WO2011077633A1 - 光画像計測装置及び光アッテネータ - Google Patents

光画像計測装置及び光アッテネータ Download PDF

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Publication number
WO2011077633A1
WO2011077633A1 PCT/JP2010/006718 JP2010006718W WO2011077633A1 WO 2011077633 A1 WO2011077633 A1 WO 2011077633A1 JP 2010006718 W JP2010006718 W JP 2010006718W WO 2011077633 A1 WO2011077633 A1 WO 2011077633A1
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Prior art keywords
light
shielding
optical
unit
image
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Ceased
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PCT/JP2010/006718
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English (en)
French (fr)
Japanese (ja)
Inventor
滋 沖川
知好 阿部
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Topcon Corp
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Topcon Corp
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Priority to US13/518,240 priority Critical patent/US9072457B2/en
Priority to EP10838873.7A priority patent/EP2518471A4/en
Publication of WO2011077633A1 publication Critical patent/WO2011077633A1/ja
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]
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B26/00—Optical devices or arrangements for the control of light using movable or deformable optical elements
    • G02B26/02—Optical devices or arrangements for the control of light using movable or deformable optical elements for controlling the intensity of light
    • G02B26/04—Optical devices or arrangements for the control of light using movable or deformable optical elements for controlling the intensity of light by periodically varying the intensity of light, e.g. using choppers

Definitions

  • the present invention relates to an optical image measurement device and an optical attenuator.
  • the optical image measurement apparatus is an apparatus that forms an image of an object to be measured using optical coherence tomography (OCT).
  • OCT optical coherence tomography
  • An optical attenuator is a device that changes the amount of light attenuation.
  • OCT that forms an image representing the surface form and internal form of an object to be measured using a light beam from a laser light source or the like has attracted attention. Since OCT has no invasiveness to the human body like X-ray CT, it is expected to be applied particularly in the medical field and the biological field. For example, in the field of ophthalmology, an apparatus for forming an image of the fundus oculi, cornea, etc. has entered a practical stage.
  • Patent Document 1 discloses an apparatus to which OCT is applied.
  • the measuring arm scans an object with a rotary turning mirror (galvanomirror)
  • a reference mirror is installed on the reference arm
  • the intensity of the interference light of the light beam from the measuring arm and the reference arm is dispersed at the exit.
  • An interferometer is provided for analysis by the instrument.
  • the reference arm is configured to change the phase of the reference light beam stepwise by a discontinuous value.
  • Patent Document 1 uses a so-called “Fourier Domain OCT (Fourier Domain OCT)” technique.
  • Fourier Domain OCT Frier Domain OCT
  • a low-coherence beam is irradiated onto the object to be measured, the reflected light and the reference light are superimposed to generate interference light, and the spectral intensity distribution of the interference light is acquired and subjected to Fourier transform.
  • the form of the object to be measured in the depth direction (z direction) is imaged.
  • this type of technique is also called a spectral domain.
  • the apparatus described in Patent Document 1 includes a galvanometer mirror that scans a light beam (signal light), thereby forming an image of a desired measurement target region of the object to be measured. Since this apparatus is configured to scan the light beam only in one direction (x direction) orthogonal to the z direction, the image formed by this apparatus is in the scanning direction (x direction) of the light beam. It becomes a two-dimensional tomogram in the depth direction (z direction) along.
  • a plurality of two-dimensional tomographic images in the horizontal direction are formed by scanning (scanning) the signal light in the horizontal direction (x direction) and the vertical direction (y direction), and based on the plurality of tomographic images.
  • a technique for acquiring and imaging three-dimensional tomographic information of a measurement range is disclosed. Examples of the three-dimensional imaging include a method of displaying a plurality of tomographic images side by side in a vertical direction (referred to as stack data) and a method of rendering a plurality of tomographic images to form a three-dimensional image. Conceivable.
  • Patent Documents 3 and 4 disclose other types of OCT apparatuses.
  • Patent Document 3 scans the wavelength of light applied to an object to be measured, acquires a spectral intensity distribution based on interference light obtained by superimposing reflected light of each wavelength and reference light
  • an OCT apparatus for imaging the form of an object to be measured by performing Fourier transform on the object is described.
  • Such an OCT apparatus is called a swept source type.
  • the swept source type is a kind of Fourier domain type.
  • Patent Document 4 the traveling direction of light is obtained by irradiating the object to be measured with light having a predetermined beam diameter, and analyzing the component of interference light obtained by superimposing the reflected light and the reference light.
  • An OCT apparatus for forming an image of an object to be measured in a cross-section orthogonal to is described. Such an OCT apparatus is called a full-field type or an en-face type.
  • Patent Document 5 discloses a configuration in which OCT is applied to the ophthalmic field.
  • fundus cameras, slit lamps, and the like Prior to the application of OCT, fundus cameras, slit lamps, and the like have been used as devices for observing the eye to be examined (see, for example, Patent Document 6 and Patent Document 7).
  • a fundus camera is a device that shoots the fundus by illuminating the subject's eye with illumination light and receiving the fundus reflection light.
  • a slit lamp is a device that acquires an image of a cross-section of the cornea by cutting off a light section of the cornea using slit light.
  • An apparatus using OCT has an advantage over a fundus camera or the like in that a high-definition image can be acquired, and further, a tomographic image or a three-dimensional image can be acquired.
  • an optical attenuator (sometimes simply referred to as “attenuator”) for adjusting the amount of light (intensity).
  • an optical attenuator for adjusting the amount of light (intensity).
  • Patent Document 8 describes an attenuator that attenuates each wavelength band with a different attenuation rate so that the amount of light is uniform. This attenuator uses a rotatable neutral density filter to adjust the attenuation factor.
  • Patent Document 9 discloses a configuration using two attenuators arranged to face each other with a parallel beam interposed therebetween. The purpose of this configuration is to eliminate the restriction of the traveling direction of the light beam and to uniformly shield the light beam.
  • the conventional attenuator often cannot achieve the operation accuracy necessary for performing a suitable OCT measurement.
  • the amount of light used is large, most of the light is shielded to obtain an appropriate amount of light.
  • precise control is required to adjust the amount of light with high accuracy. That is, since the light passing through the attenuator is only a part of the original light, in order to change the amount of the passing light by, for example, several percent, the shield must be moved by a very small distance.
  • the amount of movement of the shielding plate when changing the amount of light by a predetermined amount depends on the amount of light of the original light (the amount of movement decreases as the amount of light increases), but the amount of movement according to the amount of light of the original light In order to realize this control with a conventional attenuator, precise control is required.
  • the present invention has been made to solve the above problems, and an object of the present invention is to provide an optical attenuator capable of performing precise light amount adjustment with a simple configuration and to use the optical attenuator. It is an object of the present invention to provide an optical image measurement apparatus capable of suitably detecting interference light.
  • the invention according to claim 1 divides low-coherence light into signal light and reference light, and passes through the signal light and reference light path passing through the signal light path toward the object to be measured.
  • An optical image measurement apparatus comprising: an optical system that generates and detects interference light by superimposing reference light; and an image forming unit that forms an image of the object to be measured based on the detection result of the interference light.
  • An optical attenuator that is provided in at least one target optical path among the optical path of the low-coherence light, the signal optical path, the reference optical path, and the optical path of the interference light, and can shield the target light traveling in the target optical path.
  • the optical attenuator includes a stepping motor, a cam surface having a shape corresponding to a light amount distribution in a cross section of the target light, and a cam rotated by the stepping motor; A contact portion that contacts the cam surface, a rotary shaft provided at a predetermined distance from the contact portion, and provided at a predetermined distance from the rotary shaft to shield the target light from the first direction.
  • the cam by the stepping motor comprising: a shielding mechanism including a first shielding unit capable of shielding; and a second shielding unit capable of shielding the target light from a second direction different from the first direction.
  • the contact portion moves following the displacement of the cam surface accompanying the rotation of the cam, and the shielding mechanism rotates around the rotation axis along with the movement of the contact portion.
  • the first shielding unit moves in the first direction along with the rotation of the shielding mechanism to change the shielding region of the target light, and the optical system includes the first shielding unit and the second shielding unit.
  • the interference light based on the target light partially shielded by the shielding part Detecting, the image forming unit forms an image of the object to be measured based on the detection result of the interference light, characterized in that.
  • the invention according to claim 2 is the optical image measurement device according to claim 1, wherein the cam surface is based on a Gaussian distribution as the light amount distribution and is based on the first shielding portion. The amount of movement of the first shielding portion corresponding to the unit rotation amount of the stepping motor in the first direction is reduced as the shielding area of the target light increases.
  • the invention according to claim 3 is the optical image measurement device according to claim 1, wherein the optical attenuator moves the second shielding part to change the shielding area of the target light.
  • a mechanism is provided.
  • the invention according to claim 4 is the optical image measurement device according to claim 3, wherein a tip side of the first shielding portion is a rotation direction of the shielding mechanism about the rotation axis.
  • the tip side of the second shielding part is formed in a substantially linear shape along the radial direction with respect to the diameter of the first shielding part in a state where the side of the first shielding part is arranged to shield the target light.
  • the drive mechanism is configured to change the shielding area of the target light by moving the second shielding part in a direction substantially orthogonal to the radial direction.
  • the invention according to claim 5 is the optical image measurement device according to claim 1, wherein the second shielding part shields only a central region of a cross section of the target light.
  • the invention according to claim 6 is the optical image measurement device according to claim 1, wherein the first shielding part and / or the second shielding part is relative to a cross section of the target light. It is arranged to be inclined.
  • the invention according to claim 7 is an optical attenuator capable of shielding a light beam, having a stepping motor, a cam surface having a shape corresponding to a light amount distribution in a cross section of the light beam, and the stepping motor.
  • a cam rotated by a motor; an abutting portion that abuts on the cam surface; a rotating shaft provided at a predetermined distance from the abutting portion; a rotating shaft provided at a predetermined distance from the rotating shaft;
  • a shielding mechanism including a first shielding part capable of shielding the beam from a first direction, and the contact part is associated with the rotation of the cam corresponding to the rotation of the cam by the stepping motor.
  • the shield mechanism moves following the displacement of the cam surface, the shield mechanism rotates around the rotation axis as the contact portion moves, and the first shield portion rotates along with the shield mechanism. Move in the direction of Changing the shielding region of the light beam Te, characterized in that.
  • the optical attenuator that shields the target light from two different directions since the optical attenuator that shields the target light from two different directions is provided, the light amount adjustment is performed more precisely than in the case of shielding from only a single direction. be able to. Further, by devising the shape of the cam surface, precise light amount adjustment is possible regardless of the shielding area of the target light. Thereby, it becomes possible to detect interference light suitably.
  • the optical attenuator since the target light is shielded from two different directions, the light amount can be adjusted more precisely than in the case of shielding from only one direction. . Further, by devising the shape of the cam surface, it is possible to adjust the light amount precisely regardless of the shielding area of the target light without using a high-resolution stepping motor. Therefore, it is possible to perform precise light amount adjustment with a simple configuration.
  • the optical image measurement device forms a tomographic image of an object to be measured using optical coherence tomography. Any type of OCT is applied to this optical image measurement device.
  • An image acquired by OCT may be referred to as an OCT image.
  • a measurement operation for forming an OCT image may be referred to as OCT measurement.
  • the fundus oculi observation device 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200.
  • the retinal camera unit 2 has almost the same optical system as a conventional retinal camera.
  • the OCT unit 100 is provided with an optical system for acquiring an OCT image of the fundus.
  • the arithmetic control unit 200 includes a computer that executes various arithmetic processes and control processes.
  • the fundus camera unit 2 shown in FIG. 1 is provided with an optical system for forming a two-dimensional image (fundus image) representing the surface form of the fundus oculi Ef of the eye E to be examined.
  • the fundus image includes an observation image and a captured image.
  • the observation image is, for example, a monochrome moving image formed at a predetermined frame rate using near infrared light.
  • the captured image is a color image obtained by flashing visible light, for example.
  • the fundus camera unit 2 may be configured to be able to acquire images other than these, such as a fluorescein fluorescent image, an indocyanine green fluorescent image, a spontaneous fluorescent image, and the like.
  • the fundus camera unit 2 is provided with a chin rest and a forehead for supporting the subject's face so that the face of the subject does not move, as in a conventional fundus camera. Further, the fundus camera unit 2 is provided with an illumination optical system 10 and a photographing optical system 30 as in the conventional fundus camera.
  • the illumination optical system 10 irradiates the fundus oculi Ef with illumination light.
  • the photographing optical system 30 guides the fundus reflection light of the illumination light to the imaging device (CCD image sensors 35 and 38).
  • the imaging optical system 30 guides the signal light from the OCT unit 100 to the fundus oculi Ef and guides the signal light passing through the fundus oculi Ef to the OCT unit 100.
  • the observation light source 11 of the illumination optical system 10 is composed of, for example, a halogen lamp.
  • the light (observation illumination light) output from the observation light source 11 is reflected by the reflection mirror 12 having a curved reflection surface, passes through the condensing lens 13, passes through the visible cut filter 14, and is converted into near infrared light. Become. Further, the observation illumination light is once converged in the vicinity of the photographing light source 15, reflected by the mirror 16, and passes through the relay lenses 17 and 18, the diaphragm 19 and the relay lens 20. Then, the observation illumination light is reflected by the peripheral part (region around the hole part) of the perforated mirror 21 and illuminates the fundus oculi Ef via the objective lens 22.
  • the fundus reflection light of the observation illumination light is refracted by the objective lens 22, passes through a hole formed in the central region of the aperture mirror 21, passes through the dichroic mirror 55, passes through the focusing lens 31, and then goes through the dichroic mirror. 32 is reflected. Further, the fundus reflection light passes through the half mirror 40, is reflected by the dichroic mirror 33, and forms an image on the light receiving surface of the CCD image sensor 35 by the condenser lens 34.
  • the CCD image sensor 35 detects fundus reflected light at a predetermined frame rate, for example.
  • the display device 3 displays an image (observation image) K based on fundus reflection light detected by the CCD image sensor 35.
  • the photographing light source 15 is constituted by, for example, a xenon lamp.
  • the light (imaging illumination light) output from the imaging light source 15 is applied to the fundus oculi Ef through the same path as the observation illumination light.
  • the fundus reflection light of the imaging illumination light is guided to the dichroic mirror 33 through the same path as that of the observation illumination light, passes through the dichroic mirror 33, is reflected by the mirror 36, and is reflected by the condenser lens 37 of the CCD image sensor 38.
  • An image is formed on the light receiving surface.
  • On the display device 3, an image (captured image) H based on fundus reflection light detected by the CCD image sensor 38 is displayed.
  • the display device 3 that displays the observation image K and the display device 3 that displays the captured image H may be the same or different.
  • the LCD 39 displays a fixation target and a visual target for visual acuity measurement.
  • the fixation target is a target for fixing the eye E to be examined, and is used at the time of fundus photographing or OCT measurement.
  • a part of the light output from the LCD 39 is reflected by the half mirror 40, reflected by the dichroic mirror 32, passes through the focusing lens 31 and the dichroic mirror 55, and passes through the hole of the perforated mirror 21.
  • the light is refracted by the objective lens 22 and projected onto the fundus oculi Ef.
  • the fixation position of the eye E can be changed by changing the display position of the fixation target on the screen of the LCD 39.
  • As the fixation position of the eye E for example, a position for acquiring an image centered on the macular portion of the fundus oculi Ef, or a position for acquiring an image centered on the optic disc as in the case of a conventional fundus camera And a position for acquiring an image centered on the fundus center between the macula and the optic disc.
  • the fundus camera unit 2 is provided with an alignment optical system 50 and a focus optical system 60 as in the conventional fundus camera.
  • the alignment optical system 50 generates a visual target (alignment visual target) for performing alignment (alignment) of the apparatus optical system with respect to the eye E.
  • the focus optical system 60 generates a visual target (split visual target) for focusing on the fundus oculi Ef.
  • the light (alignment light) output from the LED (Light Emitting Diode) 51 of the alignment optical system 50 is reflected by the dichroic mirror 55 via the apertures 52 and 53 and the relay lens 54, and passes through the hole portion of the perforated mirror 21. It passes through and is projected onto the cornea of the eye E by the objective lens 22.
  • the corneal reflection light of the alignment light passes through the objective lens 22 and the hole, and a part thereof passes through the dichroic mirror 55, passes through the focusing lens 31, is reflected by the dichroic mirror 32, and passes through the half mirror 40. Then, it is reflected by the dichroic mirror 33 and projected onto the light receiving surface of the CCD image sensor 35 by the condenser lens 34.
  • a light reception image (alignment target) by the CCD image sensor 35 is displayed on the display device 3 together with the observation image K.
  • the user performs alignment by performing the same operation as that of a conventional fundus camera. Further, the arithmetic control unit 200 may perform alignment by analyzing the position of the alignment target and moving the optical system.
  • the reflecting surface of the reflecting rod 67 is obliquely provided on the optical path of the illumination optical system 10.
  • the light (focus light) output from the LED 61 of the focus optical system 60 passes through the relay lens 62, is separated into two light beams by the split target plate 63, passes through the two-hole aperture 64, and is reflected by the mirror 65.
  • the light is once focused on the reflecting surface of the reflecting bar 67 by the condenser lens 66 and reflected. Further, the focus light passes through the relay lens 20, is reflected by the perforated mirror 21, and forms an image on the fundus oculi Ef by the objective lens 22.
  • the fundus reflection light of the focus light is detected by the CCD image sensor 35 through the same path as the corneal reflection light of the alignment light.
  • a light reception image (split target) by the CCD image sensor 35 is displayed on the display device 3 together with the observation image.
  • the arithmetic and control unit 200 analyzes the position of the split target and moves the focusing lens 31 and the focus optical system 60 to focus, as in the conventional case. Alternatively, focusing may be performed manually while visually checking the split target.
  • An optical path including a mirror 41, a collimator lens 42, and galvanometer mirrors 43 and 44 is provided behind the dichroic mirror 32. This optical path is guided to the OCT unit 100.
  • the galvanometer mirror 44 scans the signal light LS from the OCT unit 100 in the x direction.
  • the galvanometer mirror 43 scans the signal light LS in the y direction.
  • the OCT unit 100 is provided with an optical system for acquiring a tomographic image of the fundus oculi Ef (see FIG. 2).
  • This optical system has the same configuration as a conventional Fourier domain type OCT apparatus. That is, this optical system divides low-coherence light into reference light and signal light, and generates interference light by causing interference between the signal light passing through the fundus oculi Ef and the reference light passing through the reference optical path. It is configured to detect spectral components. This detection result (detection signal) is sent to the arithmetic control unit 200.
  • the light source unit 101 outputs a broadband low-coherence light L0.
  • the low coherence light L0 includes, for example, a near-infrared wavelength band (about 800 nm to 900 nm) and has a temporal coherence length of about several tens of micrometers. Note that near-infrared light having a wavelength band invisible to the human eye, for example, a center wavelength of about 1050 to 1060 nm, may be used as the low-coherence light L0.
  • the light source unit 101 includes a super luminescent diode (Super Luminescent Diode: SLD), an LED, and an optical output device such as an SOA (Semiconductor Optical Amplifier).
  • SLD Super Luminescent Diode
  • LED an LED
  • SOA semiconductor Optical Amplifier
  • the low coherence light L0 output from the light source unit 101 is guided to the fiber coupler 103 by the optical fiber 102, and is divided into the signal light LS and the reference light LR.
  • the fiber coupler 103 functions as both a means for splitting light (splitter) and a means for combining light (coupler), but here it is conventionally referred to as a “fiber coupler”.
  • the signal light LS is guided by the optical fiber 104 and becomes a parallel light beam by the collimator lens unit 105. Further, the signal light LS is reflected by the respective galvanometer mirrors 44 and 43, collected by the collimator lens 42, reflected by the mirror 41, transmitted through the dichroic mirror 32, and through the same path as the light from the LCD 39, the fundus oculi Ef. Is irradiated. The signal light LS is scattered and reflected on the fundus oculi Ef. The scattered light and reflected light may be collectively referred to as fundus reflected light of the signal light LS. The fundus reflection light of the signal light LS travels in the opposite direction on the same path and is guided to the fiber coupler 103.
  • the fiber coupler 103 combines the fundus reflection light of the signal light LS and the reference light LR reflected by the reference mirror 114.
  • the interference light LC thus generated is guided by the optical fiber 115 and emitted from the emission end 116. Further, the interference light LC is converted into a parallel light beam by the collimator lens 117, dispersed (spectral decomposition) by the diffraction grating 118, condensed by the condenser lens 119, and projected onto the light receiving surface of the CCD image sensor 120.
  • the diffraction grating 118 shown in FIG. 2 is a transmission type, but a reflection type diffraction grating may be used.
  • the CCD image sensor 120 is, for example, a line sensor, and detects each spectral component of the split interference light LC and converts it into electric charges.
  • the CCD image sensor 120 accumulates this electric charge and generates a detection signal. Further, the CCD image sensor 120 sends this detection signal to the arithmetic control unit 200.
  • a Michelson type interferometer is used, but any type of interferometer such as a Mach-Zehnder type can be appropriately used.
  • any type of interferometer such as a Mach-Zehnder type can be appropriately used.
  • another form of image sensor for example, a CMOS (Complementary Metal Oxide Semiconductor) image sensor or the like can be used.
  • CMOS Complementary Metal Oxide Semiconductor
  • the attenuator 300 and the light shielding plate 400 will be described.
  • the reference light LR that passes through the attenuator 300 and the light shielding plate 400 is a parallel light flux.
  • the combination of the attenuator 300 and the light shielding plate 400 is an example of the “optical attenuator” of the present invention.
  • the light (target light) to be shielded by the optical attenuator is the reference light LR.
  • the attenuator 300 and the light shielding plate 400 will be described with reference to FIGS.
  • the light shielding plate 400 of this embodiment is disposed on the fiber coupler 103 side of the attenuator 300 in the reference optical path, it may be disposed on the reference mirror 114 side.
  • the holding plate 301 of the attenuator 300 is attached to a housing (not shown) of the OCT unit 100, for example.
  • the holding plate 301 holds various members described later.
  • a stepping motor 302 is mounted on one surface side of the holding plate 301.
  • the stepping motor 302 receives the pulse signal (driving pulse) from the arithmetic control unit 200 and rotates the rotating shaft 302a by the amount of rotation corresponding to the number of pulses.
  • the rotating shaft 302a protrudes through the holding plate 301 to the other surface side.
  • the cam 303 is attached to the rotating shaft 302a.
  • the cam 303 rotates integrally with the rotation shaft 302a.
  • the cam 303 has a cam surface 303a having the following characteristic shape.
  • the cam surface 303 a is a peripheral surface of the cam 303.
  • the cross section of the reference light LR (cross section orthogonal to the traveling direction) has a predetermined light quantity distribution.
  • This light quantity distribution is approximated by a Gaussian distribution. Therefore, the cam curve is obtained assuming that the light amount distribution of the reference light LR is a Gaussian distribution.
  • This cam curve is a curve having a shape that defines the motion to be generated by the cam 303.
  • this cam curve is set so that the moving amount of the shielding portion 313 (described later) corresponding to the unit rotation amount of the stepping motor 302 becomes smaller as the shielding region of the reference light LR by the attenuator 300 increases.
  • the unit rotation amount of the stepping motor 302 means a minimum rotation angle (for example, a rotation angle corresponding to one pulse) by the stepping motor 302.
  • the unit rotation amount is called a step angle.
  • the moving amount of the shielding unit 313 means the moving distance of the shielding unit 313 when the stepping motor 302 is driven by a unit rotation amount. This amount of movement represents the positioning accuracy of the attenuator 300 and is called resolution or the like. That is, the cam curve is set so that the resolution is higher as the reference light LR is shielded more greatly.
  • the cam surface 303a is formed by cutting the peripheral edge of the original shape of the cam 303 along the cam curve set in this way. As shown in FIG. 3, the cam 303 has a shape like a ball.
  • the rotating shaft 302a is eccentrically arranged on one end side of the cam 303.
  • a light shielding link 310 is attached to a surface of the holding plate 301 on the same side as the cam 303 via a rotating shaft 311.
  • the light shielding link 310 is a member that changes the shielding region of the reference light LR in response to the operation of the cam 303.
  • the light shielding link 310 is an example of the “shielding mechanism” of the present invention.
  • the rotation shaft 311 is disposed at a position near the reference light path (the optical axis A) of the light shielding link 310.
  • the light shielding link 310 rotates (swings) about the rotation shaft 311.
  • the rotation direction of the light shielding link 310 is indicated by a symbol B (see FIG. 3 and the like).
  • the light shielding link 310 has a contact portion 312 that contacts the cam surface 303a.
  • the contact portion 312 is provided at a position opposite to the reference optical path with the rotation shaft 311 interposed therebetween.
  • the contact portion 312 has a surface that contacts the cam surface 303a.
  • the light shielding link 310 is urged by the elastic force of the spring 320 in the direction in which the contact portion 312 is pressed against the cam surface 303a. Thereby, when the cam 303 rotates, the contact part 312 follows the displacement of the cam surface 303a.
  • the distance from the rotation shaft 302a of the portion of the cam surface 303a facing the contact portion 312 is displaced, but the contact portion 312 is in contact with the cam surface 303a by the action of the spring 320. It is displaced together with the cam surface 303a while maintaining the state. Due to the displacement of the contact portion 312, the light shielding link 310 swings about the rotation shaft 311.
  • the shielding part 313 is provided in the edge part on the opposite side to the contact part 312 in the light-shielding link 310. As shown in FIG.
  • the shielding part 313 is an example of the “first shielding part” in the present invention.
  • the shielding part 313 is inserted into and removed from the reference optical path by the swinging of the light shielding link 310.
  • the shielding part 313 is a plate-like part extending in the insertion / removal direction with respect to the reference optical path in the light shielding link 310.
  • a side 313 a at the tip of the shielding portion 313 that is inserted into the reference optical path is formed in a substantially linear shape along the radial direction C with respect to the rotational direction B of the light shielding link 310.
  • the light shielding link 310 is inserted into the reference optical path from the right direction in FIG. 3, and the shielding area is one area obtained by cutting the disk with a straight line (the shielding area indicated by the oblique lines in FIGS. 6A and 6B). See UR).
  • the surface (irradiation surface) irradiated with the reference light LR in the shielding unit 313 is inclined with respect to the cross section of the reference light LR. That is, the shielding part 313 is disposed such that the normal direction of the irradiation surface is inclined with respect to the optical axis A of the reference optical path. Thereby, it is possible to avoid a situation in which the reflected light of the reference light LR from the irradiation surface is mixed into the interference light LC. Similarly, with respect to the light shielding plate 400, the irradiated noodles are inclined with respect to the optical axis A.
  • FIG. 4 shows a state in which the shielding unit 313 completely shields the reference light path, that is, a state in which the reference light LR does not pass at all.
  • FIG. 5 shows a state in which the shielding portion 313 is completely opened in the reference light path, that is, when all the reference light LR passes (more specifically, if the light is blocked by the light shielding plate 400, all the passing light passes therethrough. Represents the case).
  • the light shielding link 310 shields / opens the reference light path by performing such a rotational operation (swinging operation) according to the rotation of the cam 303. As shown in these drawings, the direction of the side 313a at the tip of the shielding portion 313 (that is, the radial direction C) changes with the rotation operation of the light shielding link 310.
  • FIG. 6A and 6B show a change state of the shielding region UR of the reference light LR by the attenuator 300.
  • FIG. FIG. 6A shows a state in which much of the reference light LR (shielded region UR) is shielded by the attenuator 300 and light corresponding to the remaining small portion passes.
  • FIG. 6B shows a state in which a small part (shielding region UR) of the reference light LR is shielded by the attenuator 300 and light corresponding to many remaining parts passes therethrough.
  • the cam surface 303a Since the cam surface 303a has the shape as described above, the resolution of the shielding operation is high in the state shown in FIG. 6A, and the resolution is low in the state shown in FIG. 6B. Thereby, it is possible to adjust the light amount with accuracy according to the size of the shielding region UR of the reference light LR (that is, the light amount of the reference light LR used for OCT measurement).
  • the light shielding plate 400 will be described. As shown in FIG. 3, the light shielding plate 400 can be inserted into and removed from the reference optical path (its optical axis A). The light shielding plate 400 is moved by a drive mechanism 410 described later, and shields the reference light LR from a different direction from the attenuator 300. The moving direction of the light shielding plate 400 is indicated by a symbol D (see FIG. 3 and the like).
  • the light shielding plate 400 is an example of the “second shielding portion” in the present invention.
  • the shielding direction (first direction) by the attenuator 300 is the rotation direction B of the light shielding link 310
  • the shielding direction (second direction) by the light shielding plate 400 is a direction orthogonal to the moving direction D of the light shielding plate 400.
  • the light shielding plate 400 is a plate-like member having a trapezoidal surface that is irradiated with the reference light LR.
  • a region on the side of the front end portion 400a corresponding to the trapezoidal oblique side shields the reference light LR.
  • the moving direction D of the light shielding plate 400 is a direction in which a side (bottom side) opposite to the oblique side extends. Therefore, when the light shielding plate 400 is moved in the direction D, the oblique side is displaced as if it moves up and down the reference optical path.
  • the side of the front end of the light shielding plate 400 (the front end portion 400a) is a substantially straight line that is oblique to the radial direction C in a state where the front end side 313a of the shielding unit 313 is disposed at a position where the reference light LR is shielded. It is formed in a shape.
  • the direction of the radial direction C changes with the rotation of the light shielding link 310, but when the shielding portion 313 shields at least part of the reference light LR, the front end portion 400a (substantially omitted) of the light shielding plate 400. Is formed obliquely with respect to the radial direction C at this time.
  • the attenuator 300 and the light shielding plate 400 can shield the reference light LR from different directions.
  • the drive mechanism 410 changes the shielding region of the reference light LR by moving the light shielding plate 400 in the direction D substantially orthogonal to the radial direction C at this time.
  • FIG. 7A and 7B show a change state of the shielding region VR of the reference light LR by the light shielding plate 400.
  • FIG. FIG. 7A shows a state where a little less than half of the reference light LR (shielded region VR) is shielded by the light shielding plate 400 and light corresponding to the remaining half of the reference light LR passes.
  • FIG. 7B shows a state in which a small part (shielding region VR) of the reference light LR is shielded by the light shielding plate 400 and light corresponding to many remaining parts passes through.
  • FIG. 8 shows an example of the shielding state of the reference light LR when the attenuator 300 and the light shielding plate 400 are used in combination.
  • the shielding region WR shown in FIG. 8 is obtained by shielding the reference light LR about half by the attenuator 300 from the right side of the drawing and further shielding about half by the shielding plate 400 from above the drawing.
  • the configuration of the arithmetic control unit 200 will be described.
  • the arithmetic control unit 200 analyzes the detection signal input from the CCD image sensor 120 and forms an OCT image of the fundus oculi Ef.
  • the arithmetic processing for this is the same as that of a conventional Fourier domain type OCT apparatus.
  • the arithmetic control unit 200 controls each part of the fundus camera unit 2, the display device 3, and the OCT unit 100.
  • the arithmetic and control unit 200 displays an OCT image such as a tomographic image G (see FIG. 2) of the fundus oculi Ef on the display device 3.
  • the arithmetic control unit 200 controls the operation of the observation light source 11, the imaging light source 15 and the LEDs 51 and 61, the operation control of the LCD 39, the movement control of the focusing lens 31, the movement control of the reflector 67, and the focus.
  • the movement control of the optical system 60, the operation control of each galvanometer mirror 43, 44, etc. are performed.
  • the arithmetic control unit 200 controls the operation of the light source unit 101, the movement control of the reference mirror 114 and the collimator lens 113, the operation control of the CCD image sensor 120, the operation control of the attenuator 300, and the light shielding plate 400. Control the operation of
  • the arithmetic control unit 200 includes, for example, a microprocessor, a RAM, a ROM, a hard disk drive, a communication interface, and the like, as in a conventional computer.
  • a computer program for controlling the fundus oculi observation device 1 is stored in a storage device such as a hard disk drive.
  • the arithmetic control unit 200 may include a dedicated circuit board that forms an OCT image based on a detection signal from the CCD image sensor 120.
  • the arithmetic control unit 200 may include an operation device (input device) such as a keyboard and a mouse, and a display device such as an LCD.
  • the fundus camera unit 2, the display device 3, the OCT unit 100, and the arithmetic control unit 200 may be configured integrally (that is, in a single casing) or may be configured separately.
  • Control system The configuration of the control system of the fundus oculi observation device 1 will be described with reference to FIG.
  • the control system of the fundus oculi observation device 1 is configured around the control unit 210 of the arithmetic control unit 200.
  • the control unit 210 includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, communication interface, and the like.
  • the control unit 210 is provided with a main control unit 211 and a storage unit 212.
  • the main control unit 211 performs the various controls described above.
  • the main control unit 211 controls the scanning driving unit 70 and the focusing driving unit 80 of the fundus camera unit 2, and further the light source unit 101, the reference driving unit 130, the stepping motor 302, and the driving mechanism 410 of the OCT unit 100.
  • the scanning drive unit 70 includes a servo motor, for example, and independently changes the directions of the galvanometer mirrors 43 and 44.
  • the focusing drive unit 80 includes, for example, a stepping motor, and moves the focusing lens 31 in the optical axis direction. Thereby, the focus position of the light toward the fundus oculi Ef is changed.
  • the reference driving unit 130 includes a stepping motor, for example, and integrally moves the collimator lens 113 and the reference mirror 114 along the traveling direction of the reference light LR.
  • the driving mechanism 410 moves the light shielding plate 400 in the direction D.
  • the driving mechanism 410 includes, for example, a stepping motor and a mechanism that moves the light shielding plate 400 by transmitting the driving force of the stepping motor.
  • the main control unit 211 performs a process of writing data to the storage unit 212 and a process of reading data from the storage unit 212.
  • the storage unit 212 stores various data. Examples of the data stored in the storage unit 212 include OCT image image data, fundus image data, and examined eye information.
  • the eye information includes information about the subject such as patient ID and name, and information about the eye such as left / right eye identification information.
  • the image forming unit 220 forms tomographic image data of the fundus oculi Ef based on the detection signal from the CCD image sensor 120.
  • This process includes processes such as noise removal (noise reduction), filter processing, and FFT (Fast Fourier Transform) as in the conventional Fourier domain type optical coherence tomography.
  • the image forming unit 220 includes, for example, the above-described circuit board and communication interface.
  • image data and “image” presented based on the “image data” may be identified with each other.
  • the image processing unit 230 performs various types of image processing and analysis processing on the image formed by the image forming unit 220. For example, the image processing unit 230 executes various correction processes such as image brightness correction and dispersion correction.
  • the image processing unit 230 forms image data of a three-dimensional image of the fundus oculi Ef by executing an interpolation process for interpolating pixels between tomographic images formed by the image forming unit 220.
  • the image data of a three-dimensional image means image data in which pixel positions are defined by a three-dimensional coordinate system.
  • image data of a three-dimensional image there is image data composed of voxels arranged three-dimensionally. This image data is called volume data or voxel data.
  • the image processing unit 230 When displaying an image based on volume data, the image processing unit 230 performs a rendering process (such as volume rendering or MIP (Maximum Intensity Projection)) on the volume data, and views the image from a specific line-of-sight direction.
  • Image data of a pseudo three-dimensional image is formed. This pseudo three-dimensional image is displayed on a display device such as the display unit 240.
  • stack data of a plurality of tomographic images is image data of a three-dimensional image.
  • the stack data is image data obtained by three-dimensionally arranging a plurality of tomographic images obtained along a plurality of scanning lines based on the positional relationship of the scanning lines. That is, the stack data is image data obtained by expressing a plurality of tomographic images originally defined by individual two-dimensional coordinate systems using one three-dimensional coordinate system (that is, embedding in one three-dimensional space). is there.
  • the image processing unit 230 can form a tomographic image at an arbitrary cross section based on image data of a three-dimensional image.
  • a cross section designated manually or automatically pixels (voxels or the like) located on the cross section are specified, and the specified pixels are two-dimensionally arranged to determine the fundus oculi Ef in the cross section. It is executed by forming image data representing the form.
  • the image processing unit 230 includes, for example, the above-described microprocessor, RAM, ROM, hard disk drive, circuit board, and the like.
  • the image forming unit 220 and the image processing unit 230 are examples of the “image forming unit” of the present invention.
  • the display unit 240 includes the display device of the arithmetic control unit 200 described above.
  • the operation unit 250 includes the operation device of the arithmetic control unit 200 described above.
  • the operation unit 250 may include various buttons and keys provided on the housing of the fundus oculi observation device 1 or outside.
  • the operation unit 250 may include a joystick, an operation panel, or the like provided on the housing.
  • the display unit 240 may include various display devices such as a touch panel monitor provided on the housing of the fundus camera unit 2.
  • the display unit 240 and the operation unit 250 need not be configured as individual devices.
  • a device in which a display function and an operation function are integrated, such as a touch panel monitor, can be used.
  • Examples of the scanning mode of the signal light LS by the fundus oculi observation device 1 include a horizontal scan, a vertical scan, a cross scan, a radiation scan, a circle scan, a concentric scan, and a spiral (vortex) scan. These scanning modes are selectively used as appropriate in consideration of the observation site of the fundus, the analysis target (such as retinal thickness), the time required for scanning, the precision of scanning, and the like.
  • the horizontal scan is to scan the signal light LS in the horizontal direction (x direction).
  • the horizontal scan also includes an aspect in which the signal light LS is scanned along a plurality of horizontal scanning lines arranged in the vertical direction (y direction). In this aspect, it is possible to arbitrarily set the scanning line interval. Further, the above-described three-dimensional image can be formed by sufficiently narrowing the interval between adjacent scanning lines (three-dimensional scanning). The same applies to the vertical scan.
  • the cross scan scans the signal light LS along a cross-shaped trajectory composed of two linear trajectories (straight trajectories) orthogonal to each other.
  • the signal light LS is scanned along a radial trajectory composed of a plurality of linear trajectories arranged at a predetermined angle.
  • the cross scan is an example of a radiation scan.
  • the circle scan scans the signal light LS along a circular locus.
  • the signal light LS is scanned along a plurality of circular trajectories arranged concentrically around a predetermined center position.
  • a circle scan is an example of a concentric scan.
  • the signal light LS is scanned along a spiral (spiral) locus while the radius of rotation is gradually reduced (or increased).
  • the galvanometer mirrors 43 and 44 are configured to scan the signal light LS in directions orthogonal to each other, the signal light LS can be scanned independently in the x direction and the y direction, respectively. Furthermore, by simultaneously controlling the directions of the galvanometer mirrors 43 and 44, it is possible to scan the signal light LS along an arbitrary locus on the xy plane. Thereby, various scanning modes as described above can be realized.
  • a tomographic image in the depth direction (z direction) along the scanning line (scanning locus) can be formed.
  • the above-described three-dimensional image can be formed.
  • the region on the fundus oculi Ef to be scanned with the signal light LS as described above, that is, the region on the fundus oculi Ef to be subjected to OCT measurement is referred to as a scanning region.
  • the scanning area in the three-dimensional scan is a rectangular area in which a plurality of horizontal scans are arranged.
  • the scanning area in the concentric scan is a disk-shaped area surrounded by the locus of the circular scan with the maximum diameter.
  • the scanning area in the radial scan is a disk-shaped (or polygonal) area connecting both end positions of each scan line.
  • the fundus oculi observation device 1 is provided with an optical attenuator for adjusting the amount of interference light LC detected by the CCD image sensor 120.
  • an optical attenuator may be provided in the optical path of the low coherence light L0, the signal optical path, and the optical path of the interference light LC. It is also possible to provide optical attenuators on any two or more of these optical paths.
  • An optical path in which an optical attenuator is provided, that is, an optical path that guides light that is an object of light amount adjustment may be referred to as a target optical path.
  • the optical attenuator includes an attenuator 300, a light shielding plate 400, and a drive mechanism 410.
  • the attenuator 300 and the drive mechanism 410 are controlled by the arithmetic control unit 200, respectively.
  • the attenuator 300 includes a stepping motor 302, a cam 303, and a light shielding link 310.
  • the cam 303 has a cam surface 303a having a shape corresponding to the light amount distribution in the cross section of the reference light LR.
  • the cam 303 is rotated by a stepping motor 302.
  • the light shielding link 310 includes a rotation shaft 311, a contact portion 312, and a shielding portion 313.
  • the contact portion 312 contacts the cam surface 303a.
  • the rotation shaft 311 is provided at a predetermined distance from the contact portion 312.
  • the shielding unit 313 is provided at a predetermined distance from the rotating shaft 311 and can shield the reference light LR from the first direction.
  • predetermined distances have various factors such as the unit rotation amount of the stepping motor 302, the size of the cam 303 (the size of the cam surface 303a), the size of the light shielding link 310, the cross-sectional diameter of the reference light LR, and the resolution of the shielding operation. Set in consideration.
  • the light shielding plate 400 can shield the reference light LR from a second direction different from the shielding direction (first direction) by the attenuator 300.
  • the light shielding plate 400 is moved by the driving mechanism 410 to change the shielding area.
  • the contact portion 312 moves following the displacement of the cam surface 303a accompanying the rotation of the cam 303.
  • the light shielding link 310 rotates about the rotation shaft 311 as the contact portion 312 moves.
  • the shielding unit 313 moves in the first direction (direction D) as the light shielding link 310 rotates, and changes the shielding region of the reference light LR.
  • the attenuator 300 and the light shielding plate 400 can be configured to control the operation according to the operation on the operation unit 250, or the attenuator 300 and the light shielding plate 400 are automatically referred to by referring to the amount of light received by the CCD image sensor 120. It is also possible to configure to control the operation.
  • the attenuator 300 and the light shielding plate 400 are used as follows, for example. First, the attenuator 300 and the light shielding plate 400 are both opened, and the CCD image sensor 120 receives the interference light LC. The suitability of this received light amount is confirmed. If the received light amount is too large, the light shielding plate 400 is moved to roughly adjust the received light amount of the interference light LC.
  • the amount of received light is precisely adjusted by changing the shielding area by the attenuator 300 while confirming the amount of received interference light LC. Since the cam surface 303a has the shape as described above, precise adjustment is possible regardless of the size of the shielding area of the reference light LR by the shielding portion 313.
  • the fundus oculi observation device 1 After changing the shielding area of the reference light LR in this way, that is, after adjusting the amount of interference light LC received by the CCD image sensor 120, the fundus oculi observation device 1 is partially shielded by the attenuator 300 and the light shielding plate 400. The interference light LC obtained by superimposing the LR and the signal light LS is detected. Furthermore, the fundus oculi observation device 1 forms an OCT image of the fundus oculi Ef based on the detection result of the interference light LC.
  • the attenuator 300 or The light amount can be precisely adjusted using the light shielding plate 400.
  • the interference light LC can be suitably detected, and a good OCT image can be obtained.
  • cam surface 303a to have the above-described shape, it is possible to achieve operation accuracy required for OCT measurement without using a stepping motor having a particularly high resolution (that is, a small step angle). In particular, even when the amount of light used is large and interference light obtained by blocking most of the light is detected, the amount of light can be adjusted with high accuracy.
  • reference light LR is configured to be shielded from two different directions, precise light amount adjustment is possible.
  • object light may be shielded from three or more different directions. This configuration is included in the scope of the present invention because it is shielded from (at least) two directions.
  • the attenuator 300 and the light shielding plate 400 do not require a complicated configuration. Therefore, the optical attenuator according to this embodiment can perform fine light amount adjustment with a simple configuration.
  • the second shielding unit may be configured such that a rectangular light shielding plate that can be translated by a driving mechanism is inserted into and removed from the target optical path.
  • the second shielding unit may be configured to insert and remove a rectangular light shielding plate that can rotate around the rotation axis outside the target optical path into the target optical path.
  • the second shielding part may be configured to shield only a region having a large amount of light in the cross section of the target light, that is, a central region of the cross section.
  • a light-shielding plate it is possible to use a light-shielding portion provided at the center of a transparent plate member.
  • a plate-like member consisting only of the light-shielding part may be hung with a thread-like member or the like and arranged in the central region of the reference optical path.
  • These light shielding portions are formed in a disk shape, for example. You may comprise so that the size of the light-shielding part of this modification can be changed. As an example, light shielding portions having different sizes can be selectively used.
  • the attenuator 300 having the first shielding part and the light shielding plate 400 as the second shielding part are provided separately.
  • the attenuator 300 a function as the second shielding part.
  • the shielding unit 313 can perform the shielding operation in the radial direction C by configuring the attenuator 300 itself or the light shielding link 310 so as to be movable in the radial direction C of FIG.
  • the shielding operation in the rotation direction B is performed in the same manner as in the above embodiment.
  • the attenuator 300 itself or the light shielding link 310 is moved in the radial direction C by a drive mechanism (not shown).
  • the position of the reference mirror 114 is changed to change the optical path length difference between the optical path of the signal light LS and the optical path of the reference light LR, but the method of changing the optical path length difference is limited to this. Is not to be done.
  • the optical path length difference can be changed by moving the fundus camera unit 2 or the OCT unit 100 with respect to the eye E to change the optical path length of the signal light LS. It is also effective to change the optical path length difference by moving the measurement object in the depth direction (z direction), particularly when the measurement object is not a living body part.
  • the computer program in the above embodiment can be stored in any recording medium readable by a computer.
  • this recording medium for example, an optical disk, a magneto-optical disk (CD-ROM / DVD-RAM / DVD-ROM / MO, etc.), a magnetic storage medium (hard disk / floppy (registered trademark) disk / ZIP, etc.), etc. are used. Is possible. It can also be stored in a storage device such as a hard disk drive or memory.

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US9072457B2 (en) 2015-07-07
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