JP2018038687A - Ophthalmologic apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ophthalmologic apparatus capable of reducing a fatigue and stress applied to a person being examined.SOLUTION: The ophthalmologic apparatus comprises a data acquisition part including an OCT (optical coherence tomography) unit 100 and an image formation part 220, a fixation system, and a control part 210. The data acquisition part includes an optical system for acquiring data on an eye being examined. The fixation system presents a fixation target to the eye being examined. The control part concurrently executes controlling the data acquisition part for acquiring the data on the eye being examined and controlling the fixation system for moving the fixation target.SELECTED DRAWING: Figure 3

Description

  The present invention relates to an ophthalmic apparatus.

  The ophthalmologic apparatus includes an ophthalmologic photographing apparatus for obtaining an image of the eye to be examined and an ophthalmologic measuring apparatus for measuring the characteristics of the eye to be examined.

  As an example of an ophthalmologic photographing apparatus, an optical coherence tomography using optical coherence tomography (OCT), an optical coherence tomograph that obtains a tomographic image, a fundus camera that photographs a fundus, or a fundus image by laser scanning using a confocal optical system There is a scanning laser ophthalmoscope (SLO) or the like.

  Examples of ophthalmic measuring devices include an ocular refraction examination device (refractometer, keratometer) that measures the refractive properties of the eye to be examined, a tonometer, a specular microscope that obtains the properties of the cornea (corneal thickness, cell distribution, etc.) There is a wavefront analyzer that obtains aberration information of an eye to be examined using a Hartmann-Shack sensor.

  Many ophthalmologic apparatuses are provided with a configuration for presenting a fixation target to an eye to be examined (or a fellow eye). The fixation target has a function of guiding a line of sight in order to acquire data of a desired part of the eye to be examined, and a function of fixing the eye to be examined during data acquisition.

JP 2014-200680 A

  In a conventional ophthalmologic apparatus, imaging or the like is performed while a subject is staring at a stationary fixation target. On the other hand, there are those that take several seconds or longer for imaging or the like, and the subject is required to stare at the fixation target throughout the imaging or the like. However, it is unnatural to keep staring at a stationary fixation target, and there is a risk of giving fatigue or stress to the subject. This problem appears to be particularly noticeable for children, the elderly and low vision people.

  An object of the present invention is to provide an ophthalmologic apparatus capable of photographing and measuring an eye to be examined in a natural state.

  The ophthalmologic apparatus of the embodiment includes a data acquisition unit, a fixation system, and a control unit. The data acquisition unit includes an optical system for acquiring data of the eye to be examined. The fixation system presents a fixation target to the eye to be examined. The control unit executes the control of the data acquisition unit for acquiring data of the eye to be examined and the control of the fixation system for moving the fixation target in parallel.

  According to the ophthalmologic apparatus according to the embodiment, it is possible to photograph and measure the eye to be examined in a natural state.

Schematic showing the example of a structure of the ophthalmologic apparatus which concerns on embodiment. Schematic showing the example of a structure of the ophthalmologic apparatus which concerns on embodiment. Schematic showing the example of a structure of the ophthalmologic apparatus which concerns on embodiment. The flowchart showing the example of operation | movement of the ophthalmologic apparatus which concerns on embodiment. The flowchart showing the example of operation | movement of the ophthalmologic apparatus which concerns on embodiment. The flowchart showing the example of operation | movement of the ophthalmologic apparatus which concerns on embodiment.

  Embodiments of the present invention will be described in detail with reference to the drawings. An ophthalmologic apparatus according to one embodiment includes an optical coherence tomography (OCT) and a fundus camera as elements for acquiring data of an eye to be examined. Here, instead of or in addition to the fundus camera, a scanning laser ophthalmoscope (SLO), a slit lamp microscope, an ophthalmic surgery microscope, an anterior ocular segment imaging camera, and the like may be provided. In the following example, swept source OCT is applied, but other types of OCT (spectral domain OCT, time domain OCT, unfath OCT, polarization OCT, etc.) may be applied.

<Constitution>
As shown in FIG. 1, the ophthalmologic apparatus 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200. The fundus camera unit 2 is provided with an optical system and a mechanism for acquiring a front image of the eye to be examined. The OCT unit 100 is provided with a part of an optical system and a mechanism for performing OCT. Another part of the optical system and mechanism for performing OCT is provided in the fundus camera unit 2. The arithmetic control unit 200 includes one or more processors that execute various types of arithmetic operations and controls. In addition to these, optional elements such as a member for supporting the subject's face (chin rest, forehead rest, etc.) and a lens unit for switching the OCT target site (for example, anterior segment OCT attachment) A unit may be provided in the ophthalmic apparatus 1.

  In this specification, the “processor” is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), or a programmable logic device (eg, SPLD (Simple ProLigL). It means a circuit such as Programmable Logic Device (FPGA) or Field Programmable Gate Array (FPGA). For example, the processor implements the functions according to the embodiment by reading and executing a program stored in a storage circuit or a storage device.

<Fundus camera unit 2>
The fundus camera unit 2 is provided with an optical system for photographing the fundus oculi Ef of the eye E to be examined. The acquired image of the fundus oculi Ef (referred to as a fundus oculi image, a fundus oculi photo, or the like) is a front image such as an observation image or a captured image. The observation image is obtained by moving image shooting using near infrared light. The photographed image is a still image using flash light.

  The fundus camera unit 2 includes an illumination optical system 10 and a photographing optical system 30. The illumination optical system 10 irradiates the eye E with illumination light. The imaging optical system 30 detects the return light of the illumination light from the eye E. The measurement light from the OCT unit 100 is guided to the eye E through the optical path in the fundus camera unit 2, and the return light is guided to the OCT unit 100 through the same optical path.

  The light (observation illumination light) output from the observation light source 11 of the illumination optical system 10 is reflected by the reflection mirror 12 having a curved reflecting surface, passes through the condensing lens 13 and passes through the visible cut filter 14. Near infrared light. Further, the observation illumination light is once converged in the vicinity of the photographing light source 15, reflected by the mirror 16, and passes through the relay lenses 17 and 18, the diaphragm 19 and the relay lens 20. The observation illumination light is reflected by the peripheral part of the perforated mirror 21 (area around the perforated part), passes through the dichroic mirror 46, and is refracted by the objective lens 22 to be examined eye E (fundus Ef or anterior eye). Part). The return light of the observation illumination light from the eye E is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through the hole formed in the central region of the perforated mirror 21, and passes through the dichroic mirror 55. The light is reflected by the mirror 32 via the photographing focusing lens 31. Further, the return light passes through the half mirror 33A, is reflected by the dichroic mirror 33, and forms an image on the light receiving surface of the image sensor 35 by the condenser lens. The image sensor 35 detects return light at a predetermined frame rate. Note that the focus of the photographing optical system 30 is adjusted to match the fundus oculi Ef or the anterior eye segment.

  The light (imaging illumination light) output from the imaging light source 15 is applied to the fundus oculi Ef through the same path as the observation illumination light. The return light of the imaging illumination light from the eye E is guided to the dichroic mirror 33 through the same path as the return light of the observation illumination light, passes through the dichroic mirror 33, is reflected by the mirror 36, and is reflected by the condenser lens 37. An image is formed on the light receiving surface of the image sensor 38.

  An LCD (Liquid Crystal Display) 39 displays a fixation target and an eyesight measurement target. A part of the light beam output from the LCD 39 is reflected by the half mirror 33 </ b> A, reflected by the mirror 32, passes through the hole of the perforated mirror 21 through the photographing focusing lens 31 and the dichroic mirror 55. The light beam that has passed through the aperture of the aperture mirror 21 passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus oculi Ef.

  By changing the display position of the fixation target on the screen of the LCD 39, the fixation position of the eye E can be changed. Examples of fixation positions include a fixation position for acquiring an image centered on the macula, a fixation position for acquiring an image centered on the optic nerve head, and between the macula and the optic nerve head. There are a fixation position for acquiring an image centered on the center of the fundus, a fixation position for acquiring an image of a part (a fundus peripheral portion) far away from the macula, and the like. A GUI (Graphical User Interface) or the like for designating at least one of such typical fixation positions can be provided. Further, a GUI or the like for manually moving the fixation position (display position of the fixation target) can be provided.

  The configuration for presenting the movable fixation target to the eye E is not limited to a display device such as an LCD. For example, a movable fixation target can be generated by selectively lighting a plurality of light sources in a light source array (light emitting diode (LED) array or the like). In addition, a movable fixation target can be generated by one or more movable light sources.

  The alignment optical system 50 generates an alignment index used for alignment of the optical system with respect to the eye E. The alignment light output from the LED 51 passes through the apertures 52 and 53 and the relay lens 54, is reflected by the dichroic mirror 55, and passes through the hole of the perforated mirror 21. The light that has passed through the hole of the perforated mirror 21 passes through the dichroic mirror 46 and is projected onto the eye E by the objective lens 22. The corneal reflection light of the alignment light is guided to the image sensor 35 through the same path as the return light of the observation illumination light. Manual alignment and auto-alignment can be executed based on the received light image (alignment index image).

  The focus optical system 60 generates a split index used for focus adjustment with respect to the eye E. The focus optical system 60 is moved along the optical path (illumination optical path) of the illumination optical system 10 in conjunction with the movement of the imaging focusing lens 31 along the optical path (imaging optical path) of the imaging optical system 30. The reflection bar 67 can be inserted into and removed from the illumination optical path. When performing the focus adjustment, the reflecting surface of the reflecting bar 67 is inclinedly arranged in the illumination optical path. The focus light output from the LED 61 passes through the relay lens 62, is separated into two light beams by the split indicator plate 63, passes through the two-hole aperture 64, is reflected by the mirror 65, and is reflected by the condenser lens 66 as a reflecting rod 67. The light is once imaged and reflected on the reflection surface. Further, the focus light passes through the relay lens 20, is reflected by the perforated mirror 21, passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus oculi Ef. The fundus reflected light of the focus light is guided to the image sensor 35 through the same path as the cornea reflected light of the alignment light. Manual alignment and auto alignment can be executed based on the received light image (split index image).

  The diopter correction lenses 70 and 71 can be selectively inserted into a photographing optical path between the perforated mirror 21 and the dichroic mirror 55. The diopter correction lens 70 is a plus lens (convex lens) for correcting the intensity hyperopia. The diopter correction lens 71 is a minus lens (concave lens) for correcting intensity myopia.

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

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

  The optical scanner 42 is disposed at a position optically conjugate with the pupil of the eye E. The optical scanner 42 deflects the measurement light LS passing through the OCT optical path. The optical scanner 42 is, for example, a galvano scanner capable of two-dimensional scanning.

  The OCT focusing lens 43 is moved along the optical path of the measurement light LS in order to adjust the focus of the OCT optical system. The movement of the photographing focusing lens 31, the movement of the focus optical system 60, and the movement of the OCT focusing lens 43 can be controlled in a coordinated manner.

<OCT unit 100>
As illustrated in FIG. 2, the OCT unit 100 is provided with an optical system for executing the swept source OCT. This optical system divides the light from the wavelength tunable light source (wavelength sweep type light source) into the measurement light and the reference light, and causes the return light of the measurement light from the eye E to interfere with the reference light via the reference light path. An interference optical system that generates interference light and detects the interference light. A detection result (detection signal) obtained by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the arithmetic control unit 200.

  The light source unit 101 includes, for example, a near-infrared wavelength variable laser that changes the wavelength of emitted light at high speed. The light L0 output from the light source unit 101 is guided to the polarization controller 103 by the optical fiber 102 and its polarization state is adjusted. Further, the light L0 is guided to the fiber coupler 105 by the optical fiber 104 and is divided into the measurement light LS and the reference light LR.

  The reference light LR is guided to the collimator 111 by the optical fiber 110 and converted into a parallel light beam, and is guided to the corner cube 114 via the optical path length correction member 112 and the dispersion compensation member 113. The optical path length correction member 112 acts to match the optical path length of the reference light LR and the optical path length of the measurement light LS. The dispersion compensation member 113 acts to match the dispersion characteristics between the reference light LR and the measurement light LS. The corner cube 114 is movable in the incident direction of the reference light LR, and thereby the optical path length of the reference light LR is changed.

  The reference light LR that has passed through the corner cube 114 passes through the dispersion compensation member 113 and the optical path length correction member 112, is converted from a parallel light beam to a focused light beam by the collimator 116, and enters the optical fiber 117. The reference light LR incident on the optical fiber 117 is guided to the polarization controller 118 and its polarization state is adjusted. The reference light LR is guided to the attenuator 120 by the optical fiber 119 and the amount of light is adjusted, and is guided to the fiber coupler 122 by the optical fiber 121. It is burned.

  On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber 127 and converted into a parallel light beam by the collimator lens unit 40, and the optical path length changing unit 41, the optical scanner 42, the OCT focusing lens 43, and the mirror 44. Then, the light passes through the relay lens 45, is reflected by the dichroic mirror 46, is refracted by the objective lens 22, and enters the eye E to be examined. The measurement light LS is scattered and reflected at various depth positions of the eye E. The return light of the measurement light LS from the eye E travels in the reverse direction on the same path as the forward path, is guided to the fiber coupler 105, and reaches the fiber coupler 122 via the optical fiber 128.

  The fiber coupler 122 combines (interferes) the measurement light LS incident through the optical fiber 128 and the reference light LR incident through the optical fiber 121 to generate interference light. The fiber coupler 122 generates a pair of interference light LC by branching the interference light at a predetermined branching ratio (for example, 1: 1). The pair of interference lights LC are guided to the detector 125 through optical fibers 123 and 124, respectively.

  The detector 125 is, for example, a balanced photodiode. The balanced photodiode has a pair of photodetectors that respectively detect the pair of interference lights LC, and outputs a difference between detection results obtained by these. The detector 125 sends this output (detection signal) to a DAQ (Data Acquisition System) 130.

  The clock 130 is supplied from the light source unit 101 to the DAQ 130. The clock KC is generated in synchronization with the output timing of each wavelength that is swept within a predetermined wavelength range by the wavelength variable light source in the light source unit 101. For example, the light source unit 101 optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then generates a clock KC based on the result of detecting these combined lights. Generate. The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC. The DAQ 130 sends the sampling result of the detection signal from the detector 125 to the arithmetic control unit 200.

  In this example, the optical path length changing unit 41 for changing the length of the optical path (measurement optical path, measurement arm) of the measurement light LS and the length of the optical path (reference optical path, reference arm) of the reference light LR are changed. However, only one of the optical path length changing unit 41 and the corner cube 114 may be provided. It is also possible to change the difference between the measurement optical path length and the reference optical path length using optical members other than these.

<Control system>
A configuration example of the control system of the ophthalmologic apparatus 1 is shown in FIG. The control unit 210, the image forming unit 220, and the data processing unit 230 are provided in the arithmetic control unit 200.

<Control unit 210>
The control unit 210 executes various controls. The control unit 210 includes a main control unit 211 and a storage unit 212.

<Main control unit 211>
The main control unit 211 includes a processor and controls each unit of the ophthalmologic apparatus 1 (including the elements shown in FIGS. 1 to 3). The imaging focusing lens 31 is moved by an imaging focusing drive unit (not shown), and the OCT focusing lens is moved by an OCT focusing drive unit. The reference driving unit 114A moves the corner cube 114.

  For example, the moving mechanism 150 moves at least the fundus camera unit 2 in a three-dimensional manner. In a typical example, the moving mechanism 150 includes an x stage that can move in the x direction (left and right direction), an x moving mechanism that moves the x stage, a y stage that can move in the y direction (up and down direction), and y A y moving mechanism that moves the stage, a z stage that can move in the z direction (depth direction), and a z moving mechanism that moves the z stage are included. Each moving mechanism includes an actuator such as a pulse motor and is controlled by the main control unit 211.

  The main control unit 211 controls the LCD 39. For example, the main control unit 211 displays a fixation target at a preset position on the screen of the LCD 39. Further, the main control unit 211 can gradually change the display position of the fixation target displayed on the LCD 39 (that is, the fixation target can be moved). The display position and movement mode of the fixation target are set manually or automatically. Manual setting is performed using, for example, a GUI. The automatic setting is performed by, for example, a movement pattern setting unit 231 described later.

<Storage unit 212>
The storage unit 212 stores various data. Examples of data stored in the storage unit 212 include OCT images, fundus images, and eye information. The eye information includes subject information such as patient ID and name, left / right eye identification information, electronic medical record information, and the like.

<Image forming unit 220>
The image forming unit 220 forms an image based on the output from the DAQ 130 (sampling result of the detection signal). For example, like the conventional swept source OCT, the image forming unit 220 performs signal processing on the spectrum distribution based on the sampling result for each A line to form a reflection intensity profile for each A line, and converts these A line profiles into images. And arrange them along the scan line. The signal processing includes noise removal (noise reduction), filter processing, FFT (Fast Fourier Transform), and the like.

<Data processing unit 230>
The data processing unit 230 performs image processing and analysis processing on the image formed by the image forming unit 220. For example, the data processing unit 230 executes creation of 3D image data (stack data, volume data, etc.) based on raster scan data, rendering of 3D image data, image correction, image analysis based on an analysis application, and the like. The data processing unit 230 includes a movement pattern setting unit 231 and a motion detection unit 232.

<Movement pattern setting unit 231>
The movement pattern setting unit 231 sets the movement pattern of the fixation target. The movement pattern represents one of a route along which the fixation target is moved, information equivalent to the route, information deriving from the route, information corresponding thereto, information related thereto, and the like.

  As a typical example, the movement pattern includes the shape of the movement path of the fixation target, the direction of the shape, the size, the movement direction, the movement speed, and the like. Examples of shapes include circles, rectangles, spirals, straight lines, and random shapes. The shape orientation may be set when the shape is asymmetric. As the moving direction, for example: in the case of a circle, rectangle, spiral, etc., it is possible to set clockwise, counterclockwise, or a combination of these; The approaching direction, a combination thereof, and the like can be set; in the case of a linear shape, the direction from the first end toward the second end, the direction from the second end toward the first end, a combination thereof (for example, the first end Reciprocation between the end and the second end) can be set. The moving speed can be selected from options such as low speed, medium speed, and high speed. Moreover, a desired moving speed may be set or the moving speed may be adjustable.

  When a movement pattern (for example, one or more of shape, shape direction, size, movement direction, movement speed, etc.) is specified using the user interface 240 (GUI or the like), the movement pattern setting unit 231 displays Set the movement pattern corresponding to the specified content.

  It is possible to set a movement pattern with reference to medical information such as an electronic medical record. For example, when a movement pattern actually applied in photographing or the like is recorded in an electronic medical record or the like, the movement pattern setting unit 231 reads a movement pattern applied in the past from the electronic medical record of the subject, and this movement pattern Can be set as the movement pattern for the current photographing. As another example, when correspondence information in which predetermined information (for example, a disease name) and a movement pattern are associated with each other is created in advance, the movement pattern setting unit 231 determines the diagnosis name (disease) from the subject's electronic medical record. Name) can be read out, and the movement pattern corresponding to the diagnosis name can be acquired from the correspondence information.

  Preliminary photographing for determining a movement pattern applied to photographing can be performed. For example, the main control unit 211 causes the ophthalmologic apparatus 1 to perform OCT of the fundus oculi Ef while controlling the LCD 39 to move the fixation target according to one or more movement patterns. When two or more movement patterns are applied, OCT of the fundus oculi Ef is executed while sequentially applying these movement patterns.

  The movement pattern setting unit 231 evaluates data collected by such preliminary OCT or an image based thereon. In a typical example, the movement pattern setting unit 231 can perform one or more of noise evaluation, image quality evaluation, contrast evaluation, sharpness evaluation, granularity evaluation, and the like.

  The movement pattern setting unit 231 determines whether the result of this evaluation is included in the allowable range. For example, the movement pattern setting unit 231 determines whether a value (evaluation value) calculated by the evaluation process exceeds a predetermined threshold value. When the evaluation result is included in the allowable range, the movement pattern setting unit 231 sets the movement pattern applied in the preliminary OCT (movement pattern applied at the time of data collection) as the movement pattern for the main imaging. When the evaluation result is not included in the allowable range (when none of the one or more movement patterns is appropriate), for example, the mode is shifted to a mode for manually setting the movement pattern.

  Any two or more of the above movement pattern setting modes (manual setting mode, medical information reference mode, preliminary imaging mode, etc.) can be combined, or any two or more can be executed sequentially.

  One example will be described. First, the movement pattern setting unit 231 determines whether or not the medical information reference mode can be executed. For example, the movement pattern setting unit 231 determines whether or not predetermined information (such as a movement pattern applied in the past) is recorded in an electronic medical record or the like.

  When predetermined information is recorded in an electronic medical record or the like, a movement pattern is set in the medical information reference mode. In order to confirm whether or not this movement pattern is appropriate, a preliminary photographing mode using this movement pattern can be executed.

  When the predetermined information is not recorded on the electronic medical record or the like, the preliminary photographing mode is entered. When an appropriate movement pattern is determined by the preliminary photographing mode, this movement pattern is adopted. When an appropriate movement pattern is not determined by the preliminary photographing mode, the mode is shifted to the manual setting mode.

  The combination and order of the movement pattern setting modes (manual setting mode, medical information reference mode, preliminary imaging mode, etc.) are not limited to the above example.

<Motion detection unit 232>
The motion detection unit 232 detects the motion of the eye E. A method for detecting the movement of the eye E is arbitrary.

  For example, the motion detection unit 232 can obtain the motion (positional change over time) of the eye E by analyzing a moving image of the eye E. As an example of this moving image, there is an observation image of the anterior segment or the fundus oculi Ef. The motion detection unit 232 identifies a predetermined region (pupil region, pupil center, iris region, iris center, macular region, optic disc region, lesion region, laser treatment spot, etc.) in each frame of the moving image, and a plurality of frames. The movement of the eye E can be detected by comparing the positions of the predetermined regions. This process is also used in conventional auto alignment and tracking.

  In another example, a projection optical system that projects a light beam onto the cornea or fundus oculi Ef of the eye E and a detection optical system that detects the reflected light beam with an area sensor or the like are provided. The motion detection unit 232 can detect the motion of the eye E based on a change over time in the detection position of the reflected light beam by the detection optical system. The method for detecting the movement of the eye E is not limited to these.

<User Interface 240>
The user interface 240 includes a display unit 241 and an operation unit 242. The display unit 241 includes the display device 3. The operation unit 242 includes various operation devices and input devices. The user interface 240 may include a device such as a touch panel in which a display function and an operation function are integrated. Embodiments that do not include at least a portion of the user interface 240 can also be constructed. For example, the display device may be an external device connected to the ophthalmologic apparatus.

<Operation>
The operation of the ophthalmologic apparatus 1 will be described.

<First operation example>
A first operation example is shown in FIG. This operation example includes parallel control of OCT scan and fixation target movement.

(S1: Fixation target movement pattern setting)
First, the movement pattern setting unit 231 sets the movement pattern of the fixation target. This process is executed as described above.

(S2: Start of fixation target presentation)
The main control unit 211 starts presenting the fixation target by controlling the LCD 39. For example, the main control unit 211 displays the fixation target at the initial position (pixel position of the LCD 39) based on the movement pattern set in step S1. Alternatively, the main control unit 211 displays a fixation target at a position set in advance for the alignment in step S3 and the like.

(S3: Alignment / Focus adjustment)
The main controller 211 controls the alignment optical system 50 to project an alignment index (two alignment bright spots) onto the eye E. As in the prior art, auto alignment or manual alignment is executed. Further, the main control unit 211 controls the focus optical system 60 to project the split index onto the fundus oculi Ef. As in the prior art, auto-focusing or manual focusing is performed.

  Furthermore, as the optimization of the photographing conditions, it is possible to execute adjustment of the optical path length of the measurement light path, adjustment of the polarization state of the measurement light LS, adjustment of the light amount of the measurement light LS, adjustment of the focus of the measurement light path, and the like. After the optimization is completed, the examiner (or the ophthalmologic apparatus 1) can check whether a problem such as flare contamination has occurred in the observation image.

(S4: Start shooting)
The examiner or the main control unit 211 gives an instruction to start imaging (OCT, fundus imaging, etc.). For example, the examiner can perform an operation for instructing to start photographing using the user interface 240. In addition, the main control unit 211 receives, for example, completion of alignment and focus adjustment, completion of optimization of imaging conditions, or absence of a problem such as flare mixture or the elimination of the problem. Thus, an instruction to start shooting can be generated.

  When an instruction to start photographing is given, the main control unit 211 executes the control in step S5A and the control in step S5B at an arbitrary timing. For example, the main control unit 211 can start step S5A and step S5B simultaneously. Alternatively, the main control unit 211 can start the other at a predetermined timing after starting one of the steps S5A and S5B.

(S5A: Start of fixation target movement)
The main control unit 211 starts moving the fixation target according to the movement pattern set in step S1.

(S5B: Start of OCT scan)
The main control unit 211 starts scanning the fundus oculi Ef using OCT by controlling the OCT unit 100, the optical scanner 42, and the like. This scan may be a scan that requires a relatively long time, such as a raster scan (three-dimensional scan), OCT angiography (OCT angiography), or OCT blood flow measurement.

(S6A: completion of movement of fixation target)
The main control unit 211 completes the movement of the fixation target at a predetermined timing. The predetermined timing is based on, for example, an examiner's instruction, completion of the OCT scan, and the like.

(S6B: Completion of OCT scan)
The main control unit 211 completes the OCT scan at a predetermined timing. The predetermined timing is based on, for example, an examiner's instruction, completion of movement of the fixation target, and the like.

  The main control unit 211 can simultaneously end the movement of the fixation target and the OCT scan. Alternatively, the main control unit 211 can end one of the fixation target movement and the OCT scan and then end the other at a predetermined timing.

  By such control, the movement of the fixation target and the OCT scan are executed in parallel. Here, executing two (or three or more) controls in parallel means overlapping at least part of a period during which one control is executed and at least part of a period during which another control is executed. Means. In this example, the main control unit 211 executes both controls so that at least a part of the period during which the fixation target is moved overlaps at least a part of the period during which the OCT scan is executed.

(S7: Formation of OCT image)
The image forming unit 220 forms an image of the fundus oculi Ef based on data collected by parallel control of the fixation target movement and the OCT scan. The data processing unit 230 can process the image formed by the image forming unit 220.

  The image formed in step S7 may be, for example, volume data representing a three-dimensional region of the fundus oculi Ef, a rendering image thereof, an angiographic image (angiogram) of the fundus oculi Ef, a blood flow image of the fundus oculi Ef, and the like.

<Second operation example>
A second operation example is shown in FIG. This operation example includes parallel control of the OCT scan, the movement of the fixation target, and the tracking using the moving mechanism 150.

(S1-S4)
Steps S1 to S4 are executed, for example, in the same manner as in the first operation example.

  When an instruction to start imaging is given in step S4, the main control unit 211 performs OCT scan control, fixation target movement control, and tracking control using the movement mechanism 150 at arbitrary timings. For example, the main control unit 211 can simultaneously start two or three of these three controls. Alternatively, the main control unit 211 starts the first control among these three controls, starts the second control at a predetermined timing thereafter, and starts the third control at the subsequent predetermined timing. be able to. In FIG. 5, the OCT scan control and the fixation target movement control are collectively referred to as step S15A, and the tracking control is defined as step S15B.

(S15A: fixation target movement / OCT scan start)
The main control unit 211 starts the movement of the fixation target according to the movement pattern set in step S1 at a predetermined timing, and starts an OCT scan at a predetermined timing. The start of movement of the fixation target is the same as step S5A in the first operation example, and the start of the OCT scan is the same as step S5B.

(S15B: Start of tracking by moving mechanism)
The main control unit 211 starts tracking by the moving mechanism 150 at a predetermined timing. The first processing example of tracking according to this example is, for example, acquisition of a moving image of the eye E, detection of the movement of the eye E by the motion detection unit 232, and the movement mechanism 150 according to the detected movement. Including control. The main control unit 211 causes the fundus camera unit 2 to follow the movement of the eye E detected by the motion detection unit 232 substantially in real time while acquiring the infrared observation image in the fundus camera unit 2 (in other words, The movement mechanism 150 is controlled so as to cancel the displacement of the eye E). According to the first processing example, the optical system can be caused to follow the movement of the eye E to be examined in substantially real time.

  The second tracking processing example according to this example includes, for example, control of the moving mechanism 150 based on the moving pattern set in step S1. The main control unit 211 controls the movement mechanism 150 so that the fundus camera unit 2 follows the movement of the eye E in the line of sight according to the movement pattern set in step S1. The second processing example is based on the premise that the eye E follows the moving fixation target.

  The first processing example and the second processing example may be combined. For example, while executing the second processing example, the displacement between the appropriate line-of-sight direction and the actual orientation (position) of the eye E to be examined is obtained, and the first processing example is executed when the displacement exceeds a predetermined threshold value. can do.

(S16A: movement of fixation target / completion of OCT scan)
The main control unit 211 completes the movement of the fixation target at a predetermined timing, as in step S6A of the first operation example. Further, the main control unit 211 completes the OCT scan at a predetermined timing, as in step S6B of the first operation example.

(S16B: completion of tracking by moving mechanism)
The main control unit 211 completes tracking by the moving mechanism 150 at a predetermined timing. The predetermined timing is based on, for example, an examiner's instruction, completion of the movement of the fixation target, completion of the OCT scan, and the like.

  By such control, the movement of the fixation target, the OCT scan, and the tracking by the moving mechanism 150 are executed in parallel. In this example, at least a part of the period during which the fixation target is moved, at least a part of the period during which the OCT scan is performed, and at least a part of the period during which tracking by the moving mechanism 150 is performed overlap. Thus, the main control unit 211 performs three controls.

(S7: Formation of OCT image)
The image forming unit 220 forms an image of the fundus oculi Ef based on data collected by parallel control of fixation target movement, OCT scan, and tracking. This process is executed in the same manner as step S7 in the first operation example.

<Third operation example>
A third operation example is shown in FIG. This operation example includes parallel control of OCT scan, movement of the fixation target, and tracking using the optical scanner 42.

(S1-S4)
Steps S1 to S4 are executed, for example, in the same manner as in the first operation example.

  When an instruction to start imaging is given in step S4, the main control unit 211 executes OCT scan control, fixation target movement control, and tracking control using the optical scanner 42 at arbitrary timings. For example, the main control unit 211 can simultaneously start two or three of these three controls. Alternatively, the main control unit 211 starts the first control among these three controls, starts the second control at a predetermined timing thereafter, and starts the third control at the subsequent predetermined timing. be able to. In FIG. 6, the OCT scan control and the fixation target movement control are collectively referred to as step S25A, and the tracking control is referred to as step S25B.

(S25A: movement of fixation target / start of OCT scan)
The main control unit 211 starts the movement of the fixation target according to the movement pattern set in step S1 at a predetermined timing, and starts an OCT scan at a predetermined timing. The start of movement of the fixation target is the same as step S5A in the first operation example, and the start of the OCT scan is the same as step S5B.

(S25B: Start of tracking by optical scanner)
The main control unit 211 starts tracking by the optical scanner 42 at a predetermined timing. The first processing example of tracking according to this example is, for example, acquisition of a moving image of the eye E, detection of the movement of the eye E by the motion detection unit 232, and the optical scanner 42 corresponding to the detected movement. Including control. The main control unit 211 causes the fundus camera unit 2 to acquire an infrared observation image and causes the projection position of the measurement light LS to follow the movement of the eye E detected by the motion detection unit 232 substantially in real time ( In other words, the optical scanner 42 is controlled so as to cancel the displacement of the eye E. According to the first processing example, the projection position of the measurement light LS can be caused to follow the movement of the eye E to be examined substantially in real time.

  The second processing example of tracking according to this example includes control of the optical scanner 42 based on the movement pattern set in step S1, for example. The main control unit 211 controls the optical scanner 42 so that the projection position of the measurement light LS follows the movement of the eye E in the line of sight according to the movement pattern set in step S1. The second processing example is based on the premise that the eye E follows the moving fixation target.

  The first processing example and the second processing example may be combined. For example, while executing the second processing example, the displacement between the appropriate line-of-sight direction and the actual orientation (position) of the eye E to be examined is obtained, and the first processing example is executed when the displacement exceeds a predetermined threshold value. can do.

(S26A: movement of fixation target / completion of OCT scan)
The main control unit 211 completes the movement of the fixation target at a predetermined timing, as in step S6A of the first operation example. Further, the main control unit 211 completes the OCT scan at a predetermined timing, as in step S6B of the first operation example.

(S26B: Completion of tracking by optical scanner)
The main control unit 211 completes tracking by the optical scanner 42 at a predetermined timing. The predetermined timing is based on, for example, an examiner's instruction, completion of the movement of the fixation target, completion of the OCT scan, and the like.

  By such control, the movement of the fixation target, the OCT scan, and the tracking by the optical scanner 42 are executed in parallel. In this example, at least a part of the period during which the fixation target is moved, at least a part of the period during which the OCT scan is performed, and at least a part of the period during which tracking by the optical scanner 42 is performed overlap. Thus, the main control unit 211 performs three controls.

(S7: Formation of OCT image)
The image forming unit 220 forms an image of the fundus oculi Ef based on data collected by parallel control of fixation target movement, OCT scan, and tracking. This process is executed in the same manner as step S7 in the first operation example.

<Action and effect>
The operation and effect of the ophthalmologic apparatus according to the embodiment will be described.

  The ophthalmologic apparatus of the embodiment includes a data acquisition unit, a fixation system, and a control unit. The data acquisition unit includes an optical system for acquiring data of the eye to be examined. In the above example, the data acquisition unit includes an optical system for executing OCT and the image forming unit 220. The fixation system presents a fixation target to the eye to be examined. In the above example, the fixation system includes the LCD 39 and an element for guiding the light output from the LCD 39 to the eye E. The control unit executes the control of the data acquisition unit for acquiring data of the eye to be examined and the control of the fixation system for moving the fixation target in parallel. In the above example, the control unit includes the main control unit 211.

  According to such an ophthalmologic apparatus, since it is possible to perform photographing and measurement while moving the fixation target, compared to a conventional ophthalmologic apparatus that requires gaze of a stationary fixation target, Imaging and measurement of the eye to be examined are possible. Thereby, for example, fatigue and stress applied to the subject can be reduced.

  The ophthalmologic apparatus of the embodiment may have a tracking function. The tracking function can be realized using, for example, a moving mechanism that moves the optical system of the data acquisition unit. In the above example, the moving mechanism 150 moves the optical system. Further, the control unit performs control of the data acquisition unit for acquiring data of the eye to be examined, control of the fixation system for moving the fixation target, and control of the moving mechanism for moving the optical system. Can be executed in parallel.

  In one example, the ophthalmologic apparatus of the embodiment may include a detection unit that detects the movement of the eye to be examined. In the above example, the detection unit includes the motion detection unit 232. Furthermore, the control unit can execute control of the movement mechanism according to the movement of the eye to be examined detected by the detection unit.

  In another example, the control unit controls the fixation system so as to move the fixation target according to a predetermined movement pattern (predetermined pattern), and executes control of the moving mechanism based on the predetermined pattern. can do.

  It is also possible to realize a tracking function using an optical scanner. The optical scanner scans the eye to be examined with light from a light source. In the above example, the optical scanner 42 for scanning the eye E with the light (measurement light LS) from the light source unit 101 is used.

  In one example, the ophthalmologic apparatus of the embodiment may include a detection unit that detects the movement of the eye to be examined. Furthermore, in the control of the data acquisition unit for acquiring the data of the eye to be examined, the control unit executes control of the optical system according to the movement of the eye to be examined detected by the detection unit. Thereby, the correction of the scan position is executed substantially in real time according to the movement of the eye to be examined. For example, when a scan of the eye to be examined is executed with a preset scan pattern, a series of scan positions corresponding to the scan pattern can be corrected according to the movement of the eye to be examined.

  In another example, the control unit executes the fixation system control so as to move the fixation target according to the predetermined pattern, and in the control of the data acquisition unit for acquiring the data of the eye to be examined, the predetermined pattern Control of the optical system based on can be executed.

  According to the functions as described above, it is possible to photograph and measure the subject's eye in a natural state, and photograph and measure an appropriate position by tracking according to the movement of the subject's eye and / or the movement of the fixation target. It becomes possible.

  The ophthalmologic apparatus of the embodiment may include a function (setting unit) for setting a movement pattern of the fixation target. In the above example, the setting unit includes a movement pattern setting unit 231. Furthermore, the control unit can execute fixation system control so as to move the fixation target according to the movement pattern set by the setting unit. The movement pattern set by the setting unit can be used as the predetermined pattern.

  As a method for setting the movement pattern of the fixation target, for example, a method in which the examiner manually sets, a method in which medical information such as an electronic medical record is referred to, a preliminary imaging for setting a movement pattern (preliminary There is a method of setting using measurement), an arbitrary combination of these, and the like.

  The preliminary imaging (preliminary measurement) is executed before the main imaging (main measurement) including parallel control of the data acquisition unit and the fixation system (and tracking). In the specific example, the control unit causes the data acquisition unit to acquire preliminary data while executing the fixation system control so as to move the fixation target according to one or more patterns. The setting unit can set a movement pattern based on the acquired preliminary data.

  By providing the movement pattern setting function exemplified above, it is possible to use the movement pattern of the fixation target corresponding to the subject and the eye to be examined. That is, when the fixation target moves, patterns (shape, direction, size, movement direction, movement speed, etc.) that are easy to follow the fixation target are considered to be different for each subject and each eye to be examined. Therefore, according to the ophthalmologic apparatus that can set the movement pattern of the fixation target, a suitable movement pattern for each subject and each eye to be examined (for example, natural movement that is considered to cause less fatigue and stress on the subject) Pattern) can be applied.

  The embodiment described above is merely an example of the present invention. A person who intends to implement the present invention can arbitrarily make modifications (omission, substitution, addition, etc.) within the scope of the present invention.

  4 to 6, the movement of the fixation target is started after the start of imaging (measurement), but the timing at which the movement of the fixation target is started is not limited after the start of imaging. For example, the fixation target can be moved while performing preparatory operations such as alignment, focus adjustment, and optimization of imaging conditions. Thereby, it is possible to practice how to move the eye according to the movement pattern of the fixation target, and to encourage the subject to get used to the movement pattern.

  Prior to the main photographing (main measurement), it is possible to practice how to move the eye to be examined by moving the fixation target in a predetermined pattern. Further, in response to a predetermined trigger, preliminary imaging (preliminary measurement) can be performed while repeating the movement of the fixation target a predetermined number of times while executing tracking. As a specific example, after starting tracking and blink detection processing, the fixation target is moved three times along a circular orbit (clockwise or counterclockwise) in response to detection of blink of the eye to be examined. However, it is possible to photograph the fundus that performs a substantially circular motion. By evaluating the data obtained by such preliminary imaging (preliminary measurement), it is possible to determine whether the guidance of the line of sight with the fixation target is appropriate. Depending on the result of this determination, it is possible to practice again how to move the eye to be examined, change the movement pattern for the practice, or start actual imaging (main measurement).

  By predicting the movement pattern of the eye to be examined, it is possible to set the movement pattern of the fixation target and the tracking pattern. The motion pattern of the eye to be examined can be predicted based on, for example, data acquired by the motion detection unit 232.

  When photographing or measurement is performed in a binocular vision state, a fixation target can be presented to both eyes of the subject. At this time, the left eye fixation target and the right eye fixation target can be controlled to move according to the same pattern. Such an operation is realized by, for example, synchronous control of a display device that displays a left eye fixation target and a display device that displays a right eye fixation target. According to this function, shooting and measurement can be performed in a natural binocular vision state.

1 Ophthalmology equipment 39 LCD
42 Optical Scanner 100 OCT Unit 101 Light Source Unit 211 Main Control Unit 220 Image Forming Unit 231 Movement Pattern Setting Unit 232 Motion Detection Unit

Claims (8)

A data acquisition unit including an optical system for acquiring data of the eye to be examined;
A fixation system for presenting a fixation target to the eye to be examined;
An ophthalmologic apparatus comprising: a control unit that executes in parallel the control of the data acquisition unit for acquiring the data and the control of the fixation system for moving the fixation target. A moving mechanism for moving the optical system;
The control unit is configured to control the data acquisition unit to acquire the data, control the fixation system to move the fixation target, and control the movement mechanism to move the optical system. The ophthalmologic apparatus according to claim 1, wherein the ophthalmologic apparatus is executed in parallel. A detection unit for detecting the movement of the eye to be examined;
The ophthalmologic apparatus according to claim 2, wherein the control unit performs control of the moving mechanism according to the movement of the eye to be examined detected by the detection unit. The control unit executes control of the fixation system so as to move the fixation target according to a predetermined pattern, and executes control of the moving mechanism based on the predetermined pattern. Item 4. The ophthalmic apparatus according to Item 2 or 3. A detection unit for detecting the movement of the eye to be examined;
The optical system includes an optical scanner for scanning the eye to be examined with light from a light source,
The said control part performs control of the said optical system according to the motion of the said to-be-tested eye detected by the said detection part in control of the said data acquisition part for acquiring the said data. The ophthalmologic apparatus in any one of 1-4. The control unit performs control of the fixation system so as to move the fixation target according to a predetermined pattern, and based on the predetermined pattern in the control of the data acquisition unit for acquiring the data The ophthalmologic apparatus according to claim 1, wherein control of the optical system is executed. A setting unit for setting a movement pattern of the fixation target;
The said control part performs control of the said fixation system so that the said fixation target may be moved according to the said movement pattern set by the said setting part. The any one of Claims 1-6 characterized by the above-mentioned. Ophthalmic equipment. At least before the parallel control of the data acquisition unit and the fixation system, the control unit performs the fixation system control to move the fixation target according to one or more patterns. Let the data acquisition unit acquire preliminary data,
The ophthalmologic apparatus according to claim 7, wherein the setting unit sets the movement pattern based on the preliminary data.