 32 and the moving position of the focusing lens 124 so that the focus position of the OCT optical system 200 can be set to a focus position corresponding to the in-focus position of the imaging optical system 30. Correspondence is made. The control unit 70 may adjust the focus of the OCT optical system 200 using the focus detection result (for example, the separation amount of the index images S1 and S2) as the focus position information of the imaging optical system 30. . For example, when the focus position of the imaging optical system 30 is a position corresponding to −3D, the focus position of the OCT optical system 200 may not be −3D, and a numerical value obtained by adding a correction value to −3D. A corresponding in-focus position may be used.

  Thus, when the focusing lens 124 of the OCT optical system 200 is moved to the focus position based on the first focus control, the fundus reflection light incident on the fiber end 39b increases, and a signal with a higher intensity is generated. Detected.

<Determining success or failure of first focus control>
When the first focus control ends, the control unit 70 determines whether the first focus control has succeeded or failed. For example, when focusing is performed using the index images S1 and S2 as described above, when the subject's eye is a small pupil, when photographing the fundus peripheral position (peripheral photographing), when photographing the luminous flux by the iris or the like There is a possibility that part of the light is shielded (vignetted). As a result, if one of the index images S1 and S2 projected onto the fundus is missing, the focusing operation using the index images S1 and S2 may not be performed. Further, not only when the index images S1 and S2 are used as described above, but also when other focusing methods are used, there is a possibility that the focusing information of the imaging optical system 30 cannot be acquired due to cloudiness of the eye to be examined. Conceivable.

  For example, the control unit 70 determines success / failure based on whether or not focus information on the fundus of the imaging optical system 30 has been acquired based on an imaging signal from the imaging element 38.

  More specifically, for example, the control unit 70 detects that the index images S1 and S2 are not detected by image processing (for example, the bright spot analysis of the index images S1 and S2), or the index images S1 and S2 are detected. However, when the indicators S1 and S2 cannot reach the coincidence state (for example, in the case of intensity myopia and intensity hyperopia), it is determined that the first focus control has failed.

  When the index images S1 and S2 are not detected from the light reception signal and the focusing operation cannot be performed, the control unit 70 determines that the photographing optical system is not in focus and performs the second focus control process. Proceed to

<First focus control: failure>
When it is determined that the first focus control is unsuccessful, the control unit 70 acquires the focus position information of the OCT optical system 200 based on the tomographic image acquired by the OCT optical system 200, and moves the focusing lens 124 to the focus position. (Second focus control).

  More specifically, the control unit 70 moves the focusing lens 124 to the in-focus position with respect to the fundus of the subject's eye based on the output signal output from the light receiving element 83 through the first automatic optical path length adjustment.

  For example, the control unit 70 controls the driving of the driving unit 124a and moves the lens 124 in a predetermined step from a predetermined initial position. Then, the control unit 70 sequentially acquires tomographic images at each moving position, and searches for an in-focus position (a position where the fundus tomographic image is in focus).

  For example, the control unit 70 moves the lens 124 by 0.5D toward a certain movement limit position, and moves the lens 124 in the opposite direction if the in-focus position is not found. In addition, the movement step of the lens 124 is not limited to this, For example, 1D may be sufficient, 2D may be sufficient, and the structure set arbitrarily may be sufficient.

  In the search for the in-focus position, every time the focusing lens 124 is stopped at a discretely set moving position of the focusing lens 124, an image acquired at that position is analyzed. For example, the control unit 70 calculates the evaluation value B of the tomographic image acquired at each position. Then, the control unit 70 stores the position of the lens 124 and the evaluation value B of the tomographic image in a memory in association with each other.

  Here, the control unit 70 detects the peak of the evaluation value B from the obtained calculation result of the evaluation value B for each position of the focusing lens 124. Then, the control unit 70 moves the focusing lens 124 to a position corresponding to the peak detection position. As described above, the focus adjustment is completed.

  Next, the control unit 70 drives and controls the drive mechanism 124a, and moves the focusing lens 124 to the movement position corresponding to the in-focus position of the OCT optical system 200 acquired as described above, so that the OCT fundus image is obtained. The focus adjustment ends.

<Second automatic optical path length adjustment (fine adjustment)>
When the focusing lens 124 is moved to the in-focus position, the control unit 70 starts the second automatic optical path length adjustment. Based on the output signal output from the light receiving element 83, the control unit 70 readjusts the position of the reference mirror 131 from the position adjusted by the first automatic optical path length adjustment.

  Specifically, when the focus adjustment is completed, the control unit 70 performs the second automatic optical path length adjustment based on the tomographic image acquired by the focus adjustment.

  Here, the control unit 70 determines whether the fundus tomographic image acquired after focus adjustment is a real image or a virtual image. For example, the control unit 70 determines the fundus image as a real image when the half-value width with respect to the peak in the luminance distribution in the depth direction is smaller than a predetermined allowable width, and determines the fundus tomographic image when the half-value width is larger than the predetermined allowable width. Is determined to be a virtual image. Note that the determination of the real / virtual shape of the tomographic image may be any method that uses the difference in image quality between the real image and the virtual image. For example, in addition to the half width, the contrast of the tomographic image, the rising edge of the tomographic image Degree etc. are used. Further, the shape of a fundus tomographic image may be used.

  When the acquired fundus tomographic image is determined to be a virtual image, the control unit 70 moves the reference mirror 131 in the direction in which the real image is acquired (the direction in which the reference light is shortened). For example, the control unit 70 calculates the amount of movement of the reference mirror 131 that makes the amount of deviation from the optical path length matching position (zero delay position) to the image detection position zero, and further refers to twice the calculated amount of movement. The mirror 131 is moved. As a result, only the real image is acquired. In this case, a deviation amount when the reference mirror 131 is moved by a certain amount may be obtained in advance. Accordingly, the control unit 70 can move the reference mirror 131 so that the amount of deviation from the optical path length matching position to the image detection position becomes a predetermined amount of deviation, and the fundus tomographic image is displayed at the predetermined display position. Can be displayed.

  The means for moving the reference mirror 131 is not limited to this. For example, when it is determined as a virtual image, a predetermined offset amount for moving the reference mirror 131 in a direction in which the real image is acquired (a direction in which the reference light is shortened) may be set in advance. Then, when the tomographic image of the fundus is determined to be a virtual image, the control unit 70 may move the reference mirror 131 by a predetermined offset amount.

  When the acquired fundus tomographic image is determined to be a real image, the control unit 70 determines the position of the real image. For example, the control unit 70 regards the position where the peak of the luminance distribution in the depth direction is detected as the image position, calculates the displacement amount between the preset optical path length adjustment position and the image position, and the displacement amount disappears. The reference mirror 131 is moved as described above (see Japanese Patent Application Laid-Open No. 2010-12111).

<Polarizer adjustment>
The control unit 70 drives the polarizer 133 based on the output signal output from the detector 120 after the second automatic optical path length adjustment, and adjusts the polarization state.

  Specifically, the control unit 70 moves the position of the polarizer 133 from the initial position to the movement start position. Note that the initial position of the polarizer 133 is arranged at a midway position between the first movement limit position and the second movement limit position. Note that the movement start position of the polarizer 133 during the polarizer adjustment is the position of the first movement limit position or the second movement limit position.

  The control unit 70 selects and moves the polarizer 133 from either the first movement limit position or the second movement limit position from the midway position. For example, the control unit 70 selects the first movement limit position as the movement start position, and moves the polarizer 133. Then, the control unit 70 moves the polarizer 133 from the first movement limit position toward the second movement limit position. When the movement start position is the second movement limit position, the movement is moved in the direction of the first movement limit position. Then, the image on the screen of the monitor 75 at each moving position is sequentially acquired, and a position where the interference light can be received strongly (a position where the polarization state of the measurement light and the reference light matches) is searched.

  The search for the position where the polarization state matches is performed by analyzing the image acquired at the arrangement position and calculating the evaluation value B every time the polarizer 133 is stopped at the movement position of the polarizer 133 set discretely. .

  The controller 70 moves the polarizer 133 by 5 degrees to the movement limit position opposite to the movement start position. In the present embodiment, the polarizer 133 is moved by 5 °. However, the present invention is not limited to this. For example, it may be 10 °, 20 °, or a configuration that can be arbitrarily set.

  Here, the control unit 70 detects the evaluation value B (peak value) that becomes a peak from the calculation result of the evaluation value B for each position of the acquired polarizer 133, and the position corresponding to the position where the peak value is detected. The heparizer 133 is moved. As described above, the polarizer adjustment is completed.

  As described above, when the optimization control is completed, the OCT fundus image can be smoothly focused. For this reason, it is possible to easily capture an OCT tomographic image at a desired fundus site.

  In this embodiment, the focus adjustment (second focus adjustment) of the OCT optical system 200 based on the separation information of the index images S1 and S2 is the focus adjustment (third focus adjustment) of the OCT optical system 200 based on the evaluation of the tomographic image. Processing is faster than that. Therefore, when the index images S1 and S2 can be detected, it is preferable to adjust the focus of the photographing optical system 30 and the OCT optical system 200 using the separation information of the index images S1 and S2.

  Note that the index images S1 and S2 may not be detected when taking sick eyes. In such a case, in the present embodiment, the focus of the OCT optical system 200 is adjusted based on the evaluation of the tomographic image taken by the OCT optical system 200 (for example, the evaluation value B).

  Therefore, in the present embodiment, focus adjustment is performed in a fast process using the index images S1 and S2 at normal times. However, when the index images S1 and S2 cannot be detected due to disease or the like, focus adjustment based on evaluation of tomographic images is performed. Switch to. Accordingly, for example, focus adjustment can be performed by a suitable method regardless of whether the subject's eye is a normal eye or a diseased eye.

  In this embodiment, when the separation information of the indices S1 and S2 of the fundus front image captured by the imaging optical system 30 cannot be acquired and the focus of the imaging optical system 30 cannot be adjusted, the third focus adjustment is performed. You may adjust the focus of the imaging optical system 30 using the focusing information acquired at that time. For example, the focus of the imaging optical system 30 may be adjusted based on the evaluation of the tomographic image captured by the OCT optical system 200 (for example, the evaluation value B). Thereby, even when the focus adjustment of the photographing optical system 30 based on the front image cannot be performed, the photographing optical system 30 can be focused. Of course, the examiner may adjust the photographing optical system 30 manually.

  The method for detecting the in-focus state of the photographic optical system 30 is not limited to the above method. For example, the accumulated luminance value of the entire fundus image may be used as the imaging state evaluation value, and the position where the accumulated luminance value shows a peak may be detected as the in-focus position, or the image data of the fundus image may be differentiated. The in-focus state may be detected on the basis of the contour image at the time. The in-focus state may be detected based on the infrared fundus image before the differentiation process. In this case, the control unit 70 may determine that the focus of the imaging optical system 30 has failed when no peak is detected or when the evaluation value is low (such as a threshold value or less).

  In the above configuration, the split target is used as the focus index, but the present invention is not limited to this, and a structure for detecting the in-focus state using an index (for example, a ring index or a point index) projected on the fundus Can be used for focus detection. In this case, similarly to the split index, the control unit 70 may determine the success or failure of the first autofocus control by analyzing the index bright spot or the like.

  In the above description, the first focus adjustment and the first optical path length adjustment are performed in parallel, but the present invention is not limited to this. For example, when several seconds (for example, 0.5 seconds) have passed since the first focus adjustment has been started, if the first focus adjustment is not completed, the first optical path length adjustment is performed in parallel, and the first focus is adjusted. If the adjustment is completed, the first optical path adjustment may be started.

  In the present embodiment, when the second shooting or the measurement mode is switched and the shooting is performed again, if the first focus adjustment is already successful, the control unit 70 initializes the first focus adjustment. The second focus adjustment may be performed without performing the above. If the first focus adjustment has already been performed but has failed, the control unit 70 may execute the third focus adjustment.

<Second embodiment>
The second embodiment will be described below with reference to the drawings. The ophthalmologic photographing apparatus according to the second embodiment performs the focus adjustment of the optical system by control different from that of the first embodiment. Since the configuration is the same as that of the first embodiment, the description thereof is omitted, and the same number as that of the first embodiment is used for each configuration.

<Focus control>
In the focus control of the second embodiment, as shown in FIG. 9, for example, the focus of the photographing optical system 30 and the focus of the OCT optical system 200 are adjusted individually. That is, the focus of the imaging optical system 30 and the OCT optical system 200 does not depend on the mutual focus position information.

  For example, the control unit 70 adjusts the focus of the photographing optical system 30. As described above, the control unit 70 drives the first focus optical member 32 by the drive unit 49 so that the index images S1 and S2 match based on the signal of the image sensor 38. Further, the control unit 70 adjusts the focus of the OCT optical system independently of the focus of the imaging optical system 30. For example, as described above, the control unit 70 focuses the OCT optical system based on the output signal from the detector 120. As a reference for focusing, for example, a tomographic image or an interference signal evaluation value is used.

  The focus position in the fundus front image captured by the imaging optical system 30 and the focus position in the fundus tomogram acquired by the OCT optical system 200 do not necessarily match. For this reason, when the focus adjustment is performed on the tomographic image using the in-focus position acquired from the fundus front image, the focus accuracy may not be sufficient.

  Therefore, the focus adjustment of both the fundus front image and the tomographic image can be performed by using the images acquired by the imaging optical system 30 and the OCT optical system 200 as in the second embodiment, and adjusting them independently of each other. Can be done appropriately.

  Note that either the focus of the imaging optical system 30 or the focus of the OCT optical system may be started first or simultaneously. From the viewpoint of shortening the control time, it is preferable to process the focus of the imaging optical system and the focus of the OCT optical system in parallel.

  Note that the control unit 70 may move one of the focusing lens 32 of the photographing optical system 30 and the focusing lens 124 of the OCT optical system 200, which are individually adjusted, in conjunction with each other. For example, when adjusting the focus of the photographing optical system 30 manually after adjusting the photographing optical system 30 and the OCT optical system 300 individually, the focusing lens 124 may be interlocked according to the movement of the focusing lens 32. At this time, it is preferable that correspondence between the moving position of the focusing lens 32 and the moving position of the focusing lens 124 is made by diopter conversion. For example, as shown in FIG. 10, when the focusing lens 124 of the OCT optical system 200 is moved by −03D, the focusing lens 32 of the imaging optical system 30 may be moved by −3D.

  Therefore, when performing the focus adjustment manually, it is possible to adjust without destroying the automatically aligned positional relationship. Further, with such a configuration, the focus adjustment can be manually performed while observing the change in the focus state of both the fundus image and the OCT image, so that the adjustment is easier.

  In addition, when there are a front image photographing mode using the photographing optical system and a tomographic image photographing mode using the OCT optical system, the focusing information of the optical system used in one photographing mode is used in the other photographing mode. It may be used for focusing. For example, the examiner captures a front image of the eye to be examined in the front image capturing mode. At this time, the control unit 70 drives the first focusing optical member to match the index images S1 and S2. The controller 70 may adjust the focus of the OCT optical system 200 in advance based on the position of the first focus optical member at this time. Thereafter, when the tomographic image capturing mode is set by the examiner, the OCT optical system 200 can perform the photographing smoothly when switching the photographing mode based on the focusing information of the photographing optical system 30. it can.

  In the above-described embodiment, it has been described that the OCT image is generated by the PC 90 arranged separately from the apparatus 1, but the present invention is not limited to this. For example, the ophthalmologic imaging apparatus 1 may include an arithmetic processing unit (for example, a board PC) for generating an OCT image from the detection signal from the detector 120. The arithmetic processing unit may generate an OCT image from the detection signal from the detector 120, and the control unit 70 may display the generated OCT image on the display unit 75 provided in the apparatus 1. Of course, the control unit 70 transmits the OCT image generated by the arithmetic processing unit to a computer connected as a viewer, and the computer receives the OCT image. The computer may display the received OCT image on a monitor provided in the computer.

DESCRIPTION OF SYMBOLS 1 Ophthalmic imaging device 30 Imaging optical system 32 Focusing lens 70 Control part 74 Operation part 75 Display part 90 Computer 95 Display part 120 Detector 124 Focusing lens 200 OCT optical system

Claims (3)

A first focus optical member that is moved in the optical axis direction by a first drive unit; and a light receiving element that receives reflected light from the fundus via the first focus optical member, and the light receiving element. A front imaging optical system for acquiring a front image of the fundus oculi based on an output signal from
A measurement optical path for guiding the measurement light to the fundus of the eye to be examined, a reference optical path for generating the reference light, and a measurement optical path provided with a second focus optical member that is moved in the optical axis direction by the second drive unit A detector for detecting a detection signal including an interference signal between the measurement light guided to the eye to be examined and the reference light from the reference light path, and a tomogram of the eye fundus to be examined based on an output signal from the detector An OCT optical system for acquiring images;
First focus position information, which is focus position information on the fundus of the front imaging optical system, is acquired based on a light reception signal output from the light receiving element, and the first focus optical member and the second focus optical A first autofocus control for moving the member to the in-focus position;
Second focus position information, which is focus position information with respect to the fundus of the OCT optical system, is acquired based on an output signal from the detector, and the second focus optical member is moved to the focus position. Control means capable of executing autofocus control, and
Wherein said control means includes determination means for determining success or failure of the first auto focus control, and executes the first auto focus control earlier, Oite a determination result of the determining means if was determined to be successful, An ophthalmologic photographing apparatus characterized by executing second autofocus control when it is determined that the second autofocus control is not executed and is failed. The front imaging optical system is provided with an index projection optical system for projecting a focus index on the fundus of the eye to be examined.
The control means acquires the first in-focus position information based on the focus index received by the light receiving element in the first autofocus control,
The determination unit determines that the first autofocus control is successful when the position of the focus index can be detected, and the first autofocus control fails when the position of the focus index cannot be detected. The ophthalmologic photographing apparatus according to claim 1, wherein An optical path length adjusting optical member disposed in the measurement optical path or the reference optical path to adjust the optical path length difference between the measurement light and the reference light, and moved by the third drive unit;
The control means determines the position of the optical member for adjusting the optical path length from which the tomographic image of the fundus of the eye to be examined is acquired before moving the second optical member for focus by the first autofocus control or the second autofocus control. The ophthalmic imaging apparatus according to claim 1, wherein the search is performed based on an output signal from the detector.

Images