JP2016106652A - Optical coherence tomography apparatus and control program for use in the same - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an optical coherence tomography apparatus that can preferably acquire the blood flow velocity of a subject.SOLUTION: An optical coherence tomography apparatus includes an OCT optical system for acquiring an OCT signal using the measuring light scanned over a subject by scanning means and the reference light corresponding to the measuring light. The optical coherence tomography apparatus is characterized by including an acquisition means for acquiring motion contrast of multiple OCT signals acquired at first time interval with respect to the same position in the subject, and for acquiring the motion contrast of multiple OCT signals acquired at second time interval different from the first time interval when a profile of a phase difference among multiple OCT signals becoming the basic of the motion contrast is discontinuous.SELECTED DRAWING: Figure 11

Description

  The present disclosure relates to an optical coherence tomography apparatus that obtains motion contrast data of a subject, and a control program used therefor.

  In a conventional optical coherence tomography apparatus (also referred to as an OCT apparatus), an apparatus for measuring the blood flow of the retina is known. This utilizes the fact that the frequency of the measurement light irradiated to the eye to be examined changes due to Doppler shift caused by blood cells flowing through the blood vessels.

International Publication No. 2010/143601

H.C.Hendargo et al. Biomed.Opt. Express, Vol. 4, No. 6, p.803 / May 2013 Yonghua Zhao et al. OPTICS LETTERS / Vol. 25, No. 2 / January 15, 2000 Adrian Mariampillai et al. OPTICS LETTERS / Vol. 33, No. 13 / July 1, 2008 Vivek J. Srinivasan et al. OPTICS LETTERS / Vol. 35, No. 1 / January 1, 2010 P. Meemon and J. Rolland, "Swept-source based, single-shot, multi-detectable velocity range Doppler optical coherence tomography," Biomed. Opt. Express, vol. 1, no. 3, pp. 3116-3121, 2010 .

  The frequency change due to the Doppler shift is slight, and the frequency change of the light wave is detected as the phase change. The phase change detection range is often limited to, for example, a range of −π to π. Therefore, when a phase change outside the detection range occurs, the actually generated phase change is different from the detected phase change, and the phase change profile waveform may be discontinuous. Thus, the discontinuous waveform profile is not suitable for blood flow measurement.

  In view of the above problems, it is an object of the present disclosure to provide an optical coherence tomography apparatus that can appropriately acquire the blood flow velocity of a subject.

  In order to solve the above problems, the present invention is characterized by having the following configuration.

(1) An optical coherence tomography apparatus including an OCT optical system for acquiring an OCT signal based on measurement light scanned on a subject by scanning means and reference light corresponding to the measurement light. With respect to the same position above, motion contrasts of a plurality of OCT signals acquired at a first time interval are acquired, and a phase difference profile between the plurality of OCT signals serving as a basis of the motion contrast is discontinuous. In this case, an acquisition means for acquiring motion contrast of a plurality of OCT signals acquired at a second time interval different from the first time interval is provided.
(2) An optical coherence tomography apparatus including an OCT optical system for acquiring an OCT signal obtained by measuring light scanned on a subject by scanning means and reference light corresponding to the measuring light. An acquisition means for acquiring motion contrast of a plurality of OCT signals acquired at a first time interval with respect to the same position above, and the diameter and type of the blood vessel based on the three-dimensional structure of the blood vessel of the subject Blood vessel information acquisition means for acquiring at least one of the blood vessel information when the profile of phase differences between the plurality of OCT signals serving as the basis of the motion contrast is discontinuous. Based on the diameter or type of the blood vessel acquired by the acquisition means, the preset in accordance with the diameter or type of the acquired blood vessel, It is characterized in that motion contrasts of a plurality of OCT signals acquired at a second time interval different from the first time interval are acquired.
(3) A control program used in an optical coherence tomography apparatus including an OCT optical system for acquiring an OCT signal based on measurement light scanned on a subject by scanning means and reference light corresponding to the measurement light. The phase difference of a plurality of OCT signals acquired with a first time interval is acquired and acquired for the same position on the subject by being executed by the processor of the optical coherence tomography apparatus. If the phase difference profile is discontinuous, a phase difference acquisition step of acquiring phase differences of a plurality of OCT signals acquired at a second time interval different from the first time interval, An optical coherence tomography apparatus is executed.

It is a block diagram explaining the structure of an optical coherence tomography apparatus. It is a figure which shows the outline of an optical system. It is a flowchart for demonstrating the process of a present Example. It is an image figure of the fundus for demonstrating the measurement of a present Example. It is an image figure which shows a tomographic blood vessel image. It is a flowchart explaining the control of the blood flow measurement of a present Example. It is a figure explaining matching of a motion contrast image and an observation image. It is a figure which shows an example of the motion contrast image displayed on the display part. It is a figure explaining how to obtain the blood flow velocity. It is a figure which shows the relationship between time and a blood flow velocity. It is a figure for demonstrating the profile of a phase difference.

<Overview>
Hereinafter, an outline of an optical coherence tomography device according to the present disclosure will be described with reference to FIGS. The optical coherence tomography device of the present disclosure (for example, the optical coherence tomography device 10) acquires motion contrast data of a subject. The motion contrast is, for example, detection information such as a subject's movement and temporal change. For example, a flow image or the like is also a kind of motion contrast image. The flow image is an image obtained by detecting the movement of a fluid or the like, for example. An angiographic image obtained by contrasting a blood vessel position obtained by detecting the movement of blood is a kind of motion contrast image.

  The optical coherence tomography apparatus of the present disclosure (hereinafter sometimes abbreviated as the present apparatus) mainly includes, for example, an OCT optical system (for example, the OCT optical system 200) and an acquisition unit (for example, the control unit 70). Prepare. The OCT optical system may acquire, for example, an OCT signal (interference signal) based on measurement light scanned on the subject by a scanning unit (for example, the optical scanner 108) and reference light corresponding to the measurement light. The acquisition unit acquires, for example, motion contrasts of a plurality of OCT signals acquired at a first time interval with respect to the same position on the subject. Then, when the phase difference profile between the plurality of OCT signals serving as the basis of motion contrast is discontinuous, the acquisition unit is acquired with a second time interval different from the first time interval. You may acquire the motion contrast of several OCT signals. The acquisition unit may change the time interval so that the phase difference profile does not become discontinuous. Note that the second time interval may be a time interval shorter than the first time interval. Thus, by obtaining a motion contrast having a continuous profile, the examiner can easily confirm the distribution of moving objects and the like.

  In addition, this apparatus may further include a determination unit (for example, the control unit 70). The determination unit may detect, for example, the inclination of the phase difference profile acquired by the acquisition unit, and determine whether the phase difference profile is continuous based on the detected inclination.

  In addition, this apparatus may further include a drive control unit (for example, the control unit 70). For example, when the phase difference profile is discontinuous, the drive control unit may control the driving of the scanning unit and change the irradiation time interval for the same position. For example, the drive control unit may change the irradiation time interval for the same position to be short.

  When the acquired phase difference profile is discontinuous, the acquisition unit determines a second time different from the first time interval from a plurality of OCT signals acquired with a first time interval. At least one set of OCT signals acquired at intervals may be selected. Then, the acquisition unit may acquire the motion contrast of the selected set of OCT signals.

  For example, the acquisition unit may select a signal by skipping one of the plurality of OCT signals acquired at the first time interval, and acquire the motion contrast based on the selected OCT signal. Accordingly, the acquisition unit acquires motion contrast based on a plurality of OCT signals acquired with a second time interval that is twice the first time interval, for example. Similarly, the acquisition unit may select signals by skipping two, three,. This makes it possible to change the calculation time interval T without bothering to control the driving of the scanning unit.

  For example, when the profile of the phase difference between the plurality of OCT signals serving as the basis of the motion contrast is continuous, the acquisition unit may increase the signal / noise ratio of the motion contrast from the first time interval. You may acquire the motion contrast of the several OCT signal acquired at long 2nd time intervals.

  Note that the present apparatus may further include a blood vessel information acquisition unit (for example, the control unit 70). For example, the blood vessel information acquisition unit acquires at least one of the diameter and type of the blood vessel based on the three-dimensional structure of the blood vessel of the subject. The acquisition unit is acquired based on the diameter or type of the blood vessel acquired by the blood vessel information acquisition unit when the profile of the phase difference between the plurality of OCT signals serving as the basis of the motion contrast is discontinuous. Alternatively, motion contrasts of a plurality of OCT signals acquired at a second time interval different from the first time interval set in advance according to the diameter or type of the blood vessel may be acquired.

  In addition, this apparatus may be provided with a processor (for example, control part 70) etc., for example, and may execute the control program memorize | stored in memory etc. The control program includes an acquisition step, for example. The acquisition step acquires, for example, motion contrasts of a plurality of OCT signals acquired with a first time interval for the same position on the subject, and the acquired phase difference profile is discontinuous. This is a step of acquiring phase differences among a plurality of OCT signals acquired at a second time interval different from the first time interval.

<Example>
In the following, one exemplary embodiment will be described with reference to the drawings. FIG. 1 is a block diagram for explaining the configuration of an optical coherence tomography apparatus (hereinafter also referred to as this apparatus) 10 according to the present embodiment. As an example, the apparatus 10 will be described as a fundus imaging apparatus that acquires a tomographic image of the fundus of the eye to be examined.

  The OCT control system 1 processes the detection signal acquired by the OCT optical system 100. The OCT control system 1 has a control unit 70. For example, the OCT optical system 100 captures a tomographic image of the fundus oculi Ef of the eye E. The OCT optical system 100 is connected to the control unit 70, for example.

  The OCT optical system 100 will be described with reference to FIG. The OCT optical system 100 irradiates the fundus with measurement light. The OCT optical system 100 detects the interference state between the measurement light reflected from the fundus and the reference light by the light receiving element (detector 120). In order to change the imaging position on the fundus oculi Ef, the OCT optical system 100 includes an irradiation position changing unit (for example, the optical scanner 108, the fixation target projection unit 300, etc.) that changes the irradiation position of the measurement light on the fundus oculi Ef. The control unit 70 controls the operation of the irradiation position changing unit based on the set imaging position information, and acquires a tomographic image based on the light reception signal from the detector 120.

<OCT optical system>
The OCT optical system 100 has an apparatus configuration of a so-called ophthalmic optical tomography (OCT: Optical coherence tomography) and takes a tomographic image of the eye E. The OCT optical system 100 splits the light emitted from the measurement light source 102 into measurement light (sample light) and reference light by a coupler (light splitter) 104. The OCT optical system 100 guides the measurement light to the fundus oculi Ef of the eye E by the measurement optical system 106 and guides the reference light to the reference optical system 110. The OCT optical system 100 causes the detector (light receiving element) 120 to receive interference light obtained by combining the measurement light reflected by the fundus oculi Ef and the reference light.

  The detector 120 detects OCT signals of the measurement light and the reference light. In the case of Fourier domain OCT, the spectral intensity (spectral OCT signal) of the interference light is detected by the detector 120, and the OCT signal is acquired by Fourier transform on the spectral intensity data. For example, by calculating the absolute value of the amplitude in the complex OCT signal, a profile (A scan signal) in the depth direction (A scan direction) in a predetermined range is acquired. OCT image data (tomographic image data) is acquired by arranging the luminance profiles in the depth direction at the scanning positions of the measurement light scanned by the optical scanner 108. Here, the luminance profile in the OCT image data is a numerical sequence in which the luminance values of each pixel are arranged in the depth direction on the A-Scan line, and is a graph of the luminance value with respect to the depth direction.

  Note that OCT three-dimensional data may be acquired by two-dimensionally scanning the measurement light. Further, an OCT front image (for example, an integrated image integrated in the depth direction) may be acquired from the OCT three-dimensional data.

  Further, the functional OCT signal may be acquired by signal processing of the OCT signal. The functional OCT image data (motion contrast image data) is obtained by arranging the functional OCT signals (motion contrast data) at each scanning position of the measurement light scanned by the optical scanner 108. Further, the three-dimensional functional OCT image data (three-dimensional motion contrast data) may be acquired by two-dimensionally scanning the measurement light. Moreover, an OCT function front (En-face) image (for example, a Doppler front (En-face) image, a speckle variance front image) may be acquired from the three-dimensional function OCT image data.

  Examples of the OCT optical system 100 include spectral-domain OCT (SD-OCT) and swept-source OCT (SS-OCT). Moreover, Time-domain OCT (TD-OCT) may be used.

  In the case of SD-OCT, a low-coherent light source (broadband light source) is used as the light source 102, and the detector 120 is provided with a spectroscopic optical system (spectrum meter) that separates interference light into each frequency component (each wavelength component). . The spectrometer includes, for example, a diffraction grating and a line sensor.

  In the case of SS-OCT, a wavelength scanning light source (wavelength variable light source) that changes the emission wavelength at a high speed in time is used as the light source 102, and a single light receiving element is provided as the detector 120, for example. The light source 102 includes, for example, a light source, a fiber ring resonator, and a wavelength selection filter. Examples of the wavelength selection filter include a combination of a diffraction grating and a polygon mirror, and a filter using a Fabry-Perot etalon.

  The light emitted from the light source 102 is split into a measurement light beam and a reference light beam by the coupler 104. Then, the measurement light flux passes through the optical fiber and is then emitted into the air. The luminous flux is condensed on the fundus oculi Ef via the optical scanner 108 and other optical members of the measurement optical system 106. Then, the light reflected by the fundus oculi Ef is returned to the optical fiber through a similar optical path.

  The optical scanner 108 scans the measurement light two-dimensionally (XY direction (transverse direction)) on the fundus. The optical scanner 108 is arranged at a position substantially conjugate with the pupil. The optical scanner 108 is, for example, two galvanometer mirrors, and the reflection angle thereof is arbitrarily adjusted by the drive mechanism 50.

  Accordingly, the reflection (advance) direction of the light beam emitted from the light source 102 is changed and scanned in an arbitrary direction on the fundus oculi Ef. Thereby, the imaging position on the fundus oculi Ef is changed. The optical scanner 108 may be configured to deflect light. For example, in addition to a reflective mirror (galvano mirror, polygon mirror, resonant scanner), an acousto-optic device (AOM) that changes the traveling (deflection) direction of light is used.

  The reference optical system 110 generates reference light that is combined with reflected light acquired by reflection of measurement light at the fundus oculi Ef. The reference optical system 110 may be a Michelson type or a Mach-Zehnder type. The reference optical system 110 is formed by, for example, a reflection optical system (for example, a reference mirror), and reflects light from the coupler 104 back to the coupler 104 by being reflected by the reflection optical system and guides it to the detector 120. As another example, the reference optical system 110 is formed by a transmission optical system (for example, an optical fiber), and guides the light from the coupler 104 to the detector 120 by transmitting the light without returning.

  The reference optical system 110 has a configuration in which the optical path length difference between the measurement light and the reference light is changed by moving an optical member in the reference optical path. For example, the reference mirror is moved in the optical axis direction. The configuration for changing the optical path length difference may be arranged in the measurement optical path of the measurement optical system 106.

<Front observation optical system>
The front observation optical system 200 is provided to obtain a front observation image of the fundus oculi Ef. The observation optical system 200 includes, for example, an optical scanner that two-dimensionally scans the fundus of measurement light (for example, infrared light) emitted from a light source, and a confocal aperture that is disposed at a position substantially conjugate with the fundus. And a second light receiving element for receiving the fundus reflection light, and has a so-called ophthalmic scanning laser ophthalmoscope (SLO) device configuration. The front observation optical system 200 may acquire a front observation image at any time in parallel with the acquisition of the OCT signal by the OCT optical system 100, for example.

  Note that the configuration of the observation optical system 200 may be a so-called fundus camera type configuration. The OCT optical system 100 may also serve as the observation optical system 200. That is, the front observation image may be acquired using data forming a two-dimensional tomographic image (for example, an integrated image in the depth direction of the three-dimensional tomographic image, each XY position) Integrated value of spectral data at XY, luminance data at each XY position in a certain depth direction, retina surface layer image, etc.).

<Fixation target projection unit>
The fixation target projecting unit 300 includes an optical system for guiding the line-of-sight direction of the eye E. The fixation target projection unit 300 has a fixation target to be presented to the eye E, and can guide the eye E in a plurality of directions.

  For example, the fixation target projection unit 300 has a visible light source that emits visible light, and changes the presentation position of the target two-dimensionally. Thereby, the line-of-sight direction is changed, and as a result, the imaging region is changed. For example, when the fixation target is presented from the same direction as the imaging optical axis, the center of the fundus is set as the imaging site. When the fixation target is presented upward with respect to the imaging optical axis, the upper part of the fundus is set as the imaging region. That is, the imaging region is changed according to the position of the target with respect to the imaging optical axis.

  As the fixation target projection unit 300, for example, the fixation position is adjusted by the lighting positions of the LEDs arranged in a matrix, the light from the light source is scanned using an optical scanner, and the fixation is performed by controlling the lighting of the light source. Various configurations such as a configuration for adjusting the position are conceivable. The projection unit 300 may be an internal fixation lamp type or an external fixation lamp type.

<Control unit>
The control unit 70 includes a CPU (processor), a RAM, a ROM, and the like. The CPU of the control unit 70 controls the entire apparatus (OCT control system 1, OCT optical system 100) such as members of each configuration. The RAM temporarily stores various information. The ROM of the control unit 70 stores various programs for controlling the operation of the entire apparatus, initial values, and the like. The control unit 70 may be configured by a plurality of control units (that is, a plurality of processors).

  As shown in FIG. 1, a nonvolatile memory (storage means) 72, an operation unit (control unit) 76, a display unit (monitor) 75, and the like are electrically connected to the control unit 70. The non-volatile memory (memory) 72 is a non-transitory storage medium that can retain stored contents even when power supply is interrupted. For example, a hard disk drive, a flash ROM, a removable USB memory, or the like can be used as the nonvolatile memory 72. The memory 72 stores an imaging control program for controlling imaging of front images and tomographic images by the OCT optical system 100. The memory 72 also stores a signal processing program that enables signal processing of the OCT signal obtained by the OCT control system 1. Further, the memory 72 stores various types of information related to imaging such as tomographic images (OCT data), three-dimensional tomographic images (three-dimensional OCT data), frontal fundus images, and information on imaging positions of tomographic images in the scanning line. Various operation instructions by the examiner are input to the operation unit 76.

  The operation unit 76 outputs a signal corresponding to the input operation instruction to the control unit 70. For the operation unit 76, for example, at least one of a mouse, a joystick, a keyboard, a touch panel, and the like may be used.

  The display unit 75 may be a display mounted on the apparatus main body or a display connected to the main body. A display of a personal computer (hereinafter referred to as “PC”) may be used. A plurality of displays may be used in combination. The display unit 75 may be a touch panel. When the display unit 75 is a touch panel, the display unit 75 functions as an operation unit. Various images including a tomographic image and a front image captured by the OCT optical system 100 are displayed on the display unit 75.

<Shooting motion contrast images>
Hereinafter, an operation method and a control operation of the apparatus 10 when taking a motion contrast image will be described with reference to FIG. The control unit 70 includes, for example, a processor (for example, a CPU) that performs various control processes and a storage medium that stores a program. The processor executes processing described below according to the program. In addition, in the following description, although the number for identifying each step of control is provided, the order of the provided number and the order of actual control do not necessarily correspond.

  First, the examiner instructs the subject to gaze at the fixation target of the fixation target projection unit 300, and then displays an anterior ocular segment observation image captured by an anterior ocular segment observation camera (not shown) on the display unit 75. While looking, an alignment operation is performed using an operation unit 76 (for example, a joystick not shown) so that the measurement optical axis is at the center of the pupil of the eye to be examined.

(Step 1: OCT imaging)
The control unit 70 acquires OCT signals of at least two frames having different times at the same position. For example, the control unit 70 controls driving of the optical scanner 108 to scan the measurement light on the fundus. For example, the measurement light is scanned in the x direction along the first scanning line S1 shown in FIG. Note that scanning the measurement light in the transverse direction (for example, the x direction) is called “B-scan”. Hereinafter, an OCT signal of one frame will be described as an OCT signal obtained by one B scan. The control unit 70 acquires the OCT signal detected by the detector 120 during scanning. In FIG. 4, the direction of the z axis is the direction of the optical axis of the measurement light. The x-axis direction is a direction perpendicular to the z-axis and left and right. The y-axis direction is perpendicular to the z-axis and up and down.

  When the first scan is completed, the control unit 70 performs the second scan at the same position as the first scan. For example, the control unit 70 scans the measurement light along the scan line S1 shown in FIG. 4, and then scans the measurement light along the scan line S1 again. The controller 70 acquires the OCT signal detected by the detector 120 during the second scan. Accordingly, the control unit 70 can acquire two frames of OCT signals at different times at the same position. In the present embodiment, scanning at the same position is repeated four times, and four consecutive frames of OCT signals with different times are acquired. For example, the control unit 70 repeats scanning on the scanning line S1 four times to obtain a 4-frame OCT signal. However, it is only necessary to acquire OCT signals of at least two frames that are not limited to four frames but differ in time.

  Note that if a signal at the same position at different times can be acquired by one scan, the second scan may not be performed. For example, when scanning two measuring beams whose optical axes are shifted by a predetermined interval at a time, it is not necessary to scan a plurality of times. It is sufficient if OCT signals having different times at the same position in the subject can be acquired.

  In addition, the control part 70 acquires the signal of the at least 2 frame from which time differs similarly in another position. As shown in FIG. 4, it is assumed that the first scanning line S1 is, for example, y = y1. The second scanning line S2 is assumed to be y = y2, for example. When the acquisition of signals with different times is completed in the first scanning line S1, the control unit 70 continues to acquire signals of at least two frames with different times in the second scanning line S2.

  As shown in FIG. 4, the control unit 70 performs raster scanning of the measurement light (raster scanning), and obtains OCT signals of at least two frames having different times in each scanning line. Thereby, three-dimensional information inside the fundus can be acquired.

  The raster scan is a pattern in which the measurement light scans the fundus in a rectangular shape. The raster scan is used as, for example, a front (En-face) image scan.

(Step 2: Acquisition of complex OCT signal group)
Subsequently, the control unit 70 processes the OCT signal acquired by the OCT optical system 100 to acquire a complex OCT signal. For example, the control unit 70 performs a Fourier transform on the OCT signal (interference signal) acquired in step 1. Here, the nth (x, z) position signal in the N frame is represented by An (x, z). The control unit 70 obtains a complex OCT signal An (x, z) by Fourier transform. The complex OCT signal An (x, z) includes a real component and an imaginary component.

(Step 3: Acquisition of tomographic image group)
Next, the control unit 70 processes the complex OCT signal acquired in step 2 to acquire a vascular tomographic group (motion contrast image group). As a method of processing the complex OCT signal, for example, a method of calculating a phase difference of the complex OCT signal, a method of calculating a vector difference of the complex OCT signal, a method of multiplying the phase difference and the vector difference of the complex OCT signal, and the like are considered. It is done. In this embodiment, a method for calculating a phase difference will be described as an example.

  First, the control unit 70 calculates a phase difference with respect to the complex OCT signal A (x, z) acquired at least two or more different times at the same position. The control unit 70 calculates a change in phase using, for example, Expression (1). In the present embodiment, for example, in order to perform measurement at four different times, T1 and T2, T2 and T3, and T3 and T4 are calculated three times in total, and three data are calculated. Note that An in the equation represents a signal acquired at time Tn, and * represents a complex conjugate.

  For example, the control unit 70 may average the signals of three frames and remove noise. Since the noise component is present randomly in each frame, it is smaller than the signal component by averaging.

  As described above, the control unit 70 obtains a profile in the depth direction related to the phase difference of the complex OCT signal, and obtains a functional OCT image of the subject by adding shading according to the size of the profile. The control unit 70 repeats the above processing for each scanning line, and generates a tomographic blood vessel image for each scanning line as shown in FIG. Thereby, the control unit 70 acquires a three-dimensional motion contrast image.

<Measurement of blood flow>
A method of obtaining the blood flow velocity using the motion contrast image photographed as described above will be described with reference to FIG. In this embodiment, the absolute velocity of the blood flow is obtained using the three-dimensional structure of the blood vessel obtained from the three-dimensional motion contrast image. In obtaining the absolute velocity of blood flow, the control unit 70 first associates the motion contrast image with an observation image (for example, an SLO image, an infrared fundus image, etc.) taken by the observation optical system 200 (step S110). 2-1). Note that the observation image associated with the motion contrast image may be an observation image taken when the OCT optical system 100 acquires the OCT signal, or may be an observation image taken after the motion trust image is generated. .

  For example, as shown in FIG. 7, the control unit 70 associates the coordinates in the XY direction in the two-dimensional observation image D2 with the coordinates in the XY direction in the three-dimensional motion contrast image D1. Examples of the association method include a method of using the lighting position of the fixation lamp and a method of using the position of the blood vessel. When using the lighting position of the fixation lamp, for example, from the relationship between the lighting position of the fixation lamp when the motion contrast image D1 is acquired and the lighting position of the fixation lamp when the observation image D2 is acquired, the motion The contrast image D1 and the observation image D2 may be associated with each other. When using the position of the blood vessel, for example, the position of the blood vessel shown in the observation image D2 and the position of the blood vessel shown in the motion contrast image D1 are detected by image processing, and both are matched so that the blood vessel positions match. May be attached.

  Note that the control unit 70 may associate pixel positions of the motion contrast image D1 and the observation image D2, for example. For example, if the coordinates of a pixel in the motion contrast image D1 are (x1, y1), the corresponding coordinates (x2, y2) of the pixel in the observation image D2 may be associated.

  As described above, the control unit 70 may associate the observation image D2 with the motion contrast image D1, and use the correspondence information acquired thereby to obtain the absolute velocity of the blood flow. Note that the control unit 70 may store the correspondence information in the memory 72.

  Next, as shown in FIG. 8, the control unit 70 displays the motion contrast image D1 acquired by the above-described method on the screen of the display unit 75 (step 2-2). The motion contrast image D1 displayed on the display unit 75 may be, for example, a three-dimensional image or a two-dimensional image. In the example of FIG. 8, a two-dimensional image obtained by adding three-dimensional data in a certain depth region is displayed. In this case, the depth area to be added may be arbitrarily set.

  The examiner confirms the motion contrast image D1 and designates a blood vessel for measuring blood flow. For example, the examiner may specify a blood vessel by inputting the position of the motion contrast image D1 by clicking or touching a pointing device (for example, a mouse, a touch panel, etc.) of the operation unit 76. In the example of FIG. 8, the control unit 70 displays a pointer 76 a that can be moved according to the operation of the operation unit 76. For example, the examiner moves the pointer 76a displayed on the screen over a desired blood vessel and performs an operation such as clicking to designate the blood vessel. In this case, the pointer 76a is used for designating an arbitrary position on the display unit 75. In the following description, the blood vessel designated by the examiner is referred to as a designated blood vessel.

  The control unit 70 accepts an examiner's instruction (step 2-3). For example, the control unit 70 receives an examiner's instruction based on a signal output from the operation unit 76. For example, the control unit 70 may acquire a position (designated position) designated by the examiner using the pointing device of the operation unit 76.

  The control unit 70 acquires to which position of the observation image D2 the designated position designated on the motion contrast image corresponds (step 2-4). For example, the control unit 70 acquires a corresponding position on the observation image corresponding to the xy coordinates of the designated position on the motion contrast image based on the correspondence information between the observation image D2 and the motion contrast image D1 stored in the memory 72. To do. For example, the control unit 70 acquires the xy coordinates on the observation image corresponding to the xy coordinates of the designated blood vessel from the correspondence information stored in the memory 72.

  When the corresponding position of the designated blood vessel on the observation image is obtained, the control unit 70 sets the corresponding position as a tracking position (step 2-5) and starts scanning (step 2-6). The control unit 70 performs scanning a plurality of times at time intervals while tracking so that the corresponding position can always be scanned. For example, the control unit 70 may take an observation image at any time in parallel with the scan of the measurement light, and correct the scan position according to the positional deviation of the fundus that appears in the updated observation image.

  More specifically, the control unit 70 compares the still image of the observation image D2 used for the association with the motion contrast image D1 with the current observation image D2, and determines the position displacement direction and the amount of displacement. It is detected (calculated) by processing. For example, the control unit 70 uses the still image data of the observation image D2 at the time of association with the motion contrast image D1 as a reference image, and sets the position shift direction and the amount of position shift between the reference image and the observation image acquired in real time. calculate. Thereby, positional deviation information with respect to the still image is obtained.

  When the position shift direction and the position shift amount are detected as described above, the control unit 70 appropriately controls the two galvanometer mirrors of the optical scanner 108 so that the scan position shift is corrected. Thereby, the scanning position is corrected. As described above, even when the eye to be examined is displaced, the scanning position is corrected, and the control unit 70 can always acquire a plurality of OCT signals having different times at the same scanning position.

  The control unit 70 calculates the absolute velocity of the blood flow by using the three-dimensional OCT signal acquired in Step 2-6 and the three-dimensional structure of the blood vessel obtained from the three-dimensional motion contrast image (Step 2). -7). For example, the control unit 70 obtains a Doppler phase shift from a plurality of OCT signals. Then, the control unit 70 may calculate the absolute velocity of the blood flow from the obtained phase difference and the blood flow direction obtained from the three-dimensional structure of the blood vessel.

  As a method for obtaining the direction of blood flow from the three-dimensional structure of the blood vessel obtained from the motion contrast image D1, for example, there is a method of thinning the three-dimensional structure of the blood vessel. For example, as shown in FIG. 9, a three-dimensional blood vessel structure K can be represented by a single line L0 by thinning processing. For example, the control unit 70 may consider the inclination of the line L0 with respect to the measurement light scanned on the scan line SL as the direction of blood flow, and calculate the absolute velocity of the blood flow from the above-described phase difference.

<Calculation of blood flow velocity>
The absolute velocity of blood flow will be described. The component v _{z in} the optical axis direction of the absolute velocity v of the blood flow can be expressed by the following equation (2) using the angle α formed by the measurement light and the blood vessel.

Here, the component v _z can be expressed by the following equation (3) using the phase difference ΔΦ _Doppler (−π to π), the refractive index n of the vascular tissue, the center wave number k, and the time interval T.

  Using the above two equations, the absolute velocity v of the blood flow is obtained from the phase difference as shown in the following equation (4).

  As described above, in the present embodiment, the control unit 70 measures the blood flow of the eye to be examined using the three-dimensional motion contrast image D1 and a plurality of temporally different OCT signals related to the same scanning position. Since the control unit 70 can acquire the blood flow direction from the three-dimensional structure of the blood vessel obtained from the three-dimensional motion contrast image D1, it can measure the absolute blood flow velocity of the eye to be examined from the Doppler shift. Thereby, the control part 70 can acquire the information useful for the diagnosis etc. of a to-be-examined eye, for example by comparing a blood-flow velocity regarding a some subject.

  In the present embodiment, the control unit 70 uses the blood flow direction obtained from the three-dimensional motion contrast image D1 acquired in advance to calculate the absolute velocity of the blood flow. For this reason, if the OCT optical system continuously obtains a plurality of temporally different OCT signals at the same position of the eye to be examined, the control unit 70 performs dynamic blood flow considering the influence of the pulsation of the subject. Can be obtained (see FIG. 10). In this way, the control unit 70 can provide information that can be used to find a disease such as arteriosclerosis by acquiring a temporal change in blood flow velocity.

  Further, in the present embodiment, the control unit 70 associates the position of the blood vessel confirmed in the motion contrast image D1 with the observation image D2, and performs tracking based on the correspondence information. For example, since the motion contrast image D1 requires time to generate an image, it is difficult to acquire shift information for following the fine movement of the eye to be examined. On the other hand, the observation image D2 is suitable for acquiring deviation information for following the fine movement of the eye to be inspected because the time until the image is acquired is shorter than that of the motion contrast image. Like the control unit 70 of the present embodiment, by tracking the position of a fine blood vessel that is difficult to confirm in the observation image D2 from the motion contrast image, tracking can be performed even for a fine blood vessel that is difficult to confirm in the observation image D2. . This makes it easy for the control unit 70 to continuously acquire a plurality of OCT signals having different times at the same position, and can appropriately determine the absolute velocity of the subject's dynamic blood flow.

  The control unit 70 may automatically set the scan width when scanning the blood vessel designated by the examiner according to the diameter of the blood vessel obtained from the motion contrast image. Of course, the examiner may set it manually.

  The control unit 70 may set the time interval T when scanning the blood vessel designated by the examiner according to the diameter of the blood vessel obtained from the motion contrast image. Of course, the examiner may set it manually.

  Note that the scan direction when scanning the blood vessel designated by the examiner may be perpendicular to the blood flow direction. For example, the control unit 70 may calculate a direction perpendicular to the blood flow direction of the designated blood vessel in En-face (direction perpendicular to the measurement light), and scan in this direction. The blood flow direction of the blood vessel may be obtained by thinning the three-dimensional structure of the blood vessel as described above. For thinning, for example, morphology processing, distance conversion processing, or existing algorithms such as Hilditch and Deutsch may be used.

  In this way, the control unit 70 performs the scan perpendicular to the blood flow direction, so that it is not necessary to consider the scan angle with respect to the blood flow direction when calculating the blood flow, thereby simplifying the calculation process. Can do. For example, the control unit 70 may automatically set the radial direction of the designated blood vessel as the scan direction. Of course, the control unit 70 may set a scan line based on an operation signal output from the operation unit 76 in accordance with the operation of the examiner.

  In the motion contrast image as shown in FIG. 8, every time the examiner designates a new blood vessel, the control unit 70 performs scanning while tracking the designated blood vessel as described above to obtain the blood flow velocity. May be.

<Position detection method>
Note that various image processing methods (methods using various correlation functions, methods using Fourier transforms, and methods based on feature point matching) are used as methods for detecting a positional deviation between two observation images during tracking. It is possible to use.

  For example, when a predetermined reference image (for example, a past front image) or a target image (current front image) is displaced by one pixel, the reference image and the target image are compared, and the two data are most consistent (correlation is It is conceivable to detect a positional deviation between the two data (when it is the highest). Further, a method of extracting a common feature point from a predetermined reference image and target image and detecting a positional shift of the extracted feature point is conceivable.

  Further, a phase-only correlation function may be used as a function for obtaining a positional deviation between two images. In this case, first, each image is Fourier transformed to obtain the phase and amplitude of each frequency component. The obtained amplitude component is normalized to a magnitude of 1 for each frequency component. Next, after calculating the phase difference for each frequency between the two images, inverse Fourier transform is applied to them.

  Here, if there is no position shift between the two images, only the cosine wave is added, and a peak appears at the origin position (0, 0). Further, when there is a positional deviation, a peak appears at a position corresponding to the positional deviation. Therefore, a position shift between two images can be obtained by obtaining a peak detection position. According to this method, the positional deviation of the front image can be detected with high accuracy and in a short time.

Note that, as described in the above equation (2), the phase difference ΔΦ _Doppler is in the range of −π to π by the arctangent calculation. Therefore, when the time interval between scans (time interval T) is long, the phase difference ΔΦ _Doppler exceeds the range of −π to π when the blood flow is fast. For example, as shown in FIG. The direction phase difference ΔΦ _Doppler profile becomes discontinuous. In such a case, it is difficult to diagnose the eye to be examined including speed measurement from the detected profile. Therefore, as in the present embodiment, for example, the control unit 70 searches for an appropriate time interval T and performs scanning.

Hereinafter, a method of performing scanning at an appropriate time interval T so that the phase difference ΔΦ _Doppler does not exceed the range of _−π to π in the process of acquiring the scan signal in Step 2-6 will be described. In the following description, the fact that the phase difference ΔΦ _Doppler exceeds the range of _−π to π and a discontinuous point occurs is expressed as “wrapped”.

As a method for performing scanning at an appropriate interval, for example, the control unit 70 may perform scanning while sequentially changing the time interval T for each scanning. In the following description, the control unit 70 performs scanning while sequentially changing the time interval T from a long interval to a short interval. In this case, the control unit 70 sequentially calculates the phase difference ΔΦ _Doppler with different time intervals T using the acquired plurality of OCT signals, and determines whether or not the calculation result of the phase difference ΔΦ _Doppler is wrapped. . For example, the control unit 70 continues the scan while fixing the time interval T when it is determined that the phase difference ΔΦ _Doppler is no longer wrapped, or the time interval T shorter than that.

Examples of a method for determining whether or not the phase difference ΔΦ _Doppler is wrapped include a method for determining based on the magnitude of the change in the phase difference ΔΦ _Doppler between adjacent pixels. In this case, the control unit 70 may apply an edge detection filter (for example, differential processing such as a Laplacian filter) to the phase difference ΔΦ _Doppler acquired from the plurality of OCT signals. For example, when the edge detection filter is applied to the profile of the wrapped phase difference ΔΦ _Doppler as shown in FIG. 11A, the intensity of the wrapped position is shown in FIG. 11B. Is locally increased. On the other hand, as shown in FIG. 11C, when the edge detection filter is applied to the profile of the unwrapped phase difference ΔΦ _Doppler , the intensity locally increases as shown in FIG. There is nothing. Therefore, for example, the control unit 70 may determine that the wrapping is stopped when the average value of the profile after application of the edge detection filter is equal to or less than a predetermined value. Of course, when the maximum value after application of the edge detection filter is equal to or less than a predetermined value, it may be determined that no wrapping has occurred.

As described above, the control unit 70 can acquire the unwrapped phase difference ΔΦ _Doppler regardless of the difference in blood flow speed by appropriately setting the time interval T. By acquiring the unwrapped phase difference ΔΦ _Doppler , the laminar flow state of the blood flow can be acquired satisfactorily and used for diagnosis of the eye to be examined. In addition, the examiner can save time and labor for setting the time interval T himself.

Note that the control unit 70 may search for a time interval T in which the signal intensity of the phase difference ΔΦ _Doppler is as large as possible. For example, if the control unit 70 determines that the phase difference ΔΦ _Doppler is no longer wrapped, the control unit 70 gradually increases the time interval T so that the maximum value of the profile of the phase difference ΔΦ _Doppler is as large as possible within the range of −π to _π. You may change long and search for the suitable time interval T. FIG.

In the above description, the control unit 70 sequentially changes the time interval T from a long interval to a short interval. When the time interval T is large, the phase difference ΔΦ _Doppler of the Doppler signal due to blood flow becomes large, and there is a high possibility of being wrapped. As described above, when the time interval T is gradually shortened from the lap state intentionally and the lap state is not set, there is a high possibility that a signal having a high intensity can be acquired in the range of −π to π.

Of course, the control unit 70 may change the time interval T from a short interval to a long interval. When the time interval T is short, the phase difference ΔΦ _Doppler of the Doppler signal due to blood flow is small, and the phase difference ΔΦ _Doppler that is not wrapped can be quickly acquired. However, if the time interval T is short, as shown in FIGS. 11 (e) and 11 (f), the signal intensity becomes small and the signal may be buried in the noise floor. You may search for the time interval T as long as possible.

  In the above example, the time interval T is gradually changed to be longer or shorter, but is not limited thereto. For example, the control unit 70 may alternately change the time interval T between a long interval and a short interval, or may randomly change the interval of the time interval T. It should be noted that whether the time interval T is shortened or lengthened may be set by an operation signal output from the operation unit by the examiner's operation.

  Note that the control unit 70 obtains the absolute velocity of the blood flow at a certain time using a plurality of OCT signals acquired to generate the three-dimensional motion contrast image D1, and based on the magnitude, The interval T may be set. Thereafter, as described above, an appropriate time interval T may be obtained by sequentially changing the time interval T. Thus, by setting the time interval T from the absolute velocity of the blood flow at the time when the three-dimensional motion contrast image D1 is acquired, the time required to set the appropriate time interval T can be shortened.

  The magnitude of the blood flow velocity can be estimated to some extent according to the thickness and type of blood vessel (for example, an artery or vein). Therefore, the control unit 70 may set the time interval T based on the blood flow velocity estimated from the thickness and type of the designated blood vessel. In this case, for example, the control unit 70 acquires a correspondence relationship between the thickness and type of the blood vessel and the magnitude of the blood flow velocity from the past measurement data, and stores it in the memory 72 as a correspondence table. Then, the control unit 70 compares at least one of the size of the designated blood vessel and the type of blood vessel estimated from the depth of the retina where the blood vessel exists with the correspondence table stored in the memory 72 and designates the designated blood vessel. The blood flow velocity may be estimated.

For example, the control unit 70 acquires a plurality of OCT signals at a plurality of different time intervals T, and among the ΔΦ _Doppler calculated from the obtained plurality of OCT signals, the unwrapped one is used as a blood flow velocity. You may use for calculation of.

In the above description, for example, the control unit 70 changes the time interval T, but is not limited thereto. For example, the control unit 70 performs scanning at a constant time interval T, and selects a combination of OCT signals in which the calculated phase difference ΔΦ _Doppler is not wrapped from among a plurality of obtained OCT signals, thereby calculating the absolute blood flow. The speed may be calculated. For example, the control unit 70 may perform scanning at a short time interval T, and calculate ΔΦ _Doppler by thinning data from a plurality of acquired OCT signals. For example, when a scan is performed at a time interval T of 0.5 ms, data is thinned out from a plurality of acquired OCT signals, and the time interval T (for example, 1.0 ms, 1.. ΔΦ _Doppler may be calculated from the OCT signal acquired in 5 ms, 2.0 ms, etc. In this case, the control unit 70 may use, for example, an OCT signal acquired at each time interval T in which ΔΦ _Doppler is not wrapped for the calculation of the blood flow velocity, or a signal having a large maximum value. You may use for calculation of flow velocity. Furthermore, among the OCT signals acquired in each time interval T, a signal having a minimum ΔΦ _Doppler slope (for example, a differential value) may be used for calculating the blood flow velocity.

  In this way, an appropriate time interval T may be searched for by changing the time interval T in calculation without changing the time interval T for actually irradiating the measurement light.

DESCRIPTION OF SYMBOLS 1 Optical coherence tomography device 70 Control part 72 Memory 75 Monitor 76 Operation part 100 Interference optical system (OCT optical system)
108 optical scanner 120 detector 200 front observation optical system 300 fixation target projection unit

Claims (9)

An optical coherence tomography apparatus comprising an OCT optical system for obtaining an OCT signal by measurement light scanned on a subject by scanning means and reference light corresponding to the measurement light,
Acquiring motion contrasts of a plurality of OCT signals acquired at a first time interval with respect to the same position on the subject;
When the phase difference profile between the plurality of OCT signals that are the basis of the motion contrast is discontinuous, the plurality of OCTs acquired at a second time interval different from the first time interval. An acquisition means for acquiring the motion contrast of the signal;
An optical coherence tomography apparatus comprising:   2. The apparatus according to claim 1, further comprising: a determination unit that detects an inclination of the phase difference profile acquired by the acquisition unit and determines whether the phase difference profile is continuous based on the detected inclination. Optical coherence tomography device.   3. The optical coherence tomography apparatus according to claim 1, wherein the second time interval is a time interval shorter than the first time interval.   The drive control means which controls the drive of the scanning means and changes the time interval of irradiation with respect to the same position when the profile of the phase difference is discontinuous is provided. Optical coherence tomography device.   The optical coherence tomography apparatus according to claim 4, wherein the drive control means changes the irradiation time interval for the same position to be shorter.   When the acquired phase difference profile is discontinuous, the acquisition means determines the first time interval different from the first time interval from the plurality of OCT signals acquired with a first time interval. 4. The light according to claim 1, wherein at least one set of OCT signals acquired with a time interval of 2 is selected, and a motion contrast of the selected set of OCT signals is acquired. Coherence tomography device. When the phase difference profile between the plurality of OCT signals that is the basis of the motion contrast is continuous,
The acquisition means acquires motion contrast of a plurality of OCT signals acquired at a second time interval longer than the first time interval in order to increase the signal-to-noise ratio of the motion contrast. The optical coherence tomography apparatus according to claim 1. An optical coherence tomography apparatus comprising an OCT optical system for obtaining an OCT signal by measurement light scanned on a subject by scanning means and reference light corresponding to the measurement light,
Acquisition means for acquiring motion contrast of a plurality of OCT signals acquired at a first time interval with respect to the same position on the subject;
Blood vessel information acquisition means for acquiring at least one of the diameter and type of the blood vessel based on the three-dimensional structure of the blood vessel of the subject,
When the phase difference profile between the plurality of OCT signals serving as the basis of the motion contrast is discontinuous, the acquisition unit is based on the diameter or type of the blood vessel acquired by the blood vessel information acquisition unit. Acquiring motion contrasts of a plurality of OCT signals acquired at a second time interval different from the first time interval, which is set in advance according to the acquired diameter or type of the blood vessel. An optical coherence tomography device. A control program used in an optical coherence tomography apparatus including an OCT optical system for acquiring an OCT signal based on measurement light scanned on a subject by scanning means and reference light corresponding to the measurement light,
Being executed by a processor of the optical coherence tomography device,
When a phase difference between a plurality of OCT signals acquired at a first time interval is acquired for the same position on the subject, and the acquired phase difference profile is discontinuous, the first time A phase difference acquisition step of acquiring phase differences of a plurality of OCT signals acquired at a second time interval different from the interval;
Is executed by the optical coherence tomography apparatus.