WO2011145182A1 - Dispositif de tomographie par cohérence optique - Google Patents

Dispositif de tomographie par cohérence optique Download PDF

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Publication number
WO2011145182A1
WO2011145182A1 PCT/JP2010/058407 JP2010058407W WO2011145182A1 WO 2011145182 A1 WO2011145182 A1 WO 2011145182A1 JP 2010058407 W JP2010058407 W JP 2010058407W WO 2011145182 A1 WO2011145182 A1 WO 2011145182A1
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WIPO (PCT)
Prior art keywords
eye
partial scan
optical
light
scan area
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PCT/JP2010/058407
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English (en)
Japanese (ja)
Inventor
原　拓也
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興和株式会社
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Publication date
Application filed by 興和株式会社 filed Critical 興和株式会社
Priority to PCT/JP2010/058407 priority Critical patent/WO2011145182A1/fr
Publication of WO2011145182A1 publication Critical patent/WO2011145182A1/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
    • 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
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/0016—Operational features thereof
    • A61B3/0025—Operational features thereof characterised by electronic signal processing, e.g. eye models

Definitions

  • the present invention relates to an optical coherence tomographic image measuring apparatus (OCT apparatus) that performs optical tomographic imaging, and more particularly to an optical coherent tomographic image measuring apparatus suitable for obtaining an optical coherent tomographic image of a fundus tissue of an eye to be examined.
  • OCT apparatus optical coherence tomographic image measuring apparatus
  • OCT Optical Coherence Tomography
  • time domain time domain
  • a one-dimensional tomographic image cannot be acquired unless the reference light mirror is scanned.
  • a two-dimensional scan raster scan
  • two galvanometer mirrors etc.
  • 3D three-dimensional scan
  • Patent Document 1 discloses OCT three-dimensional distribution measurement using a MEMS (Micro Electronic Mechanical System) optical scanning mirror instead of a galvanometer mirror.
  • the processing time for image acquisition is about 4.8 seconds, which is not realistic.
  • accurate measurement data cannot be obtained due to fixation eye movement or blinking of the subject's eye during the measurement time of several seconds as described above, resulting in measurement failure. Therefore, the current OCT of each company reduces the spatial resolution so that the measurement is completed in about 1 to 1.5 seconds.
  • one example of an optical coherence tomography that has already been sold is one with specifications that the camera performance is 53 k scans / second, and 3D scanning of 9 mm ⁇ 9 mm is performed in 1.6 seconds.
  • the time required for one B scan is About 9.7 msec.
  • about 166 B scans can be performed in 1.6 seconds, and the resolution in the X-axis direction is calculated to be about 17.6 ⁇ m and the resolution in the Y-axis direction is calculated to be about 54.2 ⁇ m.
  • the resolution in the depth (Z-axis) direction is 5 to 6 ⁇ m in the Fourier domain method and about 10 ⁇ m in the time domain method, so in this example, the resolution in the Y-axis direction is particularly insufficient.
  • image processing is performed so as to complement between lines, so that accuracy is inferior.
  • the clinical issue is whether to give priority to spatial resolution or measurement time.
  • An object of the present invention is to provide an optical coherence tomographic image measurement apparatus capable of solving the above-described problems and performing 3D imaging of the retina of an eye to be examined without acquiring a tomographic image with a large objective lens and a wide angle of view. It is in.
  • a light source that emits partially coherent light, a light beam emitted from the light source, a signal light that passes through a placement position of the eye to be examined, and the eye placement to be examined
  • the signal light after passing through the position of the eye to be examined and the reference light passing through the different optical path are interfered with each other by being divided into reference light passing through a different optical path from the optical path passing through the position.
  • An interference optical system for generating light, a diffraction grating for splitting the interference light generated by the interference optical system, a photosensor array for detecting the split interference light, and the photosensor array detected In an optical coherence tomographic image measuring apparatus having a fast Fourier transformer that performs fast Fourier transform of a signal and a control unit that images the output of the fast Fourier transformer and displays or records the optical coherent tomographic image Based on the control of the control unit, the signal light includes scanning means for two-dimensionally scanning a predetermined partial scan area of the eye to be examined at a predetermined scanning speed, and the eye to be examined is two-dimensionally scanned by the scanning means.
  • the entire measurement range of the eye to be examined is divided into a plurality of partial scan areas, each partial scan area is sequentially scanned by the scanning means, and optical coherence tomographic images obtained from each partial scan area are panorama synthesized.
  • a configuration for acquiring an optical coherence tomographic image of the measurement range of the eye to be examined was adopted.
  • each partial scan area is a minute area, and a wide range of measurement areas are covered by photographing a plurality of partial scan areas, and images obtained in each partial scan area are panorama synthesized.
  • the image of the entire measurement area can be acquired by this, the effect of fixation movement and blinking in each partial scan area can be reduced, and the measurement time for each partial scan can be shortened. It has an excellent effect that the measurement time and resolution can be changed by variously selecting the number of measurement areas (number of acquired images), size, etc. .
  • reference numeral 1 is a high-intensity light emitting diode (Super Luminescent Diode: SLD) that emits partially coherent light, and has low coherence (coherence is necessary) for observing a tomographic image.
  • SLD Super Luminescent Diode
  • This is a light source having a small number of properties.
  • the center wavelength is assumed to generate light in the infrared (invisible) band of 840 nm, for example.
  • the light beam from the light source 1 is collimated by the lens 2, and the light beam passing through the mirror 3 is expanded into a light beam of a predetermined size via the lenses 4 and 5, and then a beam splitter (BS: light
  • BS beam splitter
  • the optical path is divided into four directions: an optical path 6a on the light source side, a reference optical path 6b, a search optical path 6c, and a detection optical path 6d.
  • another light source for example, an SLD or LD (Laser Diode: semiconductor laser) that emits visible light (for example, red having a wavelength of about 670 nm) is provided, and this is used as a light source 1 using a dichroic mirror or the like. By matching with the optical axis, it can be used as an auxiliary light source for confirming the optical path of the light beam with visible light against invisible infrared rays for measurement.
  • SLD SystemLD
  • LD Laser Diode: semiconductor laser
  • the light beam traveling in the reference light path 6 b is reflected by the reference light mirror 9, and the light beam reflected by the reference light mirror 9 returns through the lens 8 to the reference light path 6 b.
  • the light beam traveling along the search optical path 6c is incident on the galvanometer mirror 10a attached to the galvanometer 10.
  • the light beam reflected by the galvanometer mirror 10a is reflected by the galvanometer mirror 11a of the second galvanometer 11, and the light beam is passed through these two galvanometer mirrors 10a or 11a in a direction perpendicular to the optical axis.
  • Each can be scanned one-dimensionally.
  • the galvanometer 11 can perform scanning in the X-axis direction
  • the galvanometer 10 can perform scanning in the Y-axis direction.
  • galvanometer mirrors 10a and 11a constitute first and second optical scanning means for scanning the light beam of the search light at the same frequency as the line sensor array constituting the spectrometer 21, respectively.
  • the light beams scanned by the galvanometer mirrors 10a and 11a enter the eye 15 (the anterior eye portion 15a or the fundus 15b) of the object to be observed after passing through the lenses 12, 13, and 14.
  • the lenses 12 and 13 constitute a focusing optical system that can be adjusted according to the diopter of the eye to be examined (myopia, hyperopia, etc.), and change the focal position of the light beam according to the optical characteristics of the target object. It is a focus adjustment means.
  • the positions of the lenses 12 and 13 can be adjusted in the optical axis direction according to the operation of a predetermined mechanism (not shown).
  • the lenses 12 and 13 and the lens 14 constitute a telecentric optical system so that the conjugate relationship between the galvanometer mirror and the eye to be examined is kept substantially constant.
  • the light beam incident on the eye 15 is converged in a dot shape at a predetermined position on the fundus 15b, for example, to be in a focused state.
  • This point-focused light beam can scan the fundus 15b of the eye to be examined in a line shape or a circle shape by scanning with galvanometer mirrors 10a and 11a (light scanning means).
  • galvanometer mirrors 10a and 11a light scanning means.
  • FIGS. 2A to 2C which will be described later, a rectangular small area is two-dimensionally scanned, and a similar rectangular area is scanned in a grid pattern while shifting the position.
  • Panorama image a rectangular small area is two-dimensionally scanned, and a similar rectangular area is scanned in a grid pattern while shifting the position.
  • Reflected light from the fundus 15b of the eye 15 to be inspected travels backward through the optical system described above, that is, reaches the beam splitter (BS) 7 via the lenses 12, 13, and 14 and the galvanometer mirrors 10a and 11a.
  • the reflected light from the eye 15 to be inspected that travels backward in the search optical path 6c and passes through the beam splitter 7 is combined with the reference light that returns from the reference optical path 6b, thereby generating interference light in the detection optical path 6d.
  • This interference light passes through the detection aperture (pinhole) 17 through the lens 16 as detection light, and further enters the diffraction grating 19 disposed at an inclination with respect to the optical axis through the lens 18.
  • the detection light passing through the diffraction grating 19 is detected by a spectrometer 21 including a line sensor array through a lens 20.
  • the output signal of the spectrometer 21 is converted into a spectrum distribution signal by a fast Fourier transformer (FFT) 22 and input to a PC (personal computer) 23.
  • FFT fast Fourier transformer
  • the PC 23 can measure the three-dimensional distribution of the biological components of the eye to be examined by performing image processing on the detection light information input from the fast Fourier transformer 22.
  • the PC 23 controls the overall operation of the optical system (particularly, the two galvanometers 10 and 11), and the measurement result of the three-dimensional distribution of the measurement target tissue in the eye to be examined is displayed on a display device 24 such as a liquid crystal television monitor. Control is performed such as outputting and displaying, and transferring the measurement result to the storage device 25 and storing it as necessary.
  • the PC 23 has a keyboard and a pointing device (such as a mouse), and can perform settings for measurement control via these user interface means.
  • the pinhole 17 provided in the optical system has a predetermined pinhole-shaped detection aperture with a gap limited in the scanning direction of the optical scanning means, and detects noise caused by unnecessary stray light and scattered light.
  • the background light amount level is reduced, thereby improving the gradation of the signal component with respect to the video signal from the image sensor.
  • the pinhole 17 may be a small square-shaped opening, and this opening can also be configured by stacking two pieces of slit-shaped parts formed in a thin plate at right angles.
  • the light beam incident on the eye 15 to be examined is focused and focused in a dot shape at a predetermined position of the fundus 15b, for example, and the fundus 15b of the eye to be examined is made into a line shape or a circle shape by the galvanometer mirrors 10a and 11a.
  • a small rectangular area is two-dimensionally scanned, and a similar rectangular area is scanned in a grid pattern while shifting the position. Then, panorama synthesis is performed on images obtained from these areas.
  • the measurement time in each area can be shortened, and the effects of eye movement and blinking can be reduced. It is possible to obtain a more accurate measurement result by panoramicly combining images obtained in each area later.
  • the imaging speed by the spectrometer 21 (line sensor array), the fast Fourier transformer 22 and the PC 23 of this apparatus is 40 k (scan / sec).
  • FIG. 2A shows the entire measurement range 101 divided by four partial scan areas 102 each having a rectangular shape (square).
  • the scan range of the two galvanometers 10 and 11 is controlled by the PC 23 so that the scan size of one partial scan area 102 is 6 mm ⁇ 6 mm, and the image acquisition point is 200 pt ⁇ 200 pt (that is, the resolution is 30 ⁇ m). ).
  • the entire measurement range 101 is 11 ⁇ 11 mm, and adjacent partial scan areas 102 have 1 mm overlap portions O that overlap each other.
  • the scan of one partial scan area 102 can be processed in one second, so that no burden is imposed on the subject. If the galvanometers 10 and 11 are controlled at a short interval each time one scan is completed and the adjacent partial scan areas 102, 102... Are sequentially photographed, four scan images are obtained as shown in the figure. It is done.
  • an image of the entire measurement range 101 is formed by performing a process of overlapping adjacent 1 mm edges of the four scan images by a known panorama synthesis process.
  • the overlap portion O of the partial scan area 102 can be used for alignment by pattern matching in the panorama synthesis process, and a known complement or blend process is performed so that the image connection is good in the overlapped portion. Can do. Since the overlap portions O of 1 mm are overlapped with each other in the adjacent partial scan areas 102, the image of the entire measurement range 101 finally obtained has a size of 11 mm ⁇ 11 mm.
  • FIG. 2B shows measurement control when a higher resolution scan is desired.
  • FIG. 2B shows the entire measurement range 101 divided by nine rectangular (square) partial scan areas 102.
  • one scan size is set to 4 mm ⁇ 4 mm, and the image acquisition point is set to 200 pt ⁇ 200 pt (that is, the resolution is 20 ⁇ m).
  • Adjacent partial scan areas 102 have 1 mm overlap portions O that overlap each other.
  • one partial scan area 102 can be scanned in one second.
  • a wide range of measurement results are obtained by obtaining nine images.
  • an image of the entire measurement range 101 of 10 mm ⁇ 10 mm is finally obtained by panoramic synthesis processing of nine images.
  • FIG. 2C shows measurement control when it is desired to perform a shorter scan.
  • FIG. 2C shows the entire measurement range 101 divided by four partial scan areas 102 each having a rectangular shape (square).
  • the method shown in FIGS. 2A and 2B does not give any burden to normal subjects because each scan is performed in one second, but it is difficult for elderly and infant subjects. There is a case. Therefore, in the case of FIG. 2C, the size of one partial scan area 102 is 4 mm ⁇ 4 mm, and adjacent partial scan areas 102 have 1 mm overlapping portions O that overlap each other.
  • the image acquisition point is 133 pt ⁇ 133 pt in order to keep the resolution at 30 ⁇ m
  • one scan can be completed in 0.44 seconds.
  • the finally obtained scan image range is 7 mm ⁇ 7 mm.
  • the probability of failure in each measurement is reduced, so that reliable measurement is possible although the measurement range is narrow.
  • the scan speed of the galvanometer mirrors 10a and 11a is set to a predetermined value, the scan size and the acquisition point (element for determining resolution) are determined, and the measurement region is further divided into several images.
  • Measurement control parameters for controlling measurement conditions such as whether to capture and combine in panorama processing can be selected in various ways using user interface means of the PC 23 including a keyboard and pointing device (such as a mouse).
  • various panoramic patterns similar to those shown in FIGS. 2A to 2C can be set by the PC 23 controlling the operation of the two galvanometers 10 and 11 of the optical system, and the command can be set via the user interface means of the PC 23. Can be set.
  • the scan range can be changed, each partial scan area is made into a minute area, and a wide range of measurement areas are covered by photographing a plurality of partial scan areas, and obtained in each partial scan area.
  • the entire measurement area can be acquired by panoramic synthesis of the image, the effects of fixation micromotion and blinking in each partial scan area can be reduced, and the measurement time for each partial scan can be shortened. Therefore, there is an excellent effect of being able to cope with the subject (the elderly or a patient with a disease).
  • the measurement time and resolution can be changed by variously selecting the number of partial scan areas (number of acquired images) and size, a measurement effect different from panoramic photography of the fundus camera can be expected.
  • the above-described panoramic pattern shown in FIGS. 2A to 2C is an example, and various measurement demands can be met by changing the number of overlapping and the overlapping distance.
  • the objective lens (14) since it is not necessary to acquire a tomographic image with a wide angle of view when photographing one partial scan area, the objective lens (14) does not have to be large. Therefore, there are excellent effects that the configuration of the apparatus is simple and inexpensive, and the panoramic function enables a three-dimensional scan of the optical coherence tomographic image with a wide range and an arbitrary resolution.
  • the gaze of the eye to be examined is reliably guided in the measurement of each partial scan area constituting a wider measurement range.
  • FIG. 3 shows an example in which an internal fixation lamp 29 having a plurality of lighting parts as a fixation target is arranged in the main body.
  • the internal fixation lamp 29 is composed of LEDs arranged in a matrix. When a specific LED of the internal fixation lamp 29 is turned on according to the control of the PC 23, the emitted light is converted into a lens 30, a total reflection mirror 28, The line of sight of the subject eye 15 can be guided and fixed in the direction of the LED that is incident on the eye 15 by the perforated total reflection mirror 26 via the lens 27 and the internal fixation lamp 29 is lit. 3 is the same as that of FIG. Alternatively, a liquid crystal display (LCD) and a backlight unit are arranged instead of the position of the internal fixation lamp 29, and a specific portion is brightly displayed to guide and fix the line of sight of the eye 15 to be examined. It may be.
  • LCD liquid crystal display
  • the internal fixation lamp 29 corresponding to each partial scan area is switched on and turned on in a direction suitable for the measurement of the partial scan area.
  • the line of sight is reliably guided for a short time during measurement of each partial scan area, and each area can be measured accurately, resulting in panorama synthesis. It is possible to accurately measure a fundus image in a wider range by performing.
  • the lighting position of the internal fixation lamp 29 can be recorded in the storage device 25 by the PC 23 in correspondence with information indicating which part of the fundus is currently being measured.
  • the optical coherence tomographic image measurement can be performed in a wider measurement range by switching on and lighting a plurality of predetermined fixation targets and guiding the line of sight in a direction suitable for the measurement of each partial scan area. .
  • the optical coherence tomographic image measurement apparatus of the present invention can be used for three-dimensional measurement of the tissue of the fundus of the eye to be examined.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Radiology & Medical Imaging (AREA)
  • Biophysics (AREA)
  • Ophthalmology & Optometry (AREA)
  • Engineering & Computer Science (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Physics & Mathematics (AREA)
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Abstract

La présente invention concerne un dispositif de tomographie par cohérence optique comprenant des galvanomètres (10, 11) comme moyen de balayage optique destiné à réaliser un balayage à deux dimensions d'une zone de balayage partielle prédéterminée de l'œil d'un sujet avec une lumière signal, la réalisation d'un balayage à deux dimensions de l'œil d'un sujet (15) permettant de diviser la plage de mesure entière du fond de l'œil du sujet (15) en une pluralité de zones de balayage partielles, de balayer de manière séquentielle chaque zone de balayage partiel et de synthétiser de manière panoramique les images de tomographie par cohérence optique obtenues de chaque zone de balayage partiel afin d'obtenir une image de tomographie par cohérence optique de la plage de mesure de l'œil du sujet. Lors de la mesure des zones de balayage partiel, les DEL prévues d'une lampe de fixation interne (29) disposées conjointement aux DEL dans une matrice sont allumées pour guider la ligne de visée de l'œil du sujet (15) dans une direction nécessaire à la mesure de chaque zone de balayage partiel.
PCT/JP2010/058407 2010-05-19 2010-05-19 Dispositif de tomographie par cohérence optique WO2011145182A1 (fr)

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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2016131845A (ja) * 2015-01-22 2016-07-25 キヤノン株式会社 眼科装置及びその制御方法、並びに、プログラム
JP2019118419A (ja) * 2017-12-28 2019-07-22 株式会社トプコン 眼科撮影装置、その制御方法、プログラム、及び記録媒体
JP2019118421A (ja) * 2017-12-28 2019-07-22 株式会社トプコン 眼科撮影装置、その制御方法、プログラム、及び記録媒体
JP2022027879A (ja) * 2017-12-28 2022-02-14 株式会社トプコン 眼科撮影装置、その制御方法、プログラム、及び記録媒体

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2009183332A (ja) * 2008-02-04 2009-08-20 Topcon Corp 眼底観察装置、眼底画像処理装置及びプログラム

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2009183332A (ja) * 2008-02-04 2009-08-20 Topcon Corp 眼底観察装置、眼底画像処理装置及びプログラム

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2016131845A (ja) * 2015-01-22 2016-07-25 キヤノン株式会社 眼科装置及びその制御方法、並びに、プログラム
JP2019118419A (ja) * 2017-12-28 2019-07-22 株式会社トプコン 眼科撮影装置、その制御方法、プログラム、及び記録媒体
JP2019118421A (ja) * 2017-12-28 2019-07-22 株式会社トプコン 眼科撮影装置、その制御方法、プログラム、及び記録媒体
JP2022027879A (ja) * 2017-12-28 2022-02-14 株式会社トプコン 眼科撮影装置、その制御方法、プログラム、及び記録媒体
JP7050488B2 (ja) 2017-12-28 2022-04-08 株式会社トプコン 眼科撮影装置、その制御方法、プログラム、及び記録媒体
JP7134324B2 (ja) 2017-12-28 2022-09-09 株式会社トプコン 眼科撮影装置、その制御方法、プログラム、及び記録媒体

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