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WO2010098204A1 - Dispositif optique de mesure d'image - Google Patents

Dispositif optique de mesure d'image Download PDF

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Publication number
WO2010098204A1
WO2010098204A1 PCT/JP2010/051911 JP2010051911W WO2010098204A1 WO 2010098204 A1 WO2010098204 A1 WO 2010098204A1 JP 2010051911 W JP2010051911 W JP 2010051911W WO 2010098204 A1 WO2010098204 A1 WO 2010098204A1
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WIPO (PCT)
Prior art keywords
light
target object
optical path
optical
objective lens
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Ceased
Application number
PCT/JP2010/051911
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English (en)
Japanese (ja)
Inventor
小林　幸治
小林　直樹
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Kowa Co Ltd
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Kowa Co Ltd
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Filing date
Publication date
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Publication of WO2010098204A1 publication Critical patent/WO2010098204A1/fr
Anticipated expiration legal-status Critical
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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
    • A61B3/102—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for optical coherence tomography [OCT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0073—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by tomography, i.e. reconstruction of 3D images from 2D projections
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02041—Interferometers characterised by particular imaging or detection techniques
    • G01B9/02044—Imaging in the frequency domain, e.g. by using a spectrometer
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02055—Reduction or prevention of errors; Testing; Calibration
    • G01B9/02062—Active error reduction, i.e. varying with time
    • G01B9/02064—Active error reduction, i.e. varying with time by particular adjustment of coherence gate, i.e. adjusting position of zero path difference in low coherence interferometry
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02055—Reduction or prevention of errors; Testing; Calibration
    • G01B9/02062—Active error reduction, i.e. varying with time
    • G01B9/02067—Active error reduction, i.e. varying with time by electronic control systems, i.e. using feedback acting on optics or light
    • G01B9/02068—Auto-alignment of optical elements
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02055—Reduction or prevention of errors; Testing; Calibration
    • G01B9/02075—Reduction or prevention of errors; Testing; Calibration of particular errors
    • G01B9/02076—Caused by motion
    • G01B9/02077—Caused by motion of the object
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/0209—Low-coherence interferometers
    • G01B9/02091—Tomographic interferometers, e.g. based on optical coherence

Definitions

  • the present invention relates to an optical image measurement device, and more specifically, irradiates a predetermined portion of an observation target object with a light beam from a light source, and detects reflected light from the target object using an optical interference phenomenon.
  • the present invention relates to an optical image measurement device that acquires image information of a target object.
  • OCT optical coherence tomography
  • Patent Document 1 discloses, as initial OCT, a beat that is output by synthesizing a reference light in which the frequency of irradiation light is shifted and a reflected light from a measurement target object and the reference light. A configuration in which a reflection tomographic image of a target object is imaged by detecting a component is shown.
  • Patent Document 2 an interferometer using a light source having a short coherence length characteristic and an optical fiber, a phase modulation means and a lateral scanning mechanism arranged in an optical path of search light toward a sample specimen, and arranged in an optical path of reference light
  • This document shows a basic technique for imaging a tomographic image of a sample specimen by detecting interference light generated between search light and reference light guided through an optical fiber.
  • a light beam is divided into a reference arm and a measurement arm, and the intensity of light that appears by interference between the measurement light via the measurement arm and the reference light via the reference arm is measured using a spectroscope.
  • the structure which detects via is disclosed.
  • the reference arm is provided with a means for changing the phase of light, and shows a configuration for optical tomography of transparent, partially transparent, and opaque objects by analyzing the signal from the spectrometer. Has been.
  • Patent Document 4 in a measuring device composed of an interferometer and a spectrometer (spectrometer), a light beam from a light source collects light in a line shape with respect to a measurement object, A configuration is disclosed in which observation light is detected by a two-dimensional image sensor via a spectroscope. It is shown that by performing arithmetic processing such as Fourier transform on the detection signal from the image sensor, the cross-sectional information of the measurement object can be obtained at high speed according to the calculation speed.
  • arithmetic processing such as Fourier transform
  • Patent Document 5 a plurality of tomographic images of a measurement object to be detected via an interferometer are acquired in an optical image measurement device including an interferometer and a spectrometer (spectrometer), and a tomographic image for correction is obtained. Based on this, a method for correcting the positional deviation of the plurality of tomographic images is disclosed. According to this method, it is possible to correct the positional deviation of the fundus tomographic image caused by the movement of the eye to be examined, particularly the positional deviation in the depth direction, and to provide highly accurate three-dimensional image information. .
  • Patent Document 6 discloses an optical image measurement device that forms a tomographic image of the fundus of a subject's eye in an optical image measurement device that includes an interferometer and a spectrometer (spectrometer).
  • a configuration is disclosed that includes driving means for moving the position of the reference object in the interferometer in the optical path direction of the reference light based on related information. According to such a configuration, since the position of the reference object in the interferometer can be automatically set based on the tomographic image information formed in the past, there is a possibility that the inspection efficiency can be improved. It is shown.
  • Non-Patent Document 1 discloses an OCT (TS-OCT) optical system using lateral scanning and a spectral domain partial coherence interferometer (SD) that performs distance measurement in the optical axis direction using a 1310 nm light source.
  • An apparatus configuration in which an optical system of -OCI) is combined is disclosed. According to such a configuration, the movement of the measurement target object (eyeball) in the optical axis direction is detected by SD-OCI, and the reference optical path length of TS-OCT is appropriately controlled to obtain 3 obtained from TS-OCT. The possibility of improving the measurement accuracy of the three-dimensional (3D) image data is shown.
  • JP-A-4-174345 Japanese Patent Publication No. 6-35946
  • JP-T 6-511312 Patent No. 3479069
  • Japanese Patent Laid-Open No. 11-325849 Japanese Patent Laid-Open No. 2006-116028 JP 2007-130403 A JP 2007-185244 A
  • Patent Documents 1 and 2 also referred to as “time domain method”
  • scanning in the depth direction (depth direction) of the observation target object is performed by movement control of the reflection mirror with respect to the reference light in the optical axis direction. Therefore, it is difficult to obtain a tomographic image of the target object at high speed.
  • this type of device it is necessary to adjust the length of the reference optical path according to the characteristics and settings of the target object. If the target object moves in the depth direction, the optical path length of the reference optical path is adjusted. There was a problem that was difficult.
  • Patent Documents 3 and 4 disclose an OCT method (also referred to as “spectral domain method”) using a spectrometer as a detection system.
  • This method is advantageous in that it does not require depth mechanical scanning in order to acquire tomographic information, and high-speed tomographic information can be acquired.
  • it is necessary to adjust the length of the reference optical path according to the characteristics and settings of the target object, as in the “time domain method”, and when the target object moves, the optical path length of the reference optical path There was a problem that adjustment was difficult.
  • the position of the reference object in the reference optical path in the interferometer is automatically set based on information related to the eye to be examined, so that it is possible to improve the efficiency when performing repeated inspections, etc.
  • Non-Patent Document 1 is configured to adjust the reference optical path length of the OCT interferometer while measuring the distance between the apparatus optical system and the eye to be examined using a partial coherence interferometer. Therefore, even if a movement in the depth direction occurs in the eye to be examined, there is little influence on the tomographic image of OCT, and a highly accurate tomographic image can be obtained.
  • the configuration of the optical system becomes expensive. Therefore, there is a problem that the handling of the apparatus is troublesome.
  • an optical image measurement device using OCT a reference optical path is set according to the setting of a target object when compared with a conventional method. It is possible to automatically adjust the optical path length of the image, and tomographic image information with high accuracy can be detected even when movement occurs in the observation target object, and the apparatus optical system is not greatly increased in cost.
  • An object of the present invention is to provide an optical image measuring device that is easy to handle.
  • the invention of claim 2 A light source that generates a low coherent light beam; A light splitting member for splitting a light beam from the light source into search light that travels toward a target object and reference light that travels toward a predetermined reference optical path; An objective lens optical system for guiding the light beam of the search light to a target object; Imaging means for acquiring two-dimensional image information of the surface of the observation target object via the objective lens optical system; An optical path length adjusting means for making the optical path length of the reference light variable; Ranging means for measuring the distance between the objective lens optical system and the observation target object based on the imaging position of the light beam reflected from the observation target object and obtained through the objective lens optical system; First signal processing means for controlling the optical path length adjusting means based on output information from the distance measuring means; Detecting means for receiving interference light synthesized between the search light via the objective lens optical system and the reference light via the optical path length adjusting means; Second signal processing means for acquiring image information inside the observation target object based on output information from the detection means; It
  • the optical path length adjusting means for making the optical path length of the reference light variable, and the measurement for measuring the distance between the objective lens optical system and the observation object. Since the distance measuring means and the signal processing means for controlling the optical path length adjusting means based on the output information from the distance measuring means are used, the observation target object is a moving object such as the fundus of the eye to be examined. However, by measuring the distance between the device optical system and the eye to be examined and automatically adjusting the optical path length of the reference optical path, it is possible to measure the automation of the measurement, and at the same time, tomographic images with extremely high accuracy Information can be acquired.
  • FIG. 1 is a configuration diagram of an optical system showing a first embodiment of an optical image measurement device according to the present invention. It is explanatory drawing which showed the optical principle of the ranging means of this invention.
  • the optical image measurement device according to the present invention it is an explanatory diagram when 3D data is acquired based on a tomographic image (XY image) in a direction perpendicular to the optical axis.
  • 3D data is acquired in a case where 3D data is acquired with spatial periods of equal pitch intervals based on a tomographic image (XY image) in a direction perpendicular to the optical axis.
  • optical image measurement device it is an explanatory diagram when 3D data is acquired without adjusting the reference optical path length based on a tomographic image (XZ image) in a direction along the optical axis.
  • the present invention will be described in detail based on the embodiments shown in the drawings.
  • the fundus of the human eye is illustrated as an observation target object, and an example of an optical system suitable for performing optometry is shown.
  • the present invention is not limited to this, and observation is performed.
  • the present invention can also be applied to a biological tissue such as skin or a biological sample having strong scattering characteristics as a target object.
  • reference numerals 1 and 2 denote high-intensity light-emitting diodes (Super Luminescent Diode: SLD) that emit partially coherent light, and have a low coherence (a small amount of light required for observing tomographic images).
  • SLD Super Luminescent Diode
  • This is a light source (first light source) having the property of coherence.
  • the center wavelengths generate light in different infrared (invisible) bands of 830 nm and 950 nm, for example.
  • the light beams from the light sources 1 and 2 are collimated by the lenses 3 and 4 and synthesized on the same optical axis via the mirror 5 and the dichroic mirror 6.
  • the light sources 1 and 2 it is possible to combine the two wavelength ranges and use them as a broadband light source, or to use the wavelength ranges properly as necessary.
  • one light source such as SLD or LD (Laser Diode: semiconductor laser) that emits visible light (for example, red having a wavelength of about 670 nm) is provided, which is invisible for measurement. It can also be used as an auxiliary light source for confirming the optical path of a light beam with visible light against infrared rays.
  • SLD System Laser Diode: semiconductor laser
  • the light beam that has passed through the mirror 5 and the dichroic mirror 6 is expanded into a light beam having a predetermined size via the lenses 7 and 8 and then enters a beam splitter (BS) 10 that functions as an optical path splitting member.
  • BS beam splitter
  • the optical path is divided into four directions: an optical path 9a on the light source side, a reference optical path 9b, a search optical path 9c, and a detection optical path 9d.
  • the light beam traveling in the reference optical path 9b passes through the lens 11, the mirror 12, and the lens 13, and then reaches the reflection mirror 14 disposed on the end face of the reference optical path, and the reflected light generated there returns the reference optical path 9b.
  • the mirror 14 is mounted on a piezoelectric element (piezoelectric vibrator) 15, and this vibrator finely vibrates the mirror 14 in the direction of the optical axis (in the direction of the arrow 14 a) at a frequency of, for example, several tens of Hz to Periodic phase shift is performed.
  • the reference mirror and the piezoelectric vibrator constitute a light phase shift means in the reference optical path for signal processing necessary for OCT image measurement.
  • the optical path length of the reference optical path 9b needs to be matched so that the distance is equal to the optical path length of the search optical path 9c.
  • the reflecting mirror 14 is fixed on the moving stage 16 via the piezoelectric element 15 and its position in the optical axis direction is appropriately adjusted according to a signal from a ranging signal processing means to be described later. .
  • the moving stage 16 can be moved in the optical axis direction (the direction of the arrow 14a) by a motor (not shown), and the optical path length of the reference optical path becomes variable by the movement of the moving stage 16 in the optical axis direction. It is possible to acquire three-dimensional tomographic image information of the optometric fundus 20b.
  • the light beam traveling in the search optical path 9c is incident on the eye 20 to be examined (anterior eye portion 20a, fundus 20b) as an observation target object via the lens 17, the dichroic mirror 18, and the objective lens (objective lens optical system) 19.
  • the optical path is branched, and a light beam from a light source (second light source) 21 having a predetermined wavelength that generates a wavelength different from that of the light sources 1 and 2 is converted into a lens 22, The light is projected toward the eye 20 via the beam splitter 23 and the dichroic mirror 18.
  • the light beam from the light source 21 is designed to be focused at the anterior eye portion 20a of the eye 20 to be examined, as will be described later. Reflected light from the anterior segment 20a is detected by a split-type sensor (for example, a four-split sensor) 26 via cylindrical lenses 24 and 25 after passing through the objective lens 19, the dichroic mirror 18, and the beam splitter 23.
  • a split-type sensor for example, a four-split sensor
  • the output signal from the sensor 26 is processed through a signal processing means (first signal processing means) 27, and then the moving stage 16 is controlled through a driver circuit 28.
  • the moving stage 16 is preferably constituted by a movement control means that is configured by a voice coil motor or the like and capable of high speed operation. This makes it possible to adjust the optical path length of the reference optical path 9b automatically and at high speed according to the distance between the objective lens 19 and the observation target object 20 (eye to be examined).
  • the reflected light from the fundus 20b of the eye 20 to be synthesized is combined with the reference light returning from the reference optical path 9b after passing through the optical system (the objective lens 19, the dichroic mirror 18, the lens 17, and the beam splitter 10). Then, interference light is generated in the detection optical path 9d.
  • This interference light is detected as detection light by a two-dimensional CCD (imaging device: interference light detection means) 30 through a lens 29.
  • the output signal from the two-dimensional CCD 30 is subjected to various signal processing via a signal processing means (second signal processing means) 31 and then processed by various software by a personal computer (PC) 32 to obtain a tomographic image. Is displayed on the display means 33.
  • the image information can be recorded in the storage unit 34 as necessary.
  • FIG. 2 is an explanatory diagram for explaining the principle of the distance measuring means for measuring the distance between the objective lens optical system and the observation target object, which is a feature of the present invention.
  • the light beam from the light source 21 is collimated by the lens 22 and then irradiated through the beam splitter 23, the dichroic mirror 18, and the objective lens 19 so as to converge on the anterior eye 20a of the eye to be examined.
  • the reflected light from the anterior segment 20a is optically designed to focus on the vicinity of the quadrant sensor 26 via the objective lens 19, the dichroic mirror 18, the beam splitter 23, and the cylindrical lenses 24 and 25.
  • the configuration from the eye 20 to the sensor 26 is drawn linearly for convenience through the dichroic mirror 18 and the beam splitter 23.
  • the four-divided sensor 26 includes four light receiving portions 26a, 26b, 26c, and 26d, and is set so that the amount of received light changes according to the focus state of the light beam. That is, when the eye 20 to be examined is farther from the objective lens 19, the spot 35 of the light beam imaged on the surface of the sensor 26 becomes horizontally long, and the light amounts detected by the light receiving portions 26a and 26c are the light amounts of the light receiving portions 26b and 26d. It becomes smaller than the detected light quantity. On the other hand, in a state where the distance between the eye 20 to be examined and the objective lens 19 is appropriately matched, the light beam spot 36 formed on the surface of the sensor 26 is approximately circular and is detected by the light receiving portions 26a and 26c.
  • the amount of light substantially matches the amount of light detected by the light receiving portions 26b and 26d. Further, when the eye 20 to be examined is close to the objective lens 19, the light beam spot 37 formed on the surface of the sensor 26 is vertically long, and the detected light amounts of the light receiving portions 26a and 26c are detected by the light receiving portions 26b and 26d. It becomes larger than the amount of light.
  • each of the four light receiving portions 26a, 26b, 26c, and 26d is A, B, C, and D, for example, by performing the following calculation, the eye 20 and the objective lens
  • the amount I corresponding to the distance to the distance 19 can be calculated approximately.
  • 3a and 3b are explanatory diagrams for explaining how a tomographic image inside the observation target object can be obtained by adjusting the reference optical path length of the interferometer described above.
  • the above-described optical system of FIG. 1 irradiates the fundus 20b with a light beam traveling in the search light path 9c, and the reflected light is combined with the light beam returning from the reference light path 9b in the beam splitter 10, and interference light is detected in the detection light path 9d. Occurs.
  • This interference light is detected as a tomographic image (XY image) of the fundus 20b in the XY plane perpendicular to the optical axis direction (Z direction) via the two-dimensional CCD 30 (imaging means) and the signal processing means 31.
  • Tomographic image information is acquired.
  • the tomographic image obtained in this way shows a tomographic image (XY image) of the fundus at the Z-direction position (depth) where the distance between the optical path length of the reference optical path 9b and the optical path length of the search optical path 9c is equal. . Even if the tomographic image is obtained at a certain time, the optical path length of the search optical path 9c changes due to the movement in the optical axis direction due to the eye movement of the eye 20 to be examined. Cannot obtain the same tomographic image.
  • the pitch interval (spatial period) when the tomographic image in the XY direction is obtained by scanning in the optical axis direction (Z direction) in time series (according to t) will be obtained.
  • the optical path length of the reference optical path 9b and the optical path length of the search optical path 9c correspond to each other during eye movement.
  • the spatial period of T1 to T7 is obtained as shown in FIG. 3a.
  • the pitch interval of the spatial periods T1 to T7 in which the tomographic image 38 is acquired according to the scanning of the reference optical path length is irregular as shown in FIG.
  • Such irregularities include a distance measuring means for measuring the distance between the optical system and the observation object as shown in FIG. 2, and an optical path length adjusting means based on output information from the distance measuring means.
  • the driver circuit 28 is controlled to control the interferometer.
  • the position of the moving stage 16 is adjusted in real time so that the optical path length of the reference optical path 9b becomes equal to the optical path length of the search optical path 9c that changes due to eye movement.
  • the movement caused by the eye movement of the eye to be examined is not limited to the optical axis direction (Z direction), and naturally involves movement in the XY directions.
  • Z direction optical axis direction
  • the movement in the XY direction is clearly recorded as a blood vessel pattern of the fundus in the XY image acquired as shown in FIG. 3a, if the intervals in the Z direction are aligned with high accuracy, Then, it is easy to correct the movement in the XY direction later by image processing, and as a result, highly accurate three-dimensional tomographic image information can be obtained.
  • FIG. 4 shows a second embodiment different from the embodiment described in FIG.
  • elements that are the same as the constituent elements in FIG. 1 (or FIG. 2) are given common reference numerals.
  • FIG. 4 shows an example of an OCT (Optical Coherence Tomography) system configuration using an optical fiber interferometer.
  • reference numerals 1 and 2 denote high-intensity light-emitting diodes (Super Luminescent Diode: SLD) that emit partially coherent light, and have a low coherence (a small amount of light required for observing a tomographic image). It is a light source having the property of coherence.
  • the SLD light source generates light of different wavelength bands, and the light beams from the light sources 1 and 2 are collimated by the lenses 3 and 4 and synthesized on the same optical axis via the mirror 5 and the dichroic mirror 6. Is done.
  • the light sources 1 and 2 it is possible to combine the two wavelength ranges and use them as a broadband light source, or different wavelength ranges may be used as needed.
  • the light beam that passes through the mirror 5 and the dichroic mirror 6 is coupled to the optical fiber 40 through the coupler 41a.
  • the optical fiber 40 has an optical path divided into four directions of a light source side optical path 40a, a reference optical path 40b, a search optical path 40c, and a detection optical path 40d, and constitutes a fiber type interferometer.
  • the light beam traveling in the reference optical path 40b is emitted from the coupler 41b, adjusted in light intensity by the ND filter 42, then reflected by the mirror 14, and returned to the reference optical path 40b.
  • the mirror 14 is mounted on a piezoelectric element (piezoelectric vibrator) 15, and this vibrator finely vibrates the mirror 14 in the direction of the optical axis at a predetermined frequency to perform a periodic phase shift of the light beam. .
  • the optical path length of the reference optical path 40b needs to be matched so that the distance is equal to the optical path length of the search optical path 40c.
  • the reflecting mirror 14 is fixed on the moving stage 16 via the piezoelectric element 15, and its position in the optical axis direction is adjusted according to the signal of the ranging signal processing means 27. To do.
  • the position adjustment of the moving stage 16 is performed in the same manner as described with reference to FIGS. That is, the light beam from the light source 21 collimated by the lens 22 is applied to the anterior eye portion 20a of the eye 20 to be examined through the beam splitter 23, the dichroic mirror 18, and the objective lens 19.
  • the reflected light from the anterior segment 20a is imaged in the vicinity of the quadrant sensor 26 via the objective lens 19, the dichroic mirror 18, the beam splitter 23, and the cylindrical lenses 24 and 25.
  • the amount of light received by each light receiving portion of the four-divided sensor 26 changes, so that the signal processing means 27 depends on the distance between the eye 20 to be examined and the objective lens 19.
  • the calculation amount I described above is calculated, and the driver circuit 28 is controlled based on the result including the correction of the nonlinearity and the position of the moving stage 16 in the optical axis direction is adjusted.
  • the driver circuit 28 is controlled based on the result including the correction of the nonlinearity and the position of the moving stage 16 in the optical axis direction is adjusted.
  • the light beam traveling on the search optical path 40c is incident on mirrors (galvano mirrors) 43a and 44a mounted on the galvanometers 43 and 44, and the light beam is scanned.
  • These two galvanometer mirrors 43a and 44a constitute a scanning unit 45 that performs one-dimensional scanning of the light beam in a direction orthogonal to the optical axis. For example, if one of the two galvanometer mirrors 43a and 44a is fixed and scanning is performed with only one, scanning in the X-axis direction or the Y-axis direction in the direction perpendicular to the optical axis (Z-axis) is possible.
  • any line-shaped scan in the XY plane direction, Or scanning in a circle or the like becomes possible. Scanning by these galvanometer mirrors 43a and 44a is appropriately performed at a predetermined frequency as necessary.
  • the light beam scanned by the galvanometer mirrors 43a and 44a passes through the dichroic mirror 46, the lens 17, the dichroic mirror 18, and the objective lens 19, and then is applied to the subject's eye 20 (anterior eye portion 20a or fundus 20b) as an observation target object.
  • the lens 17 can also constitute a focusing optical system that can be adjusted according to the diopter of the eye to be examined (myopia, hyperopia, etc.) as a plurality of lenses.
  • the lens 17 and the objective lens 19 constitute a telecentric optical system so that the conjugate relationship between the scanning unit 45 including the galvanometer mirror and the anterior eye portion 20a of the eye 20 to be examined can be maintained substantially constant. it can.
  • the reflected light from the eye to be examined travels backward through the above-described optical system (objective lens 19, dichroic mirror 18, lens 17, dichroic mirror 46), and is guided to the optical fiber 40 after passing through the scanning unit 45 and the coupler 41c. .
  • the search light passing through the search optical path 40c of the optical fiber 40 is combined with the reference light passing through the reference optical path 40b, and interference light (detection light) is generated on the detection optical path 40d side.
  • the detection light emitted from the optical fiber via the coupler 41d is dispersed by a spectroscope (spectrometer) 47, detected by a one-dimensional CCD (line sensor) 48, and output as an electrical signal.
  • the output signal from the CCD line sensor 48 is sent to a personal computer (PC) 32 after undergoing predetermined signal processing such as filter processing via the signal processing device 31.
  • PC personal computer
  • tomographic image information of the observation target object is calculated after predetermined calculation processing necessary for a spectral domain OCT technique such as fast Fourier transform (FFT) is performed by predetermined software.
  • FFT fast Fourier transform
  • the final result is displayed on the monitor screen of the display device 33 such as a liquid crystal display monitor.
  • a two-dimensional imaging means 49 using observation light having a wavelength (for example, wavelength 750 nm) different from that of the OCT optical system that measures tomographic image information is provided.
  • the imaging means 49 may be a fundus camera or a scanning laser ophthalmoscope, and its output signal (video signal) is supplied to the display device 33 via the PC 32 to present predetermined image information.
  • the video signal from the imaging means 49 is an alignment monitor image when the apparatus optical system is aligned with the eye 20 to be examined, or a normal reflected image of the fundus 20b of the eye to be examined, and is used as necessary. Can do.
  • the OCT tomographic image information obtained via the line sensor 48 and the signal processing means 31 and the two-dimensional reflection image information obtained from the imaging means 49 are stored via the PC 32 as necessary, such as a storage device 34 such as an optical disk. Can be recorded.
  • the tomographic image obtained by using the OCT optical system of FIG. 4 is a tomographic image (for example, an XZ image 50) in a direction along the optical axis, and is a time series (for example, Y direction) perpendicular to the optical axis.
  • a tomographic image for example, an XZ image 50
  • a time series for example, Y direction
  • cross-sectional image information three-dimensional information
  • This image information is affected by the movement in the depth direction indicated by the double arrow line 51 due to the eye movement of the eye 20 to be examined. Therefore, when the reference optical path length is not corrected, the vertical position of the XZ image is indicated by the tomographic images of A1, A2, A3, and A4 in FIG. It is irregular depending on eye movement.
  • the signal processing means 27 causes the eye to be examined.
  • An amount of calculation I corresponding to the distance between 20 and the objective lens 19 and a correction amount taking into account a predetermined nonlinearity are calculated.
  • the signal processing means 27 controls the driver circuit 28 so that the optical path length of the reference optical path 40b of the optical fiber 40 becomes equal to the optical path length of the search optical path 40c that changes due to eye movement or the like. Adjust the position of in real time.
  • each piece of tomographic image information can be irrelevant to the movement in the depth direction caused by eye movement or the like. That is, the tomographic images B1, B2, B3, and B4 in FIG. 5b were acquired at different times, but the position of the tomographic surface indicated by the arrow 52 is different even when the tomographic image acquisition times are different.
  • the tomographic images B1, B2, B3, and B4 are substantially coincident, and highly accurate three-dimensional tomographic information that is aligned in the depth direction can be obtained.
  • the movement caused by the eye movement of the eye to be examined is not limited to the depth direction (Z direction), and is naturally accompanied by movement in the XY direction.
  • the movement in the XY direction is also recorded as a shadow of the blood vessel pattern of the fundus in the XZ image acquired as shown in FIGS. 5a and 5b, and further two-dimensional imaging means (FIG. 4). If simultaneous photographing is performed according to 49), the movement in the XY direction is clearly recorded in the reflected image obtained by the imaging means 49. Therefore, if these pieces of information are used, it is easy to correct the movement in the XY direction later by image processing. If the movement in the Z direction can be optically corrected in real time, the result is highly accurate 3. It is possible to obtain dimensional information.
  • FIGS. 6A and 6B are explanatory diagrams of the final result displayed as the tomographic image information obtained by the OCT interferometer of FIG. 4 as three-dimensional image information.
  • the tomographic image information obtained by the OCT interference optical system in FIG. 4 when there is no control by the distance measuring unit described in FIG. 2 is affected by the movement of the observation target object (the eye 20 to be examined).
  • An image in which the final result is three-dimensionally displayed is often an image as indicated by reference numeral 53 in which fluctuations such as waves occur in the Z direction.
  • reference numeral 53 in which fluctuations such as waves occur in the Z direction.
  • the optical path length of the reference optical path is controlled in real time using the distance measuring means illustrated in FIG. 2, as indicated by the reference numeral 54 with high accuracy that suppresses the influence of fluctuation in the Z direction.
  • Such three-dimensional tomographic image information is one of the important applications of OCT in clinical medicine.
  • precise diagnosis and surgical planning of various ophthalmic diseases such as various retinal degenerations and retinal detachment. In this case, it can be effectively used.

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Abstract

La présente invention concerne un dispositif optique permettant de détecter des informations d'image tomographique très précises même si l'objet observé se déplace dans la direction de l'axe de la lumière, grâce à la correction de la longueur du trajet d'une lumière de référence. Pour ce faire, des faisceaux de lumière à faible interférence (1, 2) sont divisés par un séparateur de faisceau (10) en une lumière d'analyse qui est dirigée en direction d'un objet observé (20) et en une lumière de référence qui est dirigée sur un trajet de lumière de référence spécifié (9b). Des informations d'image provenant de l'intérieur de l'objet observé sont acquises grâce à la détection par un CCD (30) d'une lumière d'interférence synthétisée entre la lumière d'analyse provenant de l'objet observé et la lumière de référence. La position focale du faisceau de lumière provenant d'une source de lumière (21) réfléchi par l'objet observé est détectée par un capteur (26) et la distance entre une lentille d'objectif et l'objet observé est mesurée par un moyen de traitement de signal (27). La position d'un étage mobile (16) est ajustée et la longueur du trajet de la lumière de référence est ajustée en temps réel sur la base des résultats de la mesure.
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CN104501738A (zh) * 2014-12-31 2015-04-08 华中科技大学 纳米尺度下大面积散射场的快速测量方法及装置
EP3170444A4 (fr) * 2014-07-17 2018-04-04 The Yoshida Dental Mfg. Co., Ltd. Sonde, dispositif de tomographie par cohérence optique et procédé de correction de point zéro
WO2019001795A1 (fr) * 2017-06-27 2019-01-03 Carl Zeiss Meditec Ag Procédé et système de correction d'image

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JP5782262B2 (ja) * 2011-01-20 2015-09-24 キヤノン株式会社 断層画像補正方法および断層画像補正装置
PT2797493T (pt) * 2011-12-28 2018-07-27 Wavelight Gmbh Processo para tomografia de coerência ótica e aparelho para tomografia de coerência ótica
JP5374598B2 (ja) 2012-01-26 2013-12-25 キヤノン株式会社 光断層撮像装置
JP6207221B2 (ja) * 2013-04-30 2017-10-04 キヤノン株式会社 光断層撮像装置
JP5995810B2 (ja) * 2013-09-17 2016-09-21 キヤノン株式会社 光断層撮像装置
JP5634587B2 (ja) * 2013-10-30 2014-12-03 キヤノン株式会社 画像処理装置、画像処理方法、及びプログラム
JP2016017762A (ja) * 2014-07-04 2016-02-01 株式会社東芝 光学遅延装置及び光コヒーレンストモグラフィー装置
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CN104501738A (zh) * 2014-12-31 2015-04-08 华中科技大学 纳米尺度下大面积散射场的快速测量方法及装置
WO2019001795A1 (fr) * 2017-06-27 2019-01-03 Carl Zeiss Meditec Ag Procédé et système de correction d'image

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