JP2019063222A - Ophthalmology imaging apparatus - Google Patents

Abstract

To provide an ophthalmology imaging apparatus capable of reducing a generation time for a tomographic image of an eye.SOLUTION: An ophthalmography apparatus includes: an interference optical system for acquiring a tomographic image of a subject's eye using interference between measuring light with which the subject's eye is irradiated and reference light; an observation optical system for acquiring a front image of the subject's eye; a host PC 110 for receiving tomographic image data and the front image acquired by the interference optical system and the observation optical system to generate a tomographic image; and a control unit 70 that includes a storage unit 73 for temporarily storing the tomographic image data and the front image and transfers the tomographic image data and the front image stored in the storage unit to the host PC. The control unit and the host PC are connected using a general-purpose communication means 115.SELECTED DRAWING: Figure 3

Description

  The present disclosure relates to an ophthalmologic imaging apparatus that captures a tomographic image of an eye to be examined.

  There is known an ophthalmologic imaging apparatus that captures a tomographic image of an eye using optical coherence tomography (OCT). As this type of ophthalmologic imaging apparatus, for example, tomographic image data (spectrum data) acquired by imaging means for OCT provided in the imaging apparatus is immediately and continuously transmitted to a PC (personal computer), and the spectrum data is transmitted by the PC There is one in which a tomographic image is generated by arithmetic processing. In this ophthalmologic photographing apparatus, spectral data is acquired in a state where the positional deviation of the frontal image (SLO image) of the eye is within the allowable range (there is no fixation disparity), and the spectral data is transmitted to the PC. ing. As a result, a tomographic image (OCT image) at a preset position is generated. Then, in order to expand the versatility of the PC connectable to the ophthalmologic imaging apparatus, the ophthalmologic imaging apparatus and the PC are connected by general communication means, for example, a universal serial bus (USB) or the like. 1).

JP, 2015-195876, A

  However, advances in OCT technology in recent years have led to an increase in the imaging speed of OCT. That is, the repetition rate of the OCT scan (eg, the repetition rate of the B scan) is much higher than the frame rate of the video camera. For example, while the repetition interval of a typical B scan is about 2 to 3 ms, the frame rate of a video camera is about 20 to 50 FPS (frame interval about 20 to 50 ms). Therefore, in the band (upper limit of data transfer rate) of the communication means (for example, USB), there is a possibility that data transfer may not be performed corresponding to the imaging speed of the OCT. That is, in the above-described ophthalmologic imaging apparatus, the imaging speed of OCT may be faster than the data transfer speed by USB, and it may not be possible to continuously transfer acquired spectrum data to a PC. is there. Further, in the above-described ophthalmologic imaging apparatus, spectral data is acquired after it is confirmed that the positional deviation of the front image (SLO image) is within the allowable range.

  From these facts, although the imaging speed of OCT has been increased, the band speed of the communication means (for example, USB) and the imaging speed of the front image (SLO image) are affected (limited). It takes time to capture spectral data necessary for generating a tomographic image to a PC. Therefore, it has been difficult to shorten the time for generating a tomographic image. In addition, since the acquired spectrum data is immediately and continuously transferred to the PC, there is no spectrum data remaining when transfer of part of the data fails during a series of sequence processing such as map imaging. Therefore, it is necessary to perform imaging again in order to acquire the lost spectrum data, and the generation time of the tomographic image becomes longer.

  Then, this indication aims at providing the ophthalmologic imaging device which can shorten the generation time of the tomographic image of an eye, in order to solve an above-mentioned problem.

One mode of the present disclosure made to solve the above problems is
An interference optical system for acquiring a tomographic image of the subject's eye using interference of the measurement light and the reference light emitted to the subject's eye;
An observation optical system for acquiring a front image of the eye to be examined;
A host PC that receives tomographic image data and a front image acquired by the interference optical system and the observation optical system and generates the tomographic image;
A storage unit that temporarily stores the tomographic image data and the front image; and a control unit that transfers the tomographic image data stored in the storage unit and the front image to the host PC.
The ophthalmologic imaging apparatus is characterized in that the control unit and the host PC are connected by a general-purpose communication unit.

  According to the ophthalmologic imaging apparatus of the present disclosure, it is possible to shorten the generation time of the tomographic image of the eye.

It is an appearance side view of an ophthalmologic imaging device of an embodiment. It is a schematic block diagram of the optical system and control system in the ophthalmologic imaging device of embodiment. It is a block diagram showing a control system in an ophthalmologic imaging device of an embodiment. It is a figure which shows typically the SLO image displayed on a monitor. It is a flowchart which shows the processing content of the data transfer to PC of the image acquisition and acquisition image which are implemented by the apparatus main body. It is a figure which illustrates the generation procedure of an OCT image notionally. It is a figure which illustrates notionally the procedure which produces | generates an OCT image, carrying out feedback control of the scan position using galvano information.

  Hereinafter, typical embodiments of the present disclosure will be described in detail based on the drawings. First, the overall configuration of the ophthalmologic imaging apparatus will be described with reference to FIGS. 1 to 3. FIG. 1 is an external side view of the ophthalmologic imaging apparatus 1 of the present embodiment. FIG. 2 is a schematic configuration diagram of an optical system and a control system in the ophthalmologic imaging apparatus 1. FIG. 3 is a block diagram showing a control system of the ophthalmologic imaging apparatus 1.

<Overall configuration>
As shown in FIGS. 1 to 3 as an example, the ophthalmologic imaging apparatus 1 according to the present embodiment includes an anterior segment observation optical system 90, a projection optical system 150, an interference optical system (OCT optical system) 200, and an observation optical system. A control unit 70, a HUB 171, a personal computer (PC) 110, and the like are provided. Each optical system is housed in the apparatus main body 4. The control unit 70 and the PC 110 are connected via a universal serial bus (USB) via the USB 3.0 HUB 171.

  Specifically, the PC 110 is connected to the HUB 171 connected to the control unit 70 provided in the device main body 4 by the USB cable 115 via the USB ports 79 a and 79 b. The control unit 70 and the HUB 171 are connected by a USB cable 78. That is, in the present embodiment, the PC 110 is connected to the ophthalmologic imaging apparatus 1 by the USB cable 115. Thereby, the versatility of the PC 110 connectable to the ophthalmologic imaging apparatus 1 can be expanded. Then, as the PC 110, for example, a tablet PC or the like can be used besides a desktop type personal computer and a notebook type personal computer.

  That is, the PC 110 may include a CPU as a processor, an operation input unit (for example, a mouse, a keyboard, and the like), a memory (nonvolatile memory), and a display unit. The PC 110 may control the device body 4. That is, the PC 110 can communicate information such as the state of each component (such as the sensor state and the status), the control command from the PC 110, and the like with the control unit 70 as well as transmitting and receiving images (data). .

  In the present embodiment, the case where the control unit 70 and the PC 110 are connected by USB is illustrated, but the connection between the control unit 70 and the PC 110 is not limited to USB, and a general purpose data communication is possible. It can be performed using a communication means, that is, a communication means that is standard mounted on a commercially available PC, such as a LAN (wired or wireless, in addition to USB), Bluetooth (registered trademark), etc. besides USB. . And the data transfer rate of such a general-purpose communication means is slower than the imaging speed (frame rate) of OCT.

  The memory of the PC 110 is a non-transitory storage medium capable of retaining stored contents even when the supply of power is shut off. For example, as the memory, a hard disk drive, a flash ROM, a USB memory detachably attached to the PC 110, an external server, or the like can be used. The memory stores an imaging control program for controlling imaging of a front image and a tomographic image by the ophthalmologic imaging apparatus 1, an image processing program for processing the imaged image, and the like.

  In addition, the memory of the PC 110 stores an ophthalmologic analysis program for the PC 110 to be used as an ophthalmologic analyzer. That is, the PC 110 may double as the ophthalmologic analyzer. The memory also stores various information related to imaging, such as tomographic images (OCT data), three-dimensional tomographic images (three-dimensional OCT data), frontal images of the fundus, and imaging positions of tomographic images in a scanning line. Various operation instructions by the examiner are input to the operation input unit.

  On the other hand, the ophthalmologic photographing apparatus 1 has a base 2, a movable base 3 movable in a lateral direction (X direction) and a longitudinal (working distance) direction (Z direction) relative to the base 2, Device main body 4 as a housing which is provided movably in a three-dimensional direction and accommodates an optical system described later, and a face supporting unit 5 fixed to the base 2 for supporting the face of the subject . The apparatus body 4 is 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 provided on the moving table 3. The movable stand 3 is moved on the base 2 in the XZ direction by the operation of the joystick 7. Further, by rotationally operating the rotation knob 7a, the XYZ drive unit 6 is driven in Y, and the device body 4 is moved in the Y direction. A monitor 75 for displaying an anterior segment observation image and the like is provided on the examiner side of the apparatus main body 4.

  The ophthalmologic imaging apparatus 1 includes an interference optical system (OCT optical system) 200 for obtaining a tomogram of the eye E, and an observation optical system (scanning laser off-salmoscope (SLO) optical system) 300 for obtaining a front image of the eye E A projection optical system 150 for projecting an alignment index onto the eye E and an anterior eye observation optical system 90 for observing a front image of the anterior eye are provided. These optical systems are incorporated in the apparatus main body 4 and moved three-dimensionally with respect to the eye E by the above-described alignment moving mechanism (manual or motorized).

<Interference optical system (OCT optical system)>
The OCT optical system 200 includes a measurement optical system 200a and a reference optical system 200b. Further, the OCT optical system 200 separates the interference light by the reference light and the measurement light into each frequency (wavelength), and makes the light receiving means (in this embodiment, a one-dimensional light receiving element) separate the dispersed interference light. An optical system 800 is included.

  The dichroic mirror 40 reflects measurement light (for example, around λ = 840 nm) emitted from the OCT light source 27 used for the OCT optical system 200, and laser light emitted from the SLO light source 61 a used for the SLO optical system 300 (OCT light source It has the property of transmitting light of a wavelength different from 27 (for example, around λ = 780 nm). In this case, the dichroic mirror 40 makes the measurement light axis L 1 of the OCT optical system 200 coaxial with the measurement light axis L 2 of the SLO optical system 300.

  First, the configuration of the OCT optical system 200 provided on the reflection side of the dichroic mirror 40 will be described. The OCT light source 27 is an OCT light source that emits low coherent light used as measurement light and reference light of the OCT optical system 200, and for example, an SLD light source or the like is used. For the OCT light source 27, for example, a light source having a center wavelength of 840 nm and a band of 50 nm is used. The fiber coupler (splitter) 26 serves as the light splitting member and the light coupling member. The light emitted from the OCT light source 27 is divided by the fiber coupler 26 into reference light and measurement light through an optical fiber 38 a as a light guide. The measurement light travels through the optical fiber 38b to the eye E, and the reference light travels through the optical fiber 38c (polarizer 33) to the reference mirror 31.

  In the optical path that emits the measurement light toward the eye E, the end 39b of the optical fiber 38b that emits the measurement light, the collimator lens 21, the focusing optical member (focusing lens) 24, the scanning unit (optical scanner) 23, and , Relay lens 22 is arranged. The scanning unit 23 is configured by two galvano mirrors, and is used to scan light emitted from the measurement light source two-dimensionally (XY direction) on the fundus (test object) by driving the scanning drive mechanism 51. Be The scanning unit 23 may be configured of, for example, an AOM (acousto-optic element) or a resonant scanner.

  The dichroic mirror 40 and the objective lens 10 have a role as a light guiding optical system for guiding the OCT measurement light from the OCT optical system 200 to the fundus of the eye to be examined. The focusing lens 24 is movable in the optical axis direction by the drive of the drive mechanism 24a, and is used to correct the diopter with respect to the subject's eye fundus.

  The measurement light emitted from the end 39 b of the optical fiber 38 b is collimated by the collimator lens 21, reaches the scanning unit 23 through the focusing lens 24, and the reflection direction is changed by driving of the two galvano mirrors. Thereafter, the measurement light is reflected by the dichroic mirror 40 through the relay lens 22 and then condensed onto the fundus of the eye to be examined through the objective lens 10.

  Then, the measurement light reflected by the fundus is reflected by the dichroic mirror 40 through the objective lens 10 and directed to the OCT optical system 200, and the relay lens 22, two galvano mirrors of the scanning unit 23, the focusing lens 24 and the collimator lens The light beam is incident on the end 39 b of the optical fiber 38 b through 21. The measurement light incident on the end 39 b reaches the end 84 a of the optical fiber 38 d through the optical fiber 38 b, the fiber coupler 26, and the optical fiber 38 d.

  The reference optical system 200b generates a reference light that is combined with the reflected light acquired by the reflection of the measurement light at the fundus oculi Ef. The reference optical system 200 b may be a Michelson type or a Mach-Zehnder type. The reference optical system 200 b is formed of, for example, a reflection optical system (for example, the reference mirror 31), reflects the light from the fiber coupler 26 back to the fiber coupler 26 by being reflected by the reflection optical system, and guides it to the light receiving element 83. As another example, the reference optical system 200 b is formed of a transmission optical system (for example, an optical fiber), and guides the light from the fiber coupler 26 to the light receiving element 83 by transmitting the light without returning it.

  For example, an optical fiber 38c, an end 39c of an optical fiber 38c for emitting reference light, a collimator lens 29, and a reference mirror 31 are disposed in an optical path for emitting the reference light toward the reference mirror 31. The optical fiber 38c is rotationally moved by the drive mechanism 34 to change the polarization direction of the reference light. That is, the optical fiber 38c and the drive mechanism 34 are used as the polarizer 33 for adjusting the polarization direction.

  The polarizer 33 according to the present embodiment adjusts the polarization direction of at least one of the measurement light and the reference light in order to make the polarization directions of the measurement light and the reference light coincide with each other. The polarizer 33 is disposed in at least one of the measurement light path and the reference light path. The polarizer 33 is not limited to the above configuration, for example, a configuration that changes the polarization direction of light by adjusting the rotation angle of a half wave plate or a quarter wave plate centering on the optical axis; In addition, a configuration in which the polarization direction of light is changed by deformation is conceivable.

  Further, the reference mirror driving mechanism 50 drives the reference mirror 31 disposed in the reference light path in order to adjust the optical path length with the reference light. In the present embodiment, the reference mirror 31 is disposed in the reference optical path, and is configured to be movable in the optical axis direction so as to change the reference optical path length.

  The reference light emitted from the end 39c of the optical fiber 38c is collimated by the collimator lens 29 and reflected by the reference mirror 31, and then collected by the collimator lens 29 and enters the end 39c of the optical fiber 38c. . The reference light incident on the end 39c reaches the fiber coupler 26 via the optical fiber 38c (polarizer 33).

  Then, the reference light generated as described above by the light emitted from the OCT light source 27 and the fundus reflection light by the measurement light irradiated to the eye fundus Ef to be examined are synthesized by the fiber coupler 26 and made into interference light. , And is emitted from the end 84a through the optical fiber 38d. Spectroscopic optical system 800 (spectrometer section) for separating interference light into frequency components in order to obtain interference signals for each frequency has collimator lens 80, grating mirror (diffraction grating) 81, condensing lens 82, and light receiving element 83. . In the present embodiment, a one-dimensional element (line CCD) having sensitivity in the infrared range is used as the light receiving element 83. The light receiving element 83 is connected to the control unit 70 (second control unit 270) by a camera link.

  Here, the interference light emitted from the end 84 a is collimated by the collimator lens 80 and then separated into frequency components by the grating mirror 81. Then, the interference light split into the frequency components is condensed on the light receiving surface of the light receiving element 83 through the condensing lens. Thereby, spectrum data of interference fringes is recorded on the light receiving element 83, and based on the data, a tomographic image of the eye to be examined E is generated in the PC 110.

  That is, by analyzing spectrum data acquired by the light receiving element 83 using Fourier transform, it becomes possible to measure information in the depth direction of the subject's eye. Then, a tomographic image can be obtained by scanning the measurement light in a predetermined transverse direction on the fundus oculi Ef by the scanning unit 23. For example, a tomographic image (fundus tomographic image) on the XZ plane or the YZ plane of the eye fundus Ef to be examined can be obtained by scanning in the X direction or Y direction (in the present embodiment, the measurement light is thus The method of obtaining a tomogram by one-dimensional scanning with respect to Furthermore, the drive of the scanning unit 23 is controlled to two-dimensionally scan the measurement light in the X and Y directions, and based on the output signal from the light receiving element 83, a two-dimensional moving image or the It is also possible to acquire a three-dimensional image of the eye fundus of an eye to be examined.

  The spectrum data acquired by the light receiving element 83 is temporarily stored in the memory 73 in the control unit 70, transferred to the PC 110 at a predetermined timing by a command of the processor 71 in the control unit 70, and received by the PC 110. . Details of the data transfer to the PC 110 will be described later.

<Observation optical system (SLO optical system)>
Next, the observation optical system (SLO optical system) 300 disposed in the transmission direction of the dichroic mirror 40 will be described. The SLO optical system 300 is an optical system for acquiring a front image of the fundus oculi Ef to be examined. The SLO optical system 300 is roughly divided into an illumination optical system for illuminating the eye fundus Ef to be examined and a light receiving optical system for receiving the reflected light of the eye to be examined illuminated by the illumination optical system by the light receiving element. A front image of the fundus oculi Ef to be examined is obtained based on the received light signal.

  The light emitting unit 61 includes a first light source (SLO light source) 61 a, a second light source (vision light source) 61 b, a mirror 69, and a dichroic mirror 101.

  The SLO light source 61a is a light source that emits highly coherent light, and for example, a light source of λ = 780 nm (a laser diode light source, an SLD light source, or the like) is used. The fixation light source 61 b is light of a wavelength in the visible range, and for example, a light source of λ = 630 nm (a laser diode light source, an SLD light source, or the like) is used. The laser light emitted from the SLO light source 61 is transmitted through the dichroic mirror 101 and travels to the beam splitter 62 through the collimator lens 102. The visible light emitted from the fixation light source 61b is bent by the mirror 69, reflected by the dichroic mirror 101, and made coaxial with the laser light emitted from the SLO light source 61a.

  In the optical path for emitting the laser light emitted from the SLO light source 61a toward the eye E to be examined, the collimator lens 102, the focusing lens 63 movable in the optical axis direction according to the refraction error of the eye to be examined, Thus, a scanning unit 64, a relay lens 65, and the objective lens 10, each of which is a combination of a galvano mirror and a polygon mirror capable of scanning the measurement light at high speed in the X and Y directions on the fundus are arranged. In addition, the reflecting surfaces of the galvano mirror and the polygon mirror of the scanning unit 64 are disposed at substantially conjugate positions with the pupil of the eye to be examined.

  Further, a beam splitter 62 is disposed between the SLO light source 61 a and the focusing lens 63. Then, in the reflection direction of the beam splitter 62, a condenser lens 66 for constituting a confocal optical system, a confocal aperture 67 placed at a position conjugate to the fundus, and a light receiving element 68 for SLO are provided. There is.

  Here, the laser light (measurement light) emitted from the SLO light source 61a passes through the beam splitter 62, reaches the scanning unit 64 through the focusing lens 63, and the reflection direction is driven by the drive of the galvano mirror and the polygon mirror. be changed. Then, the laser light reflected by the scanning unit 64 is transmitted through the dichroic mirror 40 through the relay lens 65 and then condensed onto the eye fundus Ef to be examined through the objective lens 10.

  The laser beam reflected by the fundus oculi Ef passes through the objective lens 10, the relay lens 65, the galvano mirror and polygon mirror of the scanning unit 64, and the focusing lens 63, and is reflected by the beam splitter 62. Thereafter, the light is condensed by the condenser lens 66 and then detected by the light receiving element 68 through the confocal aperture 67. The SLO image detected by the light receiving element 68 is input to the control unit 70 and temporarily stored in the memory 72 of the control unit 70. The SLO image is obtained by scanning the laser beam in the vertical direction (sub-scan) by the galvano mirror provided in the scanning unit 64 and scanning the laser beam in the horizontal direction (main scan) by the polygon mirror. Thereafter, the SLO image stored in the memory 72 is transferred to the PC 110 at a predetermined timing according to an instruction of the processor 71 of the control unit 70 and received by the PC 110, and then the fundus of the eye to be examined based on the SLO image received by the PC 110 A front image of Ef is generated. The details of data transfer to the PC 110 will be described later.

<Projection optical system>
The projection optical system 150 is used to project an index on the cornea Ec. In the light projecting optical system 150, as shown in the lower left dotted line in FIG. 2, a plurality of near infrared light sources are arranged concentrically around the optical axis at an interval of 45 degrees. The light projection optical system 150 includes an infrared light source 151 and a first index light projection optical system (0 degrees and 180 degrees) having a collimating lens 152, which are arranged symmetrically with respect to a vertical plane passing through the optical axis L1. And a second index projection optical system having six near infrared light sources 153 disposed at a position different from the first index projection optical system. In FIG. 2, for convenience, only the first index projection optical system (0 degrees and 180 degrees) and a part of the second index projection optical system (45 degrees and 135 degrees) are illustrated. The light source 151 doubles as the anterior segment illumination. Of course, a light source for illuminating the anterior segment may be separately provided.

Front eye observation optical system
The anterior eye observation optical system 90 is disposed to image the eye E to obtain an anterior eye image. The anterior eye observation optical system 90 includes an objective lens 10, a dichroic mirror 91, an imaging lens 95, and a two-dimensional imaging element (two-dimensional light receiving element) 97.

  The anterior eye part reflected light and alignment light flux by the light projecting optical system 150 are reflected by the dichroic mirror 91 through the objective lens 10, and then received by the two-dimensional imaging element 97 through the imaging lens 95. The dichroic mirror 91 transmits the measurement light of the OCT optical system 200, and reflects the light from the anterior segment illuminated by the light projecting optical system 150. The output of the two-dimensional imaging element 97 is transmitted to the control unit 70, and the monitor 75 displays an anterior segment image captured by the two-dimensional imaging element 97.

  In the present embodiment, the projection optical system 150 and the anterior eye observation optical system 90 are used as alignment detection optical systems for guiding the apparatus main body 4 to a predetermined positional relationship with the eye E. For example, the light projection optical system 150 and the anterior eye observation optical system 90 are used to guide the eye E and the apparatus main body 4 to a predetermined proper working distance.

  The alignment detection optical system, as a configuration for detecting the alignment state of the device main body 4 with respect to the eye E in the Z direction, projects alignment light obliquely to the eye E and reflects light reflected from the eye E It is also possible to receive light from to detect the Z alignment.

<Control system>
The control unit 70 performs control of the entire apparatus, measurement, processing of image data, and the like. The control unit 70 is connected to the monitor 75 and controls the display image. The control unit 70 also includes an operation unit 74 for performing various operations, drive mechanisms 24 a, 34, 50, 51, 52, 63 a, light sources 27, 61 a, 61 b, 151, 153, light receiving elements 83, and imaging elements 97. The light receiving element 68, the XYZ drive unit 6, the joystick 7 and the like are connected.

  The control unit 70 detects the alignment state between the eye E and the apparatus main body 4 based on the imaging signal output from the imaging element 97, and outputs the detection result to the monitor 75. Of course, the detection result may also be output to a monitor provided in the PC 110. In addition, the control unit 70 controls the drive of the XYZ drive unit 6 so that the alignment detection result (for example, the amount of alignment deviation) satisfies a predetermined allowable range, and automatically aligns the device relative to the eye E May be performed.

  As shown in FIG. 3, such a control unit 70 includes a processor 71 and memories 72 and 73, and performs control, measurement, processing of image data, and the like in each optical system. The processor 71 may be, for example, a central processing unit (CPU), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), a programmable logic device (for example, a simple programmable logic device (SPLD), a complex programmable logic device (CPLD)). And circuits such as FPGA (Field Programmable Gate Array). The processor reads out and executes a program stored in the memory, for example, to perform processing for attaching additional information to an acquired image, which will be described later, and processing for transferring data to the PC 110.

  The control unit 70 is connected to the SLO light receiving element 68 and the two-dimensional imaging element 97 by the video cables 173 a and 173 b, and is connected to the light receiving element 83 by the camera link 273. Further, the control unit 70 is connected to the HUB 171 by the USB cable 172.

<Operation of the ophthalmologic imaging apparatus>
Subsequently, the operation of the ophthalmologic imaging apparatus 1 having the above configuration will be described. First, the examiner causes the face support unit 5 to fix the face of the subject and instructs the subject to fixate a fixation target (not shown). At this time, the anterior segment image captured by the two-dimensional imaging element 97 is displayed on the monitor 75.

<Setting of shooting conditions>
Next, the examiner operates the joystick 7 to move the apparatus main body 4 and performs alignment work so that the measurement optical axis is positioned at the pupil center of the anterior segment. This alignment operation may be performed using an automatic alignment mode or may be performed manually.

  Then, the control unit 70 determines the suitability of the alignment state, and starts optimization control based on the determination result. Control unit 70 determines whether the amount of alignment deviation (displacement) is within a predetermined allowable range (for example, the deviation from the alignment reference position in the XYZ directions is within 0.5 mm). For example, the control unit 70 determines the suitability of the alignment in the XYZ directions based on whether or not the alignment deviation amount in the XYZ directions is within the allowable range of the alignment completion.

  The control unit 70 determines that the alignment is appropriate when the amount of alignment deviation in the XYZ directions is within the allowable range of the alignment completion. When the control unit 70 determines that the alignment in the XYZ directions is appropriate, the control unit 70 stops the drive of the XYZ drive unit 6 and outputs an alignment completion signal. On the other hand, when the alignment displacement amount in the XYZ directions is not within the allowable range of the alignment completion, the control unit 70 determines that the alignment is not appropriate and performs the automatic alignment.

  When the alignment completion signal is output, the control unit 70 issues a trigger signal for starting optimization control, and starts the control operation of optimization. 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, control of optimization is control of optical path length adjustment, focus adjustment, and adjustment of polarization state (polarizer adjustment). In optimization control, it is sufficient that a certain tolerance condition for the fundus can be met, and it is not necessary to adjust to the most appropriate state.

  During the optimization control, the control unit 70 performs control (tracking) to cause the subject eye to track the device main body 4 so that the alignment displacement amount satisfies the allowable range. For example, the control unit 70 determines whether the alignment deviation amount in the X, Y, and Z directions continues within the allowable range of alignment completion for a predetermined time (for example, 10 frames of image processing or 0.3 seconds). It is determined whether the proper state of orientation alignment continues. The control unit 70 determines that the appropriate state of alignment continues if the alignment deviation amount in the XYZ directions continues to be within the allowable range of alignment completion for a certain period of time, and the XYZ drive unit 6 The drive maintains the stopped state.

  Further, the control unit 70 continues the appropriate state of alignment if the amount of alignment deviation in the XYZ directions does not continuously fall within the allowable range of alignment completion for a certain period of time and deviates from the allowable range. It judges that it does not carry out and starts the drive of the XYZ drive part 6, and performs automatic alignment. In this case, for example, the control unit 70 continuously performs optimization control even during driving of the XYZ driving unit 6 (during automatic alignment).

  Of course, the control unit 70 may be configured to stop the optimization control when the alignment deviation amount is out of the allowable range. In addition, after the optimization control is stopped, the control unit 70 may be configured to restart the optimization control when the alignment deviation amount returns to within the allowable range. When automatic alignment is performed, optimization control may be performed again from the initial position.

  In optimization control, the control unit 70 sets the positions of the reference mirror 31 and the focusing lens 24 to initial positions as control of initialization. After the initialization is completed, the control unit 70 moves the reference mirror 31 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 acquires in-focus position information with respect to the fundus of the eye to be examined based on the SLO fundus image acquired by the light receiving signal output from the light receiving element 68. When the in-focus position information is acquired, the control unit 70 moves the focusing lens 24 to the in-focus position, and performs auto-focus adjustment (focus adjustment). The in-focus position may be any position at which the contrast of the tomographic image acceptable as the observation image can be acquired, and is not necessarily the optimum position of the in-focus state.

  Then, after the focus adjustment is completed, the control unit 70 again moves the reference mirror 31 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 completion of the second optical path length adjustment, the control unit 70 drives the polarizer 33 for adjusting the polarization state of the reference light to adjust the polarization state of the measurement light (for details, see Japanese Patent Application No. 2012-56292). In this manner, completion of the optimization control enables observation of the fundus site desired by the examiner with high sensitivity and high resolution.

  Thereby, the SLO image 15 of high sensitivity and high resolution as shown in FIG. 4 is displayed on the monitor 75. Of course, the SLO image 15 may be displayed on a monitor provided in the PC 110. Then, the examiner sets the position of the tomographic image (OCT image) to be captured from the SLO image 15 on the monitor 75 observed in real time. Here, the examiner moves the scan line SL with respect to the SLO image 15 using the operation unit 74, and sets a scan position (for example, a drag operation of the scan line SL). When the scanning line SL is set to be in the X direction, imaging of the tomographic image on the XZ plane is performed, and when the scanning line SL is set to be in the Y direction, imaging of the tomographic image on the YZ plane is performed. It is supposed to be. In addition, the scan line SL may be set to an arbitrary shape (for example, an oblique direction, a circle, or the like).

<Shooting operation>
As described above, when the imaging start switch 74a provided on the operation unit 74 is operated by the examiner after the setting of the imaging conditions is completed, the control unit 70 starts imaging of the image. Note that the switch for starting imaging can also be provided in a portion different from the operation unit 74. For example, the button 7b of the joystick 7 can be used as a shooting start switch. Then, the SLO image and the OCT image (spectrum data) are acquired in parallel by the control unit 70, and each acquired image is transferred to the PC 110, and a plurality of OCT images (spectrum data) are added and averaged by the PC 110. As a result, an OCT image in which noise components are suppressed is generated.

  Therefore, a photographing operation for generating such an OCT image will be described with reference to FIGS. 5 to 7. FIG. 5 is a flow chart showing the processing contents of image acquisition performed in the apparatus main body and data transfer to the PC of the acquired image. FIG. 6 is a diagram for conceptually explaining an OCT image generation procedure. FIG. 7 is a diagram conceptually illustrating a procedure of generating an OCT image while performing feedback control of a scan position using galvano information.

  First, the process performed on the device body side will be described with reference to FIG. When the imaging start signal from the operation unit 74 is input, the control unit 70 starts an operation of capturing the OCT image (spectral data) and the SLO image. That is, the control unit 70 starts capturing the SLO image from the light receiving element 68, and starts capturing tomographic image data at a scanning position corresponding to the scanning line SL detected by the light receiving element 83. In this case, for example, the spectrum data acquired by the device main body 4 may be transferred to the PC 110, and an OCT image may be generated by the PC 110. Further, the present invention is not limited to this, and an OCT image may be generated in the device main body 4 based on the spectrum data acquired in the device main body 4, and the generated OCT image may be transferred to the PC 110. That is, as tomographic image data, for example, spectral data may be used, or an OCT image based on spectral data may be used.

  Specifically, the processor 71 creates a buffer in the memory 72 (step S10). Next, the processor 71 obtains an SLO image. That is, the processor 71 acquires the SLO image illuminated by the SLO light source 61a and captured by the SLO light receiving element 68 as a still image (step S11). If the SLO image is acquired (step S11: YES), the processor 71 attaches a time stamp to the SLO image as additional information (step S12). Then, the processor 71 develops (temporarily stores) the SLO image with the time stamp attached thereto in the buffer created in the memory 72 (step S13). That is, the processor 71 attaches a time stamp when expanding the SLO image into the buffer of the memory 72.

  In parallel to the SLO image capturing process, an OCT image (spectral data) capturing process is performed. That is, the processor 71 creates a buffer in the memory 73 (step S20). Then, the processor 71 acquires an OCT image (spectral data) (for example, data for 1 B scan) (step S21). That is, the processor 71 causes the scanning unit 23 to obtain a tomographic image (B-scan image) of the fundus oculi corresponding to the position of the scanning line SL based on the display position of the scanning line SL set on the SLO image 15. Is driven to scan the measurement light. Then, the detection signal from the light receiving element 83 at that time is acquired. If an OCT image (spectrum data) is acquired (step S21: YES), the processor 71 attaches a time stamp and / or galvano information (scanning position information) as additional information to the OCT image (spectrum data) (step S22). That is, a timestamp and / or galvano information (scanning position information) is attached to each OCT image (spectral data) for 1 B scan. Then, the processor 71 develops (temporarily stores) the OCT image (spectral data) for 1 B scan attached with the time stamp and / or the galvano information in the buffer created in the memory 73 (step S23). That is, the processor 71 attaches a time stamp and / or galvano information when expanding 1 B scan of OCT images (spectral data) in the buffer of the memory 73.

  Here, the time stamp is attached at the timing of being expanded in the buffer created in each of the memories 72, 73 based on the counter provided in each of the memories 72, 73. The counters provided in the memories 72 and 73 start counting up and are synchronized when the power of the ophthalmologic imaging apparatus 1 is turned on or when an imaging start signal is input. Thus, it is possible to synchronize the time stamp attached to the SLO image with the time stamp attached to 1 B scan of spectrum data.

  In the present embodiment, for example, as shown in FIG. 6, a timestamp is attached to the OCT image (spectral data) in order as T1, T2, T3, T4,. Galvano information G1, G1,... For specifying the 23 states (scanning positions) are attached. On the other hand, since the SLO image has a slower imaging speed (frame rate) than the OCT image (spectral data), time stamps such as T1, T4, T7, T10, ... are attached in the order of acquisition of the SLO image. .

  Then, since the time stamp attached to the SLO image and the time stamp attached to the OCT image (spectral data) for 1 B scan are synchronized, for example, the same time stamps T1, T4, T7, T10, It can be determined that the image to which ... is attached is acquired (photographed) at the same timing. That is, by using the time stamp attached to each image, the SLO image and the OCT image (spectral data) can be associated with each other. Therefore, an OCT image (spectral data) acquired at the same timing as the SLO image is acquired can be identified. In addition, when a time stamp is attached to the SLO image and the OCT image, the time stamp is considered in consideration of the timing shift from the scan timing (for example, at the start of scan, at the end of scan) for image acquisition to the buffer. May be attached. For example, the control unit 70 may add an offset to the timing when the SLO image or the OCT image is developed in the buffer by the timing deviation. The offset amount may be, for example, a known value, and may be different between the SLO image and the OCT image. According to this, since the time stamp can be added at the scanning operation timing for acquiring the SLO image or the OCT image, it is possible to grasp the timing for acquiring each image more accurately, and various controls can be performed with high accuracy. it can.

  Moreover, the state (scanning position) of the scanning part 23 when each OCT image (spectrum data) is acquired by using the Galvano information G1, G1, ... attached to each OCT image (spectrum data) Can understand.

  In the present embodiment, a time stamp or galvano information is attached to the image as the additional information, but other information (for example, information of each part, setting value, etc.) may be attached as the additional information. The additional information includes, for example, alignment information between the device body and the eye (for example, the working distance between the eye and the device), the completion position of the optical path length adjustment (for example, the drive position of the optical path length adjustment member after optical path length adjustment) ) May be. In addition, as an optical path length adjustment member, it may be a reference mirror, for example, it is not limited to this, and an optical path length adjustment member may be an optical member arrange | positioned in the optical path of measurement light.

  In this manner, the SLO image and the OCT image (spectral data) are acquired by the control unit 70, and when each image is expanded in the buffer of each of the memories 72 and 73, each of those images is transferred to the PC 110. Specifically, in the control unit 70, the processor 71 detects the state of the communication band α (upper limit of data transfer rate) of the USB cable 115 connected to the PC 110. That is, it is detected how much data transferable capacity in the USB cable 115 at the present time is. Then, if there is a vacancy in the communication band α of the USB cable 115 (step S14: YES), in other words, if the data transferable capacity of the USB cable 115 at this time is larger than the data capacity to be transferred, The expanded SLO image is transferred to the PC 110 via the USB cable 172, the HUB 171, and the USB cables 78 and 115 (step S15). At this time, the PC 110 receives the SLO image output (transferred) from the memory 72.

  Then, when the transfer of the SLO image expanded in the buffer of the memory 72 to the PC 110 is completed and the reception of the PC 110 is completed, the processor 71 makes the buffer of the memory 72 empty (step S16). Therefore, the acquired SLO image is stored in the buffer of the memory 72 until the transfer to the PC 110 is completed. Thereafter, the acquisition of the SLO image and the transfer processing to the PC 110 are repeated until the predetermined termination condition A described later is satisfied, and when the termination condition A is satisfied (step S17: YES), the SLO image is captured (photographed) Ends.

  Further, the processor 71 detects the state of the communication band α (upper limit of data transfer rate) of the USB cable 115 connected to the PC 110 and expands it in the buffer of the memory 72 if there is space (step S24: YES). The OCT image (spectrum data) is transferred to the PC 110 via the USB cable 172, the HUB 171, and the USB cables 78 and 115 (step S25). At this time, the communication band α of the USB cable 115 has a vacancy, but the OCT image (spectrum data) expanded in the buffer of the memory 72 has a large capacity, and it is difficult to transmit data at one time in the vacancy of the communication band α In this case, the data capacity to be transmitted may be varied according to the free space of the communication band α. That is, in order to stably secure the USB communication band α, the band α may be managed at the transmission timing of the OCT image (spectrum data), or the band α is free by the response from the communication partner side (PC 110). It may be monitored and managed.

  As a result, even when the acquisition (shooting) speed of the OCT image (spectrum data) at the light receiving element 83 exceeds the transfer upper limit speed of USB 3.0, the B scan is performed until the end condition A described later is satisfied. It can be performed continuously without interruption and OCT images (spectral data) can be acquired continuously. That is, an OCT image (spectral data) can be acquired at the maximum frame rate of the light receiving element 83. Therefore, still images of the OCT images necessary for generating the OCT image can be acquired in a short time.

  When the transfer of the OCT image (spectrum data) expanded in the buffer of the memory 72 to the PC 110 is completed and the reception of the PC 110 is completed, the processor 71 opens the buffer of the memory 72 (step S26). Therefore, the OCT image (spectral data) acquired in the buffer of the memory 72 is stored until the transfer to the PC 110 is completed. Thereby, for example, even when transfer of a part of OCT images (spectrum data) fails during a series of sequence processing such as map imaging, the OCT images (spectrum data) stored in the buffer of the memory 72 It can be retransmitted. Therefore, even if the transfer of the OCT image (spectral data) fails, there is no need to re-acquire (capture) the OCT image (spectral data).

  Thereafter, the acquisition and transfer processing of the above-described OCT image (spectral data) is repeated until the predetermined end condition A is satisfied (step S27). Note that the predetermined end condition A is that the still image of the OCT image determined to be usable for the addition averaging process by the PC 110 reaches the number of sheets set to the upper limit of the number of sheets to be added. That is, capturing (photographing) of the OCT image (spectrum data) is performed until the still image of the OCT image used for the addition averaging process in the PC 110 reaches the setting upper limit number of addition sheets.

<OCT image generation>
Next, processing (generation of an OCT image) performed by the PC 110 will be described with reference to FIG. The PC 110 that has received each image from each of the memories 72 and 73 of the control unit 70 first sets the SLO image when the scanning line SL is set as the reference image. Then, the PC 110 detects the positional deviation (displacement amount) of the SLO image sequentially received from the control unit 70 with respect to the reference image by image processing.

  At this time, if the positional deviation of the received SLO image is within the allowable range, the PC 110 captures the OCT image (spectrum data) acquired at the same timing as the SLO image into the memory of the PC 110 as a still image (decision ○ ). On the other hand, when the positional deviation of the received SLO image is not within the allowable range, the PC 110 discards the OCT image (spectrum data) acquired at the same timing as the SLO image (determination x).

  Specifically, in the present embodiment, for example, when it is determined that the positional deviation of the SLO image of the time stamp T1 is within the allowable range (decision ○), the OCT image of the time stamp T1 is a still image and stored in the memory of the PC 110. It is captured. Galvano information G1 is also attached to the OCT image (spectral data).

  Next, if it is determined that the positional deviation of the SLO image at time stamp T4 is not within the allowable range (judgment x), the OCT images (spectral data) of time stamps T2 to T4 are acquired in a state of positional deviation It is judged that is and is destroyed.

  Then, if it is determined that the positional deviation of the SLO image of the time stamp T7 is within the allowable range (decision O), the OCT image of the time stamp T7 is taken into the memory of the PC 110 as a still image. In addition, an OCT image (spectral data) of T5 or later (T5, T6) before time stamp T7 is determined to be acquired in a misaligned state and discarded.

  Furthermore, if it is determined that the positional deviation of the SLO image of the time stamp T10 is within the allowable range (decision O), the OCT image of the time stamp T10 is taken into the memory of the PC 110 as a still image. In addition, it is determined that the OCT image (spectral data) of T8 or later (T8, T9) before time stamp T10 is acquired without displacement, and is taken into the memory of the PC 110 as a still image.

  Thereafter, such processing is repeatedly performed, and when the still image of the OCT image acquired in the memory of the PC 110 reaches the set upper limit of the number of additions after being judged as “decision ○”, the PC 110 receives the OCT image acquired in the memory Of the still images are subjected to an averaging process to generate an OCT image (B-scan image).

  As described above, in the ophthalmologic imaging apparatus 1 of the present embodiment, a buffer is created in the memory 73, and the OCT image (spectral data) is temporarily stored in the buffer. In addition, when storing in the buffer of the memory 73, a time stamp that associates the SLO image with the OCT image (spectral data) is attached. That is, the OCT image (spectral data) to which the time stamp is attached is stored in the buffer of the memory 73. Thereby, after acquiring an OCT image (spectrum data), using the time stamp, the OCT image (spectrum data) acquired (photographed) in a state where the positional deviation of the SLO image is not within the allowable range is specified. Can. Therefore, it is possible to capture (capture) an OCT image (spectral data) without being affected (limited) by the USB band or the SLO image capture speed as in the prior art. As a result, it is possible to shorten the generation time of the arithmetically averaged OCT image.

  Further, in the ophthalmologic imaging apparatus 1 of the present embodiment, since the connection with the PC 110 is performed by the USB, the versatility of the connected PC 110 is high. Therefore, according to the ophthalmologic photographing apparatus 1 of the present embodiment, it is possible to generate a high quality OCT image with reduced noise in a short time while the versatility of the connected PC 110 is high. As a result, the examination time is shortened, so that the burden on the subject can be reduced.

  Here, in the case of generating a three-dimensional OCT image, the above-described acquisition (shooting) of the OCT image (spectral data) is performed on a plurality of scan lines (for example, 256 lines). For this reason, in the band α (upper limit of data transfer rate) of the USB cable 115, there is a possibility that data transfer to the PC 110 can not be performed corresponding to the imaging rate of the OCT image (spectral data).

  However, in the ophthalmologic imaging apparatus 1 of the present embodiment, the controller 70 causes the controller 72 to temporarily write the OCT image (spectral data) in the buffer of the memory 72, and when there is a space in the band α of the USB cable 115, the memory 72 The OCT image (spectral data) temporarily written in the buffer of is transferred to the PC 110. Thus, even when generating a three-dimensional OCT image, an OCT image (spectrum data) can be acquired at the maximum frame rate of the light receiving element 83 without being restricted by the band α of the USB cable 115.

  Further, as described above, the OCT image (spectral data) is associated with the SLO image by the time stamp. Therefore, it is possible to specify an OCT image in which the subject's eye has a positional shift (fixation shift) after photographing by using a time stamp. As a result, the imaging speed of the OCT image (spectral data) is not limited to the imaging speed of the SLO image as in the related art. Therefore, the OCT image (spectral data) required to generate a three-dimensional OCT image can be acquired in a very short time.

  Then, when a three-dimensional OCT image is generated from the acquired OCT image (spectrum data) in the PC 110, the OCT image (spectrum data) in a certain scan line becomes defective due to positional deviation, or the data amount is insufficient. In some cases, based on the galvano information attached to the OCT image (spectral data), the OCT image (spectral data) in the scan line can be reacquired.

  For example, the PC 110 can receive, from the memory 72, OCT images (spectral data) for scan lines, for example, 256 lines necessary for generating a three-dimensional OCT image at one time, and generates the three-dimensional OCT image In this case, it is assumed that a defect or deficiency of data in a certain scan line is detected. In that case, a scan line in which a defect or deficiency of data is detected is identified based on galvano information, and an OCT image (spectral data) in the identified scan line is reacquired. Then, using the reacquired OCT image (spectral data), a three-dimensional OCT image is generated.

  Alternatively, while processing for generating a three-dimensional OCT image is being performed on an OCT image (spectral data) for an example of scan lines that the PC 110 sequentially receives from the memory 72, defect / insufficient data in a certain scan line Is detected. In that case, the imaging of the OCT image (spectral data) currently being acquired is temporarily suspended, and a scan line in which a defect or deficiency of data is detected is identified based on the galvano information, and the OCT image in the identified scan line Reacquire (spectral data).

  As described above, the acquired OCT image (the case where the PC 110 receives the OCT images (spectral data) for the scan line necessary for generation of the three-dimensional OCT image collectively or collectively every few sequences) When a defect or deficiency occurs in the spectrum data), it is possible to instantly reacquire an OCT image (spectrum data) for the defect or deficiency. Therefore, an OCT image (spectral data) required to generate a high-quality three-dimensional OCT image can be acquired in a very short time. Therefore, a high quality three-dimensional OCT image can be generated in a very short time.

  Further, in the ophthalmologic imaging apparatus 1, when the positional displacement is detected in the SLO image when generating the OCT image by the PC 110, the OCT image (spectral data) corresponding to the SLO image is discarded and displacement of the positional displacement is performed. A galvano correction command (scanning position correction command: a galvano control signal corresponding to the displacement amount of positional deviation) according to the amount may be transmitted to the control unit 70. As a result, the control unit 70 that has received the galvano correction command controls the drive mechanism 24 a based on the galvano correction command, and appropriately drives the two galvano mirrors provided in the scanning unit 23. As a result, even if positional deviation occurs in the SLO image, an OCT image (spectral data) of the fundus oculi corresponding to the position of the scanning line SL can be acquired.

  Specifically, as shown in FIG. 7, when the PC 110 determines that the positional deviation of the SLO image of the time stamp T1 is within the allowable range (decision ○), the OCT image of the time stamp T1 is taken as a still image of the PC 110. Capture to memory. Galvano information G1 is attached to the OCT images (spectral data) of time stamps T1 to T3.

  Next, when it is determined that the positional deviation of the SLO image at time stamp T4 is not within the allowable range (decision x), the PC 110 discards the OCT image (spectral data) at time stamps T2 to T4 and performs galvano correction. The command is sent to the control unit 70. The control unit 70 controls the drive mechanism 24 a based on the galvano correction command to appropriately drive the two galvano mirrors provided in the scanning unit 23. Assuming that an OCT image (spectrum data) after time stamp T6 is acquired after the galvano mirror of scanning unit 23 is driven, galvano information is changed from G1 to G2 from the OCT image (spectrum data) of time stamp T6 Attached. In this case, the PC 110 may cancel the scan at the time of obtaining the OCT image (spectral data) of the time stamp T5 and shift to the scan for obtaining the next OCT image (time stamp T6).

  Then, when receiving the SLO image of the time stamp T7, the PC 110 determines that it matches the previous SLO image (time stamp T4) from the displacement amount of the positional deviation with respect to the reference image (decision ○). That is, although the SLO image of the time stamp T7 has a positional deviation with respect to the reference image, it does not change from the state in which the galvano correction with respect to the positional deviation is performed. Therefore, the OCT images (spectral data) of the time stamps T6 and T7 acquired at this time are at the tomographic position of the fundus corresponding to the position of the scanning line SL. Therefore, the OCT images of the time stamps T6 and T7 are taken into the memory of the PC 110 as a still image. Galvano information G2 is attached to the OCT images (spectral data) of the time stamps T6 and T7.

  Thereafter, while performing such feedback control, processing for capturing still images of OCT images into the memory of the PC 110 is repeatedly performed. When the number of still images captured in the memory of the PC 110 reaches the required number, the PC 110 generates an OCT image based on the still images captured in the memory.

  As described above, in the ophthalmologic imaging apparatus 1 according to the present embodiment, a general-purpose communication unit (USB as an example) whose upper limit is the transfer speed slower than the OCT imaging speed (frame rate of the light receiving element 83). When connecting the PC 110 via the PC, the OCT image (spectral data) can be captured (captured) without the influence (restriction) of the USB band and SLO image capture speed as in the prior art, and a light receiving element for OCT It can be done at a maximum frame rate of 83. In addition, even if the transfer to the PC 110 fails, the OCT image (spectral data) is stored in the buffer of the memory 72, so that the same OCT image (spectrum data) can be immediately re-transferred. As a result, it is possible to capture an OCT image (spectral data) to the PC 110 following the speeding up of the imaging speed of the light receiving element 83 for OCT. Therefore, the generation time of the OCT image can be shortened. In particular, the generation time of a three-dimensional OCT image in which the amount of captured OCT image (spectral data) (data amount) increases can be significantly shortened.

  Further, in the ophthalmologic imaging apparatus 1 of the present embodiment, since the connection with the PC 110 is performed by the USB, the versatility of the connected PC 110 is high. Therefore, according to the ophthalmologic photographing apparatus 1 of the present embodiment, it is possible to generate a high quality OCT image with high noise and reduced noise in a short time with high versatility of the connected PC 110. As a result, the examination time is shortened, so that the burden on the subject can be reduced.

  The embodiment described above is merely an example, and does not limit the present disclosure in any way, and it goes without saying that various improvements and modifications are possible without departing from the scope of the present invention. For example, although the above embodiment exemplifies the case where the setting of the photographing condition and the instruction to start the photographing are performed by the device main body 4, the setting and the instruction of the setting and the instruction etc. It can also be done from).

  Further, in the above embodiment, after generating an OCT image, the PC 110 performs layer detection or optic disc analysis by analyzing the image, and displays the analysis result on the monitor or monitor 75 of the PC 110 or printout. You may do it.

  Further, in the above embodiment, although the case of using Spectral-domain OCT (SD-OCT) as the OCT of the ophthalmologic imaging apparatus 1 is illustrated, OCT other than this, for example, Swept-source OCT (SS- OCT) etc. can also be used.

  In the above embodiment, the time stamp as the additional information is attached to each image when taken into the memories 72 and 73, but the time stamp is attached when each image is captured by the light receiving element 68 and 83. It may be attached when outputting from the memories 72 and 73.

In the above embodiment, when the OCT image (spectral data) is selected based on the positional deviation of the SLO image (for example, see FIG. 7), the PC 110 sequentially receives the SLO image after the acquisition of the reference image. The presence or absence of partial distortion with respect to the reference image may be determined, and the OCT image may be selected according to the determination result. In this case, for example, the PC 110 stores a partial region in the SLO image at the timing when each OCT image is acquired as additional information (for example, scan position information or a time stamp).
The PC 110 determines the presence or absence of distortion with respect to the reference image, for example, by comparing the partial image of the SLO image corresponding to the timing at which one OCT image is acquired with the reference image. Here, if the positional deviation is large, it is determined that there is distortion, and if the positional deviation is small, it may be determined that there is no distortion, or the presence or absence of distortion may be determined by predetermined image processing.
As described above, by comparing the sequentially received SLO image with the reference image in OCT image units, the presence or absence of partial distortion between SLO images is determined in OCT image units, and the distortion is detected OCT By discarding the image and adopting the OCT image without distortion, it is possible to more accurately select each OCT image.

1 ophthalmologic photographing apparatus 15 SLO image 70 control part 71 processor 72 memory 73 memory 74 operation part 75 monitor 83 light receiving element 110 PC
115 USB cable 200 interference optical system (OCT optical system)
300 Observation optics (SLO optics)
E Eyes to be examined G1, G2 ... Galvano information SL scanning lines T1, T2 ... Time stamp

Claims (10)

An interference optical system for acquiring a tomographic image of the subject's eye using interference of the measurement light and the reference light emitted to the subject's eye;
An observation optical system for acquiring a front image of the eye to be examined;
A host PC that receives tomographic image data and a front image acquired by the interference optical system and the observation optical system and generates the tomographic image;
A storage unit that temporarily stores the tomographic image data and the front image; and a control unit that transfers the tomographic image data stored in the storage unit and the front image to the host PC.
An ophthalmologic imaging apparatus, wherein the control unit and the host PC are connected by a general-purpose communication unit. In the ophthalmologic photographing apparatus according to claim 1,
An ophthalmologic imaging apparatus characterized in that the universal communication means is a universal serial bus (USB). In the ophthalmologic imaging apparatus according to claim 1 or 2,
The ophthalmologic photographing apparatus characterized in that the control unit adds additional information for correlating the front image and the tomographic image data. In the ophthalmologic photographing apparatus according to claim 3,
The ophthalmologic photographing apparatus characterized in that the additional information is time stamp information given when taken into the storage unit. In the ophthalmologic photographing apparatus according to claim 3 or 4,
An ophthalmologic photographing apparatus characterized in that the control unit gives scanning position information to each of the tomographic image data of 1 B scan. In any one of the ophthalmologic imaging apparatus according to any one of claims 3 to 5,
The host PC is characterized in that, upon detection of positional deviation of the front image, the tomographic image data associated with the front image in which positional deviation has occurred from the additional information is not used when generating the tomographic image. Ophthalmologic imaging device. In the ophthalmologic photographing apparatus according to claim 5,
When the host PC detects positional deviation of the front image, the host PC discards the tomographic image data associated with the front image in which positional deviation occurs from the additional information, and the scan position information of the discarded tomographic image data An ophthalmologic imaging apparatus characterized by reacquiring tomographic image data at the same scanning position as the discarded tomographic image data, based on the above. In the ophthalmologic photographing apparatus according to claim 5,
The host PC, upon detecting the positional deviation of the front image, transmits a scanning position correction command for correcting the scanning position for acquiring the tomographic image data by an amount corresponding to the positional deviation to the control unit.
The said control part correct | amends the scanning position which acquires the said tomographic image data based on the received said scanning position correction command, The ophthalmologic imaging device characterized by the above-mentioned. The ophthalmic photographing apparatus according to any one of claims 1 to 8,
An ophthalmologic photographing apparatus characterized in that the control unit controls timing of data transfer to the host PC based on the communication status of the communication unit. The ophthalmic photographing apparatus according to any one of claims 1 to 8,
An ophthalmologic imaging apparatus, wherein the control unit controls a data volume to be transferred to the host PC based on a communication status of the communication unit.