WO2017131004A1 - Dispositif de traitement de données d'image, procédé de traitement de données d'image, et programme de traitement de données d'image - Google Patents

Dispositif de traitement de données d'image, procédé de traitement de données d'image, et programme de traitement de données d'image Download PDF

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WO2017131004A1
WO2017131004A1 PCT/JP2017/002465 JP2017002465W WO2017131004A1 WO 2017131004 A1 WO2017131004 A1 WO 2017131004A1 JP 2017002465 W JP2017002465 W JP 2017002465W WO 2017131004 A1 WO2017131004 A1 WO 2017131004A1
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image data
data processing
displacement
test object
processing apparatus
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PCT/JP2017/002465
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English (en)
Japanese (ja)
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安野　嘉晃
和博 鈴木
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株式会社ニデック
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Publication of WO2017131004A1 publication Critical patent/WO2017131004A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F9/00—Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/008—Methods or devices for eye surgery using laser
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/20—Analysis of motion

Definitions

  • the present disclosure relates to an image data processing device, an image data processing method, and an image data processing program for processing image data of a test object.
  • the displacement measuring device disclosed in Patent Document 1 uses a correspondence relationship between a displacement amount of a minute region in the axial direction and the lateral direction of the imaging optical axis and attenuation of a correlation coefficient between a plurality of tomographic images. The amount of displacement of the minute region in the axial direction and the lateral direction is measured.
  • the measured displacement of the test object is treated as a vector field.
  • it is sometimes difficult to appropriately grasp for example, visualization, qualification, quantification, etc. regarding information regarding the displacement of each part in the imaging region.
  • a typical object of the present disclosure is to provide an image data processing device, an image data processing method, and an image data processing program capable of appropriately grasping information related to the displacement of a test object.
  • An image data processing apparatus includes a control unit that controls processing of image data, and the control unit includes a plurality of times acquired at different times with respect to a target imaging position of a test object.
  • a vector field indicating the displacement of each of a plurality of parts in the imaging region is calculated from the image data, and a potential field is calculated by performing Helmholtz decomposition on the vector field.
  • An image data processing method provided by an exemplary embodiment of the present disclosure is an image data processing method executed by an image data processing apparatus, and a plurality of images acquired at different times with respect to a target imaging position of a test object. From the data, a vector field calculation step for calculating a vector field indicating the displacement of each of a plurality of parts in the imaging region, a potential field calculation step for calculating a potential field by performing Helmholtz decomposition on the vector field, including.
  • An image data processing program provided by an exemplary embodiment of the present disclosure is an image data processing program executed in an image data processing device, and a processor of the image data processing device executes the image data processing program
  • a vector field calculating step for calculating a vector field indicating a displacement of each of a plurality of parts in the imaging region from a plurality of image data acquired at different times with respect to the target imaging position of the test object
  • a potential field calculation step of calculating a potential field by performing Helmholtz decomposition on the image data processing apparatus is executed.
  • the image data processing device According to the image data processing device, the image data processing method, and the image data processing program according to the present disclosure, information regarding the displacement of the test object can be appropriately grasped.
  • the control unit of the image data processing device uses a plurality of pieces of image data acquired at different times with respect to the target imaging position of the object to be detected in the imaging area.
  • a vector field indicating the displacement of each of the plurality of parts at is calculated.
  • the control unit calculates the potential field by performing Helmholtz decomposition on the vector field. According to the calculated potential field, at least one of a field without rotation and a field without divergence is grasped. Accordingly, at least one of visualization, qualification, quantification, and the like of information regarding the displacement of each part in the imaging region is appropriately performed.
  • the control unit may calculate a scalar potential field that is a potential field indicating a distribution of energy that causes displacement in the test object by performing Helmholtz decomposition on the vector field. According to the scalar potential field, the distribution of energy causing the displacement appears clearly. Therefore, information regarding the displacement of the test object can be grasped more appropriately.
  • control unit may calculate a vector potential field without divergence by performing Helmholtz decomposition on the vector field. In this case, information regarding rotation in each part is appropriately grasped.
  • the control unit may create image data that displays a distribution of energy that causes displacement in the test object based on the calculated scalar potential field.
  • the image data processing apparatus can make the user easily and appropriately grasp information regarding the displacement of the test object.
  • the information regarding the displacement is appropriately grasped by the user without performing a process such as separately creating an image according to the direction of the displacement.
  • the plurality of image data from which the vector field is calculated may be image data (OCT image data) acquired using optical coherence tomography (OCT).
  • OCT image data image data acquired using optical coherence tomography
  • the image data processing apparatus can appropriately grasp information relating to the internal displacement of the test object.
  • the vector field may be calculated from image data other than OCT image data.
  • an optical scanner that scans measurement light two-dimensionally on the test object, and a light receiving element that receives reflected light from the test object through a confocal aperture disposed at a position substantially conjugate with the test object.
  • Image data acquired by a photographing apparatus (Scanning Laser Optoscope: SLO) may be used.
  • Image data acquired by an imaging device (for example, a fundus camera) that images a two-dimensional region on the surface of the test object may be used. In these cases, information regarding the displacement of the surface of the test object is appropriately grasped.
  • the control unit calculates a two-dimensional vector field in the direction (axial direction) along the optical axis of the imaging light emitted from the OCT apparatus and in the lateral direction intersecting the axial direction, and generates a potential field from the two-dimensional vector field. May be calculated. However, even when a one-dimensional vector field or a three-dimensional vector field is used, at least a part of the technique exemplified in this embodiment can be applied.
  • the control unit may analyze the displacement generated in the test object from the potential field calculated by Helmholtz decomposition.
  • the displacement is appropriately analyzed without performing a process of analyzing the displacement separately according to the direction of the displacement.
  • Various methods can be adopted as the analysis method.
  • the analysis may be a qualitative analysis or a quantitative analysis.
  • the image data processing apparatus may execute both an image data creation process for displaying the energy distribution and an analysis process for displacement generated in the test object.
  • the image data processing apparatus does not need to execute both the image data creation process and the displacement analysis process.
  • the device for calculating the potential field and the device for executing the image data creation process or the displacement analysis process may be different devices.
  • the PC may create image data based on the potential field calculated by the OCT apparatus.
  • the plurality of image data from which the vector field is calculated may include image data acquired regarding the position of the test object irradiated with the treatment light.
  • the image data processing apparatus can appropriately grasp information related to the displacement of the test object irradiated with the treatment light by calculating the potential field.
  • control unit may determine whether or not the energy of the treatment light applied to the test object is appropriate by analyzing the displacement generated in the test object from the potential field.
  • the image data processing apparatus determines the suitability of the energy of the treatment light from the displacement of the test object generated by the irradiation of the treatment light while suppressing various influences such as individual differences in the living body. Can do.
  • At least a part of the technique exemplified in this embodiment can be adopted.
  • some kind of energy for example, ultrasonic energy, electromagnetic wave energy, wind pressure energy, etc.
  • the properties of the test object for example, hardness, internal pressure, etc.
  • At least a part of the technique exemplified in this embodiment can be applied.
  • at least a part of the technique exemplified in this embodiment can be applied to processing image data of a test object other than the eye.
  • control unit may execute a process of returning the potential field calculated by performing Helmholtz decomposition on the vector field to the vector field again.
  • control unit may calculate the vector field from which the rotation component and the noise are removed by differentiating the scalar potential field calculated by Helmholtz decomposition with respect to the vector field.
  • the finally calculated vector field makes it easier to quantify the displacement.
  • control unit may perform a process of returning to the vector field after performing a smoothing process or the like on the potential field.
  • the image data processing apparatus exemplified in the present embodiment is an optical coherence tomography apparatus (OCT apparatus) that acquires internal information (for example, a tomographic image or the like) of a test object using interference light in which measurement light and reference light are combined.
  • OCT apparatus optical coherence tomography apparatus
  • another device may perform image data processing as an image data processing device.
  • the image data processing apparatus may be a personal computer (hereinafter referred to as “PC”), a server, or a portable terminal connected to the OCT apparatus.
  • the image data processing apparatus may be a PC or the like that can acquire image data captured by an imaging apparatus such as an OCT apparatus via wired communication, wireless communication, or a removable memory.
  • the image data processing device may be a treatment device capable of performing both imaging of the test object and treatment of the test object with therapeutic light.
  • a plurality of devices may function as an image data processing apparatus.
  • the OCT apparatus may execute processing for calculating a vector field
  • the PC may execute processing for calculating a potential field from the vector field.
  • both the OCT apparatus and the PC function as an image data processing apparatus.
  • the image data processing apparatus 1 acquires a signal (for example, an OCT signal) by the OCT optical system (interference optical system) 100, and acquires image data from the acquired signal. That is, the image data processing apparatus 1 of the present embodiment has a function as an OCT apparatus that acquires internal information of a test object. The image data processing apparatus 1 calculates a vector field and a potential field by processing image data. Further, the image data processing apparatus 1 of the present embodiment also has a function as a treatment apparatus that irradiates treatment light (for example, treatment laser light) to a test object that is a living body (eye E in the present embodiment).
  • treatment light for example, treatment laser light
  • the image data processing apparatus 1 includes a control unit 10, a display unit 21, an operation unit 22, an OCT optical system 100, a front observation optical system 200, and a treatment light irradiation optical system 300.
  • the control unit 10 controls processing (for example, various data processing and operation processing) of the image data processing apparatus 1.
  • the control unit 10 includes a CPU (processor) 11, a ROM 12, a RAM 13, and a non-volatile memory (NVM) 14.
  • the CPU 11 manages various controls in the image data processing apparatus 1.
  • the ROM 12 stores various programs, initial values, and the like.
  • the RAM 13 temporarily stores various information.
  • the nonvolatile memory 14 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, and a removable USB memory may be used as the nonvolatile memory 14.
  • an image data processing program for executing image data processing described later is stored in the nonvolatile memory 14.
  • an integrated image data processing apparatus 1 in which the OCT optical system 100, the treatment light irradiation optical system 300, the control unit 10, and the like are incorporated in one housing is illustrated.
  • the image data processing apparatus 1 may include a plurality of apparatuses having different housings.
  • the image data processing apparatus 1 may include an OCT apparatus incorporating the OCT optical system 100 and a PC connected to the OCT apparatus by wire or wirelessly.
  • both the control unit included in the OCT apparatus and the control unit of the PC may function as the control unit 10 of the image data processing apparatus 1.
  • the control unit 10 may include a plurality of processors.
  • a commercially available PC may be used as a part of the image data processing apparatus 1.
  • at least a part of the image data processing program can be installed in a commercially available PC.
  • a treatment apparatus including the treatment light irradiation optical system 300 may be used separately from the image data processing apparatus.
  • the display unit 21 may be a display mounted on the apparatus main body, or may be a display separate from the apparatus main body.
  • the operation unit 22 outputs a signal corresponding to the input operation instruction to the control unit 10.
  • the operation unit 22 for example, at least one of a mouse, a joystick, a keyboard, a touch panel, and the like can be used.
  • the OCT optical system 100 has a configuration of a so-called optical tomography interferometer (OCT: Optical coherence tomography), and acquires internal information (for example, image data of a tomographic image) of a test object (in this embodiment, eye E). Used for.
  • OCT optical system 100 of this embodiment divides the light emitted from the measurement light source 102 into measurement light (sample light) and reference light by a light splitter (for example, a coupler) 104.
  • the OCT optical system 100 guides the measurement light to the test object (for example, 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 a detector (for example, a light receiving element) 120 to receive interference light obtained by combining reference light and measurement light reflected by a test object.
  • the detector 120 detects an interference signal between the measurement light and the reference light.
  • the spectral intensity (spectral interference signal) of the interference light is detected by the detector 120, and a complex OCT signal is obtained by Fourier transform on the spectral intensity data.
  • a depth profile (A scan signal) in a predetermined range is acquired by calculating the absolute value of the amplitude in the complex OCT signal.
  • OCT image data (tomographic image data) is acquired by arranging the depth profiles at each scanning position of the measurement light scanned by the optical scanner 108.
  • the control unit 10 may acquire the three-dimensional OCT image data (three-dimensional tomographic image data) by scanning the measurement light in the two-dimensional direction on the tissue.
  • tissue from the axial direction (front direction) along the optical axis of measurement light may be acquired from three-dimensional OCT image data.
  • SD-OCT Spectral-domain-OCT
  • SS-OCT Swept-source-OCT
  • TD-OCT Time-domain-OCT
  • SD-OCT a low coherent light source (broadband light source) is used as the measurement light source 102, and the interference light is split into frequency components (each wavelength component) in the vicinity of the detector 120 in the optical path of the interference light.
  • a spectroscopic optical system spectrometer
  • SS-OCT for example, as the measurement light source 102, a wavelength swept light source that changes the emission wavelength at high speed in time is used.
  • the light emitted from the measurement light source 102 is divided into a measurement light beam and a reference light beam by the coupler 104.
  • the measurement light is emitted into the air after passing through the optical fiber.
  • the measurement light emitted into the air is condensed on the test object via the optical scanner 108 of the measurement optical system 106 or the like.
  • the measurement light reflected by the test object is returned to the optical fiber through the same optical path.
  • the optical scanner 108 scans the measurement light in the two-dimensional direction (XY direction) on the tissue.
  • the optical scanner 108 of this embodiment is disposed at a position substantially conjugate with the pupil of the eye E.
  • the optical scanner 108 of the present embodiment includes two galvanometer mirrors.
  • the reflection angle of the galvanometer mirror is arbitrarily adjusted by the drive mechanism 50.
  • the configuration of the optical scanner 108 can be changed.
  • a polygon mirror, a resonant scanner, an acoustooptic device (AOM), or the like may be employed for the optical scanner 108.
  • the reference optical system 110 generates reference light that is combined with the measurement light reflected by the test object.
  • the reference optical system 110 may be a Michelson type or a Mach-Zehnder type.
  • the reference optical system 110 of the present embodiment reflects light incident from the coupler 104 by a reflection optical system (for example, a reference mirror), thereby returning the light to the coupler 104 again and guiding it to the detector 120.
  • the configuration of the reference optical system 110 can also be changed.
  • the reference optical system 110 may transmit the light incident from the coupler 104 to the detector 120 without reflecting the light.
  • the reference optical system 110 can change the optical path length difference between the measurement light and the reference light by moving the optical member in the optical path. In this embodiment, the optical path length difference is changed by moving the reference mirror in the optical axis direction. Note that a configuration for changing the optical path length difference may be provided in the optical path of the measurement optical system 106.
  • the front observation optical system 200 acquires front image data of the test object.
  • the front image data may be data of a completed two-dimensional image, or may be signal data at each measurement point used for calculating the luminance of each pixel of the two-dimensional image.
  • the front observation optical system 200 of the present embodiment includes an optical scanner that scans measurement light (for example, infrared light) emitted from a light source in a two-dimensional direction (XY direction) on a test object, and a test target. And a light receiving element that receives the reflected light through a confocal aperture disposed at a substantially conjugate position with the object. That is, the front observation optical system 200 of this embodiment has a so-called scanning laser ophthalmoscope (SLO) configuration.
  • SLO scanning laser ophthalmoscope
  • the configuration of the front observation optical system 200 can also be changed.
  • the front observation optical system 200 may have a fundus camera type configuration.
  • the treatment light irradiation optical system 300 irradiates treatment light (treatment laser light in the present embodiment) for treating the living body toward the test object.
  • the treatment light may be used to coagulate the living body.
  • treatment light for example, a micro pulse laser
  • the therapeutic light irradiation optical system 300 may be provided with a therapeutic light optical scanner (not shown) for causing the therapeutic light to scan the subject.
  • the therapeutic light optical scanner and the optical scanner 108 of the OCT optical system 100 may be controlled in synchronization. The same optical scanner may be used.
  • the optical axis of the therapeutic light irradiation optical system 300 is coaxial with the optical axis of the OCT optical system 100 by an optical path coupling member (for example, a dichroic mirror).
  • an optical path coupling member for example, a dichroic mirror.
  • the image data processing executed by the image data processing apparatus 1 according to the present embodiment will be described with reference to FIGS.
  • the CPU 11 of the image data processing apparatus 1 executes the image data processing illustrated in FIG. 3 according to the image data processing program stored in the nonvolatile memory 14 or the like.
  • the test object is the retina of the eye E and information regarding the displacement of the retina irradiated with the treatment light is illustrated.
  • the CPU 11 acquires a plurality of image data at different times with respect to the target imaging position of the test object (S1). That is, the CPU 11 images the target imaging position of the test object a plurality of times at different times.
  • various processes are performed based on the OCT image data.
  • the CPU 11 acquires a plurality of OCT image data relating to the same position by scanning the measurement light a plurality of times at the same position of the test object (however, it may be displaced in time).
  • the target shooting positions from which a plurality of image data are acquired are not necessarily the same position.
  • the target shooting position may be set so that the shooting position is shifted by a minute distance for each shooting.
  • the CPU 11 may acquire data of an image captured by another OCT apparatus through communication or the like.
  • the CPU 11 calculates a vector field indicating the displacement of each of a plurality of parts (for example, each pixel included in the imaging region) in the imaging region based on the plurality of image data acquired in S1 (S2).
  • the vector field in this embodiment can also be said to be a map (displacement map) occupying the displacement of each part.
  • the CPU 11 uses the correspondence relationship between the displacement of each part in the axial direction and the horizontal direction (X direction) of the imaging optical axis and the attenuation of the correlation coefficient between a plurality of tomographic images, and thereby each part in the horizontal direction.
  • the displacement of is calculated.
  • the vector field of each part is calculated.
  • the method of calculating the vector field from a plurality of image data can be changed as appropriate.
  • the CPU 11 may calculate the vector field by calculating the displacements related to all of the plurality of directions (for example, both the axial direction and the horizontal direction) using the correlation coefficient.
  • the displacement of each part may be calculated by a technique such as speckle tracking. In the present embodiment, a two-dimensional vector field is calculated, but a one-dimensional or three-dimensional vector field may be calculated.
  • the CPU 11 calculates a correlation coefficient between two images (two B scans in the present embodiment).
  • the correlation coefficient is expressed by the following (Equation 1).
  • ⁇ x is the lateral displacement
  • ⁇ z is the axial displacement
  • C is a constant indicating the influence of the scattering process and the reproducibility of the scanning system
  • w is the lateral resolution defined by 1 / e2
  • ⁇ k is the light source.
  • the correlation coefficient decreases as a function of displacement, which follows a Gaussian function. That is, the correlation coefficient attenuates in a Gaussian function with respect to the displacement amount.
  • the CPU 11 of this embodiment sets one of the plurality of B scans as a reference B scan and the other B scan as a target B scan. For example, the CPU 11 can obtain a correlation coefficient between a reference B scan and a B scan obtained by shifting the reference B scan by digital processing.
  • the CPU 11 calculates a correlation coefficient ⁇ measurement (x, y) between the reference B scan and the target B scan using (Equation 1). Further, the CPU 11 calculates a Doppler phase shift ⁇ (x, y) between the reference B scan and the target B scan.
  • the Doppler phase shift ⁇ (x, y) is expressed by the following (Equation 2).
  • the CPU 11 calculates the axial displacement ⁇ z by unwrapping the phase shift using the route tracking method with priority order and converting the phase shift into the axial displacement using the following (Equation 3).
  • n is the refractive index of the sample
  • ⁇ is the center wavelength of the light source
  • ⁇ unwrapped is the unwrapped phase shift.
  • (Equation 1) when (Equation 1) is solved for the lateral displacement ⁇ x, it is expressed as (Equation 4) below.
  • the CPU 11 calculates the lateral displacement ⁇ x by substituting the correlation coefficient ⁇ measurement (x, y) calculated by the reference B scan and the target B scan and the calculated axial displacement ⁇ z into (Equation 4). .
  • a method of determining the lateral displacement direction (+ x direction or -x direction) can be selected as appropriate.
  • the CPU 11 may determine the direction of lateral displacement based on the increase or decrease of the correlation coefficient when two B scans are shifted in the + direction and the ⁇ direction by digital processing.
  • a two-dimensional vector field V on the XZ plane is calculated by the processing described above.
  • the details of the processing described above are described in, for example, JP-A-2015-169650.
  • the CPU 11 calculates a potential field by performing Helmholtz decomposition on the calculated vector field (S3).
  • Helmholtz decomposition An arbitrary vector field can be decomposed into a field without rotation and a field without divergence. This theorem is called Helmholtz theorem. Decomposing a vector field using Helmholtz's theorem is called Helmholtz's Decomposition.
  • the Helmholtz decomposition method itself has been used in fields such as electromagnetics.
  • V the vector field (displacement map)
  • ⁇ the scalar potential
  • A the vector potential
  • the displacement map V is represented by the sum of the gradient of the scalar potential and the rotation of the vector field, as shown in the following (Equation 5).
  • a scalar potential field without rotation is calculated from the vector field V as a potential field.
  • the scalar potential field in the present embodiment indicates a distribution of energy that causes displacement in the test object.
  • the CPU 11 creates an image displaying the energy distribution (hereinafter referred to as “displacement energy distribution image”) from the calculated scalar potential field.
  • the CPU 11 displays the created scalar potential field on the display unit 21 (S4).
  • FIG. 4 shows an example of a displacement energy distribution image (the lowest stage “Scalar potential” in FIG. 4).
  • a color indicating the distribution of energy that causes displacement is superimposed on a two-dimensional image (B-scan image).
  • FIG. 4 is a black-and-white image, it is difficult to understand, but the red part is a part with high energy and the blue part is a part with low energy. Accordingly, in the test object, displacement occurs from the red portion toward the blue portion. It is possible to change the mode of the displacement energy distribution image.
  • the magnitude of energy may be expressed not by color but by lightness or numerical values.
  • the uppermost “Intensity” in FIG. 4 is a captured two-dimensional image (B-scan image).
  • the CPU 11 analyzes the displacement generated in the test object (specifically, within the imaging range of the image of the test object) from the potential field calculated in S3 (S5).
  • the treatment light is irradiated for 50 ms on the test object.
  • the vector field and the potential field within the imaging range are calculated at timings of 12.5 ms, 50 ms, 50 ms, 100 ms, 200 ms, and 2000 ms after the start of treatment light irradiation.
  • the displacement generated in the test object is analyzed by comparing each of the potential fields at a plurality of different timings. For example, in the example shown in FIG.
  • the amount of displacement (expansion) generated from the center toward the outside gradually increases with the start of treatment light irradiation.
  • the amount of displacement (shrinkage) that occurs from the outside toward the center gradually increases. Therefore, in the example illustrated in FIG. 4, an analysis result indicating that displacement has occurred in the order of “irradiation start, expansion, irradiation end, contraction” is acquired.
  • the above-described displacement analysis method is merely an example. Therefore, it is also possible to change the displacement analysis method.
  • the displacement is analyzed by comparing each of the potential fields at a plurality of different timings.
  • the CPU 11 can also analyze the displacement from one potential field. In this case, for example, it is conceivable to analyze the displacement by analyzing the width of the region where the energy is equal to or greater than the threshold.
  • the CPU 11 analyzes the mode of displacement generated in the test object (specifically, the fact that displacement has occurred in the order of expansion and contraction).
  • the CPU 11 may classify the mode of displacement generated in the test object by another method. For example, the CPU 11 may determine from the potential field which one of a plurality of displacement modes including a displacement mode in the order of “expansion and contraction” and a displacement mode in the order of “shrinkage and expansion” has occurred.
  • the CPU 11 determines the suitability of the energy of the treatment light irradiated to the test object from the calculated potential field (S6). For example, there are cases where whether or not the energy of the treatment light is appropriate depends on whether the displacement occurs in the order of “expansion and contraction” and when the displacement occurs in the order of “contraction and expansion”. In this case, the CPU 11 may determine whether or not the energy of the treatment light is appropriate depending on whether or not the analyzed displacement mode is a displacement mode in the order of “expansion and contraction”.
  • the CPU 11 analyzes the width of the portion where the energy causing the displacement is equal to or greater than the threshold after a predetermined time has elapsed from the start of the treatment light irradiation, and determines whether the width is within a certain range. Thus, it may be determined whether or not the energy of the treatment light is appropriate.
  • the CPU 11 may determine the parameter of the treatment light emitted from the treatment light irradiation optical system 300 based on the determination result. For example, in the case where the trial light of the treatment light is performed on the test object, the CPU 11 may determine the parameter of the treatment light used for the actual treatment from the potential field of the site where the treatment light is trial-fired. . Further, when the treatment light is continuously irradiated to a plurality of parts, the CPU 11 may determine a parameter of the treatment light to be irradiated to the next part from the potential field of one part irradiated with the treatment light. . Further, the CPU 11 may appropriately determine the timing of ending the treatment light irradiation by calculating the potential field during the treatment light irradiation.
  • the vector field and the potential field are calculated from the OCT image data.
  • the vector field and the potential field may be calculated from image data other than the OCT image data.
  • the vector field and the potential field may be calculated from the image data acquired by the SLO included in the front observation optical system 200 or the imaging device.
  • the displacement of the test object is analyzed based on the potential field.
  • the CPU 11 may execute processing for returning the potential field calculated by the Helmholtz decomposition to the vector field again to the vector field.
  • the CPU 11 may calculate the vector field from which the rotational component is removed by differentiating the calculated scalar potential field.
  • the CPU 11 may analyze (quantify) the displacement of the test object by, for example, integrating the recalculated vector field so as to include the irradiation position of the treatment light.
  • Image Data Processing Device 10 Control Unit 11 CPU 100 OCT optical system 300 therapeutic light irradiation optical system

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  • Investigating Or Analysing Materials By Optical Means (AREA)

Abstract

L'invention concerne un dispositif de traitement de données d'image, comprenant une unité de commande qui commande un traitement de données d'image. À partir d'une pluralité d'instances de données d'image qui, à différents moments, ont été obtenues en lien avec une position photographique cible d'un sujet, l'unité de commande calcule un champ vectoriel qui indique des déplacements de chacun d'une pluralité de sites dans une région photographique (S2). En réalisant une décomposition de Helmholtz sur le champ vectoriel calculé, l'unité de commande calcule un champ potentiel (S3). Au moyen du dispositif de traitement de données d'image, du procédé de traitement de données d'image et du programme de traitement de données d'image selon la présente invention, des informations concernant le déplacement d'un sujet sont vérifiées de manière appropriée.
PCT/JP2017/002465 2016-01-28 2017-01-25 Dispositif de traitement de données d'image, procédé de traitement de données d'image, et programme de traitement de données d'image WO2017131004A1 (fr)

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Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2012135550A (ja) * 2010-12-27 2012-07-19 Nidek Co Ltd レーザ治療用眼科装置
JP2013048808A (ja) * 2011-08-31 2013-03-14 Nidek Co Ltd 眼底撮影装置
JP2015169650A (ja) * 2014-03-11 2015-09-28 国立大学法人 筑波大学 光コヒーレンストモグラフィーによる変位測定装置及び測定方法

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2012135550A (ja) * 2010-12-27 2012-07-19 Nidek Co Ltd レーザ治療用眼科装置
JP2013048808A (ja) * 2011-08-31 2013-03-14 Nidek Co Ltd 眼底撮影装置
JP2015169650A (ja) * 2014-03-11 2015-09-28 国立大学法人 筑波大学 光コヒーレンストモグラフィーによる変位測定装置及び測定方法

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JPWO2017131004A1 (ja) 2018-11-22

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