JP7192204B2 - ophthalmic imaging equipment - Google Patents

Description

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

2. Description of the Related Art An ophthalmologic imaging apparatus that captures a tomographic image of an eye using optical coherence tomography (OCT) is known. In this type of ophthalmologic imaging apparatus, for example, tomographic image data (spectral data) acquired by an OCT imaging means provided in the imaging apparatus is immediately and continuously transmitted to a PC (personal computer), and the spectral data is transmitted by the PC. Some of them are arithmetically processed to generate a tomographic image. In this ophthalmologic imaging apparatus, spectrum data is acquired in a state in which the positional shift of the front image (SLO image) of the eye is within an allowable range (no fixation shift), and the spectrum data is transmitted to the PC. ing. Thereby, a tomographic image (OCT image) at a preset position is generated. In order to expand the versatility of a PC connectable to an ophthalmologic imaging apparatus, the ophthalmologic imaging apparatus and a PC are connected by general-purpose communication means such as a universal serial bus (USB) (Patent Document 2). 1).

JP 2015-195876 A

However, due to recent advances in OCT technology, the imaging speed of OCT is increasing. That is, the OCT scan repetition rate (eg, the B-scan repetition rate) is much higher than the video camera frame rate. For example, a typical B-scan repetition interval is on the order of 2-3 ms, whereas the frame rate of a video camera is on the order of 20-50 FPS (frame interval on the order of 20-50 ms). Therefore, there is a possibility that the data transfer cannot be performed in accordance with the OCT imaging speed in the bandwidth (the upper limit of the data transfer speed) of the communication means (for example, USB). That is, in the ophthalmologic imaging apparatus described above, the OCT imaging speed is faster than the USB data transfer speed, and there is a possibility that the acquired spectral data cannot be continuously transferred to the PC. be. Further, in the ophthalmologic imaging apparatus described above, the spectrum data is acquired after confirming that the positional deviation of the front image (SLO image) is within the allowable range.

For these reasons, despite attempts to increase the imaging speed of OCT, it is affected (restricted) by the bandwidth of communication means (for example, USB) and the imaging speed of front images (SLO images). It takes a long time to load the spectral data required to generate the tomographic image into the PC. Therefore, it has been difficult to shorten the generation time of the tomographic image. In addition, since the acquired spectrum data is immediately and continuously transferred to the PC, if the transfer of some data fails during a series of sequence processing such as map photography, no spectrum data remains. Therefore, it is necessary to redo imaging in order to acquire the lost spectrum data, which further lengthens the generation time of the tomographic image.

Therefore, in order to solve the above-described problems, an object of the present disclosure is to provide an ophthalmologic imaging apparatus capable of shortening the generation time of a tomographic image of an eye.

One aspect of the present disclosure made to solve the above problems is
an interference optical system for acquiring a tomographic image of the eye to be inspected using interference between the measurement light and the reference light irradiated to the eye to be inspected;
an observation optical system for acquiring a front image of the subject's eye;
a control unit including a storage unit that temporarily stores the tomographic image data and the front image acquired by the interference optical system and the observation optical system;
a host PC that receives the tomographic image data and the front image transferred from the storage unit and generates the tomographic image;
The control unit and the host PC are connected by general-purpose communication means,
As additional information for associating the front image and the tomographic image data, the control unit is configured to time each of the tomographic image data and the front image before being transferred from the storage unit to the host PC. An ophthalmologic photographing apparatus characterized by adding stamp information.

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.

1 is an external side view of an ophthalmologic imaging apparatus according to an embodiment; FIG. 1 is a schematic configuration diagram of an optical system and a control system in an ophthalmologic imaging apparatus according to an embodiment; FIG. 3 is a block diagram showing a control system in the ophthalmologic imaging apparatus of the embodiment; FIG. FIG. 4 is a diagram schematically showing an SLO image displayed on a monitor; 4 is a flow chart showing the processing contents of image acquisition and data transfer of the acquired image to a PC, which are performed by the apparatus main body. It is a figure which explains notionally the generation procedure of an OCT image. FIG. 4 is a diagram conceptually explaining a procedure for generating an OCT image while feedback-controlling a scanning 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 an ophthalmologic imaging apparatus will be described with reference to FIGS. 1 to 3. FIG. FIG. 1 is an external side view of an ophthalmologic imaging apparatus 1 of this embodiment. FIG. 2 is a schematic configuration diagram of an optical system and a control system in the ophthalmologic imaging apparatus 1. As shown in FIG. FIG. 3 is a block diagram showing the control system of the ophthalmologic imaging apparatus 1. As shown in FIG.

<Overall composition>
As shown in FIGS. 1 to 3 as an example, the ophthalmologic imaging apparatus 1 of 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. 300, a control unit 70, a HUB 171, a personal computer (PC) 110, and the like. Each optical system is housed in the device body 4 . The control unit 70 and the PC 110 are connected by a universal serial bus (USB) via a USB 3.0 standard HUB 171 .

Specifically, the PC 110 is connected to a HUB 171 connected to the control unit 70 provided in the device main body 4 by a USB cable 115 via USB ports 79a and 79b. Note that the controller 70 and the HUB 171 are connected by a USB cable 78 . That is, in this embodiment, the PC 110 is connected to the ophthalmologic imaging apparatus 1 via the USB cable 115 . As a result, the versatility of the PC 110 that can be connected to the ophthalmologic imaging apparatus 1 can be expanded. As the PC 110, for example, a tablet PC or the like can be used in addition to a desktop personal computer or a notebook personal computer.

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

In this embodiment, the control unit 70 and the PC 110 are connected by USB, but the connection between the control unit 70 and the PC 110 is not limited to the USB, and a general Communication means, that is, communication means such as those standardly installed in commercially available PCs, such as USB, LAN (whether wired or wireless), Bluetooth (registered trademark), etc. can be used. . The data transfer speed of such 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 that can retain stored content even when the power supply is interrupted. 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 the imaging of front images and tomographic images by the ophthalmologic imaging apparatus 1, an image processing program for processing the captured images, and the like.

The memory of the PC 110 also stores an ophthalmologic analysis program for using the PC 110 as an ophthalmologic analysis apparatus. In other words, the PC 110 may double as an ophthalmologic analysis device. In addition, the memory stores various information related to imaging such as a tomographic image (OCT data) in a scanning line, a three-dimensional tomographic image (three-dimensional OCT data), a front fundus image, and information on the imaging position of the tomographic image. Various operation instructions by the examiner are input to the operation input unit.

On the other hand, the ophthalmologic imaging apparatus 1 includes a base 2 , a movable base 3 that can move in the horizontal direction (X direction) and the front-back (working distance) direction (Z direction) with respect to the base 2 , and and a face support unit 5 fixed to the base 2 to support the face of the subject. . The apparatus main body 4 is moved relative to the subject's eye E in the left-right direction, the up-down direction (Y direction), and the front-rear direction by an XYZ drive unit 6 provided on the moving table 3 . The movable table 3 is moved on the base 2 in the XZ direction by operating the joystick 7 . Further, by rotating the rotary knob 7a, the XYZ driving section 6 is Y-driven, and the apparatus 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's side of the apparatus main body 4 .

The ophthalmologic imaging apparatus 1 includes an interference optical system (OCT optical system) 200 for obtaining a tomographic image of the eye E, an observation optical system (scanning laser ophthalmoscope (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 segment observation optical system 90 for observing a front image of the anterior segment are provided. These optical systems are built in the device main body 4 and three-dimensionally moved with respect to the eye E by the above-described alignment movement mechanism (manual or electric).

<Interference optical system (OCT optical system)>
The OCT optical system 200 includes a measurement optical system 200a and a reference optical system 200b. In addition, the OCT optical system 200 splits the interference light of the reference light and the measurement light for each frequency (wavelength), and causes the split interference light to be received by the light receiving means (one-dimensional light receiving element in this embodiment). It has an optical system 800 .

The dichroic mirror 40 reflects measurement light (e.g., around λ=840 nm) emitted from the OCT light source 27 used in the OCT optical system 200, and reflects laser light (OCT light source 27, for example, around λ=780 nm). In this case, the dichroic mirror 40 makes the measurement optical axis L1 of the OCT optical system 200 and the measurement optical axis L2 of the SLO optical system 300 coaxial.

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 for the OCT optical system 200, and for example, an SLD light source is used. For the OCT light source 27, for example, a light source having a central wavelength of 840 nm and a band of 50 nm is used. A fiber coupler (splitter) 26 serves both as a light splitting member and as a light coupling member. Light emitted from the OCT light source 27 is split into reference light and measurement light by the fiber coupler 26 via an optical fiber 38a as a light guide. The measurement light travels to the subject's eye E via the optical fiber 38b, and the reference light travels to the reference mirror 31 via the optical fiber 38c (polarizer (polarization element) 33).

The optical path through which the measurement light is emitted toward the eye to be examined E includes an end portion 39b of an optical fiber 38b through which the measurement light is emitted, a collimator lens 21, a focusing optical member (focusing lens) 24, and a scanning section (optical scanner) 23. , a relay lens 22 is arranged. The scanning unit 23 is composed of two galvanometer mirrors, and is used to two-dimensionally (XY directions) scan the fundus (subject) with the light emitted from the measurement light source by driving the scanning drive mechanism 51 . be done. Note that the scanning unit 23 may be configured by, for example, an AOM (acousto-optic device), a resonant scanner, or the like.

The dichroic mirror 40 and the objective lens 10 serve as a light guide optical system that guides the OCT measurement light from the OCT optical system 200 to the fundus of the subject's eye. The focusing lens 24 is movable in the optical axis direction by being driven by a driving mechanism 24a, and is used to correct the diopter for the subject's fundus.

The measurement light emitted from the end 39b of the optical fiber 38b is collimated by the collimator lens 21, passes through the focusing lens 24, reaches the scanning unit 23, and is reflected in a different direction by driving the two galvanomirrors. After that, the measurement light passes through the relay lens 22 and is reflected by the dichroic mirror 40, and then condenses on the fundus of the subject's eye through the objective lens 10. FIG.

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

The reference optical system 200b generates reference light that is combined with reflected light obtained by reflection of the measurement light on the fundus oculi Ef. The reference optical system 200b may be of the Michelson type or of the Mach-Zehnder type. The reference optical system 200 b is formed by, for example, a reflecting optical system (for example, the reference mirror 31 ), and the light from the fiber coupler 26 is reflected by the reflecting optical system, returned to the fiber coupler 26 again, and guided to the light receiving element 83 . As another example, the reference optical system 200b is formed by a transmissive 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 portion 39c of the optical fiber 38c for emitting the reference light, the collimator lens 29, and the reference mirror 31 are arranged in an optical path for emitting the reference light toward the reference mirror 31. FIG. The optical fiber 38c is rotationally moved by the driving mechanism 34 to change the polarization direction of the reference light. That is, the optical fiber 38c and the driving mechanism 34 are used as a polarizer 33 for adjusting the polarization direction.

Note that the polarizer 33 of the present embodiment adjusts the polarization direction of at least one of the measurement light and the reference light in order to match the polarization directions of the measurement light and the reference light. A polarizer 33 is arranged in at least one of the measurement beam path and the reference beam path. The polarizer 33 is not limited to the configuration described above, and includes, 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 about the optical axis, or a configuration that applies pressure to the fiber. In addition, a configuration in which the direction of polarization of light is changed by deformation is conceivable.

Also, the reference mirror driving mechanism 50 drives the reference mirror 31 arranged in the reference light path in order to adjust the optical path length with the reference light. In this embodiment, the reference mirror 31 is arranged 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, reflected by the reference mirror 31, condensed by the collimator lens 29, and incident on 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 reflected light by the measurement light irradiated to the fundus oculi Ef of the subject's eye are combined by the fiber coupler 26 to form interference light. , is emitted from the end portion 84a through the optical fiber 38d. A spectroscopic optical system 800 (spectrometer section) that disperses interference light into frequency components to obtain an interference signal for each frequency has a collimator lens 80, a grating mirror (diffraction grating) 81, a condenser lens 82, and a light receiving element 83. . In this embodiment, a one-dimensional element (line CCD) having sensitivity in the infrared region is used as the light receiving element 83 . The light receiving element 83 is connected to the control section 70 (second control section 270) by camera link.

Here, the interference light emitted from the end portion 84 a is collimated by the collimator lens 80 and then split into frequency components by the grating mirror 81 . The interference light split into frequency components is condensed on the light receiving surface of the light receiving element 83 via the condensing lens 82 . Thereby, spectral data of the interference fringes are recorded on the light receiving element 83, and a tomographic image of the subject's eye E is generated in the PC 110 based on the data.

That is, by analyzing the 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. A tomographic image can be obtained by scanning the fundus oculi Ef with the measuring light by the scanning unit 23 in a predetermined transverse direction. For example, by scanning in the X direction or Y direction, a tomographic image (fundus tomographic image) in the XZ plane or YZ plane of the fundus Ef of the subject's eye can be obtained (in the present embodiment, the measurement light is used to scan the fundus in this way). B-scan is a method of one-dimensional scanning for obtaining a tomographic image). Furthermore, by controlling the driving of the scanning unit 23 to two-dimensionally scan the measurement light in the XY directions, a two-dimensional moving image of the fundus of the examinee's eye in the XY directions based on the output signal from the light receiving element 83, and It is also possible to acquire a three-dimensional image of the fundus of the eye to be examined.

The spectral 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, and received by the PC 110, according to a command from the processor 71 in the control unit 70. . Details of the data transfer to the PC 110 will be described later.

<Observation optical system (SLO optical system)>
Next, an observation optical system (SLO optical system) 300 arranged 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 Ef of the subject's eye. The SLO optical system 300 is roughly divided into an illumination optical system that illuminates the fundus Ef of the subject's eye and a light receiving optical system that receives the reflected light of the subject's eye illuminated by the illumination optical system with a light receiving element. A front image of the fundus oculi Ef of the subject's eye is obtained based on the received light signal.

The light emitting section 61 has a first light source (SLO light source) 61 a, a second light source (fixation 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 uses, for example, a light source of λ=780 nm (laser diode light source, SLD light source, etc.). The fixation light source 61b is light with a wavelength in the visible range, and for example, a light source (laser diode light source, SLD light source, etc.) with λ=630 nm is used. A laser beam emitted from the SLO light source 61 passes through the dichroic mirror 101 and travels to the beam splitter 62 via the collimating 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.

The optical path through which the laser light emitted from the SLO light source 61a is emitted toward the eye to be inspected E includes a collimating lens 102, a focusing lens 63 movable in the optical axis direction in accordance with the refractive error of the eye to be inspected, and a scanning driving mechanism 52. A scanning unit 64, a relay lens 65, and an objective lens 10, which are a combination of a galvanomirror and a polygon mirror capable of scanning the fundus in the XY directions at high speed, are arranged. Further, the reflecting surfaces of the galvanometer mirror and the polygon mirror of the scanning unit 64 are arranged at positions substantially conjugate with the pupil of the subject's eye.

A beam splitter 62 is arranged between the SLO light source 61 a and the focusing lens 63 . In the reflection direction of the beam splitter 62, there are provided a condensing lens 66 for forming a confocal optical system, a confocal aperture 67 positioned conjugate to the fundus, and an SLO light receiving element 68. there is

Here, the laser light (measurement light) emitted from the SLO light source 61a passes through the beam splitter 62, passes through the focusing lens 63, reaches the scanning unit 64, and is reflected in the direction of reflection by driving the galvanomirror and the polygon mirror. be changed. The laser light reflected by the scanning unit 64 passes through the dichroic mirror 40 via the relay lens 65, and then is focused on the fundus Ef of the subject's eye via the objective lens 10. FIG.

The laser beam reflected by the fundus oculi Ef passes through the objective lens 10 , the relay lens 65 , the galvanometer mirror and polygon mirror of the scanning unit 64 , and the focusing lens 63 and is reflected by the beam splitter 62 . After that, after being condensed by a condensing lens 66 , it is detected by a light receiving element 68 via a confocal aperture 67 . The SLO image detected by the light receiving element 68 is input to the controller 70 and temporarily stored in the memory 72 of the controller 70 . The acquisition of the SLO image is performed by scanning the laser light in the vertical direction (sub-scanning) with the galvanomirror provided in the scanning unit 64 and scanning the laser light in the horizontal direction (main scanning) with the polygon mirror. After that, the SLO image stored in the memory 72 is transferred to the PC 110 at a predetermined timing according to an instruction from the processor 71 of the control unit 70, and after being received by the PC 110, the PC 110 performs a fundus image of the subject's eye based on the received SLO image. A frontal image of Ef is generated. Details of data transfer to the PC 110 will be described later.

<Light projection optical system>
A projection optical system 150 is used to project a target onto the cornea Ec. In the projection 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 intervals of 45 degrees. The projection optical system 150 includes a first index projection optical system (0 degrees and 180 degrees) having an infrared light source 151 and a collimating lens 152 arranged symmetrically with respect to a vertical plane passing through the optical axis L1, a second index projection optical system having six near-infrared light sources 153 arranged at a position different from that of the first index projection optical system. For convenience, FIG. 2 shows only the first index projection optical system (0 degrees and 180 degrees) and part of the second index projection optical system (45 degrees and 135 degrees). The light source 151 also serves as illumination for the anterior segment. Of course, a configuration may be adopted in which a light source for illuminating the anterior segment is provided separately.

<Anterior segment observation optical system>
The anterior segment observation optical system 90 is arranged to image the subject's eye E and obtain an anterior segment image. The anterior segment 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 ocular segment reflected light and the alignment light flux from the projection optical system 150 are reflected by the dichroic mirror 91 via the objective lens 10 and then received by the two-dimensional imaging device 97 via 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 irradiated by the projection optical system 150 . The output of the two-dimensional image pickup device 97 is transmitted to the control unit 70 , and the anterior segment image picked up by the two-dimensional image pickup device 97 is displayed on the monitor 75 .

In this embodiment, the projection optical system 150 and the anterior segment observation optical system 90 are used as an alignment detection optical system for guiding the device body 4 to a predetermined positional relationship with respect to the eye E to be examined. For example, the projection optical system 150 and the anterior segment observation optical system 90 are used to guide the subject's eye E and the device body 4 to a predetermined proper working distance.

The alignment detection optical system detects the alignment state of the apparatus main body 4 with respect to the eye E to be inspected in the Z direction. It is also possible to detect the Z alignment by receiving light from .

<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 its display image. Further, the control unit 70 includes an operation unit 74 for performing various operations, drive mechanisms 24a, 34, 50, 51, 52, 63a, light sources 27, 61a, 61b, 151, 153, a light receiving element 83, an imaging element 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 state of alignment between the eye E and the device 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 driving of the XYZ driving unit 6 so that the alignment detection result (for example, the amount of misalignment) satisfies a predetermined allowable range, and automatically moves the apparatus with respect 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, image data processing, etc. in each optical system.なお、プロセッサ７１は、例えば、ＣＰＵ（Ｃｅｎｔｒａｌ Ｐｒｏｃｅｓｓｉｎｇ Ｕｎｉｔ）、ＧＰＵ（Ｇｒａｐｈｉｃｓ Ｐｒｏｃｅｓｓｉｎｇ Ｕｎｉｔ）、ＡＳＩＣ（Ａｐｐｌｉｃａｔｉｏｎ Ｓｐｅｃｉｆｉｃ Ｉｎｔｅｇｒａｔｅｄ Ｃｉｒｃｕｉｔ）、プログラマブル論理デバイス（例えば、ＳＰＬＤ（Ｓｉｍｐｌｅ Ｐｒｏｇｒａｍｍａｂｌｅ Ｌｏｇｉｃ Ｄｅｖｉｃｅ）、ＣＰＬＤ（Ｃｏｍｐｌｅｘ Ｐｒｏｇｒａｍｍａｂｌｅ Ｌｏｇｉｃ Ｄｅｖｉｃｅ ) and FPGA (Field Programmable Gate Array)). This processor reads out and executes a program stored in the memory, for example, to perform a process of attaching additional information to an acquired image, a process of transferring data to the PC 110, and the like, which will be described later.

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

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

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

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

The control unit 70 determines that the alignment is proper when the alignment deviation amount in the XYZ directions is within the allowable range for alignment completion. When the control section 70 determines that the alignment in the XYZ directions is proper, the control section 70 stops driving the XYZ driving section 6 and outputs an alignment completion signal. On the other hand, if the alignment deviation amount in the XYZ directions does not fall within the alignment completion allowable range, the control unit 70 determines that the alignment is not proper, and performs automatic alignment.

When the alignment completion signal is output, the control unit 70 issues a trigger signal for starting optimization control, and starts optimization control operation. By performing optimization, the control unit 70 enables the examiner to observe the fundus region desired by the examiner with high sensitivity and high resolution. In this embodiment, optimization control is control of optical path length adjustment, focus adjustment, and polarization state adjustment (polarizer adjustment). In addition, in optimization control, it is only necessary to satisfy a certain allowable condition for the fundus, and it is not always necessary to adjust to the most appropriate state.

During the optimization control, the control unit 70 performs control (tracking) for causing the apparatus main body 4 to track the subject's eye so that the alignment deviation amount satisfies the allowable range. For example, the control unit 70 determines whether the amount of alignment deviation in the XYZ directions is within the allowable range for alignment completion and continues for a certain period of time (for example, 10 frames of image processing or 0.3 seconds). It is determined whether or not the proper state of directional alignment continues. If the alignment deviation amount in the XYZ directions is within the allowable range for completion of alignment continuously for a certain period of time, the control unit 70 determines that the proper state of alignment continues, and the XYZ driving unit 6 is operated. The drive remains stopped.

Further, if the alignment deviation amount in the XYZ directions does not fall within the allowable range for alignment completion continuously for a certain period of time and is out of the allowable range, the proper state of alignment continues. Then, the XYZ driving unit 6 is started to drive and automatic alignment is performed. In this case, for example, the control unit 70 continues optimization control even while the XYZ drive unit 6 is being driven (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. Further, the control unit 70 may be configured to restart the optimization control when the alignment deviation amount returns to within the allowable range after the optimization control is stopped. Further, when performing automatic alignment, the configuration may be such that the optimization control is restarted from the initial position.

In the optimization control, the control unit 70 sets the positions of the reference mirror 31 and the focusing lens 24 to initial positions as initialization control. After completion of the initialization, the control unit 70 moves the reference mirror 31 in one direction from the set initial position in predetermined steps to perform the first optical path length adjustment (first automatic optical path length adjustment). Also, in parallel with the first optical path length adjustment, the control unit 70 acquires focus position information for the fundus of the subject's eye based on the SLO fundus image acquired by the light receiving signal output from the light receiving element 68 . When the focus position information is acquired, the control unit 70 moves the focusing lens 24 to the focus position and performs autofocus adjustment (focus adjustment). Note that the in-focus position may be any position at which contrast of a tomographic image acceptable as an observation image can be obtained, and does not necessarily have to be the optimum position for the focus state.

After the focus adjustment is completed, the control unit 70 moves the reference mirror 31 in the optical axis direction again to perform the second optical path length adjustment for readjusting the optical path length (fine adjustment of the optical path length). After the second optical path length adjustment is completed, the controller 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). By completing the optimization control in this way, the examiner can observe the fundus region desired by the examiner with high sensitivity and high resolution.

As a result, the high-sensitivity, high-resolution SLO image 15 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. FIG. Then, the examiner sets the position of the tomographic image (OCT image) desired to be captured from the SLO image 15 on the monitor 75 observed in real time. Here, the examiner uses the operation unit 74 to move the scanning line SL with respect to the SLO image 15 to set the scanning position (for example, drag operation of the scanning line SL). If the scanning line SL is set in the X direction, a tomographic image of the XZ plane is captured, and if the scanning line SL is set in the Y direction, a tomographic image of the YZ plane is captured. It's like Also, the scanning line SL may be set to have any shape (for example, oblique direction, circle, etc.).

<Shooting operation>
After the setting of the imaging conditions is completed as described above, when the examiner operates the imaging start switch 74a provided in the operation unit 74, the control unit 70 starts imaging of images. Note that the switch for starting photographing 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, an SLO image and an OCT image (spectral data) are acquired in parallel by the control unit 70, each acquired image is transferred to the PC 110, and a plurality of OCT images (spectral data) are averaged by the PC 110. As a result, an OCT image with suppressed noise components is generated.

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

First, the processing performed on the apparatus main body side will be described with reference to FIG. When an imaging start signal is input from the operation unit 74, the control unit 70 starts capturing an OCT image (spectrum data) and an SLO image. That is, the control unit 70 starts capturing the SLO image from the light receiving element 68 and also starts capturing tomographic image data at the 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 the OCT image may be generated by the PC 110. Alternatively, the apparatus main body 4 may generate an OCT image based on the spectrum data acquired by the apparatus main body 4 , and the generated OCT image may be transferred to the PC 110 . That is, the tomographic image data may be, for example, spectral data or an OCT image based on spectral data.

Specifically, the processor 71 creates a buffer in the memory 72 (step S10). Processor 71 then acquires 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). When the SLO image is acquired (step S11: YES), the processor 71 attaches a time stamp as additional information to the SLO image (step S12). Then, the processor 71 develops (temporarily stores) the SLO image with the time stamp in the buffer created in the memory 72 (step S13). That is, the processor 71 attaches a time stamp to the SLO image when developing it in the buffer of the memory 72 .

In parallel with this SLO image fetching process, the OCT image (spectral data) fetching process is performed. That is, processor 71 creates a buffer in memory 73 (step S20). Then, the processor 71 acquires an OCT image (spectral data) (for example, data for 1B scan) (step S21). That is, based on the display position of the scanning line SL set on the SLO image 15, the processor 71 causes the scanning unit 23 to obtain a fundus tomographic image (B-scan image) corresponding to the position of the scanning line SL. is driven to scan the measurement light. Then, the detection signal from the light receiving element 83 at that time is acquired. When the OCT image (spectral 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 (spectral data) (step S22). That is, a time stamp and/or galvano information (scanning position information) is attached to each OCT image (spectral data) for 1B scan. Then, the processor 71 expands (temporarily stores) the OCT image (spectrum data) for 1B scan with the time stamp and/or 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 developing the OCT image (spectral data) for 1B scans in the buffer of the memory 73 .

Here, the time stamp is attached at the timing of expansion to the buffer created in each memory 72, 73 based on the counter provided in each memory 72, 73. FIG. 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. Thereby, the time stamp attached to the SLO image can be synchronized with the time stamp attached to the spectrum data for 1B scan.

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

Since the time stamp attached to the SLO image is synchronized with the time stamp attached to the OCT image (spectrum data) for 1B scan, for example, the same time stamps T1, T4, T7, T10, It can be determined that the images attached with . . . were acquired (captured) at the same timing. That is, by using the time stamp attached to each image, the SLO image and the OCT image (spectrum data) can be associated. Therefore, an OCT image (spectrum data) acquired at the same timing as the SLO image is acquired can be specified. Note that when a time stamp is attached to an SLO image or an OCT image, the time stamp should be set in consideration of the timing deviation from the scanning timing for image acquisition (for example, at the start of scanning, at the end of scanning) to the development in the buffer. may be attached. For example, the control unit 70 may add an offset corresponding to the timing shift to the timing at which the SLO image or the OCT image is developed in the buffer. The offset amount may be, for example, a known value, and may differ between the SLO image and the OCT image. According to this, since the time stamp can be added at the scanning operation timing for obtaining the SLO image or the OCT image, the timing for obtaining each image can be grasped more accurately, and various controls can be performed with high accuracy. can.

Also, by using the galvanometer information G1, G1, ... attached to each OCT image (spectrum data), the state (scanning position) of the scanning unit 23 when each OCT image (spectrum data) is acquired can be grasped.

In the present embodiment, the time stamp and galvanometer information are attached to the image as additional information, but information other than these (for example, information on each part, setting values, etc.) may be attached as additional information. Additional information includes, for example, alignment information between the device main body and the eye (e.g., working distance between the eye and the device), optical path length adjustment completion position (e.g., driving position of the optical path length adjustment member after optical path length adjustment). ). The optical path length adjusting member may be, for example, a reference mirror, but is not limited to this. The optical path length adjusting member may be an optical member arranged in the optical path of the measurement light.

In this manner, the SLO image and the OCT image (spectrum data) are obtained by the control unit 70, and when the images are developed in the buffers of the memories 72 and 73, the images are transferred to the PC 110, respectively. Specifically, processor 71 in control unit 70 detects the state of communication band α (upper limit of data transfer rate) of USB cable 115 connected to PC 110 . In other words, it detects how much data transfer capacity is available in the USB cable 115 at the present time. Then, if the communication band α of the USB cable 115 has a free space (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 buffer of the memory 72 The expanded SLO image is transferred to the PC 110 via the USB cable 172, HUB 171, 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 developed in the buffer of the memory 72 to the PC 110 is completed and reception by 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. After that, the acquisition of the SLO image and the transfer processing to the PC 110 are repeated until a predetermined end condition A, which will be described later, is satisfied. ends.

Also, the processor 71 detects the state of the communication band α (the upper limit of the data transfer speed) of the USB cable 115 connected to the PC 110, and if there is a free space (step S24: YES), the data is loaded into the buffer of the memory 72. The OCT image (spectral data) is transferred to the PC 110 via the USB cable 172, HUB 171, USB cables 78, 115 (step S25). At this time, the communication band α of the USB cable 115 is free, but the OCT image (spectrum data) developed in the buffer of the memory 72 is large, and it is difficult to transmit data at once in the free communication band α. , the amount of data to be transmitted may be varied according to the free space of the communication band α. In other words, 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 vacant band α may be determined by a response from the communication partner (PC 110). can be monitored and managed.

As a result, even if the acquisition (capture) 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. OCT images (spectral data) can be acquired continuously without interruption. That is, an OCT image (spectral data) can be obtained at the maximum frame rate of the light receiving element 83 . Therefore, the number of still images of OCT images necessary for generating OCT images can be obtained in a short time.

When the transfer of the OCT image (spectrum data) developed in the buffer of memory 72 to PC 110 is completed and reception by PC 110 is completed, processor 71 makes the buffer of memory 72 empty (step S26). Therefore, the acquired OCT image (spectrum data) is stored in the buffer of the memory 72 until the transfer to the PC 110 is completed. As a result, even if transfer of a part of the OCT image (spectral data) fails during a series of sequence processing such as map imaging, the OCT image (spectral data) stored in the buffer of the memory 72 can be transferred. can be retransferred. Therefore, even if the transfer of the OCT image (spectral data) fails, there is no need to reacquire (capture) the OCT image (spectral data).

After that, the acquisition and transfer processing of the OCT image (spectral data) are repeated until a predetermined end condition A is satisfied (step S27). Note that the predetermined end condition A is that the number of still images of the OCT images determined to be usable for the averaging process by the PC 110 reaches the set upper limit of the number of images to be added. That is, the OCT images (spectrum data) are captured (captured) until the number of still images of the OCT images used for the averaging process in the PC 110 reaches the set upper limit of the number of images to be added.

<Generation of OCT image>
Next, processing (generation of OCT images) performed by the PC 110 will be described with reference to FIG. The PC 110 that has received the images from 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 images 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 loads the OCT image (spectrum data) acquired at the same timing as the SLO image as a still image into the memory of the PC 110 (judgment ◯). ). On the other hand, if 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 this embodiment, for example, if it is determined that the positional deviation of the SLO image with the time stamp T1 is within the allowable range (determination ◯), the OCT image with the time stamp T1 is stored in the memory of the PC 110 as a still image. 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 (determination x), the OCT images (spectrum data) at time stamps T2 to T4 are acquired in a positionally shifted state. is determined to be and discarded.

Then, if it is determined that the positional deviation of the SLO image with the time stamp T7 is within the allowable range (determination ◯), the OCT image with the time stamp T7 is loaded into the memory of the PC 110 as a still image. Also, the OCT images (spectral data) before time stamp T7 and after T5 (T5, T6) are determined to have been acquired in a positionally shifted state and are discarded.

Furthermore, if it is determined that the positional deviation of the SLO image with the time stamp T10 is within the allowable range (determination ◯), the OCT image with the time stamp T10 is loaded into the memory of the PC 110 as a still image. Also, the OCT images (spectral data) before time stamp T10 and after T8 (T8, T9) are determined to have been acquired without positional deviation, and are captured in the memory of PC 110 as still images.

Thereafter, such processing is repeatedly performed, and when the number of still images of the OCT image captured in the memory of the PC 110 reaches the set upper limit of the number of images to be added, the PC 110 reads the OCT image captured in the memory. are averaged to generate an OCT image (B-scan image).

As described above, the ophthalmologic imaging apparatus 1 of the present embodiment creates a buffer in the memory 73 and temporarily stores the OCT image (spectrum data) in the buffer. In addition, when storing in the buffer of the memory 73, a time stamp that associates the SLO image and the OCT image (spectrum data) is attached. That is, the OCT image (spectrum data) attached with the time stamp is stored in the buffer of the memory 73 . Thereby, after the OCT image (spectral data) is acquired, the time stamp is used to specify the OCT image (spectral data) acquired (captured) in a state where the positional deviation of the SLO image is not within the allowable range. can be done. Therefore, an OCT image (spectrum data) can be captured (captured) without being affected (restricted) by the USB bandwidth or the SLO image capturing speed, unlike the conventional art. As a result, it is possible to shorten the time required to generate an OCT image subjected to averaging.

In addition, since the ophthalmologic photographing apparatus 1 of the present embodiment is connected to the PC 110 via USB, the PC 110 to be connected has high versatility. Therefore, according to the ophthalmologic imaging apparatus 1 of the present embodiment, the connected PC 110 has high versatility, and high-quality OCT images with reduced noise can be generated in a short period of time. This shortens the examination time, thereby reducing the burden on the subject.

Here, when generating a three-dimensional OCT image, the capture (imaging) of the OCT image (spectral data) is performed in a plurality of scan lines (for example, 256 lines). Therefore, in the band α (upper limit of data transfer speed) of the USB cable 115, data transfer to the PC 110 may not be possible in accordance with the imaging speed of the OCT image (spectrum data).

However, in the ophthalmologic imaging apparatus 1 of the present embodiment, the OCT image (spectrum data) is temporarily written in the buffer of the memory 72 in the control unit 70, and when there is 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 . Accordingly, even when generating a three-dimensional OCT image, the OCT image (spectral 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 .

Also, as described above, the OCT image (spectral data) is associated with the SLO image by the time stamp. Therefore, an OCT image in which the eye to be inspected has a positional shift (fixation shift) can be identified by using the time stamp after imaging. Accordingly, the imaging speed of the OCT image (spectrum data) is not limited to the imaging speed of the SLO image as in the conventional art. Therefore, an OCT image (spectral data) necessary for generating a three-dimensional OCT image can be acquired in a very short time.

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

For example, the PC 110 can receive, from the memory 72, OCT images (spectral data) for scan lines, for example, 256 lines, which are necessary for generating a three-dimensional OCT image, at a time, and perform processing for generating a three-dimensional OCT image. Suppose that a defect or lack of data is detected in a certain scan line when performing In that case, the scan line in which the data defect/insufficiency is detected is specified based on the galvanometer information, and the OCT image (spectrum data) in the specified scan line is reacquired. Then, using the reacquired OCT image (spectral data), a three-dimensional OCT image is generated.

Alternatively, during execution of processing for generating a three-dimensional OCT image for OCT images (spectrum data) for several scan lines sequentially received by the PC 110 from the memory 72, there is a defect or lack of data in a certain scan line. is detected. In that case, the imaging of the OCT image (spectrum data) currently being acquired is temporarily interrupted, the scan line in which defective or insufficient data is detected is specified based on the galvano information, and the OCT image in the specified scan line (spectral data) is reacquired.

In this way, regardless of whether the PC 110 receives the OCT images (spectral data) for the scan lines necessary for generating a three-dimensional OCT image all at once or sequentially in sequence, the acquired OCT images ( When a defect or shortage occurs in the spectral data), the defective or insufficient OCT image (spectral data) can be reacquired instantly. Therefore, an OCT image (spectral data) required for generating 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 an OCT image is generated by the PC 110, if a positional deviation is detected in the SLO image, the OCT image (spectrum data) corresponding to the SLO image is discarded and the displacement of the positional deviation is detected. A galvano correction command (scanning position correction command: a galvano control signal corresponding to the displacement amount of the positional deviation) corresponding to the amount may be transmitted to the control unit 70 . Accordingly, the control unit 70 that has received the galvano correction command controls the drive mechanism 24a based on the galvano correction command to appropriately drive the two galvano mirrors provided in the scanning unit 23 . As a result, even if the SLO image is misaligned, an OCT image (spectral data) of the fundus 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 with the time stamp T1 is within the allowable range (determination ◯), the PC 110 uses the OCT image with the time stamp T1 as a still image. fetch into memory. Galvano information G1 is attached to the OCT images (spectral data) with time stamps T1 to T3.

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

Then, when the PC 110 receives the SLO image with the time stamp T7, it 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 (determination ◯). In other words, although the SLO image with time stamp T7 is misaligned with respect to the reference image, it has not changed from the state in which the galvano correction for the misalignment has been 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 with time stamps T6 and T7 are loaded into the memory of the PC 110 as still images. Galvano information G2 is attached to the OCT images (spectral data) of time stamps T6 and T7.

After that, while performing such feedback control, the process of loading the still image of the OCT image into the memory of the PC 110 is repeatedly performed. Then, 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, the ophthalmologic imaging apparatus 1 of the present embodiment uses general-purpose communication means (USB as an example) whose upper limit is a transfer rate lower than the OCT imaging speed (the frame rate of the light receiving element 83). When the PC 110 is connected via the USB, the OCT image (spectrum data) can be captured (captured) without being affected (restricted) by the USB band or the SLO image capturing speed as in the past. 83 maximum frame rate. Also, even if the transfer to the PC 110 fails, the OCT image (spectral data) is saved in the buffer of the memory 72, so the same OCT image (spectral data) can be immediately retransferred. As a result, the OCT image (spectrum data) can be loaded into the PC 110 following the speedup of the imaging speed of the light receiving element 83 for OCT. Therefore, the OCT image generation time can be shortened. In particular, it is possible to greatly reduce the time required to generate a three-dimensional OCT image, which requires a large amount of captured OCT image (spectrum data).

In addition, since the ophthalmologic photographing apparatus 1 of the present embodiment is connected to the PC 110 via USB, the PC 110 to be connected has high versatility. Therefore, according to the ophthalmologic imaging apparatus 1 of the present embodiment, the PC 110 to be connected has high versatility, and high-quality OCT images with reduced noise can be generated in a short period of time. This shortens the examination time, thereby reducing the burden on the subject.

It should be noted that the above-described embodiment is merely an example and does not limit the present disclosure in any way, and of course various improvements and modifications are possible without departing from the gist of the present disclosure. For example, in the above-described embodiment, the setting of imaging conditions and the instruction to start imaging are performed by the apparatus main body 4, but these settings and instructions are input to the input instruction unit (eg, mouse, keyboard, etc.) of the PC 110. ).

In the above-described embodiment, the PC 110 generates an OCT image and then performs image analysis such as layer detection and optic nerve papilla analysis. You may make it

Further, in the above embodiment, the case of using Spectral-domain OCT (SD-OCT) as the OCT of the ophthalmologic imaging apparatus 1 is exemplified, but other OCT such as Swept-source OCT (SS- OCT) and the like can also be used.

In the above embodiment, the time stamp as additional information is attached to each image when it is taken into the memories 72 and 73. However, when each image is captured by the light receiving elements 68 and 83, the time stamp is attached. Alternatively, it may be attached when output from the memories 72 and 73 .

In the above-described embodiment, when selecting OCT images (spectral data) based on the positional shift of the SLO image (see, for example, FIG. 7), the PC 110 sequentially receives the SLO images after acquiring 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 the partial area in the SLO image at the timing when each OCT image is acquired as additional information (for example, scanning position information or time stamp).
For example, the PC 110 compares a partial area of the SLO image corresponding to the timing at which one OCT image is acquired with the reference image to determine the presence or absence of distortion with respect to the reference image. Here, if the positional deviation is large, it may be 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.
By comparing the sequentially received SLO images with the reference image in units of OCT images as described above, the presence or absence of partial distortion between the SLO images is determined in units of OCT images, and the OCT where distortion is detected is determined. By discarding the images and adopting the OCT images that were not distorted, the selection of each OCT image can be made more accurately.

1 ophthalmic photographing device 15 SLO image 70 control unit 71 processor 72 memory 73 memory 74 operation unit 75 monitor 83 light receiving element 110 PC
115 USB cable 200 interference optical system (OCT optical system)
300 observation optical system (SLO optical system)
E Subject's eye G1, G2... Galvano information SL Scanning line T1, T2... Time stamp

Claims (7)

an interference optical system for acquiring a tomographic image of the eye to be inspected using interference between the measurement light and the reference light irradiated to the eye to be inspected;
an observation optical system for acquiring a front image of the subject's eye;
a control unit including a storage unit that temporarily stores the tomographic image data and the front image acquired by the interference optical system and the observation optical system;
a host PC that receives the tomographic image data and the front image transferred from the storage unit and generates the tomographic image;
The control unit and the host PC are connected by general-purpose communication means,
As additional information for associating the front image and the tomographic image data, the control unit is configured to time each of the tomographic image data and the front image before being transferred from the storage unit to the host PC. An ophthalmic photographing apparatus characterized by adding stamp information. In the ophthalmic imaging apparatus according to claim 1,
The ophthalmologic imaging apparatus, wherein the control unit gives scanning position information to each of the tomographic image data for 1B scans. an interference optical system for acquiring a tomographic image of the eye to be inspected using interference between the measurement light and the reference light irradiated to the eye to be inspected;
an observation optical system for acquiring a front image of the subject's eye;
a control unit including a storage unit that temporarily stores the tomographic image data and the front image acquired by the interference optical system and the observation optical system;
a host PC that receives the tomographic image data and the front image transferred from the storage unit and generates the tomographic image;
The control unit and the host PC are connected by general-purpose communication means,
As additional information for associating the front image and the tomographic image data, the control unit is configured to time each of the tomographic image data and the front image before being transferred from the storage unit to the host PC. Give stamp information ,
When the host PC detects the positional displacement of the front image, the host PC does not use the tomographic image data associated with the front image in which the positional displacement has occurred from the additional information when generating the tomographic image. ophthalmic imaging equipment. an interference optical system for acquiring a tomographic image of the eye to be inspected using interference between the measurement light and the reference light irradiated to the eye to be inspected;
an observation optical system for acquiring a front image of the subject's eye;
a control unit including a storage unit that temporarily stores the tomographic image data and the front image acquired by the interference optical system and the observation optical system;
a host PC that receives the tomographic image data and the front image transferred from the storage unit and generates the tomographic image;
The control unit and the host PC are connected by general-purpose communication means,
As additional information for associating the front image and the tomographic image data, the control unit is configured to time each of the tomographic image data and the front image before being transferred from the storage unit to the host PC. Attaching stamp information and attaching scanning position information to each of the tomographic image data for 1B scan,
When the host PC detects the positional displacement of the front image, the host PC discards the tomographic image data associated with the front image in which the positional displacement occurs from the additional information, and the scanning position information of the discarded tomographic image data. an ophthalmologic imaging apparatus for reacquiring tomographic image data at the same scanning position as the discarded tomographic image data based on. an interference optical system for acquiring a tomographic image of the eye to be inspected using interference between the measurement light and the reference light irradiated to the eye to be inspected;
an observation optical system for acquiring a front image of the subject's eye;
a control unit including a storage unit that temporarily stores the tomographic image data and the front image acquired by the interference optical system and the observation optical system;
a host PC that receives the tomographic image data and the front image transferred from the storage unit and generates the tomographic image;
The control unit and the host PC are connected by general-purpose communication means,
When the host PC detects a positional deviation of the front image, the host PC transmits to the control unit a scanning position correction command for correcting a scanning position for acquiring the tomographic image data by an amount corresponding to the positional deviation,
As additional information for associating the front image and the tomographic image data, the control unit is configured to time each of the tomographic image data and the front image before being transferred from the storage unit to the host PC. Stamp information is added, scanning position information is added to each of the tomographic image data for 1B scan, and the scanning position for acquiring the tomographic image data is corrected based on the scanning position correction command received from the host PC. An ophthalmologic imaging apparatus characterized by: In any one ophthalmic imaging apparatus according to claims 1 to 5,
The ophthalmologic imaging apparatus, wherein the control unit controls timing of data transfer to the host PC based on the communication status of the communication means. In any one ophthalmic imaging apparatus according to claims 1 to 5,
The ophthalmologic imaging apparatus, wherein the control unit controls the amount of data to be transferred to the host PC based on the communication status of the communication means.

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