JP5415902B2 - Ophthalmic observation device - Google Patents

Description

  The present invention relates to an ophthalmologic observation apparatus that forms an image of an eye to be examined using optical coherence tomography (OCT).

  In recent years, OCT that forms an image representing the surface form or internal form of an object to be measured using a light beam from a laser light source or the like has attracted attention. Since OCT has no invasiveness to the human body like X-ray CT, it is expected to be applied particularly in the medical field and the biological field. For example, in the field of ophthalmology, an apparatus for forming an image of the fundus oculi, cornea, etc. has entered a practical stage.

  Patent Document 1 discloses an apparatus to which OCT is applied. In this device, the measuring arm scans an object with a rotary turning mirror (galvanomirror), a reference mirror is installed on the reference arm, and the intensity of the interference light of the light beam from the measuring arm and the reference arm is dispersed at the exit. An interferometer is provided for analysis by the instrument. Further, the reference arm is configured to change the phase of the reference light beam stepwise by a discontinuous value.

  The apparatus of Patent Document 1 uses a so-called “Fourier Domain OCT (Fourier Domain OCT)” technique. In other words, a low-coherence beam is irradiated onto the object to be measured, the reflected light and the reference light are superimposed to generate interference light, and the spectral intensity distribution of the interference light is acquired and subjected to Fourier transform. Thus, the form of the object to be measured in the depth direction (z direction) is imaged. Note that this type of technique is also called a spectral domain.

  Furthermore, the apparatus described in Patent Document 1 includes a galvanometer mirror that scans a light beam (signal light), thereby forming an image of a desired measurement target region of the object to be measured. Since this apparatus is configured to scan the light beam only in one direction (x direction) orthogonal to the z direction, the image formed by this apparatus is in the scanning direction (x direction) of the light beam. It becomes a two-dimensional tomogram in the depth direction (z direction) along.

  In Patent Document 2, a plurality of two-dimensional tomographic images in the horizontal direction are formed by scanning (scanning) the signal light in the horizontal direction (x direction) and the vertical direction (y direction), and based on the plurality of tomographic images. A technique for acquiring and imaging three-dimensional tomographic information of a measurement range is disclosed. Examples of the three-dimensional imaging include a method of displaying a plurality of tomographic images side by side in a vertical direction (referred to as stack data) and a method of rendering a plurality of tomographic images to form a three-dimensional image. Conceivable.

  Patent Documents 3 and 4 disclose other types of OCT apparatuses. Patent Document 3 scans the wavelength of light applied to an object to be measured, acquires a spectral intensity distribution based on interference light obtained by superimposing reflected light of each wavelength and reference light, On the other hand, an OCT apparatus for imaging the form of an object to be measured by performing Fourier transform on the object is described. Such an OCT apparatus is called a swept source type. The swept source type is a kind of Fourier domain type.

  In Patent Document 4, the traveling direction of light is obtained by irradiating the object to be measured with light having a predetermined beam diameter, and analyzing the component of interference light obtained by superimposing the reflected light and the reference light. An OCT apparatus for forming an image of an object to be measured in a cross-section orthogonal to is described. Such an OCT apparatus is called a full-field type or an en-face type.

  Patent Document 5 discloses a configuration in which OCT is applied to the ophthalmic field. Prior to the application of OCT, a fundus camera, a slit lamp, or the like was used as an apparatus for observing the eye to be examined (see, for example, Patent Document 6 and Patent Document 7). A fundus camera is a device that shoots the fundus by illuminating the subject's eye with illumination light and receiving the fundus reflection light. A slit lamp is a device that acquires an image of a cross-section of the cornea by cutting off a light section of the cornea using slit light.

  An apparatus using OCT has an advantage over a fundus camera or the like in that a high-definition image can be acquired, and further, a tomographic image or a three-dimensional image can be acquired.

  As described above, an apparatus using OCT can be applied to observation of various parts of an eye to be examined, and can acquire high-definition images, and thus has been applied to diagnosis of various ophthalmic diseases.

JP 11-325849 A JP 2002-139421 A JP 2007-24677 A JP 2006-153838 A JP 2008-73099 A JP-A-9-276232 JP 2008-259544 A JP 2008-154939 A

  In OCT measurement, a technique for adjusting an optical path length difference between signal light and reference light so that an observation target site is depicted at a suitable position in a frame is known (see, for example, Patent Document 8). . This suitable position is a position with high measurement sensitivity.

  As described above, there is a technique for arranging the observation target portion at a suitable position, but there may be a case where it is desired to correct the automatically arranged position. Some devices do not have this technology. In these cases, there is a possibility that the site to be observed protrudes from the frame. Further, when a tomographic image of a predetermined cross section of the object to be measured is displayed as a moving image, there is a possibility that the observation target part may protrude from the frame due to movement of the object to be measured.

  For example, in the medical field, there are cases where the displayed tomographic image cannot be continuously observed. Then, even if the observation target part protrudes from the frame, the measurement may be continued without noticing it.

  In particular, when observing a deep part such as the optic nerve head of the fundus, the upper part or the lower part of the part tends to protrude from the frame. In addition, when performing OCT measurement of the eye to be examined, the image is often inclined due to the alignment state, the shape of the observation target part, and the like, and the observation target part (particularly, both ends thereof) protrudes from the frame.

  As described above, in the conventional technique, the examiner could not recognize that the observation target part protruded from the frame, so the measurement was performed again, the examination time became long, or the subsequent analysis failed. There were problems such as.

  The present invention has been made to solve such a problem, and an object of the present invention is to provide an ophthalmologic observation apparatus capable of notifying an examiner that an observation target part is protruding from the frame. is there.

In order to achieve the above object, the invention according to claim 1 divides the light from the light source into signal light and reference light, and the signal light passing through the eye to be examined and the reference light passing through the reference light path An optical system that generates and detects interference light by superimposing, an image forming unit that forms a tomographic image of the eye to be examined based on a detection result of the interference light, and analyzes the tomographic image, An identification means for identifying an image area corresponding to a predetermined part, a determination means for determining a positional relationship between the specified image area and a frame periphery of the tomographic image, and notification based on a determination result by the determination means Bei example a notification means, for performing said determination means, said both ends of the identified image region is determined whether contact with both the left and right sides of said frame, said informing means is in contact by the determining means When it is determined that it is not Knowledge is a ophthalmologic observation apparatus characterized that you perform.
The invention according to claim 2 divides the light from the light source into signal light and reference light, and superimposes the signal light passing through the eye to be examined and the reference light passing through the reference light path to interfere light. An optical system that generates and detects the image, an image forming unit that forms a tomographic image of the eye to be examined based on the detection result of the interference light, and an image that analyzes the tomographic image and corresponds to a predetermined part of the eye to be examined Specifying means for specifying an area; determining means for determining a positional relationship between the specified image area and a frame periphery of the tomographic image; and notifying means for performing notification based on a determination result by the determining means; The optical system includes a scanning unit that repeatedly scans the signal light along a predetermined scanning line for the eye to be inspected, and the image forming unit is scanned along the predetermined scanning line. A static tomographic image along the scanning line And display control for displaying a moving tomographic image along the predetermined scanning line by updating and displaying the display unit and the stationary tomographic image sequentially formed by the image forming unit on the display unit at a predetermined time interval. Means for specifying the image region by analyzing the sequentially formed tomographic images, and the determining unit is configured to determine the image region and the frame of each of the still tomographic images. determining a positional relationship between the peripheral edge of said notification means, wherein for each still image, a ophthalmologic observation apparatus characterized that you perform notification based on the determination result by said determining means.
The invention according to claim 3 divides the light from the light source into signal light and reference light, and superimposes the signal light passing through the eye to be examined and the reference light passing through the reference light path to interfere light. An optical system that generates and detects the image, an image forming unit that forms a tomographic image of the eye to be examined based on the detection result of the interference light, and an image that analyzes the tomographic image and corresponds to a predetermined part of the eye to be examined Specifying means for specifying an area; determining means for determining a positional relationship between the specified image area and a frame periphery of the tomographic image; and notifying means for performing notification based on a determination result by the determining means; The optical system includes a scanning unit that sequentially scans the signal light along a plurality of scanning lines for the eye to be examined, and the image forming unit forms a tomographic image along each of the plurality of scanning lines. And the determination means When it is determined that the relationship is inappropriate, the positional information of the scanning line corresponding to the tomographic image is stored, and after the scanning of all the scanning lines is completed by the scanning unit, the storage is performed. Ru ophthalmic observation apparatus der, characterized by further comprising a scanning control means for controlling said scanning means so as to scan said signal light again along the lines of position information.
The invention according to claim 4 is the ophthalmologic observation apparatus according to any one of claims 1 to 3 , wherein the determination unit is configured such that the specified image region is an upper side of the frame or It is determined whether or not it is in contact with a lower side, and the notifying unit performs notification when it is determined that the determining unit is in contact.
The invention according to claim 5 is the ophthalmologic observation apparatus according to any one of claims 1 to 4, wherein the notification means is configured such that the specified image region is out of the frame. It includes a notification display means for performing the notification by displaying notification information to the effect.
The invention according to claim 6 is the ophthalmologic observation apparatus according to any one of claims 1 to 5 , wherein when the positional relationship is determined to be inappropriate by the determination means. And a control means for changing the optical path length of the reference light so that the positional relationship between the image area and the periphery of the frame is an appropriate positional relationship .

  According to the present invention, the tomographic image of the eye to be examined can be notified based on the positional relationship between the image region corresponding to the predetermined part of the eye to be examined and the periphery of the frame of the tomographic image. It is possible to notify the examiner that the site to be observed protrudes from the frame.

It is the schematic showing an example of composition of an embodiment of a fundus oculi observation device functioning as an ophthalmologic observation device concerning this invention. It is the schematic showing an example of composition of an embodiment of a fundus oculi observation device functioning as an ophthalmologic observation device concerning this invention. It is a schematic block diagram showing an example of composition of an embodiment of a fundus observation device functioning as an ophthalmologic observation device concerning this invention. It is the schematic for demonstrating the process which embodiment of the fundus observation apparatus which functions as an ophthalmologic observation apparatus concerning this invention performs. It is the schematic for demonstrating the process which embodiment of the fundus observation apparatus which functions as an ophthalmologic observation apparatus concerning this invention performs. It is the schematic for demonstrating the process which embodiment of the fundus observation apparatus which functions as an ophthalmologic observation apparatus concerning this invention performs. It is the schematic for demonstrating the process which embodiment of the fundus observation apparatus which functions as an ophthalmologic observation apparatus concerning this invention performs. It is the schematic for demonstrating the process which embodiment of the fundus observation apparatus which functions as an ophthalmologic observation apparatus concerning this invention performs. It is a flowchart showing an example of operation | movement of embodiment of the fundus observation apparatus which functions as an ophthalmologic observation apparatus according to the present invention.

  An example of an embodiment of an ophthalmologic observation apparatus according to the present invention will be described in detail with reference to the drawings. The ophthalmologic observation apparatus according to the present invention forms a tomographic image or a three-dimensional image of the eye to be examined using OCT. In this specification, images acquired by OCT may be collectively referred to as OCT images. In addition, a measurement operation for forming an OCT image may be referred to as OCT measurement.

  In the following embodiment, a configuration for forming a fundus image by applying Fourier domain type OCT will be described in detail. In the following embodiment, a fundus oculi observation device capable of acquiring both an OCT image and a fundus oculi image of the fundus as in the device disclosed in Patent Document 5 will be taken up. The ophthalmologic observation apparatus according to the present invention may form an image of a part other than the fundus. As an example, an ophthalmologic observation apparatus that forms an image of the anterior segment (particularly the cornea) can be configured. An ophthalmologic observation apparatus for measuring the anterior segment will be described later as a modified example.

[Constitution]
As shown in FIGS. 1 and 2, the fundus oculi observation device 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200. The retinal camera unit 2 has almost the same optical system as a conventional retinal camera. The OCT unit 100 is provided with an optical system for acquiring an OCT image of the fundus. The arithmetic control unit 200 includes a computer that executes various arithmetic processes and control processes.

[Fundus camera unit]
The fundus camera unit 2 shown in FIG. 1 is provided with an optical system for acquiring a two-dimensional image (fundus photographed image) representing the surface form of the fundus oculi Ef of the eye E to be examined. The fundus photographed image includes an observation image and a photographed image. The observation image is, for example, a monochrome moving image formed at a predetermined frame rate using near infrared light. The captured image is a color image obtained by flashing visible light, for example. The fundus camera unit 2 may be configured to be able to acquire images other than these, such as a fluorescein fluorescent image, an indocyanine green fluorescent image, a spontaneous fluorescent image, and the like.

  The fundus photographed image used in the present invention is mainly a photographed image. The fundus photographic image is not limited to a color image, and may be any two-dimensional image depicting the surface form of the fundus, such as a fluorescent image or a stereoscopic fundus image. In general, a stereoscopic fundus image is composed of two fundus images having different viewing angles, but in recent years, a technique for stereoscopically viewing a single fundus image is also used.

  The fundus camera unit 2 is provided with a chin rest and a forehead for supporting the subject's face so as not to move. Further, the fundus camera unit 2 is provided with an illumination optical system 10 and a photographing optical system 30. The illumination optical system 10 irradiates the fundus oculi Ef with illumination light. The photographing optical system 30 guides the fundus reflection light of the illumination light to the imaging device (CCD image sensors 35 and 38). The imaging optical system 30 guides the signal light from the OCT unit 100 to the fundus oculi Ef and guides the signal light passing through the fundus oculi Ef to the OCT unit 100.

  The observation light source 11 of the illumination optical system 10 is constituted by a halogen lamp, for example. The light (observation illumination light) output from the observation light source 11 is reflected by the reflection mirror 12 having a curved reflection surface, passes through the condensing lens 13, passes through the visible cut filter 14, and is converted into near infrared light. Become. 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. Then, the observation illumination light is reflected by the peripheral part (region around the hole part) of the perforated mirror 21 and illuminates the fundus oculi Ef via the objective lens 22.

  The fundus reflection light of the observation illumination light is refracted by the objective lens 22, passes through a hole formed in the central region of the aperture mirror 21, passes through the dichroic mirror 55, passes through the focusing lens 31, and then goes through the dichroic mirror. 32 is reflected. Further, the fundus reflection light passes through the half mirror 40, is reflected by the dichroic mirror 33, and forms an image on the light receiving surface of the CCD image sensor 35 by the condenser lens 34. The CCD image sensor 35 detects fundus reflected light at a predetermined frame rate, for example. The display device 3 displays an image (observation image) K based on fundus reflected light detected by the CCD image sensor 35.

  The imaging light source 15 is constituted by, for example, a xenon lamp. 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 fundus reflection light of the imaging illumination light is guided to the dichroic mirror 33 through the same path as that 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 of the CCD image sensor 38. An image is formed on the light receiving surface. On the display device 3, an image (captured image) H based on fundus reflection light detected by the CCD image sensor 38 is displayed. The display device 3 that displays the observation image K and the display device 3 that displays the captured image H may be the same or different.

  An LCD (Liquid Crystal Display) 39 displays a fixation target and an eyesight measurement target. The fixation target is a target for fixing the eye E to be examined, and is used at the time of fundus photographing or OCT measurement.

  A part of the light output from the LCD 39 is reflected by the half mirror 40, reflected by the dichroic mirror 32, passes through the focusing lens 31 and the dichroic mirror 55, and passes through the hole of the perforated mirror 21. The light is refracted by the objective lens 22 and 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. As the fixation position of the eye E, for example, a position for acquiring an image centered on the macular portion of the fundus oculi Ef, or a position for acquiring an image centered on the optic disc as in the case of a conventional fundus camera And a position for acquiring an image centered on the fundus center between the macula and the optic disc.

  Further, the fundus camera unit 2 is provided with an alignment optical system 50 and a focus optical system 60 as in a conventional fundus camera. The alignment optical system 50 generates a visual target (alignment visual target) for performing alignment (alignment) of the apparatus optical system with respect to the eye E. The focus optical system 60 generates a visual target (split visual target) for focusing on the fundus oculi Ef.

  Light (alignment light) output from an LED (Light Emitting Diode) 51 of the alignment optical system 50 is reflected by the dichroic mirror 55 via the apertures 52 and 53 and the relay lens 54, and passes through the hole portion of the perforated mirror 21. It passes through and is projected onto the cornea of the eye E by the objective lens 22.

  The corneal reflection light of the alignment light passes through the objective lens 22 and the hole, and a part thereof passes through the dichroic mirror 55, passes through the focusing lens 31, is reflected by the dichroic mirror 32, and passes through the half mirror 40. Then, it is reflected by the dichroic mirror 33 and projected onto the light receiving surface of the CCD image sensor 35 by the condenser lens 34. A light reception image (alignment target) by the CCD image sensor 35 is displayed on the display device 3 together with the observation image K. The user performs alignment by performing the same operation as that of a conventional fundus camera. Further, the arithmetic control unit 200 may perform alignment by analyzing the position of the alignment target and moving the optical system.

  When performing the focus adjustment, the reflecting surface of the reflecting rod 67 is obliquely provided on the optical path of the illumination optical system 10. The light (focus light) output from the LED 61 of the focus optical system 60 passes through the relay lens 62, is separated into two light beams by the split target plate 63, passes through the two-hole aperture 64, and is reflected by the mirror 65. The light is once focused on the reflecting surface of the reflecting bar 67 by the condenser lens 66 and reflected. Further, the focus light passes through the relay lens 20, is reflected by the perforated mirror 21, and forms an image on the fundus oculi Ef by the objective lens 22.

  The fundus reflection light of the focus light is detected by the CCD image sensor 35 through the same path as the cornea reflection light of the alignment light. A light reception image (split target) by the CCD image sensor 35 is displayed on the display device 3 together with the observation image. The arithmetic and control unit 200 analyzes the position of the split target and moves the focusing lens 31 and the focus optical system 60 to focus, as in the conventional case. Alternatively, focusing may be performed manually while visually checking the split target.

  An optical path including a mirror 41, a collimator lens 42, and galvanometer mirrors 43 and 44 is provided behind the dichroic mirror 32. This optical path is guided to the OCT unit 100.

  The galvanometer mirror 44 scans the signal light LS from the OCT unit 100 in the x direction. The galvanometer mirror 43 scans the signal light LS in the y direction. By these two galvanometer mirrors 43 and 44, the signal light LS can be scanned in an arbitrary direction on the xy plane.

[OCT unit]
The OCT unit 100 is provided with an optical system for acquiring an OCT image of the fundus oculi Ef (see FIG. 2). This optical system has the same configuration as a conventional Fourier domain type OCT apparatus. That is, this optical system divides low-coherence light into reference light and signal light, and generates interference light by causing interference between the signal light passing through the fundus oculi Ef and the reference light passing through the reference optical path. It is configured to detect spectral components. This detection result (detection signal) is sent to the arithmetic control unit 200.

  The light source unit 101 outputs a broadband low-coherence light L0. The low coherence light L0 includes, for example, a near-infrared wavelength band (about 800 nm to 900 nm) and has a temporal coherence length of about several tens of micrometers. Note that near-infrared light having a wavelength band that cannot be visually recognized by the human eye, for example, a center wavelength of about 1050 to 1060 nm, may be used as the low-coherence light L0.

  The light source unit 101 includes a light output device such as a super luminescent diode (SLD), an LED, or an SOA (Semiconductor Optical Amplifier).

  The low-coherence light L0 output from the light source unit 101 is guided to the fiber coupler 103 by the optical fiber 102 and split into the signal light LS and the reference light LR. The fiber coupler 103 functions as both a means for splitting light (splitter) and a means for combining light (coupler), but here it is conventionally referred to as a “fiber coupler”.

  The signal light LS is guided by the optical fiber 104 and becomes a parallel light beam by the collimator lens unit 105. Further, the signal light LS is reflected by the respective galvanometer mirrors 44 and 43, collected by the collimator lens 42, reflected by the mirror 41, transmitted through the dichroic mirror 32, and through the same path as the light from the LCD 39, the fundus oculi Ef. Is irradiated. The signal light LS is scattered and reflected on the fundus oculi Ef. The scattered light and reflected light may be collectively referred to as fundus reflected light of the signal light LS. The fundus reflection light of the signal light LS travels in the opposite direction on the same path and is guided to the fiber coupler 103.

  The reference light LR is guided by the optical fiber 106 and becomes a parallel light beam by the collimator lens unit 107. Further, the reference light LR is reflected by the mirrors 108, 109, 110, is attenuated by the ND (Neutral Density) filter 111, is reflected by the mirror 112, and forms an image on the reflection surface of the reference mirror 114 by the collimator lens 113. . The reference light LR reflected by the reference mirror 114 travels in the opposite direction on the same path and is guided to the fiber coupler 103. An optical element for dispersion compensation (such as a pair prism) and an optical element for polarization correction (such as a wavelength plate) may be provided in the optical path (reference optical path) of the reference light LR.

  The fiber coupler 103 combines the fundus reflection light of the signal light LS and the reference light LR reflected by the reference mirror 114. The interference light LC thus generated is guided by the optical fiber 115 and emitted from the emission end 116. Further, the interference light LC is converted into a parallel light beam by the collimator lens 117, dispersed (spectral decomposition) by the diffraction grating 118, condensed by the condenser lens 119, and projected onto the light receiving surface of the CCD image sensor 120. The diffraction grating 118 shown in FIG. 2 is a transmission type, but a reflection type diffraction grating may be used.

  The CCD image sensor 120 is, for example, a line sensor, and detects each spectral component of the split interference light LC and converts it into electric charges. The CCD image sensor 120 accumulates this electric charge and generates a detection signal. Further, the CCD image sensor 120 sends this detection signal to the arithmetic control unit 200.

  In this embodiment, a Michelson type interferometer is employed, but any type of interferometer such as a Mach-Zehnder type can be appropriately employed. Further, in place of the CCD image sensor, another form of image sensor such as a CMOS (Complementary Metal Oxide Semiconductor) image sensor can be used.

[Calculation control unit]
The configuration of the arithmetic control unit 200 will be described. The arithmetic control unit 200 analyzes the detection signal input from the CCD image sensor 120 and forms an OCT image of the fundus oculi Ef. The arithmetic processing for this is the same as that of a conventional Fourier domain type OCT apparatus.

  The arithmetic control unit 200 controls each part of the fundus camera unit 2, the display device 3, and the OCT unit 100. For example, the arithmetic and control unit 200 displays an OCT image such as a tomographic image G (see FIG. 2) of the fundus oculi Ef on the display device 3.

  As the control of the fundus camera unit 2, the arithmetic control unit 200 controls the operation of the observation light source 11, the imaging light source 15 and the LEDs 51 and 61, the operation control of the LCD 39, the movement control of the focusing lens 31, and the movement control of the reflector 67. Further, movement control of the focus optical system 60, operation control of the galvanometer mirrors 43 and 44, and the like are performed.

  As control of the OCT unit 100, the arithmetic control unit 200 performs operation control of the light source unit 101, movement control of the reference mirror 114 and collimator lens 113, operation control of the CCD image sensor 120, and the like.

  The arithmetic control unit 200 includes, for example, a microprocessor, a RAM, a ROM, a hard disk drive, a communication interface, etc., as in a conventional computer. A computer program for controlling the fundus oculi observation device 1 is stored in a storage device such as a hard disk drive. The arithmetic control unit 200 may include a dedicated circuit board that forms an OCT image based on a detection signal from the CCD image sensor 120. The arithmetic control unit 200 may include an operation device (input device) such as a keyboard and a mouse, and a display device such as an LCD.

  The retinal camera unit 2, the display device 3, the OCT unit 100, and the arithmetic control unit 200 may be configured integrally (that is, in a single casing) or may be configured separately.

[Control system]
The configuration of the control system of the fundus oculi observation device 1 will be described with reference to FIG.

(Control part)
The control system of the fundus oculi observation device 1 is configured around the control unit 210 of the arithmetic control unit 200. The control unit 210 includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, communication interface, and the like. The control unit 210 is provided with a main control unit 211 and a storage unit 212.

(Main control unit)
The main control unit 211 performs the various controls described above. In particular, the main control unit 211 controls the scanning drive unit 70 and the focusing drive unit 80 of the fundus camera unit 2, and further the light source unit 101 and the reference drive unit 130 of the OCT unit 100. The main control unit 211 controls the display unit 240 to display various data and various images. The main control unit 211 is an example of the “control unit” and “display control unit” of the present invention.

  The scanning drive unit 70 includes, for example, a servo motor, and independently changes the directions of the galvanometer mirrors 43 and 44. The focusing drive unit 80 includes, for example, a pulse motor, and moves the focusing lens 31 in the optical axis direction. Thereby, the focus position of the light toward the fundus oculi Ef is changed. The reference driving unit 130 includes, for example, a pulse motor, and moves the collimator lens 113 and the reference mirror 114 integrally along the traveling direction of the reference light LR.

  Further, the main control unit 211 performs processing for writing data into the storage unit 212 and processing for reading data from the storage unit 212.

(Memory part)
The storage unit 212 stores various data. The data stored in the storage unit 212 includes, for example, image data of an OCT image, image data of a fundus image, and eye information to be examined. The eye information includes information about the subject such as patient ID and name, and information about the eye such as left / right eye identification information.

(Image forming part)
The image forming unit 220 forms tomographic image data of the fundus oculi Ef based on the detection signal from the CCD image sensor 120. This process includes processes such as noise removal (noise reduction), filter processing, and FFT (Fast Fourier Transform) as in the conventional Fourier domain type optical coherence tomography.

  The image forming unit 220 includes, for example, the above-described circuit board and communication interface. The image forming unit 220 is an example of the “image forming unit” in the present invention. In this specification, “image data” and “image” presented based on the “image data” may be identified with each other.

(Image processing unit)
The image processing unit 230 performs various types of image processing and analysis processing on the image formed by the image forming unit 220. For example, the image processing unit 230 executes various correction processes such as image brightness correction and dispersion correction.

  The image processing unit 230 executes known image processing such as interpolation processing for interpolating pixels between tomographic images to form image data of a three-dimensional image of the fundus oculi Ef.

  Note that the image data of a three-dimensional image means image data in which pixel positions are defined by a three-dimensional coordinate system. As image data of a three-dimensional image, there is image data composed of voxels arranged three-dimensionally. This image data is called volume data or voxel data. When displaying an image based on volume data, the image processing unit 230 performs rendering processing (volume rendering, MIP (Maximum Intensity Projection), etc.) on the volume data, and views the image from a specific gaze direction. Image data of a pseudo three-dimensional image is formed. This pseudo three-dimensional image is displayed on a display device such as the display unit 240.

  It is also possible to form stack data of a plurality of tomographic images as image data of a three-dimensional image. The stack data is image data obtained by three-dimensionally arranging a plurality of tomographic images obtained along a plurality of scanning lines based on the positional relationship of the scanning lines. That is, stack data is image data obtained by expressing a plurality of tomographic images originally defined by individual two-dimensional coordinate systems by one three-dimensional coordinate system (that is, by embedding them in one three-dimensional space). is there.

  The image processing unit 230 is further provided with an image region specifying unit 231 and an image position determining unit 232.

(Image area identification part)
The image region specifying unit 231 analyzes the tomographic image formed by the image forming unit 220 and specifies an image region (predetermined image region) corresponding to a predetermined part of the fundus oculi Ef. The image area specifying unit 231 is an example of the “specifying means” in the present invention.

  An example of processing executed by the image area specifying unit 231 will be described. The image area specifying unit 231 specifies a predetermined image area based on the pixel values of the pixels constituting the tomographic image.

  For example, when specifying an image region (fundus surface region) corresponding to the fundus surface, the image region specifying unit 231 analyzes pixels on each A scan line along the z direction, and specifies pixels whose pixel values greatly change. By doing so, the fundus surface area is specified. At this time, if the fundus oculi Ef is depicted at a suitable position in the frame, the vitreous body depicted with low luminance should be presented near the upper side of the frame. By utilizing this, the pixels on the A scan line are analyzed in order from the upper side to the lower side, and the pixels whose luminance has increased rapidly can be estimated as the pixels of the fundus surface area. The A scan line means the position of the A scan image obtained by one OCT measurement, that is, one irradiation of the low coherence light L0. In other words, the A scan line passes through one scanning point in the z direction. It means the position of the straight line along.

  When the luminance of the uppermost pixel is higher than the luminance corresponding to the vitreous body, it is desirable to determine whether this is noise. This discrimination process can be executed with reference to the luminance of the neighboring pixels. That is, if the brightness of the neighboring pixels is high, it can be estimated as the fundus surface area, and if not, it can be estimated as noise.

  The fundus oculi Ef is composed of a plurality of layer tissues that overlap in the z direction. The fundus surface area is the top layer of this layer structure. Therefore, the fundus surface region is generally depicted as a layer region extending in the left-right direction (arbitrary direction in the xy plane) in the tomographic image frame. As described above, the fundus surface area may be inclined with respect to the left-right direction depending on the measurement conditions.

  When the predetermined image area is other than the fundus surface area, it can be identified basically in the same manner. For example, when specifying an image region (layer region) corresponding to an arbitrary layer tissue of the fundus oculi Ef, for example, a layer region is specified based on a method of specifying a layer region having the maximum luminance or a depth from the fundus surface region There are ways to do it.

  Further, it is possible to specify an image area other than the layer area. For example, when an image region corresponding to a lesioned part is specified, a typical shape or luminance of the lesioned part can be referred to.

(Image position determination unit)
The image position determining unit 232 determines the positional relationship between the predetermined image region specified by the image region specifying unit 231 and the frame periphery of the tomographic image. The image position determination unit 232 is an example of the “determination means” in the present invention.

  An example of processing executed by the image position determination unit 232 will be described. As a first example, the image position determination unit 232 determines whether or not the predetermined image region is in contact with the upper side or the lower side of the tomographic image frame. This determination process is executed, for example, by determining whether or not at least one of the pixels constituting the predetermined image region is present at a position corresponding to the upper side or the lower side of the tomographic image frame. More specifically, this determination process determines whether or not the coordinate values of the pixels constituting the predetermined image area are coordinate values (addresses) corresponding to the upper side or the lower side of the frame. The upper side represents a portion having the smallest z coordinate value in the frame, and the lower side represents a portion having the largest z coordinate value in the frame (see FIG. 1 for the z coordinate).

  Specific examples of this processing are shown in FIGS. These drawings show a tomogram of the optic disc of the fundus oculi Ef and the vicinity thereof. The tomographic image G1 in FIG. 4 shows an image region (nipple image region) OP1 corresponding to the optic nerve head and an image region in the vicinity thereof. The fundus surface area B1 is not in contact with the upper side U1 or the lower side D1 of the frame. For such a tomographic image G1, the image position determination unit 232 determines that “the fundus surface region B1 is not in contact with the upper side or the lower side of the frame”.

  The fundus surface area B1 may include a nipple image area OP1 (a side surface or a bottom surface thereof). When it is determined whether it is in contact with the upper side U1, only the portion of the fundus surface area B1 excluding the portions corresponding to the side surface and the bottom surface of the nipple image area OP1 may be determined. Further, when it is determined whether it is in contact with the lower side D1, only a portion corresponding to the nipple image region OP1 may be determined. However, it is desirable to consider the entire fundus surface region B1 in consideration of the case where the fundus surface region B1 is inclined.

  The tomographic image G2 in FIG. 5 shows the nipple image region OP2 and an image region in the vicinity thereof. The fundus surface area B2 is depicted with an inclination. The fundus surface area B2 is in contact with the upper side U2 of the frame at the position P2. For such a tomographic image G2, the image position determination unit 232 determines that “the fundus surface area B2 is in contact with the upper side of the frame”.

  A tomographic image G3 in FIG. 6 shows a nipple image region OP3 and an image region in the vicinity thereof. The fundus surface area B3 is depicted with an inclination. The fundus surface area B3 is in contact with the lower side D3 of the frame at the position P3. For such a tomographic image G3, the image position determination unit 232 determines that “the fundus surface area B3 is in contact with the lower side of the frame”.

  A second example of processing executed by the image position determination unit 232 will be described. The image position determining unit 232 determines whether or not both ends of the image region specified by the image region specifying unit 231 are in contact with both the left side and the right side of the frame. This process is suitable for specifying an image region corresponding to a tissue spreading on the xy plane, such as an arbitrary layer tissue of the fundus oculi Ef. Here, “left” and “right” represent directions when facing the tomographic image with the upper side on the upper side and the lower side on the lower side.

  A specific example of this process will be described. First, the image position determination unit 232 identifies the leftmost pixel and the rightmost pixel among the pixels constituting the image area to be processed. Next, the image position determination unit 232 determines whether the specified leftmost pixel is in contact with the left side of the frame. That is, it is determined whether the coordinate value of the pixel and the coordinate value of the left side of the frame are the same in the left-right direction. A process for determining whether the rightmost pixel is in contact with the right side of the frame is executed in the same manner.

  In the tomographic image G4 shown in FIG. 7, a nipple image region OP4 and an image region in the vicinity thereof are shown. In the fundus surface area B4, the leftmost pixel is in contact with the left side L4 of the frame at the position P4. Further, the rightmost pixel of the fundus surface area B4 is in contact with the right side R4 of the frame at the position Q4. For such a tomographic image G4, the image position determination unit 232 determines that “the fundus surface region B4 is in contact with both the left side and the right side of the frame”.

  A tomographic image G5 shown in FIG. 8 shows a nipple image region OP5 and an image region in the vicinity thereof. In the fundus surface area B5, the leftmost pixel is in contact with the left side L5 of the frame at the position P5. However, the rightmost pixel of the fundus surface area B5 is in contact with the upper side U5 of the frame at the position Q5 and is not in contact with the right side R5. For such a tomographic image G5, the image position determination unit 232 determines that “the fundus surface region B5 is not in contact with both the left side and the right side of the frame”.

  The image processing unit 230 that functions as described above includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, circuit board, and the like. In a storage device such as a hard disk drive, a computer program for causing the microprocessor to execute the above functions is stored in advance.

(Display section, operation section)
The display unit 240 includes the display device of the arithmetic control unit 200 described above. The operation unit 250 includes the operation device of the arithmetic control unit 200 described above. The operation unit 250 may include various buttons and keys provided on the housing of the fundus oculi observation device 1 or outside. For example, when the fundus camera unit 2 has a housing similar to that of a conventional fundus camera, the operation unit 250 may include a joystick, an operation panel, or the like provided on the housing. In addition, the display unit 240 may include various display devices such as a touch panel monitor provided on the housing of the fundus camera unit 2.

  The display unit 240 and the operation unit 250 do not need to be configured as individual devices. For example, a device in which a display function and an operation function are integrated, such as a touch panel monitor, can be used.

  The display unit 240 is an example of the “display unit” and “notification display unit” of the present invention. The display unit and the notification display unit may be a single display device or may be different display devices. The display unit 240, together with the main control unit 211, constitutes “notification means” of the present invention.

[Scanning signal light and OCT images]
Here, the scanning of the signal light LS and the OCT image will be described.

  Examples of scanning modes of the signal light LS by the fundus oculi observation device 1 include horizontal scanning, vertical scanning, cross scanning, radiation scanning, circular scanning, concentric scanning, and spiral (vortex) scanning. These scanning modes are selectively used as appropriate in consideration of the observation site of the fundus, the analysis target (such as retinal thickness), the time required for scanning, the precision of scanning, and the like.

  The horizontal scan scans the signal light LS in the horizontal direction (x direction). The horizontal scan also includes an aspect in which the signal light LS is scanned along a plurality of horizontal scanning lines arranged in the vertical direction (y direction). In this aspect, it is possible to arbitrarily set the scanning line interval. Further, the above-described three-dimensional image can be formed by sufficiently narrowing the interval between adjacent scanning lines (three-dimensional scanning). The same applies to the vertical scan.

  In the cross scan, the signal light LS is scanned along a cross-shaped trajectory composed of two linear trajectories (straight trajectories) orthogonal to each other. In the radiation scan, the signal light LS is scanned along a radial trajectory composed of a plurality of linear trajectories arranged at a predetermined angle. The cross scan is an example of a radiation scan.

  In the circle scan, the signal light LS is scanned along a circular locus. In the concentric scan, the signal light LS is scanned along a plurality of circular trajectories arranged concentrically around a predetermined center position. A circle scan is an example of a concentric scan. In the spiral scan, the signal light LS is scanned along a spiral (spiral) locus while the radius of rotation is gradually reduced (or increased).

  Since the galvanometer mirrors 43 and 44 are configured to scan the signal light LS in directions orthogonal to each other, the signal light LS can be scanned independently in the x and y directions, respectively. Furthermore, by simultaneously controlling the directions of the galvanometer mirrors 43 and 44, it is possible to scan the signal light LS along an arbitrary locus on the xy plane. Thereby, various scanning modes as described above can be realized.

  By scanning the signal light LS in the above-described manner, a tomographic image in the fundus depth direction (z direction) along the scanning line (scanning locus) can be formed. In particular, when the interval between scanning lines is narrow, the above-described three-dimensional image can be formed.

  A region on the fundus oculi Ef to be scanned with the signal light LS as described above, that is, a region on the fundus oculi Ef to be subjected to OCT measurement is referred to as a scanning region. The scanning area in the three-dimensional scan is a rectangular area in which a plurality of horizontal scans are arranged. The scanning area in the concentric scan is a disk-shaped area surrounded by the locus of the circular scan with the maximum diameter. In addition, the scanning area in the radial scan is a disk-shaped (or polygonal) area connecting both end positions of each scan line.

[Operation]
The operation of the fundus oculi observation device 1 will be described. FIG. 9 shows an example of the operation of the fundus oculi observation device 1. In this operation example, a case will be described in which the characteristic processing of the present invention is executed when a live moving image of the fundus oculi Ef is acquired. A live moving image is a real-time moving image representing a state of a predetermined cross section of the fundus oculi Ef.

  When displaying a live moving image, the signal light LS is repeatedly scanned along a predetermined scanning line at predetermined time intervals, and a tomographic image (static tomographic image) is formed each time the scanning line is scanned. Then, the static tomographic images sequentially formed in this manner are updated and displayed on the display unit 240 at the time intervals. Thereby, a moving image tomographic image along the scanning line is displayed. The frame rate of this moving tomographic image is the reciprocal of the time interval.

  As an inspection preparation stage, the eye E is placed in front of the objective lens 22, and alignment and focus are executed. Also, the fixation target corresponding to the desired fixation position is presented to the eye E by controlling the LCD 39. Here, a fixation target for measuring the optic disc is assumed to be presented.

  In response to the measurement start instruction, the main control unit 211 controls the light source unit 101, the scanning drive unit 70, the CCD image sensor 120, and the like to perform a predetermined scanning line (here, a horizontal scan or a vertical scan across the optic disc). ) Starts scanning of the signal light LS, and further, the display unit 240 starts displaying the live moving image. (S1).

  The image area specifying unit 231 analyzes the still tomographic images that are sequentially formed, and specifies the fundus surface area (S2).

  The image position determination unit 232 determines the positional relationship between the identified fundus surface area and the frame periphery of the still tomographic image for each of the sequentially formed tomographic images (S3). Here, the first example is applied, and it is determined whether the fundus surface area is in contact with the upper side or the lower side of the frame. Even if the second example is applied, the subsequent processing is the same.

  When it is determined that the fundus surface area is not in contact with the upper side or the lower side of the frame (S4: No), the process proceeds to the next tomographic image processing.

  On the other hand, when it is determined that the fundus surface area is in contact with the upper side or the lower side of the frame (S4: Yes), the main control unit 211 notifies the display unit 240 that the fundus surface area is out of the frame. The information is displayed and notified to the examiner (S5).

  The notification information may be character string information or image information. As the character string information, there is a message such as “Image is out of frame”. Image information includes images such as exclamation marks and cross marks. The notification information is desirably displayed in a predetermined color. This display color is set to a color that is easily noticed by the examiner, for example, orange. The notification information is stored in advance in the storage unit 212. The main control unit 211 reads notification information from the storage unit 212 and displays it on the display unit 240 in response to the determination that the fundus surface area is in contact with the upper side or the lower side of the frame. The notification information is not limited to visual information, and may be information that stimulates other senses such as auditory information and tactile information. The notification information may include information indicating in which direction the image is shifted, information indicating in which direction the measurement depth should be corrected, and the like.

  The examiner recognizes that the measurement depth is shifted by visually recognizing the notification information. Then, the examiner moves the reference mirror 114 using the operation unit 250 while observing the displayed live moving image, and adjusts the measurement depth so that the image is positioned at a suitable position in the frame (S6). ).

  Instead of manually adjusting the measurement depth, it may be automatically adjusted. This automatic adjustment can be executed based on, for example, the z-coordinate values of the pixels constituting the fundus surface area. As a specific example, the main control unit 211 can be configured to adjust the position of the reference mirror 114 until the image position determination unit 232 determines that the fundus surface area is not in contact with the upper and lower sides of the frame. It is. Here, when the fundus surface area is in contact with the upper side (lower side) of the frame, the reference mirror 114 is moved in a direction to shorten (longen) the optical path length of the reference light LR. As another method, the movement amount of the reference mirror 114 may be estimated based on the position (coordinates) where the fundus surface area is in contact with the upper side or the lower side. At this time, the degree of inclination of the fundus surface area with respect to the z direction can be taken into consideration. It should be noted that the same processing can be executed when processing that considers the left and right sides of the frame is executed.

  The above process is repeated until the display of the live moving image is completed.

[Action / Effect]
The operation and effect of the fundus oculi observation device 1 as described above will be described.

  The fundus oculi observation device 1 analyzes a tomographic image of the fundus oculi Ef to identify a predetermined image region, determines the positional relationship between the predetermined image region and the frame periphery of the tomographic image, and performs notification based on the determination result. It is configured as follows.

  Here, the peripheral edge of the frame means an end of the frame and is a concept including at least one of the upper side, the lower side, the left side, and the right side. In this embodiment, the case where the upper side and the lower side of the frame are considered and the case where the left side and the right side are taken into account have been described, but the configuration is such that any combination of one or more of the four sides is considered. It is also possible to do.

  In this embodiment, the notification is made when it is determined that the predetermined image area is in contact with the upper side or the lower side of the frame, and the notification is made when both ends of the predetermined image area are not in contact with both the left side and the right side of the frame. The configuration and the configuration for informing when both ends of the predetermined image area are in contact with only one of the left side and the right side of the frame have been described.

  By adopting such a configuration, it is possible to detect whether the image is shifted in the z direction in the frame, that is, whether the measurement depth is shifted, and if it is shifted, notification can be performed. Therefore, according to the fundus oculi observation device 1, it is possible to notify the examiner that the site to be observed protrudes from the frame.

  In particular, the fundus oculi observation device 1 can detect and notify in real time when an observation target part protrudes from a frame in a live moving image of the fundus oculi Ef.

  Further, according to the fundus oculi observation device 1, when the positional relationship is determined to be inappropriate by the image position determination unit 232, the positional relationship between the predetermined image region and the peripheral edge of the frame becomes an appropriate positional relationship. The optical path length of the reference light can be changed. Here, the optical path length of the reference light is changed by moving the reference mirror 114.

  When considering the upper and lower sides of the frame, “inappropriate positional relationship” means that the predetermined image area is in contact with the upper and lower sides of the frame, and is not in contact with “appropriate positional relationship”. Means state. In addition, when considering the left side and right side of the frame, “inappropriate positional relationship” means a state where both ends of the predetermined image area are not in contact with at least one of the left side and the right side of the frame. “Positive positional relationship” means a state in contact with both. Even in cases other than these, “inappropriate positional relationship” and “appropriate positional relationship” can be appropriately defined.

  According to such a fundus oculi observation device 1, it is possible to notify that the positional relationship is inappropriate, and the adjustment is automatically performed so that the positional relationship is appropriate. Can be shortened. The positional relationship after the automatic adjustment may be manually adjusted.

[Modification]
The configuration described above is merely an example for favorably implementing the present invention. Therefore, arbitrary modifications within the scope of the present invention can be made as appropriate.

  In the above embodiment, when the signal light LS is sequentially scanned along a plurality of scanning lines for the eye E to form a plurality of tomographic images, the following configuration can be applied. . Assume that the image position determination unit 232 determines that the positional relationship between the predetermined image area and the frame periphery is inappropriate. In response to this, the main control unit 211 records the position information of the scanning line corresponding to this tomographic image in the storage unit 212. This position information may be, for example, the scanning order of the scanning lines among the plurality of scanning lines, or may be the positions of the galvano mirrors 43 and 44.

  After the scanning of all the scanning lines is completed, the main control unit 211 reads position information from the storage unit 212. Further, the main control unit 211 controls the scan driving unit 70 to scan the signal light LS again along the scanning line indicated by the position information.

  With this configuration, a tomographic image whose positional relationship is determined to be inappropriate is automatically acquired again. Therefore, even when an inappropriate tomographic image is obtained during measurement, a plurality of tomographic images corresponding to a plurality of scanning lines can be easily and reliably acquired. The main control unit 211 and the storage unit 212 are examples of the “scanning control unit” of the present invention.

  In the above embodiment, the position of the reference mirror 114 is changed to change the optical path length difference between the optical path of the signal light LS and the optical path of the reference light LR, but the method of changing the optical path length difference is limited to this. Is not to be done. For example, the optical path length difference can be changed by moving the fundus camera unit 2 or the OCT unit 100 with respect to the eye E to change the optical path length of the signal light LS. It is also effective to change the optical path length difference by moving the measurement object in the depth direction (z direction), particularly when the measurement object is not a living body part.

  The computer program in the above embodiment can be stored in any recording medium readable by a computer. As this recording medium, for example, an optical disk, a magneto-optical disk (CD-ROM / DVD-RAM / DVD-ROM / MO, etc.), a magnetic storage medium (hard disk / floppy (registered trademark) disk / ZIP, etc.), etc. are used. Is possible. It can also be stored in a storage device such as a hard disk drive or memory.

  It is also possible to transmit / receive this program through a network such as the Internet or a LAN.

  In the above embodiment, the apparatus for forming an OCT image of the fundus has been described. However, the configuration according to the present invention can also be applied to an apparatus for forming OCT images of other parts. As an example, an apparatus for forming an OCT image of the anterior segment (particularly the cornea) will be described.

  The ophthalmologic observation apparatus according to this modification can form a tomographic image of the anterior segment using OCT. This ophthalmic observation apparatus has the same arithmetic control unit as that in the above embodiment. Hereinafter, description will be made with reference to FIG.

  The image area specifying unit 231 analyzes the acquired tomographic image of the anterior eye part and specifies an image area (corneal surface area) corresponding to a predetermined part (for example, the corneal surface) of the eye E to be examined. This process can be executed in the same manner as in the above embodiment.

  The image position determination unit 232 determines the positional relationship between the identified corneal surface region and the periphery of the frame of the tomographic image. This positional relationship is determined based on, for example, the contact state between the corneal surface region and the upper side or the lower side of the frame, or the contact state between the corneal surface region and the left side or the right side of the frame, as in the above embodiment.

  The main control unit 211 performs notification based on the determination result by the image position determination unit 232. This notification mode is the same as in the above embodiment.

  Various configurations described in the above embodiments can be appropriately applied to such an ophthalmologic observation apparatus for the anterior segment.

1 Fundus observation device (ophthalmic observation device)
2 fundus camera unit 3 display device 10 illumination optical system 30 imaging optical system 43, 44 Galvano mirror 100 OCT unit 200 arithmetic control unit 210 control unit 211 main control unit 212 storage unit 220 image forming unit 230 image processing unit 231 image area specifying unit 232 Image position determination unit 240 Display unit E Examination eye Ef Fundus

Claims (6)

An optical system that divides light from a light source into signal light and reference light, and generates and detects interference light by superimposing the signal light passing through the eye to be examined and the reference light passing through a reference optical path;
Image forming means for forming a tomographic image of the eye to be examined based on the detection result of the interference light;
A specifying means for analyzing the tomographic image and specifying an image region corresponding to a predetermined part of the eye to be examined;
Determining means for determining a positional relationship between the identified image region and a frame periphery of the tomographic image;
Notification means for performing notification based on the determination result by the determination means;
Bei to give a,
The determination means determines whether or not both ends of the identified image region are in contact with both the left side and the right side of the frame;
The notification means notifies when it is determined by the determination means that it is not in contact;
Ophthalmic observation apparatus according to claim and this. An optical system that divides light from a light source into signal light and reference light, and generates and detects interference light by superimposing the signal light passing through the eye to be examined and the reference light passing through a reference optical path;
Image forming means for forming a tomographic image of the eye to be examined based on the detection result of the interference light;
A specifying means for analyzing the tomographic image and specifying an image region corresponding to a predetermined part of the eye to be examined;
Determining means for determining a positional relationship between the identified image region and a frame periphery of the tomographic image;
Notification means for performing notification based on the determination result by the determination means;
With
The optical system includes scanning means for repeatedly scanning the signal light along a predetermined scanning line for the eye to be examined,
The image forming unit forms a static tomographic image along the scanning line every time scanning is performed along the predetermined scanning line.
Display means;
Display control means for displaying moving tomographic images along the predetermined scanning lines by updating and displaying the stationary tomographic images sequentially formed by the image forming means on the display means at predetermined time intervals;
Further comprising
The specifying unit specifies the image area by analyzing the sequentially formed tomographic images,
The determining means determines a positional relationship between the image area of each stationary tomographic image and a peripheral edge of the frame;
The notifying means notifies the respective still images based on a determination result by the determining means.
Ophthalmic observation apparatus according to claim and this. An optical system that divides light from a light source into signal light and reference light, and generates and detects interference light by superimposing the signal light passing through the eye to be examined and the reference light passing through a reference optical path;
Image forming means for forming a tomographic image of the eye to be examined based on the detection result of the interference light;
A specifying means for analyzing the tomographic image and specifying an image region corresponding to a predetermined part of the eye to be examined;
Determining means for determining a positional relationship between the identified image region and a frame periphery of the tomographic image;
Notification means for performing notification based on the determination result by the determination means;
With
The optical system includes a scanning unit that sequentially scans the signal light along a plurality of scanning lines for the eye to be examined.
The image forming unit forms a tomographic image along each of the plurality of scanning lines;
When the determination unit determines that the positional relationship is inappropriate, the positional information of the scanning line corresponding to the tomographic image is stored, and further, the scanning unit performs all scanning of the plurality of scanning lines. And further comprising a scanning control means for controlling the scanning means so that the signal light is scanned again along the scanning line of the stored position information.
Ophthalmic observation apparatus according to claim and this. The determination means determines whether the specified image region is in contact with an upper side or a lower side of the frame;
The notification means performs notification when it is determined that the determination means is in contact;
The ophthalmic observation apparatus according to any one of claims 1 to 3, wherein the ophthalmologic observation apparatus is characterized. The notification means includes notification display means for performing the notification by displaying notification information indicating that the specified image region is out of a frame,
The ophthalmologic observation apparatus according to any one of claims 1 to 4, wherein the ophthalmologic observation apparatus is characterized. Control for changing the optical path length of the reference light so that the positional relationship between the image area and the peripheral edge of the frame is an appropriate positional relationship when the determining unit determines that the positional relationship is inappropriate. Further comprising means,
The ophthalmologic observation apparatus according to any one of claims 1 to 5 , wherein