OPHTHALMOLOGIC APPARATUS

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates to an ophthalmologic apparatus.

2. Description of the Related Art

An optical coherence tomography (OCT) imaging apparatus such as an OCT for an eye part allows three-dimensional observation of a state within retinal layers and a state of an anterior segment such as an angle, a cornea, and an iris. Such an optical coherence tomography imaging apparatus is recently attracting attention as being useful in more accurately diagnosing of diseases. More specifically, Japanese Patent Application Laid-Open No. 2011-072716 discusses using tomographic images in diagnosing glaucoma. Further, tomographic images are used in diagnosing angle closure.

In glaucoma, there is a symptom referred to as an acute glaucoma attack. The acute glaucoma attack occurs when a pupil of a patient having a narrow angle dilates, so that a root of the iris becomes thick and blocks a trabecula in the angle through which aqueous humor flows out. If the trabecula becomes blocked by the iris, eye pressure increases, pressing a crystalline lens towards the cornea. The iris is thus pushed forward by the lens, and further blocks the trabecula, so that the eye pressure rapidly increases, and the optic nerve is damaged.

In particular, the pupil dilates, the iris contracts, and the root of the iris becomes thick in a darkened area, so that there is maximum contact between the trabecula and the iris. An acute glaucoma attack thus occurs more often in a darkened area as compared to a bright area, and less likely to occur in the bright area as compared to the darkened area. As a result, likelihood of an occurrence of the acute glaucoma attack depends on a surrounding lighting environment. In other words, unique information such as an image or a measurement value acquired from a subject's eye may depend on the lighting environment.

However, the unique information of the subject's eye is not associated with the lighting environment when the unique information has been acquired, so that it is difficult for an examiner to accurately perform diagnosis.

SUMMARY OF THE INVENTION

The present invention is directed to more accurately performing diagnosis. Such an effect can be acquired by each of configurations illustrated in exemplary embodiments of the present invention to be described below. Further, other operational effects that have not been acquired by conventional techniques are also included in the present invention.

According to an aspect of the present invention, an ophthalmologic apparatus includes an ophthalmologic apparatus configured to acquire unique information of a subject's eye, an acquisition unit configured to acquire a value indicating brightness of surroundings of the ophthalmologic apparatus, and a recording unit configured to record in a storing unit a value indicating brightness acquired by the acquisition unit, associated with a tomographic image.

According to the present invention, an accurate diagnosis can be performed.

Further features and aspects of the present invention will become apparent from the following detailed description of exemplary embodiments with reference to the attached drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated in and constitute a part of the specification, illustrate exemplary embodiments, features, and aspects of the invention and, together with the description, serve to explain the principles of the invention.

FIG. 1 is a schematic diagram illustrating an example of a configuration of an ophthalmologic apparatus according to a first exemplary embodiment of the present invention.

FIGS. 2A and 2B illustrate examples of the tomographic images captured by the ophthalmologic apparatus according to the first exemplary embodiment.

FIG. 3 is a flowchart illustrating an example of a process performed by the ophthalmologic apparatus according to the first exemplary embodiment.

FIG. 4 illustrates a display example on a display unit according to the first exemplary embodiment.

FIG. 5 illustrates a display example on the display unit according to the first exemplary embodiment.

FIG. 6 illustrates a display example on the display unit according to the first exemplary embodiment.

FIG. 7 illustrates a display example on the display unit according to the first exemplary embodiment.

FIG. 8 illustrates a display example on the display unit according to the first exemplary embodiment.

FIGS. 9A and 9B illustrates display examples on the display unit according to the present exemplary embodiment.

FIG. 10 illustrates a display example on the display unit according to the first exemplary embodiment.

FIG. 11 is a lateral view illustrating an imaging apparatus according to a second exemplary embodiment of the present invention.

FIG. 12 is a schematic diagram illustrating an example of an optical system in a fundus camera main body according to the second exemplary embodiment.

FIG. 13 illustrates a display example on a display unit according to a third exemplary embodiment.

FIG. 14 illustrates a display example on the display unit according to the third exemplary embodiment.

FIG. 15 illustrates an example of parameters acquired from an anterior segment image.

DESCRIPTION OF THE EMBODIMENTS

Various exemplary embodiments, features, and aspects of the invention will be described in detail below with reference to the drawings.

The apparatus according to the present invention is applicable to a subject such as the subject's eye, the skin, and internal organs. Further, the apparatus according to the present invention is, for example, an ophthalmologic apparatus or an endoscope.

FIG. 1 is a schematic diagram illustrating an example of a configuration of the ophthalmologic apparatus according to the first exemplary embodiment.

Referring to FIG. 1, the ophthalmologic apparatus includes a swept source OCT (SS-OCT, or may be simply referred to as OCT) 100, a scanning laser ophthalmoscope (SLO) 140, an anterior segment imaging unit 160, an internal fixation lamp 170, and a control unit 200. The ophthalmologic apparatus illustrated in FIG. 1 thus acquires the unique information of the subject's eye. Further, according to the present exemplary embodiment, the ophthalmologic apparatus includes a spectral illuminometer 500. The spectral illuminometer 500 measures the value indicating brightness (e.g., luminance) of an examination room in which the tomographic image is captured. In other words, the spectral illuminometer 500 measures the value indicating the brightness of the ophthalmologic apparatus surroundings. The spectral illuminometer 500 may be integrated with the ophthalmologic apparatus or separately configured.

The ophthalmologic apparatus is aligned by lighting and causing the subject's eye to gaze at the internal fixation lamp 170, and using the image of the anterior segment of the subject captured by the anterior segment imaging unit 160. After completing the alignment, the OCT 100 and the SLO 140 perform imaging of the fundus. The OCT 100 and the SLO 140 are not limited to imaging the fundus and are capable of imaging the anterior segment.

An example of the configuration of the OCT 100 will be described below.

The OCT 100 is an example of the tomographic image acquisition unit configured to acquire the tomographic image of the subject's eye. A light source 101 which is a variable wavelength light source emits light having a central wavelength of 1040 nm and a bandwidth of 100 nm. A control unit 191 controls the wavelength of the light emitted from the light source 101. More specifically, when the OCT 100 captures the tomographic image, the control unit 191 sweeps the wavelength of the light emitted from the light source 101. The control unit 191 thus is an example of a control unit configured to sweep the wavelength of the light emitted from the light source.

The light emitted from the light source 101 is guided by a fiber 102 and a polarization controller 103 to a fiber coupler 104, and is divided to be guided to a fiber 130 for measuring a light amount, and a fiber 105 for performing OCT measurement. A power meter (PM) 131 measures the power of the light guided to the fiber 130. The light guided to the fiber 105 is then guided to a second fiber coupler 106, which splits the light into a measuring beam (also referred to as an OCT measuring beam) and a reference beam.

The polarization controller 103 adjusts a polarization state of the beam emitted from the light source 101, and adjusts the beam to a linearly-polarized beam. A branching ratio of the fiber coupler 104 is 99:1, and the branching ratio of the fiber coupler 106 is 90 (reference beam):10 (measuring beam). The branching ratios are not limited thereto, and may be other values.

The measuring beam acquired by the fiber coupler 106 is output from a collimator 117 via a fiber 118 as a parallel beam. The output measuring beam reaches a dichroic mirror 111 via an X scanner 107 and lenses 108 and 109, and a Y scanner 110. The X scanner 107 includes a galvano mirror that scans the measuring beam in a horizontal direction (i.e., in a vertical direction with respect to the drawing) on a fundus Er, and the Y scanner 110 includes a galvano mirror that scans the measuring beam in a vertical direction (i.e., in a depth direction with respect to the drawing) on the fundus Er. The X scanner 107 and the Y scanner 110 are controlled by a drive control unit 180, and are capable of scanning the measuring beam in a desired range on the fundus Er. The dichroic mirror 111 reflects light having wavelengths of 950 nm to 1100 nm, and transmits light of other wavelengths.

The measuring beam reflected off the dichroic mirror 111 reaches via a lens 112 a focus lens 114 mounted on a stage 116. The focus lens 114 focuses the measuring beam on the retinal layers in the fundus Er via an anterior segment Ea of the subject's eye. The optical system from the light source 101 to the subject's eye thus is an example of an irradiation optical system that guides the light emitted from the light source to the subject's eye. The measuring beam irradiating the fundus Er is reflected and scattered by each retinal layer, returns to the fiber coupler 106 via the above-described optical path, and reaches a fiber coupler 126 via a fiber 125.

The drive control unit 180 controls the movement of the focus lens 114 in an optical axis direction. Further, according to the present exemplary embodiment, the focus lens 114 is shared by the OCT 100 and the SLO 140. However, it is not limited thereto, and each optical system may respectively include a focus lens. Further, the drive control unit 180 may control driving of the focus lens based on the difference between the wavelength employed by the light source 101 and the wavelength employed by a light source 141. For example, if the OCT 100 and the SLO 140 share the focus lens, the drive control unit 180 moves, when an operator switches between performing imaging by the SLO 140 and by the OCT 100, the focus lens according to the difference in the wavelengths. Further, if the OCT 100 and the SLO 140 respectively include the focus lens, the drive control unit 180 moves, when the focus lens in one of the optical systems is adjusted, the focus lens in the other optical system according to the difference in the wavelengths.

If an imaging mode for imaging the tomographic image of the anterior segment is selected, a focus position is set to a predetermined portion in the anterior segment instead of the fundus. Such focus adjustment with respect to the anterior segment may be performed by moving the position of the focus lens 114, or by inserting an optical member such as a dedicated lens in an optical path in front or in back of the focus lens 114. In such a case, a drive unit can insert or remove the optical member with respect to the optical path. The drive control unit 180 thus inserts, if an anterior segment imaging mode is selected, the optical member in the optical path, and removes, if a fundus imaging mode is selected, the optical member from the optical path.

The reference beam branched by the fiber coupler 106 is output via a fiber 119 from a collimator 120-a as a parallel beam. The output reference beam is then reflected via a dispersion compensation glass 121 by mirrors 123-a and 123-b mounted on a coherence gate stage 122, and reaches the fiber coupler 126 via a collimator 120-b and a fiber 124. The coherence gate stage 122 is controlled by the drive control unit 180 to deal with differences in an axial length of the subject's eye.

The return beam and the reference beam that have reached the fiber coupler 126 are combined into an interference beam. The interference beam then reaches a balanced receiver 129, i.e., a light detection unit, via fibers 127 and 128, and the balanced receiver 129 converts the interference signal to an electrical signal. A signal processing unit 190 analyzes the converted electrical signal. The optical system from the subject's eye to the balanced receiver 129 thus is an example of an imaging optical system configured to guide to an imaging unit the return beam from the subject's eye of the beam swept by the control unit. The light detection unit is not limited to the balanced receiver, and other detection units may be used.

Further, according to the present exemplary embodiment, the measuring beam and the reference beam interfere with each other in the fiber coupler 126. However, it is not limited thereto, and the mirror 123-a may be arranged so that the reference beam is reflected to the fiber 119, and the measuring beam and the reference beam may be caused to interfere with each other in the fiber coupler 106. In such a case, the mirror 123-b, the collimator 120-b, the fiber 124, and the fiber coupler 126 become unnecessary. It is desirable to use a circulator in such a configuration.

An example of the configuration of the SLO 140 will be described below.

The SLO 140 is an example of the fundus image acquisition unit configured to acquire the fundus image of the subject's eye. The light source 141, i.e., a semiconductor laser, emits light having a central wavelength of 780 nm. The measuring beam emitted from the light source 141 (also referred to as a SLO measuring beam) is polarized via a fiber 142 by a polarizing controller 145 to a linearly-polarized beam, and is output from a collimator 143 as a parallel beam.

The output measuring beam then passes through a perforated portion of a perforated mirror 144, and reaches, via a lens 155, a dichroic mirror 154 via an X scanner 146, lenses 147 and 148, and a Y scanner 149. The X scanner 146 includes a galvano mirror that scans the measuring beam in the horizontal direction on the fundus Er, and the Y scanner 149 includes a galvano mirror that scans the measuring beam in the vertical direction on the fundus Er. It is not necessarily required to include the polarization controller 145. The X scanner 146 and the Y scanner 149 are controlled by the drive control unit 180, and are capable of scanning with the measuring beam in the desired range on the fundus. The dichroic mirror 154 reflects light having wavelengths of, for example, 760 nm to 800 nm, and transmits light of other wavelengths.

The linearly-polarized measuring beam reflected by the dichroic mirror 154 passes through the dichroic mirror 111 and reaches the fundus Er via the optical path similar to that of the OCT 100.

The SLO measuring beam with which the fundus Er is irradiated is reflected and scattered by the fundus Er, and reaches the perforated mirror 144 via the above-described optical path. The beam reflected by the perforated mirror 144 is received via a lens 150 by an avalanche photodiode (APD) 152, converted into an electrical signal, and received by the signal processing unit 190. The position of the perforated mirror 144 is conjugate with the position of the pupil in the subject's eye. The perforated mirror 144 reflects the light that has passed through a peripheral region of the pupil among the light reflected and scattered by the fundus Er irradiated with the measuring beam.

An example of the configuration of the anterior segment imaging unit 160 will be described below. The anterior segment imaging unit 160 includes lenses 162, 163, and 164, and an anterior segment camera 165.

An irradiation light source 115, including light emitting diodes (LED) 115-a and 115-b that emit irradiation light having a wavelength of, e.g., 850 nm, irradiates the anterior segment Ea. The light reflected by the anterior segment Ea reaches a dichroic mirror 161 via the focus lens 114, the lens 112, and the dichroic mirrors 111 and 154. The dichroic mirror 161 reflects light having wavelengths of, e.g., 820 nm to 900 nm, and transmits light of other wavelengths. The light reflected by the dichroic mirror 161 is then received by the anterior segment camera 165 via the lenses 162, 163, and 164. The light received by the anterior segment camera 165 is converted into an electrical signal and is received by the signal processing unit 190.

The internal fixation lamp 170 will be described below.

The interior fixation lamp 170 includes a display unit 171 and a lens 172. A plurality of LEDs arranged in a matrix shape is used as the display unit 171. A lighting position of the LED is changed by control performed by the drive control unit 180 according to a region to be imaged. The light emitted from the display unit 171 is guided to the subject's eye via the lens 172. The display unit 171 emits light having a wavelength of, e.g., 520 nm, and the drive control unit 180 displays a desired pattern.

The control unit 200 will be described below. The control unit 200 includes the drive control unit 180, the signal processing unit 190, the control unit 191, and the display unit 192.

The drive control unit 180 controls each unit as described above.

The signal processing unit 190 generates images based on the signals output from the balanced receiver 129, the APD 152, and the anterior segment camera 165, analyzes the generated images, and generates visualization information of the analysis results. The image generation process will be described in detail below. The control unit 191 controls the entire apparatus and displays, on a display screen in the display unit 192, the images generated by the signal processing unit 190. The display unit 192 is an example of a display unit or a display apparatus. Further, the image data generated by the signal processing unit 190 may be transmitted to the control unit 191 via wired or wireless communication.

Furthermore, the control unit 191 acquires the value of the spectral illuminometer 500 measured when tomographic imaging is started. The control unit 191 then stores in a storing unit 600 the tomographic image of the anterior segment Ea generated by the signal processing unit 190 associated with the acquired measurement value of the spectral illuminometer 500. The control unit 191 is thus an example of the acquisition unit configured to acquire a value indicating the brightness of the ophthalmologic apparatus surroundings. Moreover, the control unit 191 is an example of the recording unit configured to record in the storing unit the value indicating brightness acquired by the acquisition unit, associated with the tomographic image.

Timing at which the control unit 191 acquires the measurement value of the spectral illuminometer 500 is not limited to when tomographic imaging is started, and may be acquired at other timings such as after imaging has been completed or before performing imaging.

Further, the luminance to be associated with the tomographic image of the anterior segment Ea by the control unit 191 is not limited to the value of the spectral illuminometer 500. For example, the examiner may determine the luminance of the examination room in which the ophthalmologic apparatus is placed, and input the determined luminance using an input unit such as a keyboard. The value to be input is not limited to a specific luminance value and may be an index which indicates a level of luminance, such as “bright”, “normal”, and “dark”. The control unit 191 thus associates with the tomographic image, the information input via the input unit such as the keyboard. The indices indicating the levels of brightness are not limited to three levels, and may be four or more levels, or two levels.

Furthermore, when the tomographic image is to be captured after dimming the lights in the examination room, it takes time before the movement of the iris becomes stable (e.g., 2 to 3 minutes). The time from dimming the light to imaging the tomographic image may thus be acquired and stored in the storing unit also associated with the tomographic image, so that the examiner can determine, after performing imaging, whether the movement of the iris has become stable.

The examiner may use a timer to measure the time, and input the time to the ophthalmologic apparatus via the input unit such as the keyboard. The control unit 191 then acquires the information input via the input unit. Moreover, the control unit 191 may use the output from the spectral illuminometer 500 and measure the time from when the luminance has become lower than or equal to a predetermined luminance to when the tomographic imaging is performed. The control unit 191 thus is an example of an acquisition unit configured to acquire time from when a value indicating the brightness of the ophthalmologic apparatus surroundings has become less than or equal to a predetermined value, to when the unique information is acquired. Further, the control unit 191 is an example of a recording unit configured to record in a storing unit the time from when a value indicating the brightness of the ophthalmologic apparatus surroundings has become less than or equal to a predetermined value, to when the unique information is acquired, acquired by an unique information acquisition unit, associated with the unique information.

The storing unit 600 is a hard disk drive (HDD) or a solid state drive (SSD), and may be included in the control unit 200 or externally connected to the control unit 200. The storing unit 600 may thus be internally installed or externally attached to the ophthalmologic apparatus. Further, the control unit 191 and the storing unit 600 are connected via wireless or wired communication. Furthermore, the control unit 191 and the spectral illuminometer 500 are connected via wireless or wired communication.

The display unit 192 such as a liquid crystal display displays various types of information as described below under control of the control unit 191. The control unit 191 may transmit the image data to the display unit 192 via wired or wireless communication. Further, according to the present exemplary embodiment, the display unit 192 is included in the control unit 200. However, it is not limited thereto, and may be separated from the control unit 200.

Furthermore, a tablet, which is an example of a portable device, configured by integrating the control unit 191 and the display unit 192, may be used. In such a case, it is desirable to include a touch panel function in the display unit 192, so that a user can operate the touch panel to move the display position of the images, enlarge and reduce the images, and change the images to be displayed. The touch panel function may be included in the display unit 192 even in the case where the control unit 191 and the display unit 192 are not integrated. In other words, the touch panel may be used as an instruction device.

Image generation and image analysis processes performed in the signal processing unit 190 will be described below.

The signal processing unit 190 performs, on the interference signal output from the balanced receiver 129, common reconfiguration processing, and thus generates a tomographic image.

More specifically, the signal processing unit 190 performs fixed pattern noise cancellation on the interference signal. The fixed pattern noise cancellation is performed by averaging a plurality of A-scan signals that has been detected and thus extracting the fixed pattern noise, and subtracting the extracted fixed pattern noise from the input interference signal.

The signal processing unit 190 then performs window function processing necessary for optimizing the depth resolution and dynamic range having a trade-off relation when performing Fourier transform in a finite interval. The signal processing unit 190 performs fast Fourier transform (FFT), and thus generates the tomographic image. If a plurality of OCT images is to be captured in one imaging without changing the position, the plurality of tomographic images is averaged, and speckle noise is removed. A high-quality image is thus captured.

FIGS. 2A and 2B illustrate examples of the tomographic images captured by the OCT 100 and generated by the signal processing unit 190.

More specifically, FIG. 2A illustrates an example of a tomographic image of a normal eye, and FIG. 2A illustrates an example of a tomographic image of a myopic eye. Referring to FIGS. 2A and 2B, a retinal pigment epithelium-choroid boundary 201, a choroid-sclera boundary 202, and boundaries of other layers are imaged. FIGS. 2A and 2B indicate that the OCT 100 is capable of capturing the tomographic image of a wider range (i.e., wider in the horizontal direction of the drawing) as compared to a spectral domain OCT (SD-OCT), due to the following reason. In the SD-OCT, there is a loss of interference light caused by the diffraction grating in the spectroscope. On the other hand, the SS-OCT which does not include the spectroscope is capable of easily improving the sensitivity by performing differential detection of the interference light. The SS-OCT is thus capable of performing high-speed processing at the same level of sensitivity as the SD-OCT, and of capturing a tomographic image of a wide viewing angle employing the high-speed capability.

Further, the OCT 100 is capable of capturing the tomographic image which is deeper in the depth direction (i.e., larger in the vertical direction of the drawing) as compared to the SD-OCT for the following reason. Since the spectroscope used in the SD-OCT disperses the interference light employing the diffraction grating, crosstalk by the interference light tends to occur between adjacent pixels of a line sensor. Furthermore, the interference light from a reflection surface positioned at a depth position Z=Z0 vibrates at a frequency of Z0/π with respect to a wave number k. A vibration frequency of the interference light thus increases as Z0 increases (i.e., as the reflection surface moves away from a coherence gate position), so that the effect of the crosstalk by the interference light between the adjacent pixels in the line sensor increases. As a result, if the SD-OCT is to perform imaging at a deeper position, sensitivity is lowered. In contrast, the SS-OCT which does not use the spectroscope is advantageous as compared to the SD-OCT in being capable of capturing the tomographic image at a deeper position.

When the tomographic image is to be displayed on the display area of the display unit 192, it is meaningless to display an area in which there is no cross-sectional image. According to the present exemplary embodiment, the control unit 191 thus recognizes from data expanded in a memory in the signal processing unit 190 a portion corresponding to the cross-sectional image. The control unit 191 then cuts out from the recognized portion the tomographic image matching the size of the display area, and displays the tomographic image. The cross-sectional image indicates the image of a fundus tissue of the subject's eye.

The signal processing unit 190 performs segmentation of the tomographic image using the above-described intensity image.

More specifically, the signal processing unit 190 applies to the tomographic image to be processed, a median filter and a Sobel filter, and thus generates respective images (hereinafter referred to as a median image and a Sobel image). The signal processing unit 190 then generates a profile for each A-scan from the generated median image and Sobel image. The signal processing unit 190 generates the profile of an intensity value from the median image and the profile of a gradient from the Sobel image. The signal processing unit 190 detects peaks in the profiles generated from the Sobel image. Further, signal processing unit 190 extracts a boundary of each layer in the retina by referring to the profiles of the median image corresponding to regions before and after the detected peaks and the regions between the detected peaks.

Furthermore, the signal processing unit 190 measures each layer thickness in the direction of the A-scan line, and generates a layer thickness map of each layer.

The processing operation performed in the ophthalmologic apparatus according to the present exemplary embodiment will be described below.

FIG. 3 is a flowchart illustrating the process performed by the ophthalmologic apparatus according to the present exemplary embodiment.

In step 5101, the ophthalmologic apparatus and the subject's eye positioned on the ophthalmologic apparatus are aligned. The process unique to the present exemplary embodiment with respect to performing alignment will be described below. Since alignment of a working distance, focusing, and adjustment of the coherence gate are common, description will be omitted.

FIGS. 4 and 5 illustrate examples of a window 400 displayed on the display unit 192 when performing adjustment or an image captured after performing imaging.

An operator using an instruction device (not illustrated) such as a mouse designates a box 412 or a box 413 by a cursor. The operator thus designates as an imaging mode, a two-dimensional (2D) imaging mode (refer to FIG. 4) or a three-dimensional (3D) imaging mode (refer to FIG. 5).

The imaging mode is then set based on the instruction and is displayed on an area 410. A fundus image (i.e., an intensity image) 411 captured by the SLO 140 and generated by the signal processing unit 190 is displayed on the area 410. The area defined by an exterior frame of the fundus image 411 is the display area of the fundus image. Hereinafter, the display area of the fundus image in the area 410 may be referred to as a fundus image display area. According to the present exemplary embodiment, the fundus image display area is an example of a first area. The fundus image 411 is a moving image captured when performing adjustment or an image captured after performing imaging.

A linear line 415 as illustrated in FIG. 4 or a rectangle 416 as illustrated in FIG. 5, indicating an imaging range of the OCT 100, is superimposed and displayed on the fundus image 411 according to the imaging mode. According to the present exemplary embodiment, a display form indicating the imaging range displayed on the fundus image 411 is not limited to the linear line and the rectangle. For example, if a circle scan is to be performed, a circle is displayed on the fundus image 411.

A tomographic image 431 illustrated in FIG. 4 is a moving image captured when performing adjustment or an image captured after performing imaging. The tomographic image 431 includes a macula lutea and an optic disk of the subject's eye. Further, a tomographic image 438 illustrated in FIG. 5 is a moving image captured when performing adjustment or an image captured after performing imaging. The areas defined by the exterior frames of the tomographic imaged 431 and 438 are the display areas of the tomographic images. Hereinafter, the display area of the tomographic image in the area 430 may be referred to as a tomographic image display area. According to the present exemplary embodiment, the tomographic image display area is an example of a second area positioned above or below the first area and which is an area wider in the horizontal direction as compared to the first area. The tomographic image display area may also be an area larger in the vertical direction (i.e., in the vertical direction with respect to the display unit 192) as compared to the fundus image display area. In other words, the second area may be larger in the vertical direction as compared to the first area.

As illustrated in FIGS. 4 and 5, the size of the tomographic image display area may be changed according to the imaging range of the tomographic image. More specifically, if the viewing angle of the tomographic image is greater than or equal to a predetermined value, the horizontal width of the tomographic image display area may be increased as illustrated in FIG. 4. Further, if the imaging range of the tomographic image is a viewing angle that is less than a predetermined value, the horizontal width of the tomographic image display area may be decreased as illustrated in FIG. 5.

The operator designates the imaging range using the instruction device (not illustrated) such as the mouse. In other words, the operator sets the size and adjusts the position of the linear line 415 and the rectangle 416 using the instruction device. The drive control unit 180 then controls a drive angle of a scanner and determines the imaging range. For example, if the operator has selected the 2D imaging mode, the imaging range may be instructed by automatically extracting the macula lutea and the optic disk from the fundus image 411, and setting a linear line that passes through the macula lutea and the optic disk as an initial tomographic image acquisition position. Further, the operator may use the instruction device to designate two points on the fundus image 411, so that a linear line connecting the two points is set as the tomographic image acquisition position.

The example illustrated in FIG. 4 is a case where one tomographic image is captured. In contrast, according to the example illustrated in FIG. 5, a three-dimensional image is captured, and a tomographic image 432 near the center of the area is displayed in the area 430. The tomographic image 438 is not limited to the tomographic image near the center of the rectangle 416, and may be the tomographic image of an edge portion of the rectangle 416. An examiner may also be allowed to preset the position in the rectangle 416 which is to be displayed as the tomographic image.

<Imaging, Image Generation, and Analysis>

In step 5102, the light sources 101 and 141 respectively emit the measuring beam based on an imaging instruction from the operator. The control unit 191 sweeps the wavelength of the light emitted from the light source 101. The balanced receiver 129 and the APD 152 then receive the return beam from the fundus Er. In step 5103 and step 5104, the signal processing unit 190 generates and analyzes each image as described above.

The process for outputting the generated image and the analysis result performed in step 5105 will be described below. After the signal processing unit 190 completes generating and analyzing each image, the control unit 191 generates output information based on the result, and outputs to and displays on the display unit 192 the output information. The display examples on the display unit 192 will be described below.

FIGS. 4, 5, 6, 7, 8, and 9 illustrate display examples on the display unit 192 according to the present exemplary embodiment. Referring to FIG. 4, the window 400 includes the area 410, an area 420, and the area 430. More specifically, the areas 410 and 420 are arranged adjacent to each other above the area 430. The display example is not limited thereto, and the areas 410 and 420 may be arranged adjacent to each other below the area 430. Further, in the example illustrated in FIG. 4, the area 410 is positioned to the left of the area 420. However, it is not limited thereto, and the area 420 may be arranged to the left of the area 410. Furthermore, in the example illustrated in FIG. 4, the window 400 includes three areas. However, it is not limited thereto, and the area may include four or more areas, or two or less areas.

The area 430 displays the tomographic image 431, and the area 410 displays the fundus image 411. In other words, the fundus image display area is positioned above or below the tomographic image display area. Further, the area 420 displays information on the apparatus and information on a subject. For example, the control unit 191 displays on the area 420 the information associated with the tomographic image displayed on the area 430, such as the measurement value of the spectral illuminometer 500. Further, the control unit 191 displays on the area 420 the value indicating the brightness input via the input unit such as the keyboard. Furthermore, the control unit 191 displays on the area 420 the time between dimming the light of the examination room and capturing of the tomographic image, associated with the tomographic image.

The control unit 191 determines whether the value indicating the brightness associated with the tomographic image is less than or equal to a predetermined value. If the value indicating the brightness is less than or equal to a predetermined value, the control unit 191 displays a display form indicating a warning on the area 420. The display form indicating a warning may be a message informing that the acquired image is in a state that may cause the symptoms of glaucoma to appear or the angle closure to occur. The control unit 191 thus is an example of a determination unit configured to determine whether a value indicating brightness acquired by the acquisition unit and associated with the unique information is less than or equal to a predetermined value. Further, the control unit 191 is an example of a display control unit configured to display, in the case where the determination unit has determined that the value indicating brightness acquired by the acquisition unit is less than or equal to a predetermined value, a display form indicating a warning on a display unit.

As illustrated in FIG. 4, the horizontal width of the area 430 is wider than those of the areas 410 and 420. Further, the horizontal width of the tomographic image 431 is wider than that of the fundus image 411. The width of the tomographic image display area is thus wider than that of the fundus image display area. Furthermore, the sum of the horizontal widths of the areas 410 and 420 is equal to the horizontal width of the area 430. However, it is not limited thereto. The control unit 191 displays on the display unit 192 the tomographic image 431 and the fundus image 411. In other words, the control unit 191 is an example of a display control unit configured to display a fundus image in the first area of a display unit, and a tomographic image in the second area of the display unit which is positioned above or below the first area and which is an area wider in the horizontal direction as compared to the first area.

Moreover, as illustrated in FIG. 4, the tomographic image 431 is displayed in the tomographic image display area set in the area 430 having a wider horizontal width as compared to the areas 410 and 420. As a result, the tomographic image 431 can be displayed wider in the horizontal direction as compared to the images displayed in the other areas. The tomographic image 431 can thus be displayed without reducing the tomographic image of a wide imaging angle, or be displayed by a smaller reduction ratio. In other words, even a tomographic image of a wide viewing angle can be easily observed.

According to the present exemplary embodiment, since the OCT 100 has a deep imaging area, a tomographic image of a predetermined depth (i.e. a length in the vertical direction with respect to the drawing) from the coherence gate position is cut out and displayed to match the tomographic image display area.

If it is determined that, as a result of cutting out the tomographic image, the cross-sectional image in the tomographic image intersects a line defining the vertical direction of the tomographic image display area, the control unit 191 displays a designation area 433 as illustrated in FIG. 7. Referring to FIG. 7, if the operator designates the designation area 433 by clicking thereon, the control unit 191 may expand the tomographic image display area as illustrated in FIG. 8, and display the entire tomographic image. As a result, a tomographic image 434 as illustrated in FIG. 8 which is larger than the tomographic image 432 in the depth direction is displayed. In other words, if it is determined that the cross-sectional image and the line defining the vertical direction of the tomographic image display area intersect, the control unit 191 expands the area 430.

Referring to FIG. 8, if the use designates a designation area 435, the display returns to the state illustrated in FIG. 7. Further, in the example illustrated in FIG. 8, the fundus image 411 is superimposed on the area 430 and displayed. However, the fundus image 411 may be reduced and displayed, so that the fundus image 411 and the area 430 do not overlap. The fundus image display area may thus be reduced.

If the operator designates the designation area 433, the tomographic image display area may be expanded over the entire window 400 to display on the display unit 192 the portions of the tomographic image 432 that has not been displayed. Further, if the operator has selected a portion of the tomographic image displayed on the entire window 400, the control unit 191 may cut out the tomographic image including the selected portion and return to the display state illustrated in FIG. 7. The control unit 191 thus displays the tomographic image including the selected portion as the tomographic image 432 as illustrated in FIG. 7. As a result, the examiner can easily display the tomographic image of the desired position. According to the above-described examples, the display form is changed by the operator designating the designation areas 433 and 435. However, it is not limited thereto, and the display form may be changed according to the operator double-clicking on the tomographic image 432.

Further, when the control unit 191 determines that the cross-sectional image and the line defining the vertical direction of the tomographic image display area intersect, it is not necessary for the control unit 191 to display the designation area 433. In such a case, the control unit 191 may automatically expand the tomographic image display area so that the tomographic image 432 becomes the tomographic image 434. In other words, if the image of the fundus tissue of the subject's eye included in the tomographic image contacts an upper edge of the second area, the control unit 191 expands the second area, and displays the tomographic image on the expanded second area. Further, in such a case, the control unit 191 reduces the fundus image 411 so that the fundus image 411 and the area 430 do not overlap. In other words, if the second area is expanded, the first area and the fundus image are reduced, so that the designation areas 433 and 435 become unnecessary.

Furthermore, as illustrated in FIGS. 9A and 9B, areas 901 and 902 for scrolling the tomographic image may be added to the tomographic image, and the operator may scroll the tomographic image by giving an instruction thereon, instead of enlarging the area as described above. FIG. 9B illustrates the display example in the case where the operator scrolls upward from the state illustrated in FIG. 9A. The control unit 191 adds the areas 901 and 902. The control unit 191 may only add the areas 901 and 902 when it is determined that the cross-sectional image and the line defining the vertical direction of the tomographic image display area intersect, or may regularly add the areas 901 and 902. The display control unit thus displays, if the image of the fundus tissue of the subject's eye included in the tomographic image contacts the upper edge of the second area, the scroll bar which allows scrolling of the tomographic image displayed on the display unit in the vertical direction.

FIG. 5 illustrates the state where the tomographic image 438 is displayed on the area 430 as the tomographic image captured in the 3D imaging mode. The OCT 100 acquires as the three-dimensional data the information of the area set by the rectangle 416, and the control unit 191 displays on the display unit 192 the tomographic image 438 near the center of the rectangle 416. The tomographic image 438 is not limited to the tomographic image near the center of the rectangle 416, and may be the tomographic image of the edge portion of the rectangle 416.

A display screen as illustrated in FIG. 6 may be displayed instead of the display screen illustrated in FIG. 5. Referring to FIG. 6, the area defined by the exterior frame of a tomographic image 421 is positioned to the right of the fundus image display area. However, it is not limited thereto, and the area may be positioned to the left of the fundus image display area. Further, the area defined by the exterior frame of a tomographic image 421 is positioned above the tomographic image display area. However, it is not limited thereto, and the area may be positioned below the tomographic image display area.

Furthermore, the area defined by the exterior frame of a tomographic image 421 is narrower in the horizontal direction as compared to the tomographic image display area. In other words, the area defined by the exterior frame of a tomographic image 421 is an example of a third area which is positioned to the left or the right of the first area and which is an area narrower in the horizontal direction as compared to the second area. In such a case, the display area of the tomographic image becomes smaller, so that the information on the apparatus can be displayed on a wide area. The display areas can thus be efficiently used in the display states illustrated in FIGS. 4 and 6.

The control unit 191 may switch between displaying as illustrated in FIG. 4 and as illustrated in FIG. 6 according to the imaging range. For example, if the viewing angle of the imaging range is wider than the predetermined value, the control unit 191 may display as illustrated in FIG. 4, and if the imaging range is less than or equal to the predetermined value, the control unit 191 may produce a display as illustrated in FIG. 6. The display control unit thus determines the area for displaying the tomographic image according to the viewing angle of the tomographic image. More specifically, the display control unit displays the tomographic image whose viewing angle is greater than or equal to a threshold value on the first area. Further, the display control unit displays the tomographic image whose viewing angle is less than the threshold value, on the third area which is positioned to the left or the right of the first area and which is an area narrower in the horizontal direction as compared to the second area.

According to the above-described example, the control unit 191 switches the display form according to the viewing angle. However, the area for displaying the tomographic image may be changed based on whether the tomographic image includes both or one of the optic disk and the macula lutea. For example, if the tomographic image includes both of the optic disk and the macula lutea, the control unit 191 displays the tomographic image as illustrated in FIG. 4. If the tomographic image only includes the optic disk or the macula lutea, the control unit 191 displays the tomographic image as illustrated in FIG. 6. The display control unit thus displays, if the tomographic image includes both the optic disk and the macula lutea of the subject's eye, the tomographic image on the first area. Further, if the tomographic image only includes the optic disk or the macula lutea, the display control unit displays the tomographic image on the third area which is positioned to the left or the right of the first area and which is an area narrower in the horizontal direction as compared to the second area.

As a result, the area to be displayed is determined according to the viewing angle or a characteristic portion such as the optic disk and the macula lutea. The area of the display screen can thus be efficiently used.

As described above, according to the present exemplary embodiment, the tomographic image and the measurement value of the spectral illuminometer are stored associated with each other. The examiner can thus easily recognize the lighting environment in which the tomographic image has been captured when diagnosing glaucoma, so that the glaucoma diagnosis can be accurately performed. Further, when the tomographic image is displayed on the display unit, the measurement value acquired by the spectral illuminometer associated with the tomographic image is also displayed on the display unit. As a result, the examiner can evaluate the tomographic image while recognizing the lighting environment, and can accurately perform the glaucoma diagnosis. Furthermore, the SS-OCT 100 is capable of capturing the tomographic image of a wider viewing angle and larger in the depth direction as compared to the SD-OCT. The glaucoma diagnosis can thus be more accurately performed by combining image acquisition using the SS-OCT 100 with information on the lighting environment. According to the present exemplary embodiment, an accurate diagnosis can be performed.

Moreover, according to the present exemplary embodiment, the examiner performs OCT imaging while recognizing the lighting environment. As a result, a patient is placed for only a minimum length of time in a dark lighting environment in which the angle closure tends to occur, so that safety of the patient in performing the OCT examination can be improved.

The display example on the display unit 192 is not limited to the above. For example, the display unit 192 may display the tomographic image as illustrated in FIG. 10. Referring to FIG. 10, the area 430 displays the tomographic image 432 captured by the OCT 100. If the operator then selects using the instruction device such as the mouse a portion of the tomographic image 432 displayed on the area 430, the control unit 191 displays on the area 420 a tomographic image 437 of a selected area 436. The area defined by the exterior frame of the tomographic image 437 is an example of the third area. Since the area defined by the exterior frame of the tomographic image 437 is proximately similar to the above-described area defined by the exterior frame of the tomographic image 421, detailed description on the positional relation with the other areas will be omitted.

The control unit 191 enlarges the tomographic image in the area 436 to match the size of the area 420 and displays the tomographic image. The display control unit thus enlarges, if a selection unit selects a portion of the tomographic image displayed on the second area, the selected portion of the tomographic image. The display control unit displays the enlarged tomographic image on the third area which is positioned to the left or the right of the first area and which is an area narrower in the horizontal direction as compared to the second area. The control unit 191 displays on the tomographic image 432 the area 436 selected by the operator using the instruction device.

According to the above-described modified example, a positional relation between the tomographic image of a wide viewing angle and a portion of the tomographic image becomes recognizable. Further, a portion of the tomographic image of a wide viewing angle can be observed in detail. As a result, an efficient diagnosis can be performed.

According to the first exemplary embodiment, the SS-OCT and the SLO are integrated in the apparatus. According to the second exemplary embodiment, the fundus camera is used instead of the SLO as the optical system for observing the fundus of the subject's eye, and the SS-OCT and the fundus camera are integrated in the apparatus.

Further, according to the first exemplary embodiment, the X scanner 107 and the Y scanner 110 are separately included in the OCT 100. In contrast, according to the present exemplary embodiment, the scanners are integrally configured as an XY scanner 338, and included in the fundus camera main body 300. However, the present invention is not limited thereto.

Furthermore, according to the second exemplary embodiment, an infrared area sensor 321 for performing infrared fundus observation is included in the fundus camera main body 300 separately from a camera unit 330. If an area sensor 331 in the camera unit 330 is sensitive to both the infrared light and the visible light, it is not necessary to include the infrared area sensor 321.

The configuration of the imaging apparatus according to the present exemplary embodiment will be described below with reference to FIG. 11. FIG. 11 is a lateral view illustrating the imaging apparatus according to the present exemplary embodiment. Referring to FIG. 11, the fundus camera main body 300 and the camera unit 330 are optically connected. Further, the fundus camera main body 300 and the OCT 100 are optically connected via an optical fiber 348. Furthermore, the fundus camera main body 300 and the OCT 100 respectively include a connector 346 and a connector 347. A chin support 323 fixes a chin and a forehead of the subject so that the subject's eye is fixed. A monitor 391 displays an infrared image for performing adjustment in imaging.

A joystick 325 is used by the examiner for controlling movement of the fundus camera main body 300 to align with the subject's eye. An operation switch 324 is a signal input unit used for inputting the operations for capturing the tomographic image and the fundus image. A control unit 325 which is a personal computer controls the fundus camera main body 300, the camera unit 330, the configuration of the tomographic image, and displaying of the tomographic image and the fundus image. A control unit monitor 328 is a display unit, and a storing unit 329 is a hard disk that stores programs and captured images. The storing unit 329 may be included in the control unit 325. The camera unit 330 is a general-purpose digital single-lens reflex camera, and is connected to the fundus camera main body 300 by a general-purpose camera mount.

The optical system of the fundus camera main body 300 will be described below with reference to FIG. 12. FIG. 12 is a schematic diagram illustrating the optical system of the fundus camera main body 300.

Referring to FIG. 12, an objective lens 302 is disposed opposing the subject's eye, and a perforated mirror 303 on the optical axis divides the optical path into an optical path 351 and an optical path 352. The optical path 352 forms an irradiation optical system that irradiates the fundus Er of the subject's eye. A halogen lamp 316 used for performing alignment of the subject's eye and a stroboscopic tube 314 used for imaging the fundus Er of the subject's eye are arranged in a lower portion of the fundus camera main body 300. Further, the fundus camera main body 300 includes condenser lenses 313 and 315 and a mirror 317.

The illuminating light from the halogen lamp 316 and the stroboscopic tube 314 is formed into a ring-shaped light bundle by a ring slit 312, reflected by the perforated mirror 303, and irradiates the fundus Er of the subject's eye. The light emitted from the halogen lamp 316 irradiates the subject's eye as light of the wavelength range of 700 nm to 800 nm. The light emitted from the stroboscopic tube 314 irradiates the subject's eye as light of the wavelength range of 400 nm to 700 nm.

Furthermore, the fundus camera main body 300 includes lenses 309 and 311, and an optical filter 310. An alignment optical system 390 projects a split image for focusing on the fundus Er, or an index for matching the subject's eye and the optical axis of the optical path of the optical system in the fundus camera main body 300.

The optical path 351 forms an imaging optical system for capturing the tomographic image and the fundus image of the fundus Er of the subject's eye. A focus lens 304 and an image forming lens 305 are arranged on the right side of the perforated mirror 303. The focus lens 304 is supported to be movable in the optical axis direction by the examiner operating a knob (not illustrated).

If an imaging mode for imaging the tomographic image of the anterior segment is selected, the focus position is set to a predetermined portion in the anterior segment instead of the fundus. Such focus adjustment with respect to the anterior segment may be performed by moving the position of the focus lens 304, or by inserting an optical member such as a dedicated lens in an optical path in front or in back of the focus lens 304. In such a case, the drive unit can insert or remove the optical member to or from the optical path. The drive control unit 180 inserts, if the anterior segment imaging mode is selected, the optical member in the optical path, and removes, if the fundus imaging mode is selected, the optical member from the optical path.

The optical path 351 is guided via a quick return mirror 318 to a fixation lamp 320 and the infrared area sensor 321. The quick return mirror 318 reflects the infrared light for capturing the fundus observation image (e.g., light of 700 nm to 800 nm wavelength range), and transmits the infrared light of the wavelength range used in capturing the tomographic image (e.g., light of 980 nm to 1100 nm wavelength range). Further, a silver film and a protection film thereof are formed in this order on the surface the quick return mirror 318. If the infrared area sensor 321 is to capture the moving image and the tomographic image of the fundus using the infrared light, the quick return mirror 318 is inserted in the optical path. It is desirable that the quick return mirror 318 does not transmit visible light (e.g., light of 400 nm to 700 nm wavelength range) that is unnecessary in capturing the moving image and the tomographic image of the fundus. On the other hand, if the still image of the fundus is to be captured using the visible light, a control unit (not illustrated) removes the quick return mirror 318 from the optical path 351.

The image information captured by the infrared area sensor 321 is displayed on the display unit 328 or the monitor 391, and used for performing alignment of the subject's eye. Further, a dichroic mirror 319 is configured such that the visible light is guided towards the fixation lamp 320 and the infrared light is guided towards the infrared area sensor 321. The optical path 351 is then guided to the camera unit 330 via a mirror 306, a field lens 322, a mirror 307, and a relay lens 308. The quick return mirror 318 may be a dichroic mirror which reflects light of 700 nm to 800 nm wavelength range and transmits light of 400 nm to 700 nm, and 980 nm to 1100 nm wavelength range.

The optical path 351 is then divided via a dichroic mirror 335 into a tomographic imaging optical path 351-1 and a visible fundus imaging optical path 351-2. The dichroic mirror 335 transmits light of a 400 nm to 700 nm wavelength range and reflects light of a 980 nm to 1100 nm wavelength range. According to the present exemplary embodiment, the tomographic imaging optical path 351-1 and the visible fundus imaging optical path 351-2 are respectively configured as the reflected light path and the transmitted light path. However, the configuration may be reversed. In such a case, the wavelength range of the light transmitted by the dichroic mirror 335 and the wavelength range of the light reflected by the dichroic mirror 335 are reversed. Further, since light of the wavelength range between the wavelength ranges of the light used in tomographic imaging and the light used in visible fundus imaging is unnecessary, the dichroic mirror 335 may be configured not to transmit or reflect (e.g., absorb) such a wavelength range. An optical member that blocks such a wavelength range may instead be disposed in a stage previous to the dichroic mirror 335.

The fundus camera main body 300 also includes relay lenses 336 and 337, an XY scanner 338, and a collimate lens 339. The XY scanner 338 is illustrated as a single mirror for ease of description. However, two mirrors, i.e., the X scan mirror and the Y scan mirror, are actually arranged close to each other, and perform raster scanning on the fundus Er in the direction perpendicular to the optical axis. Further, the optical axis of the tomographic imaging optical path 351-1 is adjusted to match the rotational center of the two mirrors of the XY scanner 338. Furthermore, the connector 346 is used for attaching the optical fiber.

The camera unit 330 is a digital single-reflex camera for imaging the fundus Er. The fundus camera main body 300 and the camera unit 330 are connected via a general-purpose camera mount, so that the fundus camera main body 300 and the camera unit 330 can be easily attached and separated. The fundus image is formed on the surface image area sensor 331.

The present exemplary embodiment is capable of acquiring a similar effect as the first exemplary embodiment.

According to the first and second exemplary embodiments, the SS-OCT 100 captures the tomographic image of the fundus. According to the third exemplary embodiment, the SS-OCT 100 captures the tomographic image of the anterior segment.

Further, according to the first and second exemplary embodiments, the SLO or the fundus camera is included for observing a surface of the fundus of the subject's eye. According to the present exemplary embodiment, since the anterior segment is to be observed instead of the fundus, it is not necessary to include the SLO or the fundus camera. In other words, the configuration of the imaging apparatus according to the present exemplary embodiment is similar to the configuration of the imaging apparatus illustrated in FIG. 1 according to the first exemplary embodiment excluding the SLO 140.

The processing operation according to the present exemplary embodiment will be described below.

According to the present exemplary embodiment, in the adjustment process of step S101 illustrated in the flowchart of FIG. 3, i.e., an example of the adjustment operation, an anterior segment surface image captured by the anterior segment camera 165 in the anterior segment imaging unit 160 is used in adjusting the OCT imaging position. The fundus image captured by the SLO or the fundus camera is thus not used in performing adjustment.

Further, according to the present exemplary embodiment, in the image analysis process of step S104 illustrated in FIG. 3, the signal processing unit 190 extracts from the tomographic image, numerical parameters unique to the anterior segment.

Furthermore, according to the presented exemplary embodiment, in the output process of step S105 illustrated in FIG. 3, the numerical parameters unique to the anterior segment acquired in step S104 are output to and displayed on the display unit 192.

As a result, according to the present exemplary embodiment, the adjustment process performed in step S101, the image analysis process performed in step S104, and the output process performed in step S105 illustrated in the flowchart of FIG. 3, i.e., an example of the processing operation, are different from those according to the first and second exemplary embodiments. The processes will be described below in order.

(Adjustment of the OCT Imaging Position)

FIGS. 13 illustrates an example of the window 400 displayed on the display unit 192 when performing adjustment or an image captured after performing imaging. The operator using the instruction device (not illustrated) such as the mouse designates a box 512 or a box 513 by the cursor. The operator thus designates as an imaging mode, a line scan imaging mode (refer to FIG. 13) or a radial scan imaging mode (refer to FIG. 14).

The line scan imaging mode is an imaging mode in which one line is scanned. In the line scan imaging mode, the same line is continuously scanned a plurality of times in one imaging, and a plurality of tomographic images is captured. The plurality of tomographic images is then averaged, and the speckle noise is removed, so that a high-quality image can be captured.

The radial scan imaging mode is an imaging mode in which a plurality of lines passing through the center of a pupil 514 is scanned. In the radial scan imaging mode, different lines are continuously scanned a plurality of times in one imaging, and a plurality of tomographic images is captured. The anterior segment can thus be observed in a wider range using such plurality of tomographic images.

If the operator selects the line scan imaging mode or the radial scan imaging mode, the selected imaging mode is set and displayed on the area 410. An anterior segment surface image (i.e., an intensity image) 511 captured by the anterior segment imaging unit 160 and generated by the signal processing unit 190 is then displayed on the area 410. The area defined by an exterior frame of the anterior segment surface image 511 is the display area of the anterior segment surface image. Hereinafter, the display area of the anterior segment surface image in the area 511 may be referred to as an anterior segment surface image display area. According to the present exemplary embodiment, the anterior segment surface image display area is an example of the first area. The anterior segment surface image 511 is a moving image captured when performing adjustment or an image captured after performing imaging.

A linear line indicating an imaging range of the OCT 100 is superimposed and displayed on the fundus image 511 according to the imaging mode as illustrated in FIGS. 13 and 14. More specifically, if the operator instructs the line scan imaging mode, a linear line 520 is displayed, and if the operator instructs the radial scan imaging mode, linear lines 501, 502, 503, 504, 505, and 506 are displayed. A tomographic image 531 illustrated in FIG. 13 and tomographic images 538 and 539 illustrated in FIG. 14 are moving images captured when performing adjustment or images captured after performing imaging. The tomographic images 531, 538, and 539 include a portion of the cornea, the iris, the angle, and the lens of the subject's eye.

The areas defined by the exterior frames of the tomographic images 531, 538, and 539 are the display areas of the tomographic images. Hereinafter, the display areas of the tomographic images in the area 430 may be referred to as the tomographic image display areas. Further, the tomographic image display area is an example of the second area positioned above or below the first area and which is an area wider in the horizontal direction as compared to the first area. The tomographic image display area may also be an area larger in the vertical direction (i.e., in the vertical direction with respect to the display unit 192) as compared to the anterior segment surface image display area. In other words, the second area may be larger in the vertical direction as compared to the first area.

Furthermore, the imaging range of the radial scan imaging mode is not limited to the six lines, i.e., the lines 501, 502, 503, 504, 505, and 506, and may be seven or more lines or five or less lines at arbitrary positions.

In the radial scan imaging mode, a plurality of tomographic image display areas may be arranged within the area 430 as illustrated by the tomographic images 538 and 539 in FIG. 14. Further, a plurality of lines to be displayed in the tomographic image display area is selected from the lines 501, 502, 503, 504, 505, and 506 in the anterior segment surface image, and the indices are displayed. According to the present exemplary embodiment, indices 601 and 502 are displayed. Further, the plurality of tomographic images 538 and 539 corresponding to the lines having the indices displayed on the anterior segment surface image is displayed on the plurality of tomographic image display areas in the area 430. The tomographic images corresponding to the arbitrary lines among the plurality of lines of the radial scan imaging mode are displayed. In the example illustrated in FIG. 14, corresponding indices 603 and 604 of the tomographic image display areas are respectively displayed on the tomographic images 538 and 539.

As described above, a plurality of tomographic image display areas is arranged within the area 430. As a result, angle openings of a plurality of portions become comparable, and the angle closure that causes acute glaucoma attack can be accurately diagnosed.

The angle may be different according to the position thereof in the anterior segment. According to the present exemplary embodiment, the tomographic images corresponding to two scan lines perpendicular to each other among the plurality of scan lines are displayed to efficiently recognize the change according to the position of the angle. In other words, the state of the angle of an examinee can be efficiently recognized by displaying the tomographic images corresponding to two scan lines perpendicular to each other. The tomographic images to be displayed are not limited to those corresponding to the indices 601 and 602, as long as the tomographic images correspond to two scan lines perpendicular to each other. Further, the scanning method may be cross scan instead of the radial scan.

The operator designates the imaging range using the instruction device (not illustrated) such as the mouse. The operator thus sets the sizes and adjusts the positions of the linear lines 520, 501, 502, 503, 504, 505, and 506 using the instruction device. The drive control unit 180 then controls the drive angle of the scanner and determines the imaging range. For example, if the operator has selected the line scan imaging mode, the imaging range may be instructed by scanning one horizontal line passing through the center of a pupil 514. Further, the operator may use the instruction device to designate two points on the anterior segment surface image 511, so that a linear line connecting the two points is set as the tomographic image acquisition position.

If the operator has selected the radial scan imaging mode, the plurality of lines passing through the center of the pupil may be automatically arranged to be equiangular by designating the number of lines. Further, the center of the pupil 514 may be manually or automatically selected. If the center of the pupil 514 is automatically selected, the pupil is approximated by a circle, and the center of the approximated circle may be set as the center of the pupil 514. Furthermore, according to the present exemplary embodiment, when the radial scan imaging mode is selected, two tomographic images are displayed. However, it is not limited thereto, and three or more tomographic images or one tomographic image may be displayed.

The signal processing unit 190 calculates the parameters indicating the angle opening as describe below from the tomographic image of the anterior segment, according to definitions described in a reference literature “Practical ophthalmology 25: Biometry of accurate measurement of the eye”, Bunkodo. The signal processing unit 190 may calculate all or a portion of the parameters to be described below.

More specifically, each parameter is calculated as described below in FIG. 15.

Referring to FIG. 15, an angle opening distance (AOD) 500 is calculated as a distance (in μm) between a point 702 which is 500 μm from a scleral spur 701 along a back surface of the cornea, and a point 703 at which a line perpendicularly drawn from the point 702 with respect to the back surface of the cornea intersects with a front surface of the iris. In the example illustrated in FIG. 15, the scleral spur 701 is the boundary between a ciliary body and the sclera. An anterior chamber angle (ACA) 500 is calculated as an angle (in degrees) formed by line segments connecting the respective points 702 and 703 at both ends of the AOD 500 and an angle recess 704.

An angle recess area (ARA) 500 is calculated as an area (in mm²) of a portion surrounded by the linear line connecting the points 702 and 703 at both ends of the AOD 500, and a back surface of the sclera and the front surface of the iris reaching the angle recess 704.

A trabecular iris space area (TISA) 500 is calculated as an area (in mm²) of the portion surrounded by the linear line connecting the points 702 and 703 at both ends of the AOD 500, and a line segment drawn in parallel with the AOD from the scleral spur 701 to a point 705 intersecting the front surface of the iris, the back surface of the cornea, and the front surface of the iris.

The operator directly designates the points 701, 702, 703, 704, and 705 on the image using the mouse, and the signal processing unit 190 calculates the parameters according to the above-described definitions. The points 701, 702, 703, 704, and 705 may also be automatically extracted from the information on the boundary positions of the image captured as a result of performing segmentation.

The parameters with respect to the angle are not limited to the above-described four parameters, and the following parameters may be calculated. The point 702 may be defined as a point which is 750 μm or an arbitrary distance from the scleral spur 701 along the back surface of the cornea, instead of 500 μm. Each of the parameters indicating the angle opening can then be calculated. When the distance is 750 μm, the acquired parameters are referred to as AOD 750, ACA 750, ARA 750, and TISA 750.

The process for outputting the generated image and the analysis result performed in step 5105 illustrated in FIG. 3 will be described below. After the signal processing unit 190 completes generating and analyzing each image, the control unit 191 generates output information based on the result, and outputs to and displays on the display unit 192 the output information. The display examples on the display unit 192 will be described below.

FIGS. 13 and 14 illustrate display examples on the display unit 192 according to the present exemplary embodiment.

Referring to FIG. 13, the area 430 displays the tomographic image 531, and the area 410 displays the anterior segment surface image 511. The anterior segment surface image display area is thus positioned above or below the tomographic image display area. Further, the area 420 displays the information on the apparatus, the information on the examinee, and the analysis result. For example, the control unit 191 displays on the area 420 the information associated with the tomographic image displayed on the area 430.

Further, the control unit 191 displays on the area 420 the values of the plurality of parameters AOD 500, ACA 500, ARA 500, and TISA 500 indicating the angle opening calculated by the signal processing unit 190. The control unit 191 may display a portion of the parameters instead of all parameters. Further, the control unit 191 may compare a normal value of each parameter with the value of each parameter acquired from the tomographic image, and issue a warning when the acquired value is not normal. The control unit 191 may issue the warning by displaying the parameter using a different color from the normal parameter, so that the normal parameter and the abnormal parameter are distinguishable.

Furthermore, the control unit 191 displays on the area 420 the measurement value of the spectral illuminometer 500. Moreover, the control unit 191 displays on the area 420 the value of the brightness input via the input unit such as the keyboard. Further, the control unit 191 displays on the area 420 the time between dimming the light of the examination room and capturing of the tomographic image, associated with the tomographic image.

Furthermore, the control unit 191 displays the display form indicating the warning when determining that the value indicating the brightness, associated with the tomographic image, is less than or equal to a predetermined value, and the time between dimming the light of the examination room and capturing of the tomographic image, associated with the tomographic image, is a predetermined value or longer. The display form indicating the warning is a message informing that the image is captured in a state where the angle closure tends to occur.

The control unit 191 thus is an example of a determination unit configured to determine as follows. The determination unit determines whether the value indicating the brightness, associated with the tomographic image captured by the acquisition unit, is less than or equal to a predetermined value. Further, the determination unit determines whether the time between dimming the light of the examination room and capturing of the tomographic image, associated with the tomographic image, is longer than or equal to a predetermined value. Further, the control unit 191 is an example of a display control unit configured to cause the display unit to display, if the determination unit determines that the brightness acquired by the acquisition unit is less than or equal to a predetermined value, a display form indicating a warning.

As described above, according to the present exemplary embodiment, the tomographic image is stored associated with the parameters indicating the angle opening calculated from the tomographic image, the measurement value of the spectral illuminometer, and the time between dimming the light of the examination room and capturing of the tomographic image. As a result, the examiner can recognize, when diagnosing glaucoma using the tomographic image and the parameters indicating the angle opening, the lighting environment in which the tomographic image has been captured. The examiner can thus accurately diagnose the angle closure.

Further, when the tomographic image is displayed on the display unit, the measurement value of the spectral illuminometer associated with the tomographic image is also displayed on the display unit. The examiner can thus evaluate the tomographic image while recognizing the lighting environment, so that accurate diagnosis of the angle closure can be performed. Furthermore, the SS-OCT 100 is capable of capturing a tomographic image having a wider imaging angle and larger in the depth direction as compared to the SD-OCT. As a result, the examiner can more accurately perform glaucoma diagnosis using such a tomographic image and by recognizing the lighting environment. According to the present exemplary embodiment, accurate diagnosis can thus be performed.

While the present invention has been described with reference to exemplary embodiments, it is to be understood that the invention is not limited to the disclosed exemplary embodiments, and various modifications and changes may be made without departing from the scope of the invention. For example, if the first exemplary embodiment and the second exemplary embodiment are to be applied to the anterior segment, the fundus Er in the above-described exemplary embodiments is replaced with the anterior segment Ea.

Further, according to the above-described exemplary embodiments, the SS-OCT 100 captures the tomographic image. However, it is not limited thereto, and the SD-OCT or a time domain OCT (TD-OCT) may also be used.

Furthermore, according to the above-described exemplary embodiments, the tomographic image of the anterior segment is associated with the value indicating the brightness output from the spectral illuminometer 500 or input via the input unit such as the keyboard. However, it is not limited thereto. For example, the tomographic image of the fundus may be associated with the value indicating the brightness, or a refractive power measured by a refractometer may be associated with the value indicating the brightness when performing measurement. Further, the value indicating the brightness when performing measurement may be associated with the fundus image or the eye pressure. As a result, if the captured image is dark, or the measurement value is an abnormal value, the cause can be determined by referring to the value indicating the brightness associated with the image or the measurement value.

Other Embodiments

Embodiments of the present invention can also be realized by a computer of a system or apparatus that reads out and executes computer executable instructions recorded on a storage medium (e.g., non-transitory computer-readable storage medium) to perform the functions of one or more of the above-described embodiment(s) of the present invention, and by a method performed by the computer of the system or apparatus by, for example, reading out and executing the computer executable instructions from the storage medium to perform the functions of one or more of the above-described embodiment(s). The computer may comprise one or more of a central processing unit (CPU), micro processing unit (MPU), or other circuitry, and may include a network of separate computers or separate computer processors. The computer executable instructions may be provided to the computer, for example, from a network or the storage medium. The storage medium may include, for example, one or more of a hard disk, a random-access memory (RAM), a read only memory (ROM), a storage of distributed computing systems, an optical disk (such as a compact disc (CD), digital versatile disc (DVD), or Blu-ray Disc (BD)™), a flash memory device, a memory card, and the like.

While the present invention has been described with reference to exemplary embodiments, it is to be understood that the invention is not limited to the disclosed exemplary embodiments. The scope of the following claims is to be accorded the broadest interpretation so as to encompass all such modifications and equivalent structures and functions.

This application claims the benefit of Japanese Patent Application No. 2012-082689, filed Mar. 30, 2012, which is hereby incorporated by reference herein in its entirety.

OPHTHALMOLOGIC APPARATUS

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