JP2015085044A - Ophthalmology imaging apparatus, ophthalmology imaging system, and ophthalmology imaging program - Google Patents

Abstract

PROBLEM TO BE SOLVED: To make it possible to solve a problem of the prior art.SOLUTION: An ophthalmology imaging apparatus comprises: an interference optical system comprising a measurement optical path for guiding light from a light source as measurement light to a subject's eye, a reference optical path for guiding the light from the light source as reference light, and a detector for detecting interference between the measurement light and reference light radiated to the subject's eye; scan means for scanning the subject's eye with the measurement light; and a front face imaging optical system for imaging a front face image of the subject's eye. The ophthalmology imaging apparatus obtains a tomographic image of the subject's eye on the basis of a detection signal from the detector at respective scan positions of the scan means. The ophthalmology imaging apparatus comprises a display control unit which is connected to a host computer for generating a tomography image on the basis of a detection signal from the detector through data communication means, transmits the detection signal to the host computer through the data communication means and receives the generated tomography image through the data communication means, and makes a display unit provided on the ophthalmology imaging apparatus display the tomography image and front face image.

Description

  The present invention relates to an ophthalmologic photographing apparatus and an ophthalmologic photographing system for photographing a subject eye.

  2. Description of the Related Art Conventionally, as an ophthalmologic apparatus capable of non-invasively capturing a tomographic image of an eye to be examined, an optical coherence tomography (Optical Coherence Tomography: OCT) using low-coherent light or the like is known (for example, a patent) Reference 1).

As a first conventional apparatus, a configuration in which an apparatus main body and a personal computer are separately arranged is known. In such an apparatus, the tomographic image generated based on the acquired signal is displayed on a display unit such as a computer connected to the main body of the ophthalmic imaging apparatus, for example. For example, the examiner confirms a real-time tomographic image displayed on the display unit of the computer. For example, a general-purpose personal computer is used as the separately arranged personal computer, which is relatively inexpensive and has high functionality. Further, in some cases, it is advantageous in that special hardware control for the apparatus main body can be executed. In addition, in a personal computer arranged separately, for example, an analysis program can be activated to perform tomographic image analysis processing.
An anterior segment image captured by a CCD camera or the like is displayed on a display unit provided in the apparatus body, and is used for alignment between the imaging apparatus body and the eye to be examined.

  As a second conventional apparatus, an apparatus having a configuration in which a personal computer board is built in an apparatus main body and an anterior ocular segment image and a tomographic image are displayed on a monitor provided in the apparatus main body has appeared.

JP 2008-29467 A

However, in the first conventional apparatus (a type in which the apparatus main body and the PC are separated), when an operator tries to operate the apparatus while checking the OCT image, the examiner uses the operation section of the apparatus and the display section of the computer. It is necessary to check alternately. This places an extra burden on the examiner.

The second conventional apparatus (stand-alone type) can confirm an OCT image on the apparatus main body, but since an expensive personal computer board is provided on the apparatus main body, the cost of the apparatus main body and vulnerability to failure remain. Furthermore, in the second conventional apparatus, since an external general-purpose personal computer is used for tomographic image analysis (for example, layer thickness measurement), two personal computers are used.
An object of the present invention is to provide an ophthalmologic photographing apparatus that can solve at least one problem of the above-described conventional technology.

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

(1) A light source, a measurement optical path for guiding light from the light source as measurement light to the eye to be examined, a reference optical path for guiding light from the light source as reference light, and the eye irradiated to the eye to be examined An interference optical system comprising: a detector for detecting interference between measurement light and the reference light; scanning means disposed in the measurement optical path for scanning the measurement light on the eye to be examined; A front imaging optical system that captures a front image of the eye, and an ophthalmic imaging apparatus that obtains a tomographic image of the eye to be inspected based on a detection signal from the detector at each scanning position of the scanning unit. The imaging apparatus is connected to a host computer that generates a tomographic image based on a detection signal from the detector via data communication means, and the detection signal from the detector is connected to the host computer via the data communication means. Send Both the tomographic image generated by the host computer is received via the data communication unit, and the tomographic image received via the data communication unit and the front image captured by the front imaging optical system are combined. And a display control unit for displaying on a display unit provided in the ophthalmologic photographing apparatus.
(2) An ophthalmic imaging system including the ophthalmic imaging apparatus according to (1) and the host computer, wherein a front image captured by the front imaging optical system is transferred to the host computer via the communication unit. The host computer includes an image processing unit that generates the tomographic image, the front image transferred via the data communication unit, the tomographic image generated by the image processing unit, and the host computer. And a second display control means for displaying on a display unit provided in the display.
(3) An ophthalmic imaging program that is executed in an ophthalmic imaging system including the ophthalmic imaging apparatus according to (1) and the host computer, and is executed by a processor of the ophthalmic imaging system, whereby the front imaging A transfer step of transferring a front image captured by an optical system to the host computer via the communication means, an image processing step of generating the tomographic image by the host computer, and a transfer via the data communication means. And displaying the front image and the tomographic image generated by the image processing unit on a display unit provided in the host computer, and causing the ophthalmic imaging system to execute the display control step. To do.

It is the schematic which shows the external appearance of the ophthalmologic apparatus of this embodiment. It is a figure which shows the optical system and control system of the ophthalmologic imaging device of this embodiment. It is a figure which shows an example of the screen displayed on the display part of this embodiment. It is an example when the anterior ocular segment image imaged by the image sensor is displayed on the display unit. It is an example when the fundus image imaged by the image sensor is displayed on the display unit. It is a block diagram which shows the control system of this embodiment. It is a figure explaining the alignment detection with respect to a to-be-tested eye.

  Embodiments of the present invention will be described with reference to the drawings. FIG. 1 is a schematic view showing the appearance of the ophthalmologic apparatus of the present embodiment. FIG. 2 is a diagram illustrating an optical system and a control system of the ophthalmologic photographing apparatus according to the present embodiment. In this embodiment, the depth direction of the eye to be examined is the Z direction (optical axis L1 direction), the horizontal component on the plane perpendicular to the depth direction (the same plane as the face of the subject) is the X direction, and the vertical direction. The component is described as the Y direction.

<Overview>
The apparatus 1 mainly includes an interference optical system (OCT optical system) 200 and a front imaging optical system (for example, the imaging optical system 30 or the anterior ocular segment observation optical system 60).

  The interference optical system 200 mainly includes a light source 102, a detector 120, and a scanning unit 108. The detector 120 detects the measurement light and the reference light irradiated on the eye E by interfering with each other. Measurement light is emitted from the light source 102 and guided to the eye E through the measurement optical path. The reference light is emitted from the light source 102 and guided to the detector through the reference light path. The front imaging optical system may capture a front image (for example, the anterior ocular segment and fundus) of the eye to be examined. For example, an SLO, a camera, or the like is used.

  The scanning unit 108 is arranged in the measurement optical path and scans the measurement light on the eye E. The scanning unit 108 may repeatedly scan the measurement light on the eye E. The front imaging optical system may capture a front image (for example, an anterior ocular segment image, fundus image) of the eye E.

  The apparatus 1 can obtain a tomographic image of the eye E based on detection signals from the detector 120 at each scanning position of the scanning unit 108.

  The apparatus 1 is connected to a host computer (for example, PC 90) that generates a tomographic image based on a detection signal from the detector 120 via a data communication unit (for example, USB signal lines 76 and 77). (See FIG. 6). Of course, the host computer is not limited to the PC 90 and may be another computer. The data communication unit may be a wired communication unit or a wireless communication unit.

  The host computer may include an image processing unit (for example, CPU 91), a display unit 95, and a second display control unit (for example, CPU 91). For example, the image processing unit generates a tomographic image. The second display control means may cause the display unit 95 to display the front image transferred via the data communication unit and the tomographic image generated by the image processing unit (see FIG. 3).

  The host computer may generate a live tomographic image (for example, a moving image) based on a plurality of temporally continuous tomographic images based on the detection signal from the detector 120.

  Further, the present apparatus 1 transmits a detection signal from the detector 120 to the host computer via the data communication means. The apparatus 1 receives a tomographic image generated by the host computer via the data communication unit. The apparatus 1 may transfer the front image to the host computer via the data communication unit.

  Furthermore, a display control unit (for example, control) that displays the tomographic image 83 received via the data communication unit and the front image captured by the front imaging optical system 20 on the display unit 75 provided in the apparatus 1. Part 70).

  The display control unit may evaluate the tomographic image and display the evaluation result on the display unit 75 together with the tomographic image.

  Further, a first communication cable (for example, USB signal line 77) may be used as the data communication unit. The detector 120 and the host computer may be directly connected using the first communication cable as a dedicated cable.

  A second communication cable (for example, USB signal line 76) may be used as the data communication unit. A tomographic image generated by the host computer may be received via the second communication cable. A universal serial bus may be used for the data communication unit.

  In addition, this apparatus 1 may transmit / receive the control signal which detects or controls an apparatus state via a data communication part.

  In addition, the apparatus 1 transmits a detection signal from the detector 120 to the host computer via the data communication unit in response to repeated scanning of the scanning unit 108, and performs live communication on the live tomographic image generated by the host computer. You may receive through the department. The display control unit (for example, the control unit 70) may cause the display unit 75 to display the live tomographic image received via the data communication unit and the live front image captured by the front imaging optical system. Good.

  Note that the apparatus 1 and the host computer may function as one ophthalmic imaging system. For example, a transfer step of transferring a front image captured by the front imaging optical system to a host computer via a data communication unit, an image processing step of generating a tomographic image by the host computer, and a data communication unit The display control step for displaying the front image and the tomographic image generated by the image processing unit on the display unit 75 may be executed by a processor of the ophthalmic imaging system.

<Display of live tomographic images on both the display unit of the ophthalmic imaging apparatus main body and the display unit of the host computer>
A typical ophthalmic imaging system includes an ophthalmic imaging apparatus (for example, the present apparatus 1), a host computer (for example, PC 90), an image processing unit (for example, CPU 90), a first display control unit, and a second display unit. A display control unit. The image processing unit may generate a live tomographic image based on a plurality of tomographic images that are temporally continuous based on the detection signal from the detector 120.

  The first display control unit may cause the live tomographic image generated by the image processor and the front image captured by the front imaging optical system 20 to be displayed on the display unit 75 provided in the ophthalmologic photographing apparatus. .

  The second display control unit may display the live tomographic image generated by the image processor and the front image captured by the front imaging optical system on the display unit 95 provided in the host computer.

  As a result, the live tomographic image and the front image are displayed on the monitors of both the ophthalmic imaging apparatus and the host computer. The front image may be displayed on either the ophthalmologic photographing apparatus or the host computer.

  As an example, the image processing unit may be provided in a host computer, and the ophthalmic imaging apparatus may receive a live tomographic image generated by the image processing unit via the data communication unit. The first display control unit may cause the live tomographic image received via the data communication unit and the front image captured by the front imaging optical system to be displayed on the display unit 75 provided in the ophthalmologic photographing apparatus. .

  As another example, the image processing unit is provided in the ophthalmologic photographing apparatus, and the host computer displays the live tomographic image generated by the image processing unit and the front image captured by the front imaging optical system as a data communication unit. The second display control unit may display the live tomographic image and the front image received via the data communication unit on the display unit 95 provided in the host computer.

The front imaging optical system may capture a live front image using a plurality of temporally continuous front images as a front image. The first display control unit may display the live tomographic image generated by the image processor and the live front image captured by the front imaging optical system on a display unit provided in the ophthalmologic photographing apparatus.
The second display control unit may display the live tomographic image generated by the image processor and the live front image captured by the front imaging optical system on the display unit 95 provided in the host computer.

<Example>
As shown in FIG. 1A, the apparatus main body 1 of 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. Note that the photographing unit 3 may be moved in the left-right direction (X direction) and the front-rear (working distance) direction (Z direction) with respect to the left and right eyes by the movement of the movable table 2 with respect to the base 4.

  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 receives the control signal, the control unit performs 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 in Y and the photographing unit 3 is moved in the Y direction. In addition, the structure which the imaging | photography part 3 is moved with respect to the eye to be examined by the XYZ drive part 6 when the joystick 74a is operated without providing the moving stand 2 may be sufficient.

  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.

  In addition, the apparatus main body 1 of the present embodiment is connected to a personal computer (hereinafter referred to as PC) 90. For example, a display unit 95 and operation members (keyboard 96, mouse 97, etc.) may be connected to the PC 90.

  As shown in FIG. 2, the optical system of the present embodiment mainly includes an illumination optical system 10, a photographing optical system 30, and an interference optical system 200 (hereinafter also referred to as an OCT optical system) 200. Furthermore, 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. The photographing optical system 30 is used as a fundus camera optical system for obtaining a color fundus image by photographing the fundus with visible light (for example, a non-mydriatic state). The imaging optical system 30 captures a fundus oculi image of the eye to be examined. 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.

<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 a halogen lamp or the like. The infrared filter 12 transmits near infrared light having a wavelength of 750 nm or more. The dichroic mirror 16 is disposed between the condenser lens 13 and the ring slit 17. The dichroic mirror 16 has a characteristic of reflecting light from the light source 11 and transmitting light from the photographing light source 14.

<Fundus camera optical system>
In the photographic optical system 30, for example, an objective lens 25, a photographing aperture 31, a focusing lens 32, an imaging lens 33, and an image sensor 35 are mainly disposed. 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 photographing having sensitivity in the visible range. 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.

  Further, a dichroic mirror 34 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 34, 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.

  A dichroic mirror (wavelength selective mirror) 24 that can be inserted and removed as an optical path branching member is provided obliquely between the objective lens 25 and the perforated mirror 22. The dichroic mirror 24 reflects 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 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. At the time of shooting, the dichroic mirror 24 is flipped up by the insertion / removal mechanism 66 and retracts 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 imaged through the objective lens 25, the dichroic mirror 24, the correction glass 28, the aperture of the perforated mirror 22, the imaging aperture 31, the focusing lens 32, the imaging lens 33, and the dichroic mirror 37. An image is formed on the element 38. The output of the image sensor 38 is input to the control unit 70, and the control unit 70 displays a fundus observation image 82 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 obliquely installed in the navigation 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 not focused, the index images S1 and S2 are projected onto the fundus in a state of being separated according to the shift direction and shift amount. 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. 5). The index images S1 and S2 are taken together with the fundus image by the image sensor 38.

<Alignment index projection optical system>
In the alignment index projection optical system 50 for projecting the alignment index beam, 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, as shown in the diagram in the upper left dotted line in FIG. Has been placed. The ophthalmologic photographing apparatus according to 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 for imaging the anterior ocular segment of the eye to be inspected has a dichroic mirror 61, a diaphragm 63, a relay lens 64, a two-dimensional imaging element (light receiving element: hereinafter) on the reflection side of the dichroic mirror 24. (It 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 FIGS. 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 (sample 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 22 and then condensed on the fundus of the eye to be examined 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 driver 151.

  Thereby, the reflection (advance) direction of the light beam emitted from the light source 102 is changed, and is scanned in an arbitrary direction on the fundus. Thereby, 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 with reference to FIG. As shown in FIG. 6, the control unit 70 of the present embodiment includes an imaging element 65 for anterior segment observation, an imaging element 38 for infrared fundus observation, a display unit 75, an operation unit 74, a USB 2. A 0 standard HUB 71 is connected to each light source (not shown), various actuators (not shown), and the like. The USB 2.0 HUB 71 is connected with an image sensor 35 built in the apparatus main body 1 and a PC (personal computer) 90.

  The PC 90 includes a CPU 91 as a processor, an operation input unit (for example, a mouse and a keyboard), a memory (nonvolatile memory) 72 as a storage unit, and a display unit 95. The CPU 91 may control the apparatus main body 1. The memory 72 is a non-transitory storage medium that can retain stored contents even when power supply is interrupted. For example, a hard disk drive, flash ROM, USB memory detachably attached to the PC 90, an external server, or the like can be used as the memory 72. The memory 72 stores an imaging control program for controlling imaging of front images and tomographic images by the apparatus main body (ophthalmic imaging apparatus) 1.

  Further, the memory 72 stores an ophthalmic analysis program for using the PC 90 as an ophthalmic analysis apparatus. That is, the PC 90 may also be used as an ophthalmologic analyzer. Further, the memory 72 stores various types of information related to imaging such as tomographic images (OCT data), three-dimensional tomographic images (three-dimensional OCT data), frontal fundus images, and information on imaging positions of tomographic images in the scanning line. Various operation instructions by the examiner are input to the operation input unit.

  When used as an ophthalmologic analyzer, the PC 90 (more specifically, the CPU 91) may detect fundus layer information in acquired tomographic image data (for example, three-dimensional OCT data) by image processing, for example. . The PC 90 may acquire the analysis information by analyzing the detection result of each layer with reference to the normal eye database. The analysis information is stored in the memory 72 together with the tomographic image. The PC 90 displays the analysis information stored in the memory 72 on the screen of the display unit 95 together with the tomographic image. Of course, the PC 90 may be configured to display at least one of analysis information or a tomographic image as an image to be displayed on the screen of the display unit 95. Note that the PC 90 may display the obtained analysis information on the display unit 75 of the apparatus main body 1.

  For example, the analysis information includes an analysis map, an analysis chart, a deviation map, and the like. For example, examples of the analysis map include a comparison map and a difference map. The comparison map indicates a comparison result between the thickness of the retinal layer of the subject eye and the thickness of the retinal layer of the predetermined subject eye stored in the normal eye database (details will be described later).

  The difference map indicates a difference result between the thickness of the retinal layer of the eye to be examined and the thickness of the retinal layer of the predetermined eye to be stored stored in the database. The deviation map is a map that shows the deviation between the thickness of the retinal layer of the eye to be examined and the thickness of the retinal layer of the predetermined eye stored in the normal eye database with a standard deviation. The analysis information is not limited to the retinal layer, and may be analysis information related to the choroid layer, or may be analysis information of the entire fundus including the retinal layer and the choroid layer.

  For example, an analysis chart is a chart which shows an analysis value for every preset section. The control unit 70 may obtain a basic statistic of the analysis result for each preset section as the analysis value. The basic statistic may be a representative value (average value, median value, mode value, maximum value, minimum value, etc.), distribution degree (dispersion, standard deviation, coefficient of variation), or the like.

  More specifically, the analysis chart may be a chart showing a representative value (for example, an average value, a median value) of analysis results for each preset section. The analysis chart may be a chart indicating the maximum value or the minimum value of the analysis result for each preset section. The analysis result for each section includes the analysis result at each position in the section, so that a stable analysis value can be obtained.

  A detector (for example, a line CCD or the like) 120 for OCT imaging built in the apparatus main body 1 is connected to the PC 90 via a USB 3.0 port 79a, 79b via a USB signal line. Thus, in the present embodiment, the apparatus main body 1 and the PC 90 are connected to each other by the two USB signal lines 76 and 77.

  Further, the control unit 70 may detect the alignment index from the anterior segment image 81 captured by the image sensor 65. The control unit 70 may detect the alignment deviation amount of the apparatus main body 1 with respect to the eye to be examined based on the imaging signal of the imaging element 65.

  Further, as shown in the anterior ocular segment image observation screen of FIG. 4 (which may be displayed on the fundus oculi observation screen of FIG. 5), the control unit 70 displays a reticle LT serving as an alignment reference on the screen of the display unit 75. The position may be formed electronically and displayed. Further, the control unit 70 may control the display of the alignment index A1 so that the relative distance from the reticle LT is changed based on the detected amount of alignment deviation.

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

  The control unit 70 also outputs an anterior ocular segment observation image and an infrared fundus image to the PC 90 via the HUB 71 and USB 2.0 ports 78a and 78b. The PC 90 included in the PC 90 displays the anterior ocular segment image and the fundus oculi observation image 82 that are output in a streaming manner on the display unit 95 of the PC 90. The anterior ocular segment observation image and the infrared fundus image may be simultaneously displayed as a live image (for example, a live front image) on the display unit 95 (the anterior ocular segment observation image 81 and the fundus oculi observation image 82 in FIG. 3). .

  On the other hand, the photographing of the color fundus image by the image sensor 35 is performed based on a trigger signal from the control unit 70. The color fundus image is also output to the control unit 70 and the PC 90 via the HUB 71 and the USB 2.0 ports 78a and 78b, and displayed on the display unit 75 or the display unit 95 of the PC 90.

  Further, the detector 120 is connected to the PC 90 via the USB 3.0 ports 79a and 79b. The light reception signal from the detector 120 is input to the PC 90. The PC 90 (more specifically, the processor (for example, CPU) of the PC 90) generates the tomographic image 83 by performing arithmetic processing on the light reception signal from the detector 120.

  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 rewritten as a function of the wavelength λ, and 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.

  Furthermore, the PC 90 may obtain information (for example, a tomographic image) of the eye to be examined by arranging internal information obtained at different positions by scanning the measurement light or the like. The PC 90 stores the obtained result in the memory 72. The PC 90 may display the obtained result on the display unit 95.

The apparatus main body 1 captures an image with a preset scan pattern based on a release signal from the PC 90. The PC 90 processes each image signal and outputs an image result on the display unit 95 of the PC 90.
At this time, the detector 120 outputs the detected detection signal to the PC 90. The PC 90 generates a tomographic image from the output from the detector 120.

  The PC 90 transfers the generated tomographic image to the apparatus main body 1 via the USB 2.0 ports 78b and 78a and the HUB 71. The control unit 70 displays the transferred tomographic image 83 on the display unit 75 (see, for example, the tomographic image 83). Note that an OCT front image may be generated by the PC 90 based on an output signal from the detector 120, and the OCT front image may be displayed on the display unit 75.

  In this embodiment, the examiner can perform each setting or alignment of OCT imaging settings, alignment, optimization, and the like while viewing the display unit 75 disposed in the apparatus main body 1 (details will be described later). ). Accordingly, as shown in FIG. 1B, the examiner can save the trouble of alternately checking the display unit 75 of the apparatus main body 1 and the display unit 95 on the PC 90 side that are arranged at different positions. Further, when taking an image with the subject's eyelid opened, the examiner may perform the opening operation more easily while checking the display unit 75 than checking the display unit of the PC 90.

  Further, since the tomographic image 83, the fundus oculi image 82, the anterior ocular segment image 81, and the like are displayed on both the display unit 75 and the display unit 95 of the PC 90, the examiner operates using the apparatus main body unit 1. , Whether to operate using the PC 90 can be selected according to preference. In addition, since various captured images are displayed on both the display unit 75 and the display unit 95 of the PC 90, the number of screens on which the image can be observed is increased, and it becomes easy for a plurality of people to check the image.

  In the case where measurement is performed separately for an examiner who observes an image with the display unit 95 of the PC 90 and an examiner who performs imaging with the apparatus main body unit 1, the examiner who performs imaging takes the tomography imaged with the display unit 75. If the image 83 is confirmed and shooting is not successful, shooting can be performed again. For this reason, the examiner observing the display unit 95 is less likely to tell the examiner who performs imaging to restart measurement.

  As described above, by displaying the tomographic image 83 on both the display section 75 of the apparatus main body 1 and the display section 95 of the PC 90, the apparatus main body 1 can be adapted to an imaging method that suits the examiner's preference. .

  The same applies to the above-described color fundus photography. The result of color fundus photography is not only input to the PC 90 but also image information such as a preview result is transferred to the apparatus main body via the USB 2.0 ports 78b and 78a and the HUB 71, and the display unit of the apparatus main body 1 is displayed. A color fundus image may be displayed on 75. Thus, the examiner can save the trouble of alternately checking the apparatus main body 1 and the PC 90 in order to see the color fundus image. Further, when operating the apparatus main body 1 while viewing a color fundus photographed image, it is not necessary to look into the display unit 95 on the computer side, and it is only necessary to check the display unit 75, thereby reducing the burden on the examiner.

  Further, the signal line via the USB port and the HUB 71 may be used for exchanging information necessary for OCT or fundus camera photography, such as the state of the apparatus at an appropriate time interval, or a control command from the PC 90. For example, the signal line via the USB port and the HUB 71 may exchange information such as the sensor state of the apparatus main body 1 or various apparatus statuses at certain time intervals, or the position control of the galvano scanner from the PC 90.

  For example, an operation signal from the operation unit 74 of the apparatus main body 1 may be transmitted to the PC 90. The PC 90 may transmit a control signal corresponding to the operation signal from the operation unit 74 to the apparatus main body 1. More specifically, the PC 90 may control driving of the scanning unit 108 of the apparatus main body 1 based on an operation signal from the operation unit 74.

  In this case, the operation signal from the operation unit 74 of the apparatus main body 1 may be temporarily input to the control unit 70 of the apparatus main body 1, and the control unit 70 may transmit the operation signal to the PC 90. The PC 90 may input a control signal corresponding to the operation signal from the operation unit 74 to the control unit 70 of the apparatus main body 1 so that the control unit 70 controls the driving of the apparatus main body 1.

  Of course, processing related to device control may be completed in the device main body 1. In this case, the control unit 70 may directly drive the apparatus main body 1 based on an operation signal from the operation unit 74.

<Control action>
An example of the control operation in the apparatus having the above configuration will be described. For example, the control unit 70 may combine the captured image from the image sensor 65, the captured image from the image sensor 38, and the OCT image from the PC 90 and display them on the screen of the display unit 75 as an observation screen. As shown in FIG. 3, a live anterior ocular segment observation image 81, a live fundus observation image 82, and a live tomographic image (hereinafter also referred to as a live tomographic image) may be simultaneously displayed on the observation screen.

  The tomographic image 83 is output from the PC 90 to the control unit 70 via the USB 2.0 ports 78b and 78a and displayed on the display unit 75. In the present embodiment, the fundus image 82 is displayed at the center of the display unit 75, the anterior eye image 81 is displayed at the upper right, and the tomographic image 83 is displayed at the lower right, but the present invention is not limited thereto. The examiner operates the apparatus main body 1 while confirming these images on the display unit 75.

  The examiner causes the face support unit 5 to support the face of the subject. Then, the examiner instructs the subject to watch the fixation target (not shown). At the initial stage, the dichroic mirror 24 is inserted in the optical path of the photographing optical system 30, and an anterior segment image captured by the image sensor 65 is displayed on the display unit 75.

  For example, the examiner operates the joystick 74a as the vertical / left / right alignment adjustment, and moves the photographing unit 3 left / right / up / down so that the anterior segment image appears on the display unit 75. When the anterior segment image appears on the display unit 75, eight index images (first alignment index images) Ma to Mh appear as shown in FIG. In this case, the imaging range by the imaging element 65 is preferably a range that includes the pupil, iris, and eyelid of the anterior eye portion when the alignment is completed.

<Alignment detection and automatic alignment in XYZ directions>
When the alignment index images Ma to Mh are detected by the two-dimensional image sensor 65, the control unit 70 starts automatic alignment control. The control unit 70 detects the alignment deviation amount Δd of the imaging unit 3 with respect to the eye to be examined based on the imaging signal output from the two-dimensional imaging element 65. More specifically, the XY coordinates of the center of the ring shape formed by the index images Ma to Mh projected in a ring shape are detected as the approximate corneal center, and the alignment reference in the XY directions set in advance on the image sensor 65 is used. A deviation amount Δd between the position O1 (for example, the intersection of the imaging surface of the imaging element 65 and the imaging optical axis L1) and the corneal center coordinates is obtained (see FIG. 7). Note that the center of the pupil may be detected by image processing, and the misalignment may be detected based on the amount of deviation between the coordinate position and the reference position O1.

  Then, the control unit 70 operates automatic alignment by drive control of the XYZ drive unit 6 so that the deviation amount Δd falls within the allowable range A for completion of alignment. Depending on whether the deviation amount Δd is within the allowable range A for completion of alignment and the time continues for a certain time (for example, 10 frames for image processing or 0.3 seconds) (whether the alignment condition A is satisfied). , Whether the alignment in the XY directions is appropriate or not is determined.

  Further, the control unit 70 obtains the alignment deviation amount in the Z direction by comparing the interval between the index images Ma and Me at infinity detected as described above and the interval between the index images Mh and Mf at finite distance. . In this case, when the photographing unit 3 is shifted in the working distance direction, the control unit 70 changes the image interval between the index images Mh and Mf while the interval between the infinite indexes Ma and Me hardly changes. The amount of alignment deviation in the working distance direction with respect to the eye to be examined is obtained using the characteristic of performing (see Japanese Patent Laid-Open No. 6-46999 for details).

  Further, the control unit 70 also obtains a deviation amount with respect to the alignment reference position in the Z direction in the Z direction, and the XYZ driving unit 6 so that the deviation amount falls within an alignment allowable range in which the alignment is completed. The automatic alignment by the drive control is activated. Whether or not the alignment in the Z direction is appropriate is determined based on whether or not the amount of deviation in the Z direction is within an allowable range for completion of alignment for a certain period of time (whether the alignment condition is satisfied).

  When the alignment operation in the XYZ directions satisfies the alignment completion condition by the alignment operation described above, the control unit 70 determines that the alignment in the XYZ directions is matched, and proceeds to the next step.

  Here, when the alignment deviation amount Δd in the XYZ directions falls within the allowable range A1, the drive of the drive unit 6 is stopped and an alignment completion signal is output. Even after the alignment is completed, the control unit 70 detects the displacement amount Δd as needed, and resumes automatic alignment when the displacement amount Δd exceeds the allowable range A1. That is, the control unit 70 performs control (tracking) for tracking the imaging unit 3 with respect to the subject's eye so that the deviation amount Δd satisfies the allowable range A1.

<Determination of pupil diameter>
After the alignment is completed, the control unit 70 starts determining whether or not the pupil state of the eye to be examined is appropriate. In this case, whether or not the pupil diameter is appropriate is determined based on whether or not the pupil edge detected from the anterior segment image by the image sensor 65 is out of a predetermined pupil determination area. The size of the pupil determination area is set as a diameter (for example, a diameter of 4 mm) through which the fundus illumination light beam can pass with the image center (imaging optical axis center) as a reference. For simplicity, four pupil edges detected in the horizontal direction and the vertical direction with respect to the center of the image are used. If the pupil edge point is outside the pupil determination area, the illumination light quantity at the time of photographing is sufficiently secured (for details, refer to Japanese Patent Application Laid-Open No. 2005-160549 by the present applicant). The pupil diameter suitability determination is continued until imaging is executed, and the determination result is displayed on the display unit 75.

<Focus state detection / Auto focus>
When the alignment using the image sensor 65 is completed, the control unit 70 performs autofocus on the fundus of the eye to be examined. FIG. 5 is an example of a 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 they are not in focus, and are projected in agreement when they are in focus. 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.

<Optimization control>
When the alignment completion signal is output, the control unit 70 issues a trigger signal for starting the optimization control, and starts the optimization control operation. The control unit 70 performs optimization so that the fundus site desired by the examiner can be observed with high sensitivity and high resolution. In the present embodiment, the optimization control is control of optical path length adjustment, focus adjustment, and polarization state adjustment (polarizer adjustment). In the optimization control, it is only necessary to satisfy a certain permissible condition for the fundus, and it is not always necessary to adjust to the most appropriate state.

  In the optimization control, 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). Further, in parallel with the first optical path length adjustment, the control unit 70, based on the focus result of the fundus camera optical system with respect to the above-described fundus camera fundus, the in-focus position information (for example, the fundus observation image 82) The movement amount of the lens 32 is acquired. When the in-focus position information is acquired, the control unit 70 moves the focussing lens 124 to the in-focus position and performs autofocus adjustment (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 to adjust the polarization state of the measurement light (for details, refer to Japanese Patent Application No. 2012-56292).

  As described above, when the optimization control is completed, the fundus site desired by the examiner can be observed with high sensitivity and high resolution. Then, the control unit 70 controls driving of the scanning unit 108 and scans the measurement light on the fundus.

  The detection signal (spectral data) detected by the detector 120 is transmitted to the PC 90 via the USB 3.0 ports 79a and 79b (see FIG. 6). The PC 90 receives the detection signal, and generates a tomographic image 83 by processing the detection signal.

  When generating the tomographic image 83, the PC 90 transmits the tomographic image 83 to the control unit 70 of the apparatus main body 1 via the USB 2.0 ports 78b and 78a and the HUB 71. The control unit 70 receives the tomographic image 83 from the PC 90 via the USB 2.0 ports 78 b and 78 a and the HUB 71 and displays the tomographic image 83 on the display unit 75. As shown in FIG. 3, the control unit 70 displays the anterior ocular segment observation image 81, the fundus oculi observation image 82, and the tomographic image 83 on the display unit 75.

  The examiner confirms the tomographic image 83 updated in real time, and adjusts the alignment in the Z direction. For example, the alignment may be adjusted so that the tomographic image 83 fits within the display frame.

  Of course, the PC 90 may display the generated tomographic image 83 on the display unit 90. The PC 90 may display the generated tomographic image 83 on the display unit 95 in real time. Further, the PC 90 may display the anterior ocular segment observation image 81 and the fundus oculi observation image 82 on the display unit 95 in real time in addition to the tomographic image 83.

  The PC 90 may evaluate the generated tomographic image 83 and display the evaluation value together with the tomographic image 83 on the display unit 75 or the like. For example, the evaluation value B that is an index of the signal intensity of the tomographic image may be displayed together with the tomographic image 83. The evaluation value B may be obtained from the equation B = ((average maximum luminance value of the image) − (average luminance value of the background region of the image)) / (standard deviation of the luminance value of the background region). As a method for obtaining the evaluation value B, for example, a method described in Japanese Patent Application Laid-Open No. 2012-213489 can be used. Of course, the tomographic image evaluation method is not limited to the above method.

  The examiner may observe the fundus observation image 82 displayed on the display unit 75 and manually adjust the focus of the image. For example, the examiner presses the function switching button 74e provided on the operation unit 74 of the apparatus main body several times. The operation unit 74 once transmits an operation signal to the control unit 70, and the control unit 70 transmits an operation signal to the PC 90. The PC 90 transmits a control signal for switching the image quality adjustment item to the focus based on the operation signal, and the control unit 70 switches the image quality adjustment item to the focus. The selected image adjustment item may be displayed on the display unit 75 by the control unit 70. In this state, the adjustment knob 74d may be operated so that the fundus observation image 82 is in focus. When the adjustment knob 74d is operated, the focus lens 24 is moved in the optical axis direction. The examiner operates the adjustment knob 74d so that the fundus observation image 82 is clearly visible.

  In addition, the examiner may perform alignment in the Z direction by observing a real-time tomographic image 83 (hereinafter also referred to as an OCT live image or a live tomographic image) displayed on the display unit. For example, the examiner presses the function switching button 74e provided on the operation unit 74 of the apparatus main body 1 several times in the same manner as described above, and switches the image quality adjustment item to the Z position (optical path length adjustment). In this state, the examiner operates the adjustment knob 74d so that the tomographic image 83 is displayed at the center of the display area of the tomographic image 83. When the adjustment knob 74d is operated, the reference mirror 131 is moved and the optical path length is adjusted. In this case, the display area of the tomographic image 83 may be intentionally limited (narrowed) in the vertical direction so that alignment is set when the tomographic image 83 is displayed at the center of the display area.

  The examiner may observe the OCT live image displayed on the display unit 75 and perform polarizer adjustment. For example, the examiner presses the function switching button 74e provided on the operation unit 74 of the apparatus main body 1 several times in the same manner as described above, and switches the image quality adjustment item to polarization. In this state, the examiner may adjust the image quality of the OCT live image 83 by adjusting the adjustment knob 74d. When the adjustment knob 74d is operated, the polarizer 133 may be rotated to adjust the polarization direction of the measurement light or the reference light.

  In the case where the focus adjustment of the image is manually performed, the examiner has described that the adjustment is performed by operating the adjustment knob 74d or the like. However, the present invention is not limited to this. For example, the examiner may adjust the image by performing a touch operation on a display unit (for example, the display unit 75) having a touch panel function.

  When the alignment and the image quality adjustment are completed, the control unit 70 controls driving of the scanning unit 108, scans the measurement light on the fundus in a predetermined direction, and outputs a predetermined value from an output signal output from the detector 120 during the scanning. A light reception signal corresponding to the scanning region is acquired to form a tomographic image.

  FIG. 3 is a diagram illustrating an example of a display screen displayed on the display unit 75. The control unit 70 displays on the display unit 75 the anterior ocular segment image 81, the fundus oculi observation image 82, the tomographic image 83, and the line 85 acquired by the anterior ocular segment observation optical system 60. A line 85 is an index representing the measurement position (acquisition position) of the tomographic image on the fundus observation image 82. The line 85 is electrically displayed on the fundus observation image 82 on the display unit 75.

  In this embodiment, the imaging condition can be set by the examiner performing a touch operation or a drag operation on the display unit 75. The examiner can specify an arbitrary position on the display unit 75 by a touch operation.

<Scanline settings>
FIG. 3 is a diagram for explaining setting of the scanning position. When the tomographic image and the fundus oculi observation image 82 are displayed on the display unit 75, the examiner sets the position of the tomographic image that the examiner wants to photograph from the fundus oculi observation image 82 on the display unit 75 observed in real time. Here, the examiner moves the line 85 with respect to the fundus oculi observation image 82 by performing a drag operation using the touch panel display 75, and sets the scanning position. If the line is set to be in the X direction, a tomographic image on the XZ plane is taken, and if the line 85 is set to be in the Y direction, a tomographic image on the YZ plane is taken. It has become. Further, the line 85 may be set to an arbitrary shape (for example, an oblique direction or a circle).

  In the present embodiment, the operation of the touch panel type display unit 75 provided in the apparatus main body 1 has been mainly described, but the present invention is not limited to this. The same operation as that of the display unit 75 may be performed by operating a joystick 74a or various operation buttons provided in the operation unit 74 of the apparatus main body 1. Also in this case, for example, the operation signal from the operation unit 74 may be transmitted to the PC via the control unit 70, and the PC may transmit a control signal corresponding to the operation signal to the control unit 70.

  When the examiner moves the line 85 relative to the fundus oculi observation image 82, the control unit 70 sets a scanning position at any time, and acquires a tomographic image at the corresponding scanning position. The acquired tomographic image is displayed on the display screen of the display unit 75 as needed. Further, the control unit 70 changes the scanning position of the measurement light based on the operation signal output from the display unit 75 and displays the line 85 at the display position corresponding to the changed scanning position. Since the relationship between the display position of the line 85 (coordinate position on the display unit) and the scanning position of the measurement light by the scanning unit 108 is determined in advance, the control unit 70 corresponds to the set display position of the line 85. The two galvanometer mirrors of the scanning unit 108 are appropriately driven and controlled so that the measurement light is scanned with respect to the scanning range.

<Acquisition of tomographic images>
When the imaging start switch 74c is operated at a desired position by the examiner after adjustment of the imaging conditions is completed, the control unit 70 acquires a tomographic image by B-scan based on the set scanning position. Do. Based on the display position of the line 85 set on the fundus observation image 82, the control unit 70 drives the scanning unit 108 so that the tomographic image of the fundus corresponding to the position of the line 85 is obtained, and emits measurement light. Let it scan.

  The PC 90 generates a tomographic still image based on the detection signal from the detector 120, and transfers the generated still image to the apparatus main body 1. The control unit 70 displays the tomographic still image transferred from the PC 90 on the display unit 75.

For example, the control unit 70 may cause the display unit 75 to display an OK button and an NG button not shown. The examiner presses the OK button when saving the tomographic image 83 displayed on the display unit 75 in the memory 72, and presses the NG button when not saving. The control unit 70 stores the tomographic image 83 in the memory 72 when the OK button is pressed. On the other hand, the control unit 70 may redo the tomographic image 83 when the NG button is pressed.
In this way, by displaying the tomographic image 83 on the display unit 75, the examiner can determine whether or not photographing has been performed appropriately without handling the PC 90.

  When the tomographic image is obtained, the control unit 70 proceeds to the step of acquiring the color fundus image 82 by the fundus camera optical system 100. While examining the fundus observation image 82 displayed on the display unit 75, the examiner performs fine adjustment of alignment and focus so that the photographer can take a picture in a desired state. When the examiner inputs the photographing start switch 74c, photographing is performed. The controller 70 drives the insertion / removal mechanism 66 based on the trigger signal from the imaging start switch 74c, thereby causing the dichroic mirror 24 to leave the optical path and causing the imaging light source 14 to emit light.

  When the imaging light source 14 emits light, the fundus of the eye to be examined is irradiated with visible light. Reflected light from the fundus passes through the objective lens 25, the aperture of the perforated mirror 22, the photographing aperture 31, the focusing lens 32, the imaging lens 33, and the dichroic mirror 37 and forms an image on the two-dimensional light receiving element 35. The color fundus image captured by the two-dimensional light receiving element 35 is received by the PC 90 via the HUB 71 and the USB 2.0 ports 78a and 78b, and then stored in the memory 72.

  The PC 90 performs an analysis process on at least one of the tomographic image and the fundus image obtained as described above, and displays the analysis result on the display unit 95. The PC 90 may display the analysis result on the display unit 75.

  In the present embodiment, the control unit of the apparatus main body 1, the fundus camera, and the PC 90 are connected via USB 2.0 ports 78a and 78b. Since the USB standard performs transmission and reception in a time-sharing manner, bidirectional communication can be performed with a single cable, and the number of cables can be reduced.

  The detector 120 and the PC 90 are connected via USB 3.0 ports 79a and 79b having a high communication speed. Accordingly, the detector 120 can output the detection signal to the PC 90 at a high speed, and the time until the tomographic image 83 is generated can be shortened. In the present embodiment, even when the control unit 70, the HUB, the image sensor 35, the PC 90, and the like are connected, communication may be performed using USB 3.0.

  In the present embodiment, communication is performed using two lines of the USB 3.0 port and the USB 2.0 port. However, the present invention is not limited to this. For example, one may also serve as the other, and communication may be performed using a single line.

  The communication standard is not limited to USB, and other standards may be used. For example, a camera link standard or a Gigabit Ethernet (registered trademark) standard may be used. A plurality of standards may be used in combination. Moreover, not only a USB terminal but other connection terminals may be used. A plurality of types of connection terminals may be used.

  Although the detector 120 and the control unit 70 of the apparatus main body 1 are indirectly connected via the PC 90, the present invention is not limited to this. For example, the detector 120 may be connected to the control unit 70 by, for example, USB 3.0. In this case, the control unit 70 transmits a detection signal from the detector 120 to the PC 90. When receiving the detection signal, the PC 90 may generate a tomographic O image by calculation and transmit it to the control unit 70 of the apparatus main body 1.

  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.

1 Ophthalmology photographing apparatus 70 Control unit 71 HUB
74 Operation unit 75 Display unit 76, 77 USB signal line 78a, 78b USB 2.0 port 79a, 79b USB 3.0 port 90 Computer 95 Display unit

Claims (13)

A light source, a measurement optical path for guiding light from the light source as measurement light to the eye to be examined, a reference light path for guiding light from the light source as reference light, and the measurement light applied to the eye to be examined A detector for detecting interference with the reference light, and an interference optical system comprising:
A scanning means arranged in the measurement optical path for scanning the measurement light on the eye to be examined;
A front imaging optical system for imaging a front image of the eye to be examined;
An ophthalmologic imaging apparatus for obtaining a tomographic image of an eye to be examined based on a detection signal from the detector at each scanning position of the scanning means,
The ophthalmologic photographing apparatus includes:
It is connected via a data communication means with a host computer that generates a tomographic image based on a detection signal from the detector,
A detection signal from the detector is transmitted to the host computer via the data communication means, and a tomographic image generated by the host computer is received via the data communication means,
And a display control unit configured to display a tomographic image received via the data communication unit and a front image captured by the front imaging optical system on a display unit provided in the ophthalmologic photographing apparatus. A characteristic ophthalmologic photographing apparatus. The ophthalmologic photographing apparatus uses a first communication cable as the data communication means,
2. The ophthalmologic photographing apparatus according to claim 1, wherein the detector and the host computer are directly connected using the first communication cable as a dedicated cable. The ophthalmologic photographing apparatus further uses a second communication cable as the data communication means,
The ophthalmologic apparatus according to claim 2, wherein a tomographic image generated by the host computer is received via the second communication cable.   The ophthalmologic photographing apparatus according to claim 1, wherein the communication unit uses a universal serial bus.   5. The ophthalmic imaging apparatus according to claim 1, wherein the ophthalmic imaging apparatus further transmits / receives a control signal for detecting or controlling an apparatus state via the communication unit.   6. The ophthalmologic according to claim 1, wherein the display control means evaluates the tomographic image and displays the evaluation result on the tomographic image and the display unit provided in the ophthalmologic photographing apparatus. Shooting device. The ophthalmologic photographing apparatus includes:
The scanning means repeatedly scans the measuring light on the eye to be examined,
Based on a detection signal from the detector, it is connected via a data communication means with a host computer that generates a live tomographic image by a plurality of temporally continuous tomographic images,
In response to repeated scanning by the scanning means, a detection signal from the detector is transmitted to the host computer via the data communication means, and the live tomographic image generated by the host computer is transmitted to the data communication means. Received through
A display control unit for displaying the live tomographic image received via the data communication unit and the live front image captured by the front imaging optical system on a display unit provided in the ophthalmologic photographing apparatus; An ophthalmologic photographing apparatus according to any one of claims 1 to 6, further comprising: An ophthalmologic photographing apparatus according to any one of claims 1 to 7,
The host computer,
The front image captured by the front imaging optical system is transferred to the host computer via the communication means,
The host computer
An image processing unit for generating the tomographic image;
The front image transferred via the data communication unit, the tomographic image generated by the image processing unit, a second display control unit for displaying on a display unit provided in the host computer,
An ophthalmologic photographing system comprising: An ophthalmologic photographing apparatus according to any one of claims 1 to 7,
An ophthalmic imaging program executed in an ophthalmic imaging system comprising the host computer,
By being executed by the processor of the ophthalmic imaging system,
A transfer step of transferring a front image captured by the front imaging optical system to the host computer via the communication means;
An image processing step of generating the tomographic image by the host computer;
A display control step of displaying the front image transferred via the data communication means and the tomographic image generated by the image processing unit on a display unit provided in the host computer;
Is executed in the ophthalmologic imaging system. A light source, a measurement optical path for guiding light from the light source as measurement light to the eye to be examined, a reference light path for guiding light from the light source as reference light, and the measurement light applied to the eye to be examined A detector for detecting interference with the reference light, and an interference optical system comprising:
A scanning means arranged in the measurement optical path for scanning the measurement light on the eye to be examined;
A front imaging optical system for imaging a front image of the eye to be examined;
An ophthalmologic photographing apparatus for obtaining a tomographic image of the eye to be examined based on a detection signal from the detector at each scanning position of the scanning means,
A host computer connected to the ophthalmic imaging apparatus via data communication means;
An image processing unit that generates a live tomographic image based on a plurality of temporally continuous tomographic images based on a detection signal from the detector;
A first display control unit that displays the live tomographic image generated by the image processor and the front image captured by the front imaging optical system on a display unit provided in the ophthalmologic photographing apparatus;
A second display control unit that displays the live tomographic image generated by the image processor and the front image captured by the front imaging optical system on a display unit provided in the host computer;
An ophthalmologic photographing system comprising: The image processing unit is provided in the host computer,
The ophthalmologic photographing apparatus receives the live tomographic image generated by the image processing unit via the data communication unit,
The first display control unit displays the live tomographic image received via the data communication unit and a front image captured by the front imaging optical system on a display unit provided in the ophthalmologic photographing apparatus. The ophthalmologic photographing system according to claim 10, which is displayed. The image processing unit is provided in the ophthalmologic photographing apparatus,
The host computer receives the live tomographic image generated by the image processing unit and the front image captured by the front imaging optical system via the data communication unit,
The said 2nd display control part displays the said live tomographic image and front image received via the said data communication means on the display part provided in the said host computer. Ophthalmic photography system. The front imaging optical system captures a live front image by a plurality of temporally continuous front images as the front image,
The first display control unit displays the live tomographic image generated by the image processor and the live front image captured by the front imaging optical system on a display unit provided in the ophthalmologic photographing apparatus. Display
The second display control unit displays the live tomographic image generated by the image processor and the live front image captured by the front imaging optical system on a display unit provided in the host computer. A second display control unit;
The ophthalmologic imaging system according to claim 10.