WO2014054394A1 - 眼科観察装置 - Google Patents
眼科観察装置 Download PDFInfo
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- WO2014054394A1 WO2014054394A1 PCT/JP2013/074616 JP2013074616W WO2014054394A1 WO 2014054394 A1 WO2014054394 A1 WO 2014054394A1 JP 2013074616 W JP2013074616 W JP 2013074616W WO 2014054394 A1 WO2014054394 A1 WO 2014054394A1
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- focusing lens
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- measurement
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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
- A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
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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]
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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
- A61B3/0016—Operational features thereof
- A61B3/0025—Operational features thereof characterised by electronic signal processing, e.g. eye models
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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
- A61B3/0016—Operational features thereof
- A61B3/0041—Operational features thereof characterised by display arrangements
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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
- A61B3/0016—Operational features thereof
- A61B3/0041—Operational features thereof characterised by display arrangements
- A61B3/0058—Operational features thereof characterised by display arrangements for multiple images
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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
- A61B3/0075—Apparatus for testing the eyes; Instruments for examining the eyes provided with adjusting devices, e.g. operated by control lever
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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
- A61B3/103—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining refraction, e.g. refractometers, skiascopes
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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
- A61B3/14—Arrangements specially adapted for eye photography
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- 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
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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
- A61B3/113—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining or recording eye movement
Definitions
- the present invention relates to an ophthalmologic observation apparatus that acquires an image of an eye to be examined.
- OCT optical coherence tomography
- Patent Document 1 discloses an apparatus using a so-called “Fourier Domain OCT (Fourier Domain OCT)” technique. That is, this apparatus irradiates the object to be measured with a beam of low coherence light, superimposes the reflected light and the reference light to generate interference light, acquires the spectral intensity distribution of the interference light, and performs Fourier transform. By performing the conversion, the form of the object to be measured in the depth direction (z direction) is imaged. Further, this apparatus includes a galvanometer mirror that scans a light beam (signal light) in one direction (x direction) orthogonal to the z direction, thereby forming an image of a desired measurement target region of the object to be measured. It has become. An image formed by this apparatus is a two-dimensional tomographic image in the depth direction (z direction) along the scanning direction (x direction) of the light beam. This method is also called a spectral domain.
- Fourier Domain OCT Frourier Domain OCT
- 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.
- this three-dimensional imaging for example, a method of displaying a plurality of tomographic images side by side in a vertical direction (referred to as stack data or the like), volume data (voxel data) based on the stack data is rendered, and a three-dimensional image is rendered. There is a method of forming.
- Patent Documents 3 and 4 disclose other types of OCT apparatuses.
- the wavelength of light irradiated to a measured object is scanned (wavelength sweep), and interference intensity obtained by superimposing reflected light of each wavelength and reference light is detected to detect spectral intensity distribution.
- an OCT apparatus for imaging the form of an object to be measured by performing Fourier transform on the obtained image 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 Prior to the application of OCT, fundus cameras, slit lamps, SLO (Scanning Laser Ophthalmoscope), and the like were used as devices for observing the subject's eye (for example, Patent Document 6, Patent Document 7, Patent Document). 8).
- 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.
- the SLO is an apparatus that images the fundus surface by scanning the fundus with laser light and detecting the reflected light with a highly sensitive element such as a photomultiplier tube. According to these apparatuses, an image (front image) obtained by photographing the fundus or anterior eye portion from the front can be obtained.
- 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 apparatus using OCT can be applied to observation of various parts of an eye to be examined and can acquire high-definition images, it has been applied to diagnosis of various ophthalmic diseases.
- an optical system for acquiring a front image and an optical for OCT measurement are used.
- the system has a common focusing lens.
- the wavelength of light for front image acquisition (visible light, etc.) is different from the wavelength of light for OCT measurement (near-infrared light, etc.)
- the optimum focus positions for both photographings are different.
- An object of the present invention is to provide a technique capable of performing both acquisition of a front image of an eye to be examined and OCT measurement in a suitable focus state.
- the invention described in claim 1 includes a first focusing lens, and includes a photographing optical system that performs photographing for acquiring a front image of the eye to be examined, and a second focusing lens.
- a measurement optical system that performs optical coherence tomography measurement for obtaining a tomographic image of the eye to be examined, and an optical path of the imaging optical system at a position closer to the eye to be examined than the first focusing lens and the second focusing lens
- an optical path of the measurement optical system, a first drive unit for moving the first focusing lens along the optical axis of the photographing optical system, and an optical axis of the measurement optical system Is an ophthalmologic observation apparatus having a second driving unit for moving the second focusing lens along the axis, and a control unit for controlling the first driving unit and the second driving unit, respectively.
- the invention according to claim 2 is the ophthalmologic observation apparatus according to claim 1, wherein the photographing optical system performs photographing to acquire a front image of the fundus of the eye to be examined, and the measuring optical system Has optical power coherence tomography measurement for acquiring a tomographic image of the fundus of the subject's eye, and has a refractive power acquisition unit that acquires the refractive power of the subject's eye, and the control unit is based on the acquired refractive power A first target position acquisition unit that acquires a target position of the first focusing lens and / or the second focusing lens, and the first focusing lens and / or the second focusing position at the acquired target position.
- the first driving unit and / or the second driving unit are controlled so as to move the focusing lens.
- the invention according to claim 3 is the ophthalmologic observation apparatus according to claim 2, wherein the photographing optical system includes an infrared photographing optical system for photographing the fundus using infrared light,
- the refractive power acquisition unit is a projection optical system that projects a focus index indicating a focus state of the photographing optical system with respect to the fundus onto the fundus, and a fundus in a state where the focus index is projected on the infrared photographing optical system.
- An analysis unit that obtains the refractive power of the eye to be examined by analyzing a front image obtained by photographing.
- the invention according to claim 4 is the ophthalmologic observation apparatus according to claim 2 or claim 3, wherein the control unit corresponds to the value of the eye refractive power and the position of the first focusing lens.
- the control unit corresponds to the value of the eye refractive power and the position of the first focusing lens.
- a storage unit that stores in advance first attached information, second correspondence information in which a value of eye refractive power and a position of the second focusing lens are associated, and the first target position acquisition unit Acquires each target position of the first focusing lens and the second focusing lens based on the refractive power acquired by the refractive power acquisition unit, the first correspondence information, and the second correspondence information. It is characterized by that.
- the invention according to claim 5 is the ophthalmic observation apparatus according to claim 1, wherein the control unit performs the second focusing when optical coherence tomography measurement is performed by the measurement optical system.
- a second target position acquisition unit configured to acquire a target position of the first focusing lens based on a lens position; and the first driving unit configured to move the first focusing lens to the acquired target position. It is characterized by controlling.
- the invention according to claim 6 is the ophthalmic observation apparatus according to claim 5, wherein the measurement optical system repeatedly performs optical coherence tomography measurement on substantially the same cross section of the eye to be examined.
- the second target position acquisition unit is configured to detect the first focusing lens based on the position of the second focusing lens set based on a plurality of tomographic images acquired by repetitive optical coherence tomography measurement. A target position is acquired.
- the invention according to claim 7 is the ophthalmologic observation apparatus according to claim 1, wherein the tomographic image acquired by optical coherence tomography measurement by the measurement optical system is displayed and displayed.
- An operation unit for designating a position in the tomographic image, and the control unit is configured to control the first focusing lens and / or the second focusing lens based on the position designated by the operation unit.
- a third target position acquisition unit configured to acquire a target position, and the first driving unit and / or the second focus lens so as to move the first focusing lens and / or the second focusing lens to the acquired target position;
- the second drive unit is controlled.
- the invention according to claim 8 is the ophthalmologic observation apparatus according to claim 7, wherein the measurement optical system repeatedly performs optical coherence tomography measurement on substantially the same cross section of the eye to be examined.
- the display unit displays a plurality of tomographic images acquired by repetitive optical coherence tomography measurement as a moving image, and the control unit displays the moving image in response to a predetermined operation performed by the operation unit.
- the invention according to claim 9 is the ophthalmic observation apparatus according to claim 7, wherein the measurement optical system repeatedly performs optical coherence tomography measurement on substantially the same cross section of the eye to be examined.
- the display unit displays a moving image of a plurality of tomographic images acquired by repetitive optical coherence tomography measurement, and is a position specifying image that can be moved with respect to the moving image by a predetermined operation by the operation unit.
- the third target position acquisition unit acquires the target position based on a position specified by an operation on the position specifying image.
- the invention according to claim 10 is the ophthalmologic observation apparatus according to claim 9, wherein the control unit performs the second focusing when the repetitive optical coherence tomography measurement is performed.
- the position specifying image indicating the position on the moving image corresponding to the position of the lens is displayed.
- the invention according to claim 11 is the ophthalmologic observation apparatus according to any one of claims 7 to 10, wherein the tomogram is analyzed by analyzing the tomogram displayed on the display unit.
- the display unit includes a layer region specifying unit that specifies a layer region corresponding to a predetermined layer, and the display unit displays a layer image indicating the specified layer region on the tomographic image.
- the invention according to claim 12 is the ophthalmic observation apparatus according to claim 1, wherein the measurement optical system performs optical coherence tomography measurement for acquiring a tomographic image of the fundus of the eye to be examined.
- a projection optical system that projects a focus index indicating the focus state of the photographing optical system with respect to the fundus onto the fundus; and an intensity acquisition unit that acquires the intensity of the interference signal obtained by the measurement optical system.
- the control unit controls the second driving unit based on the intensity acquired by the intensity acquisition unit.
- the invention according to claim 13 is the ophthalmologic observation apparatus according to claim 12, wherein the control unit controls the second driving unit to move the second focusing lens.
- a plurality of interference signals corresponding to a plurality of positions of the second focusing lens are acquired, and based on the intensity of the plurality of interference signals acquired by the intensity acquisition unit, the first A fourth target position acquisition unit that acquires a target position of the two focusing lens is included, and the second driving unit is controlled to move the second focusing lens to the acquired target position.
- the invention according to claim 14 is the ophthalmologic observation apparatus according to claim 13, wherein the fourth target position acquisition unit specifies and specifies a maximum intensity among the intensities of the plurality of interference signals. The position of the focusing lens corresponding to the maximum intensity is set as a target position.
- the invention according to claim 15 is the ophthalmologic observation apparatus according to claim 13 or claim 14, wherein the control unit determines the second focusing lens in the acquisition of the plurality of interference signals. It moves within the range.
- the invention described in claim 16 is the ophthalmologic observation apparatus according to claim 15, wherein the predetermined range includes a position of the second focusing lens determined in advance based on the focusing index. It is characterized by that.
- the invention according to claim 17 is the ophthalmologic observation apparatus according to claim 16, characterized in that the center of the predetermined range is the position determined in advance.
- the invention according to claim 18 is the ophthalmologic observation apparatus according to any one of claims 12 to 17, wherein the photographing optical system uses infrared light to detect the fundus of the eye to be examined.
- a front image obtained by photographing the fundus in a state in which a focus index is projected with the infrared photographing optical system including an infrared photographing optical system that performs photographing for obtaining a front image; And moving the first focusing lens and the projection optical system to focus the photographing optical system, and focusing the measurement optical system based on the focusing result.
- the invention according to claim 19 is the ophthalmologic observation apparatus according to claim 1, wherein the measurement optical system performs optical coherence tomography measurement for acquiring a tomographic image of the fundus of the subject eye, The imaging based on the measurement value, including a storage unit that stores a measurement value of the refractive power of the eye to be obtained in advance and an intensity acquisition unit that acquires an intensity of an interference signal obtained by the measurement optical system After the focusing of the optical system and the measurement optical system, the control unit controls the second driving unit based on the intensity acquired by the intensity acquisition unit.
- the invention described in claim 20 is the ophthalmologic observation apparatus according to claim 19, further comprising a refractive power acquisition unit that acquires the refractive power of the eye to be examined, and the control unit acquires the acquired refractive power. Is stored in the storage unit as the measured value.
- the ophthalmic observation apparatus has a function of acquiring a tomographic image or a three-dimensional image of the eye to be examined (fundus, anterior eye portion, etc.) using OCT, and a function of acquiring a front image by photographing the eye to be examined.
- OCT image an image acquired by OCT
- OCT measurement optical coherence tomography measurement
- the ophthalmic observation apparatus described below can acquire an OCT image using the spectral domain OCT technique, as in the apparatus disclosed in Patent Document 5.
- the configuration according to the present invention can be applied to an ophthalmic observation apparatus using a type other than the spectral domain, for example, a swept source OCT technique.
- an apparatus combining an OCT apparatus and a fundus camera will be described.
- the ophthalmologic observation apparatus 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200.
- the fundus camera unit 2 includes an optical system that is substantially the same as a conventional fundus 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 acquiring a front 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 may be, for example, a color image obtained by flashing visible light, or a monochrome still image using near infrared light or visible light as illumination light.
- 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. Further, the fundus camera unit 2 is provided with an illumination optical system 10 and a photographing optical system 30.
- 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 an imaging device (CCD image sensor (sometimes simply referred to as a CCD) 35, 38).
- CCD image sensor sometimes simply referred to as a CCD
- 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 at the peripheral portion (region around the hole portion) of the aperture mirror 21, passes through the dichroic mirror 46, and is refracted by the objective lens 22 to illuminate the fundus oculi Ef.
- An LED Light Emitting Diode
- the fundus reflection light of the observation illumination light is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through the hole formed in the central region of the perforated mirror 21, passes through the dichroic mirror 55, and is a focusing lens. It is reflected by the mirror 32 via 31. Further, the fundus reflection light passes through the half mirror 39A, 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.
- the CCD image sensor 35 detects fundus reflected light at a predetermined frame rate, for example.
- On the display device 3 an image (observation image) based on fundus reflection light detected by the CCD image sensor 35 is displayed.
- an observation image based on fundus reflection light detected by the CCD image sensor 35 is displayed.
- the optical system that illuminates the eye E with the observation illumination light and detects the reflected light is an example of an infrared imaging optical system.
- 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) based on fundus reflection light detected by the CCD image sensor 38 is displayed.
- the display device 3 that displays the observation image and the display device 3 that displays the captured image may be the same or different.
- an infrared captured image is displayed. It is also possible to use an LED as a photographing light source.
- the LCD (Liquid Crystal Display) 39 displays a fixation target and an eyesight measurement index.
- the fixation target is an index 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 39A, reflected by the mirror 32, passes through the focusing lens 31 and the dichroic mirror 55, passes through the hole of the perforated mirror 21, and reaches the dichroic.
- the light passes through the mirror 46, is refracted by the objective lens 22, and is 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. It is also possible to arbitrarily change the display position of the fixation target.
- 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 an index (alignment index) for performing alignment (alignment) of the apparatus optical system with respect to the eye E.
- the focus optical system 60 generates an index (split index) for focusing on the fundus oculi Ef.
- the light (alignment light) output from the LED 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, passes through the hole of the perforated mirror 21, and reaches the dichroic mirror 46. 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, the dichroic mirror 46 and the hole, part of which passes through the dichroic mirror 55, passes through the focusing lens 31, is reflected by the mirror 32, and is half mirror
- the light passes through 39A, is reflected by the dichroic mirror 33, and is projected onto the light receiving surface of the CCD image sensor 35 by the condenser lens.
- the light reception image (alignment index) by the CCD image sensor 35 is displayed on the display device 3 together with the observation image.
- 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 index and moving the optical system (auto-alignment function).
- 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 indicator plate 63, passes through the two-hole aperture 64, and is reflected by the mirror 65, The light is 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, passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus oculi Ef.
- 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 index) 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 index and moves the focusing lens 31 and the focus optical system 60 to perform focusing as in the conventional case (autofocus function). Alternatively, focusing may be performed manually while visually checking the split indicator.
- the dichroic mirror 46 combines the optical path for fundus imaging and the optical path for OCT measurement.
- the dichroic mirror 46 reflects light in a wavelength band used for OCT measurement and transmits light for fundus photographing.
- the dichroic mirror 46 is an example of an optical path combining unit.
- a collimator lens unit 40, an optical path length changing unit 41, a galvano scanner 42, a focusing lens 43, a mirror 44, and a relay lens 45 are provided in this order from the OCT unit 100 side. ing.
- the optical system constituting the optical path for OCT measurement and the optical system included in the OCT unit 100 are examples of the measurement optical system.
- the optical path length changing unit 41 is movable in the direction of the arrow shown in FIG. 1, and changes the optical path length of the optical path for OCT measurement. This change in the optical path length is used for correcting the optical path length according to the axial length of the eye E or adjusting the interference state.
- the optical path length changing unit 41 includes, for example, a corner cube and a mechanism for moving the corner cube.
- the galvano scanner 42 changes the traveling direction of light (signal light LS) passing through the optical path for OCT measurement. Thereby, the fundus oculi Ef can be scanned with the signal light LS.
- the galvano scanner 42 includes, for example, a galvano mirror that scans the signal light LS in the x direction, a galvano mirror that scans in the y direction, and a mechanism that drives these independently. Thereby, the signal light LS can be scanned in an arbitrary direction on the xy plane.
- the OCT unit 100 is provided with an optical system for acquiring an OCT image of the fundus oculi Ef.
- This optical system has the same configuration as a conventional spectral 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.
- a wavelength swept light source is provided instead of a light source that outputs a low coherence light source, and an optical member that spectrally decomposes interference light is not provided.
- a known technique according to the type of optical coherence tomography can be arbitrarily applied.
- 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 1040 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 reference light LR is guided by the optical fiber 104 and reaches an optical attenuator (attenuator) 105.
- the optical attenuator 105 automatically adjusts the amount of the reference light LR guided to the optical fiber 104 under the control of the arithmetic control unit 200 using a known technique.
- the reference light LR whose light amount has been adjusted by the optical attenuator 105 is guided by the optical fiber 104 and reaches the polarization adjuster (polarization controller) 106.
- the polarization adjuster 106 is, for example, a device that adjusts the polarization state of the reference light LR guided in the optical fiber 104 by applying a stress from the outside to the optical fiber 104 in a loop shape.
- the configuration of the polarization adjuster 106 is not limited to this, and any known technique can be used.
- the reference light LR whose polarization state is adjusted by the polarization adjuster 106 reaches the fiber coupler 109.
- the signal light LS generated by the fiber coupler 103 is guided by the optical fiber 107 and converted into a parallel light beam by the collimator lens unit 40. Further, the signal light LS reaches the dichroic mirror 46 via the optical path length changing unit 41, the galvano scanner 42, the focusing lens 43, the mirror 44, and the relay lens 45. The signal light LS is reflected by the dichroic mirror 46, is refracted by the objective lens 22, and is applied to the fundus oculi Ef. The signal light LS is scattered (including reflection) at various depth positions of the fundus oculi Ef. The backscattered light of the signal light LS from the fundus oculi Ef travels in the same direction as the forward path in the reverse direction, is guided to the fiber coupler 103, and reaches the fiber coupler 109 via the optical fiber 108.
- the fiber coupler 109 causes the backscattered light of the signal light LS and the reference light LR that has passed through the optical fiber 104 to interfere with each other.
- the interference light LC generated thereby is guided by the optical fiber 110 and emitted from the emission end 111. Further, the interference light LC is converted into a parallel light beam by the collimator lens 112, dispersed (spectral decomposition) by the diffraction grating 113, condensed by the condenser lens 114, and projected onto the light receiving surface of the CCD image sensor 115.
- the diffraction grating 113 shown in FIG. 2 is a transmission type, other types of spectroscopic elements such as a reflection type diffraction grating may be used.
- the CCD image sensor 115 is a line sensor, for example, and detects each spectral component of the split interference light LC and converts it into electric charges.
- the CCD image sensor 115 accumulates this electric charge, generates a detection signal, and sends it 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 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 115 and forms an OCT image of the fundus oculi Ef.
- the arithmetic processing for this is the same as that of a conventional spectral 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. For example, the arithmetic control unit 200 displays an OCT image 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 lenses 31 and 43, and the reflector 67. Movement control, movement control of the focus optical system 60, movement control of the optical path length changing unit 41, operation control of the galvano scanner 42, and the like are performed.
- the arithmetic control unit 200 performs operation control of the light source unit 101, operation control of the optical attenuator 105, operation control of the polarization adjuster 106, operation control of the CCD image sensor 115, and the like.
- 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 ophthalmic observation apparatus 1 is stored in a storage device such as a hard disk drive.
- the arithmetic control unit 200 may include various circuit boards, for example, a circuit board for forming an OCT image.
- 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 calculation control unit 200 may be configured integrally (that is, in a single housing) or separated into two or more cases. It may be.
- Control system The configuration of the control system of the ophthalmologic observation apparatus 1 will be described with reference to FIG.
- the control system of the ophthalmologic observation apparatus 1 is configured around the control unit 210.
- the control unit 210 includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, communication interface, and the like.
- the control unit 210 includes a main control unit 211, a storage unit 212, and a target position acquisition unit 213.
- the main control unit 211 performs the various controls described above.
- the main control unit 211 includes the focusing drive units 31A and 43A, the optical system drive unit 60A, the LED 61, the reflector driving unit 67A, the CCDs 35 and 38, the optical path length changing unit 41, and the galvano scanner 42 of the fundus camera unit 2.
- the main control unit 211 controls the light source unit 101, the optical attenuator 105, the polarization adjuster 106, and the CCD image sensor (sometimes simply referred to as a CCD) 115 of the OCT unit 100.
- the focusing drive unit 31A moves the focusing lens 31 along the optical axis under the control of the main control unit 211. Thereby, the focus position of the photographic optical system 30 is changed.
- the focusing drive unit 31 ⁇ / b> A includes an actuator such as a pulse motor and a mechanism that transmits a driving force generated by the actuator to the focusing lens 31.
- the focusing lens 31 is an example of a first focusing lens.
- the focusing drive unit 31A is an example of a first drive unit.
- the focusing drive unit 43A moves the focusing lens 43 along the optical axis under the control of the main control unit 211. Thereby, the focus position of the measurement optical system for OCT measurement is changed.
- the in-focus position of the measurement optical system defines the amount of signal light LS incident on the optical fiber 107 via the collimator lens unit 40. That is, the optimum focusing position of the measurement optical system is realized by arranging the focusing lens 43 at a position where the fiber end of the optical fiber 107 on the collimator lens unit 40 side and the fundus oculi Ef are optically conjugate.
- the focusing drive unit 43 ⁇ / b> A includes an actuator such as a pulse motor and a mechanism that transmits a driving force generated by the actuator to the focusing lens 43.
- the optical system driving unit 60A moves the focus optical system 60 along the optical axis under the control of the main control unit 211. Thereby, the projection mode of the split indicator on the fundus oculi Ef is changed.
- the optical system driving unit 60 ⁇ / b> A includes an actuator such as a pulse motor and a mechanism that transmits a driving force generated by the actuator to the focus optical system 60.
- the focus optical system 60 is configured as a unit, for example.
- the focus optical system 60 projects a split index (focus index) indicating the focus state (focus state) of the photographing optical system 30 with respect to the fundus oculi Ef onto the fundus oculi Ef, and is an example of a projection optical system.
- the reflector driving unit 67A inserts and removes the reflector 67 with respect to the optical path under the control of the main controller 211.
- the reflector 67 is inserted into the optical path when projecting the split index, that is, at the start of focus adjustment, and is retracted from the optical path at the end of focus adjustment.
- the reflector driving unit 67A includes an actuator such as a solenoid and a mechanism for transmitting the driving force generated by the actuator to the reflector 67.
- the main control unit 211 controls a driving mechanism (not shown) to move the fundus camera unit 2 three-dimensionally. This control is used in alignment and tracking. Tracking is to move the apparatus optical system in accordance with the eye movement of the eye E. When tracking is performed, alignment and focusing are performed in advance. Tracking is a function of maintaining a suitable positional relationship in which the alignment and focus are achieved by causing the position of the apparatus optical system to follow the eye movement.
- 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 storage unit 212 stores various programs and data for operating the ophthalmologic observation apparatus 1.
- correspondence information 212a is stored in advance.
- Correspondence information 212 a corresponds to first correspondence information in which an eye refractive power value (diopter) and the position of the focusing lens 31 are associated, and an eye refractive power value (diopter) and the position of the focusing lens 43.
- the attached second correspondence information may be individual information or information combined into one.
- the correspondence information 212a may be information in which discrete values such as table information are associated with each other, or information in which continuous values such as graph information are associated with each other. May be.
- the target position acquisition unit 213 acquires the target positions of the focusing lens 31 and the focusing lens 43 based on the refractive power of the eye E.
- the target position acquisition unit 213 is an example of a first target position acquisition unit.
- the target position is position information that is a movement target of the focusing lens 31 (or the focusing lens 43).
- This position information indicates a position along the optical axis of the optical system provided with the focusing lens 31 (or the focusing lens 43).
- This position information may be any form of information.
- this position information may be information indicating the position itself on the optical axis, or the content of the control signal for moving the focusing lens 31 (or the focusing lens 43) (for example, the number of pulses of the signal sent to the pulse motor) ) May be used.
- the refractive power of the eye E is acquired by an arbitrary refractive power acquisition unit.
- the refractive power acquisition unit (the control unit 210 or the like) can be configured to read the value of the eye refractive power recorded in the electronic medical record or the like. Further, although details will be described later, it is also possible to configure so that the refractive power of the eye E is acquired by the analysis unit 231 of the image processing unit 230.
- the target position acquisition unit 213 acquires the target positions of the focusing lens 31 and the focusing lens 43 based on the refractive power acquired by the refractive power acquisition unit and the correspondence information 212a. That is, the target position acquisition unit 213 acquires the position of the focusing lens 31 associated with the eye refractive power value acquired by the refractive power acquisition unit with reference to the first correspondence information, and focuses this The target position of the lens 31 is set. Similarly, the target position acquisition unit 213 acquires the position of the focusing lens 43 associated with the eye refractive power value acquired by the refractive power acquisition unit with reference to the second correspondence information, and aligns this. The target position of the focal lens 43 is set.
- the image forming unit 220 forms tomographic image data of the fundus oculi Ef based on the detection signal from the CCD image sensor 115. This process includes processes such as noise removal (noise reduction), filter processing, dispersion compensation, and FFT (Fast Fourier Transform) as in the conventional spectral domain type optical coherence tomography. In the case of another type of OCT apparatus, the image forming unit 220 executes a known process corresponding to the type.
- the image forming unit 220 includes, for example, the circuit board described above. In this specification, “image data” and “image” based thereon may be identified.
- 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. The image processing unit 230 performs various types of image processing and analysis processing on the image (fundus image, anterior eye image, etc.) obtained by the fundus camera unit 2.
- the image processing unit 230 executes known image processing such as interpolation processing for interpolating pixels between tomographic images to form image data of a three-dimensional image of the fundus oculi Ef.
- 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.
- the pseudo three-dimensional image is displayed on the display unit 240A.
- 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, stack data is image data obtained by expressing a plurality of tomographic images originally defined by individual two-dimensional coordinate systems by one three-dimensional coordinate system (that is, by embedding them in one three-dimensional space). is there.
- the image processing unit 230 has an analysis unit 231.
- the analysis unit 231 obtains the refractive power of the eye E by analyzing a front image obtained by photographing the fundus oculi Ef on which the split index is projected with an infrared imaging optical system.
- This front image is, for example, the aforementioned observation image.
- FIG. 4 An example of the observation image is shown in FIG.
- a pair of split index images (split index images) B1 and B2 are drawn together with the form of the fundus oculi Ef.
- Reference symbol A is a shadow (reflecting rod image) of the reflecting rod 67 arranged in the optical path of the illumination optical system 10.
- the split index images B1 and B2 are drawn in a straight line in the vertical direction in FIG.
- the split index images B1 and B2 are drawn shifted in the left-right direction in FIG.
- the shift direction and shift amount of the split index images B1 and B2 correspond to the shift direction and shift amount from the proper focus state. This focus shift corresponds to the refractive power of the eye E.
- the analyzing unit 231 previously stores information (index image / eye refractive power correspondence information) in which the shift direction and shift amount of the split index images B1 and B2 are associated with the value of the eye refractive power.
- the analysis unit 231 acquires the shift information (shift direction and shift amount) of the split index images B1 and B2 drawn on the observation image by analyzing the observation image (the still image constituting the observation image). Further, the analysis unit 231 obtains the eye refractive power corresponding to the acquired deviation information based on the index image / eye refractive power correspondence information. The obtained eye refractive power value is used as the refractive power of the eye E to be examined.
- the target position acquisition unit 213 acquires the target position of the focusing lens 31 and the target position of the focusing lens 43 based on the refractive power information and the correspondence information 212a. This process is executed as described above.
- the image processing unit 230 that functions as described above includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, circuit board, and the like.
- a storage device such as a hard disk drive, a computer program for causing the microprocessor to execute the above functions is stored in advance.
- the user interface 240 includes a display unit 240A and an operation unit 240B.
- the display unit 240A includes the display device of the arithmetic control unit 200 and the display device 3 described above.
- the operation unit 240B includes the operation device of the arithmetic control unit 200 described above.
- the operation unit 240B may include various buttons and keys provided on the housing of the ophthalmologic observation apparatus 1 or outside.
- the operation unit 240B may include a joystick, an operation panel, or the like provided on the housing.
- the display unit 240 ⁇ / b> A may include various display devices such as a touch panel provided on the housing of the fundus camera unit 2.
- the display unit 240A and the operation unit 240B do not need to be configured as individual devices.
- a device in which a display function and an operation function are integrated such as a touch panel
- the operation unit 240B includes the touch panel and a computer program.
- the operation content for the operation unit 240B is input to the control unit 210 as an electrical signal. Further, operations and information input may be performed using a graphical user interface (GUI) displayed on the display unit 240A and the operation unit 240B.
- GUI graphical user interface
- the scan mode of the signal light LS by the ophthalmic observation apparatus 1 includes, for example, a horizontal scan, a vertical scan, a cross scan, a radiation scan, a circle scan, a concentric scan, and a spiral (vortex) scan. These scan 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) trajectory while gradually reducing (or increasing) the radius of rotation.
- the galvano scanner 42 is 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. Further, by simultaneously controlling the directions of the two galvanometer mirrors included in the galvano scanner 42, the signal light LS can be scanned along an arbitrary locus on the xy plane. Thereby, various scan modes as described above can be realized.
- a tomographic image on a plane stretched by the direction along the scanning line (scanning locus) and the fundus depth direction (z direction) can be acquired.
- the above-described three-dimensional image can be acquired particularly when the scanning line interval is narrow.
- 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 called 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.
- FIG. 5 shows an example of the operation of the ophthalmologic observation apparatus 1.
- an observation image of the fundus oculi Ef is obtained by continuously illuminating the fundus oculi Ef with observation illumination light.
- the observation image is a near-infrared moving image obtained in real time until the continuous illumination ends.
- a fixation target by the LCD 39 is projected onto the eye E.
- the analysis unit 231 obtains the refractive power of the eye E by analyzing the observation image (the frame thereof). More specifically, the analysis unit 231 obtains the refractive power of the eye E based on the positions of the split index images B1 and B2 drawn on the observation image.
- the target position acquisition unit 213 sets the target position (first position) of the focusing lens 31 of the imaging optical system 30. 1 target position) and the target position (second target position) of the focusing lens 43 of the OCT measurement optical system (measurement optical system).
- the main control unit 211 controls the focusing drive unit 31 ⁇ / b> A so as to move the focusing lens 31 to the first target position acquired in step 4. Further, the main control unit 211 controls the focusing drive unit 43A so as to move the focusing lens 43 to the second target position acquired in Step 4.
- the main control unit 211 may perform these two controls in parallel, or may perform the other control after performing one control.
- the main control unit 211 can recognize the current positions of the focusing lenses 31 and 43. For example, a position sensor that detects the positions of the focusing lenses 31 and 43 can be provided.
- a control history (for example, contents of pulse signals transmitted to the focusing drive units 31A and 43A between the state where the focusing lenses 31 and 43 are arranged at a predetermined initial position to the present) is recorded. It is also possible to apply a configuration.
- the main control unit 211 transmits a control signal for moving the focusing lens 31 from the current position to the first target position to the focusing driving unit 31A, and moves the focusing lens 43 from the current position to the second target position. Control signal for transmitting to the in-focus driving unit 43A. Thereby, the focusing lens 31 is moved to the first target position, and the focusing lens 43 is moved to the second target position.
- the main control unit 211 controls the OCT unit 100, the optical path length changing unit 41, the galvano scanner 42, and the like to perform OCT measurement of the fundus oculi Ef.
- Data acquired by OCT measurement is sent from the CCD 115 to the image forming unit 220 as a detection signal.
- the image forming unit 220 forms a tomographic image of the fundus oculi Ef based on this detection signal.
- the main controller 211 displays the formed tomographic image on the display 240A.
- the main control unit 211 stores the formed tomographic image in the storage unit 212.
- the main controller 211 controls the illumination optical system 10 (such as the imaging light source 15) and the imaging optical system 30 to acquire a captured image of the fundus oculi Ef.
- the main control unit 211 causes the display unit 240A to display the acquired captured image.
- the main control unit 211 causes the storage unit 212 to store the acquired captured image. This is the end of this operation example.
- the ophthalmic observation apparatus 1 includes a photographing optical system, a measurement optical system, an optical path synthesis unit, a first drive unit, a second drive unit, and a control unit.
- the imaging optical system performs imaging for acquiring a front image of the eye E and includes a first focusing lens.
- the photographing optical system includes the illumination optical system 10 and the photographing optical system 30, and the focusing lens 31 corresponds to the first focusing lens.
- the measurement optical system performs optical coherence tomography measurement (OCT measurement) for acquiring a tomographic image of the eye E, and includes a second focusing lens.
- OCT measurement optical coherence tomography measurement
- the measurement optical system includes an optical system stored in the OCT unit 100 and an optical system that forms an optical path from the collimator lens unit 40 to the objective lens 22, and the focusing lens 43 is in the second focusing state.
- the optical path combining unit combines the optical path of the imaging optical system and the optical path of the measurement optical system at a position closer to the subject's eye than the first focusing lens and the second focusing lens. “Position on the eye side relative to the focusing lens” indicates a position on the eye side relative to the focusing lens in the optical path of each optical system.
- the dichroic mirror 46 corresponds to an optical path combining unit.
- the first focusing lens and the second focusing lens are separate optical elements.
- the first drive unit is for moving the first focusing lens along the optical axis of the photographing optical system.
- the focusing drive unit 31A corresponds to the first drive unit.
- the second drive unit is for moving the second focusing lens along the optical axis of the measurement optical system.
- the focusing drive unit 43A corresponds to the second drive unit.
- the control unit controls the first driving unit and the second driving unit, respectively.
- the control unit 210 corresponds to the control unit.
- each of the photographing optical system and the measurement optical system has the focusing lens individually, and these focusing lenses can be individually controlled. Therefore, it is possible to arrange the first focusing lens at the optimum focus position for acquiring the front image and to arrange the second focusing lens at the optimum focus position for OCT measurement. Therefore, it is possible to perform both the acquisition of the front image of the eye E and the OCT measurement in a suitable focus state.
- the imaging optical system performs imaging for acquiring a front image of the fundus oculi Ef
- the measurement optical system performs optical coherence tomography measurement for acquiring a tomographic image of the fundus oculi Ef.
- the ophthalmologic observation apparatus 1 includes a refractive power acquisition unit that acquires the refractive power of the eye E to be examined.
- the control unit 210 also acquires a first target position acquisition unit (target position acquisition unit 213) that acquires target positions of the first focusing lens and the second focusing lens based on the refractive power acquired by the refractive power acquisition unit. )including.
- control unit 210 controls the first driving unit so as to move the first focusing lens to the first target position acquired by the first target position acquisition unit, and sets the second focusing position to the second target position.
- the second drive unit is controlled to move the focal lens.
- both the movement control of the first focusing lens and the movement control of the second focusing lens are performed, but only one of the movement controls may be performed. In that case, the other movement control can be performed by an arbitrary method.
- the process for acquiring the refractive power of the eye E can be performed as follows, for example. It is assumed that the imaging optical system includes an infrared imaging optical system that performs imaging of the fundus using infrared light.
- the infrared imaging optical system includes an optical system that irradiates the fundus oculi with observation illumination light from the observation light source 11, and an optical system that detects fundus reflection light of the observation illumination light with the CCD image sensor 35.
- the refractive power acquisition unit includes a projection optical system and an analysis unit.
- the projection optical system projects a focus index indicating the focus state of the photographing optical system with respect to the fundus oculi Ef onto the fundus oculi Ef.
- the projection optical system includes a focus optical system 60, and the split index corresponds to the focus index.
- the analysis unit 231 obtains the refractive power of the eye E by analyzing the front image obtained by photographing the fundus oculi Ef on which the focus index is projected with the infrared photographing optical system.
- the refractive power can be acquired by actually measuring the eye E, focus adjustment can be performed with high accuracy.
- the process of acquiring the target position of the focusing lens can be performed as follows, for example.
- the control unit 210 stores in advance correspondence information 212a in which the value of the eye refractive power and the position of the focusing lens are associated with each other.
- the correspondence information 212a is associated with the first correspondence information in which the value of the eye refractive power is associated with the position of the first focusing lens, and the value of the eye refractive power is associated with the position of the second focusing lens.
- Second correspondence information is included.
- the first target position acquisition unit (target position acquisition unit 213), based on the refractive power acquired by the refractive power acquisition unit, the first correspondence information, and the second correspondence information, the first focusing lens and the second focusing lens. Get each target position. More specifically, the first target position acquisition unit acquires the target position of the first focusing lens based on the refractive power acquired by the refractive power acquisition unit and the first correspondence information.
- the target position of the second focusing lens is acquired based on the two correspondence
- an ophthalmologic observation apparatus configured to perform focusing for acquiring a front image using a focusing result in OCT measurement will be described.
- imaging with visible light is generally performed after OCT measurement. This embodiment is effective in the inspection performed in such a flow.
- the ophthalmic observation apparatus of this embodiment has the same overall configuration and optical system configuration as those of the first embodiment.
- the configuration of the control system is almost the same as that of the first embodiment.
- the same components as those in the first embodiment will be described using the same reference numerals.
- FIG. 6 shows a configuration example of the control system of the ophthalmic observation apparatus of this embodiment.
- a target position acquisition unit 214 is provided instead of the target position acquisition unit 213 of the first embodiment.
- the correspondence information 212 a does not need to be stored in the storage unit 212, and the analysis unit 231 does not need to be provided in the image processing unit 230.
- these differences will be mainly described.
- the target position acquisition unit 214 acquires the target position of the focusing lens 31 of the photographing optical system 30 based on the position of the focusing lens 43 of the measurement optical system when the OCT measurement is performed.
- the target position acquisition unit 214 is an example of a second target position acquisition unit.
- OCT moving image a moving image of the cross section can be acquired.
- the frame rate of this OCT moving image corresponds to the repetition frequency of OCT measurement.
- the user can manually perform focus adjustment.
- an ophthalmic observation apparatus automatically performs focus adjustment by analyzing an OCT moving image (a still image constituting the OCT moving image).
- the image processing unit 230 analyzes a pixel value (luminance value) of a still image constituting an OCT moving image to identify a region with high image quality (high image quality region), and determines the depth of the frame.
- the current focus position is specified based on the position (z coordinate) of the high quality area in the vertical direction (z direction).
- the image processing unit 230 identifies a region (target region) corresponding to the tissue in the still image.
- the target area may be designated by the user.
- the image processing unit 230 obtains the position (z coordinate) of the target area in the depth direction (z direction) of the frame.
- the main control unit 211 generates a control signal for changing the current focus position of the measurement optical system to a focus position corresponding to the target area, and sends the control signal to the focusing drive unit 43A. Accordingly, the focusing lens 43 is disposed at a position corresponding to the focus position corresponding to the target area.
- the position in the depth direction (z direction) of the frame and the position of the focusing lens 43 of the measurement optical system can be associated in advance. Furthermore, it is possible to provide a function of correcting the association in consideration of the refractive power of the eye E to be examined.
- the fundus oculi Ef drawn as an OCT moving image by eye movement or pulsation moves in the frame.
- the optical path length changing unit 41 is controlled so as to follow the movement of the image, and the image of the fundus oculi Ef is moved in the frame.
- the focus adjustment using the OCT image is not limited to that described above, and any method can be used.
- the target position acquisition unit 214 acquires the target position of the focusing lens 31 of the imaging optical system 30 based on the position of the focusing lens 43 set by the focus adjustment using the OCT image as described above.
- Information in which the position of the focusing lens 31 and the position of the focusing lens 43 are associated with each other is stored in the storage unit 212 in advance, and the position of the focusing lens 43 applied in the OCT measurement by referring to this information. It is possible to obtain the position of the focusing lens 31 corresponding to.
- this information can be created using the value of the eye refractive power as a medium. This information can also be created with reference to the configuration of the imaging optical system and the measurement optical system, the difference between the wavelength of light used for fundus imaging and the wavelength of light used for OCT measurement, and the like.
- requires the position of the focusing lens 31 from the position of the focusing lens 43 in OCT measurement is not limited to this,
- the target position acquisition part 214 can perform the said process with arbitrary methods.
- the main control unit 211 controls the focusing drive unit 31A so as to move the focusing lens 31 to the target position acquired by the target position acquisition unit 214.
- FIG. 7 shows an example of the operation of the ophthalmologic observation apparatus.
- the main control unit 211 controls the OCT unit 100, the optical path length changing unit 41, the galvano scanner 42, and the like, and starts OCT measurement of the fundus oculi Ef.
- This OCT measurement is repeatedly performed on substantially the same cross section of the fundus oculi Ef. That is, this OCT measurement is performed in an operation mode for acquiring an OCT moving image.
- the main control unit 211 controls the OCT unit 100, the optical path length changing unit 41, the galvano scanner 42, etc. OCT measurement of the fundus oculi Ef is performed. This OCT measurement is executed in a preset scan mode. Thereby, a tomographic image for diagnosis is acquired.
- the target position acquisition unit 214 In response to the end of the OCT measurement or a predetermined operation by the user, the target position acquisition unit 214 detects the position of the focusing lens 43 applied in the OCT measurement in step 15, that is, the focus adjustment in step 14. Based on the set position of the focusing lens 43, the target position of the focusing lens 31 of the photographing optical system is obtained.
- the main control unit 211 controls the focusing drive unit 31A so as to move the focusing lens 31 to the target position acquired in step 16.
- the main controller 211 controls the illumination optical system 10 (such as the photographing light source 15) and the photographing optical system to acquire a photographed image of the fundus oculi Ef.
- the main control unit 211 causes the display unit 240A to display the acquired captured image.
- the main control unit 211 causes the storage unit 212 to store the acquired captured image. This is the end of this operation example.
- the ophthalmic observation apparatus includes a photographing optical system, a measurement optical system, an optical path synthesis unit, a first drive unit, a second drive unit, and a control unit. . Therefore, each of the photographing optical system and the measurement optical system has a focusing lens, and these focusing lenses can be individually controlled. Therefore, it is possible to arrange the first focusing lens at the optimum focus position for acquiring the front image and to arrange the second focusing lens at the optimum focus position for OCT measurement. Thereby, it is possible to perform both the acquisition of the front image of the eye E and the OCT measurement in a suitable focus state.
- control unit 210 acquires the target position of the focusing lens 31 of the imaging optical system based on the position of the focusing lens 43 of the measurement optical system when the OCT measurement is performed.
- a target position acquisition unit 214 (second target position acquisition unit) is included. Further, the control unit is configured to control the focusing drive unit 31 ⁇ / b> A so as to move the focusing lens 31 to the target position acquired by the target position acquisition unit 214.
- the focus adjustment on the imaging optical system side can be performed with reference to the result of the high-accuracy and high-accuracy focus adjustment using the OCT image, the eye E to be examined with a good focus state The front image of can be acquired. Further, there is a possibility that the focus of the photographing optical system is shifted due to eye movement or the like during the OCT measurement. In this case, according to this embodiment, since the focus adjustment of the photographing optical system can be performed from the focus state at the time of OCT measurement, photographing for acquiring a front image is performed in a suitable focus state. Is possible. Further, since the focus adjustment of the photographing optical system can be automatically performed after the OCT measurement, the user's hand is not bothered.
- the process of acquiring the target position of the focusing lens 31 of the photographing optical system can be performed based on the OCT moving image. That is, in this embodiment, the OCT moving image of the cross section can be acquired by repeatedly performing OCT measurement on substantially the same cross section of the eye E with the measurement optical system. Further, the target position acquisition unit 214 determines the alignment of the imaging optical system based on the position of the focusing lens 43 set based on a plurality of tomographic images (OCT moving image frames) acquired by this repetitive OCT measurement. The target position of the focal lens 31 can be acquired.
- the image of the fundus oculi Ef can be held at a predetermined position in the frame as described above. Therefore, even when eye movement or pulsation occurs during OCT measurement, the target position of the focusing lens 31 of the photographing optical system can be acquired with high accuracy.
- a user interface for performing focus adjustment of an imaging optical system and a measurement optical system based on an OCT image will be described.
- the ophthalmic observation apparatus of this embodiment has the same overall configuration and optical system configuration as those of the first embodiment.
- the configuration of the control system is almost the same as that of the first embodiment.
- the same components as those in the first embodiment will be described using the same reference numerals.
- FIG. 8 shows a configuration example of the control system of the ophthalmic observation apparatus according to this embodiment.
- a target position acquisition unit 215 is provided instead of the target position acquisition unit 213 of the first embodiment.
- the correspondence information 212 a does not need to be stored in the storage unit 212, and the analysis unit 231 does not need to be provided in the image processing unit 230.
- the image processing unit 230 is provided with a layer region specifying unit 232.
- the main control unit 211 displays a tomographic image of the fundus oculi Ef acquired by OCT measurement by the measurement optical system on the display unit 240A.
- the user designates a desired position in the displayed tomogram using the operation unit 240B.
- This desired position is a position (focus target position) where the user wants to focus in the tomographic image.
- the focus target position may be the focus target position of the measurement optical system or the focus target position of the photographing optical system. Further, a user interface capable of designating both focus target positions may be provided, or a user interface capable of designating only one of them may be provided.
- the focus target positions of both optical systems may be the same or different from each other.
- a user interface capable of individually specifying both focus target positions or a user interface capable of collectively specifying both focus target positions is provided.
- a user interface capable of individually specifying both focus target positions is provided.
- the relationship between both focus target positions is determined in advance based on the eye refractive power, wavelength, etc., it is configured to automatically specify the other upon receiving the result of specifying one focus target position. Is possible.
- the specific configuration of the user interface exemplified here is arbitrary.
- the target position acquisition unit 215 uses the operation unit 240B to specify the target position (first target position) of the focusing lens 31 and / or the target position of the focusing lens 43 (first target position) based on the position specified for the tomographic image. 2nd target position) is acquired.
- the target position acquisition unit 215 is an example of a third target position acquisition unit.
- the processing executed by the target position acquisition unit 215 to acquire these target positions is arbitrary.
- a configuration of the user interface and an example of processing executed by the target position acquisition unit 215 will be described.
- a first processing example will be described with reference to FIG.
- the focus position is designated by freezing (still image display) the OCT moving image.
- the main control unit 211 controls the OCT unit 100, the optical path length changing unit 41, the galvano scanner 42, and the like to repeatedly perform OCT measurement on substantially the same cross section of the eye E (fundus Ef).
- the main control unit 211 causes the display unit 240A to display the OCT moving image in real time based on the plurality of tomographic images acquired by the repetitive OCT measurement.
- the main control unit 211 switches the tomographic image display mode from moving image display to still image display in response to a predetermined operation (an operation for instructing still image display) performed by the operation unit 240B.
- the still image and the moving image may be displayed side by side.
- a display area (still image display area) for displaying a still image is provided on the display screen separately from the display area of the real-time OCT moving image.
- the OCT moving image frame (still image) corresponding to the timing at which the operation is performed is displayed as a still image while the OCT moving image is displayed as it is. It can be configured to be displayed in the area.
- the still image displayed in the still image display area may be updated every time the operation is performed.
- still images obtained at each operation may be displayed side by side.
- a plurality of still images may be displayed in the same size, a part of the plurality of still images may be displayed in a reduced size (thumbnail display or the like), or the display may be terminated.
- the user operates the operation unit 240B to designate a desired position in the tomographic image displayed as a still image.
- This designated position is, for example, a position indicating a desired tissue of the fundus oculi Ef drawn on the tomographic image.
- the number of specified positions is arbitrary. For example, it is possible to specify a position indicating a part (fundus surface, etc.) to be observed in detail in a captured image and a position indicating a part (retinal pigment epithelium, choroid, etc.) to be observed in detail in a tomographic image. .
- information enabling each designated position to be determined may be input. For example, information indicating that the first designated position is a fundus photographing position and information indicating that the second designated position is an OCT measurement position can be input.
- the designated position is for a predetermined use (for OCT measurement or fundus imaging).
- Information indicating the specified position can be displayed together with the tomographic image. For example, it is possible to display an image indicating the designated position so as to overlap the tomographic image.
- the information indicating the designated position can be changed with time so as to follow the eye movement or the like.
- the display position of the image indicating the designated position is also changed over time.
- the acquisition processing of the first target position is performed based on, for example, the coordinates (z coordinate) of the first designated position in the depth direction (z direction) of the tomographic image frame.
- the second target position acquisition process is performed based on, for example, the coordinates (z coordinate) of the second designated position in the depth direction (z direction) of the tomographic image frame.
- the z coordinate of the frame is associated with the position of the focusing lens 31 and / or the position of the focusing lens 43 in advance. It is also possible to correct the target position based on the eye refractive power or the like.
- the main control unit 211 controls the OCT unit 100, the optical path length changing unit 41, the galvano scanner 42, and the like to perform OCT measurement of the fundus oculi Ef.
- the image forming unit 220 forms a tomographic image of the fundus oculi Ef based on the detection signal from the CCD 115.
- the main controller 211 displays the formed tomographic image on the display 240A.
- the main control unit 211 stores the formed tomographic image in the storage unit 212.
- the main controller 211 controls the illumination optical system 10 (such as the imaging light source 15) and the imaging optical system 30 to acquire a captured image of the fundus oculi Ef.
- the main control unit 211 causes the display unit 240A to display the acquired captured image.
- the main control unit 211 causes the storage unit 212 to store the acquired captured image. This is the end of this operation example.
- the focus position is designated by moving the position designation image displayed on the OCT moving image to a desired position.
- the main control unit 211 controls the OCT unit 100, the optical path length changing unit 41, the galvano scanner 42, and the like to repeatedly perform OCT measurement on substantially the same cross section of the eye E (fundus Ef).
- the main control unit 211 causes the display unit 240A to display the OCT moving image in real time based on the plurality of tomographic images acquired by the repetitive OCT measurement.
- the main control unit 211 places a predetermined position designation image at a position on the OCT moving image corresponding to the focus position (that is, the position of the focusing lens 43) when the repetitive OCT measurement in step 31 is performed. Display.
- the main control unit 211 corresponds to the position of the focusing lens 43 during OCT measurement.
- the middle position (z coordinate) is obtained, and the position designation image is displayed so as to overlap this position. Further, the display position of the position designation image may be corrected based on the refractive power of the eye E or the like.
- the position designation image is, for example, a linear image that passes through the position (z coordinate) and is orthogonal to the depth direction (z direction).
- the position designation image is a linear or arrow image displayed at a position outside the frame of the OCT moving image corresponding to the position (z coordinate).
- the position designation image is an image superimposed on the OCT moving image or displayed in the vicinity of the OCT moving image, and is an image having a function of presenting a focus position in the OCT moving image.
- the display position of the position designation image can be changed with time so as to follow the eye movement or the like.
- the number of position designation images displayed is arbitrary. For example, a first position designating image for designating a site (fundus surface etc.) to be observed in detail in the photographed image and a site for designating a site (retinal pigment epithelium, choroid, etc.) to be observed in detail in the tomographic image. It is possible to display two position designation images. When two or more position designation images are displayed, each position designation image may be displayed so as to be distinguishable. For example, the display mode (display color or the like) of the first position designation image may be configured to be different from the display mode of the second position designation image.
- the position designation image is for a predetermined application (for OCT measurement or fundus imaging).
- the user operates the operation unit 240B to move the position designation image to a desired position.
- This desired position is, for example, a position indicating a desired tissue of the fundus oculi Ef drawn on the tomographic image.
- the target position acquisition unit 215 performs the target position (first target position) of the focusing lens 31 and / or the target position (first position) of the focusing lens 43 based on the position of the position designation image after being moved in Step 33. 2 target position).
- the acquisition processing of the first target position is performed based on, for example, the coordinates (z coordinate) of the first position designation image in the depth direction (z direction) of the tomographic image frame.
- the second target position acquisition process is performed based on, for example, the coordinates (z coordinate) of the second position designation image in the depth direction (z direction) of the tomographic image frame.
- the z coordinate of the frame is associated with the position of the focusing lens 31 and / or the position of the focusing lens 43 in advance. It is also possible to correct the target position based on the eye refractive power or the like.
- the main control unit 211 controls the OCT unit 100, the optical path length changing unit 41, the galvano scanner 42, and the like to perform OCT measurement of the fundus oculi Ef.
- the image forming unit 220 forms a tomographic image of the fundus oculi Ef based on the detection signal from the CCD 115.
- the main controller 211 displays the formed tomographic image on the display 240A.
- the main control unit 211 stores the formed tomographic image in the storage unit 212.
- the main controller 211 controls the illumination optical system 10 (such as the imaging light source 15) and the imaging optical system 30 to acquire a captured image of the fundus oculi Ef.
- the main control unit 211 causes the display unit 240A to display the acquired captured image.
- the main control unit 211 causes the storage unit 212 to store the acquired captured image. This is the end of this operation example.
- the layer region specifying unit 232 analyzes a tomographic image (still image constituting the OCT moving image) displayed on the display unit 240A, and specifies a layer region corresponding to a predetermined layer in the tomographic image.
- This layer region is an image region corresponding to at least one of predetermined layer tissues of the fundus oculi Ef having a layer structure.
- the layer structure of the fundus oculi Ef includes the inner boundary membrane, nerve fiber layer, ganglion cell layer, inner reticular layer, inner granule layer, outer reticular layer, outer granule layer, outer boundary membrane, photoreceptor layer, and retinal pigment layer.
- the main control unit 211 displays an image (layer image) indicating the layer region specified by the layer region specifying unit 232 so as to overlap the tomographic image.
- the main control unit 211 can change the display position of the position designation image with time so as to follow the eye movement or the like. It is.
- the ophthalmic observation apparatus includes a photographing optical system, a measurement optical system, an optical path synthesis unit, a first drive unit, a second drive unit, and a control unit. . Therefore, each of the photographing optical system and the measurement optical system has a focusing lens, and these focusing lenses can be individually controlled. Therefore, it is possible to arrange the first focusing lens at the optimum focus position for acquiring the front image and to arrange the second focusing lens at the optimum focus position for OCT measurement. Thereby, it is possible to perform both the acquisition of the front image of the eye E and the OCT measurement in a suitable focus state.
- the ophthalmic observation apparatus of this embodiment has a display unit (display unit 240A) and an operation unit (operation unit 240B).
- the display unit displays a tomographic image acquired by OCT measurement by the measurement optical system.
- the operation unit is used for designating a position in the tomographic image displayed on the display unit.
- the control unit (control unit 210) of this embodiment includes a third target position acquisition unit (target position acquisition unit 215).
- the third target position acquisition unit acquires the target position of the first focusing lens (focusing lens 31) and / or the second focusing lens (focusing lens 43) based on the position specified by the operation unit. .
- the control unit moves the first focusing lens and / or the second focusing lens to the target position acquired by the third target position acquisition unit, and the first driving unit (focusing driving unit 31A) and The second drive unit (focus drive unit 43A) is controlled.
- the display unit can display a plurality of tomographic images acquired by this repeated OCT measurement as a moving image. Furthermore, the control unit switches the moving image display to the still image display in response to a predetermined operation performed by the operation unit.
- the third target position acquisition unit can acquire the target positions of the first focusing lens and the second focusing lens based on the position designated by the operation unit with respect to the tomographic image displayed as a still image. it can.
- the display unit displays a position designation image that is movable with respect to the moving image by a predetermined operation by the operation unit.
- the third target position acquisition unit can acquire the target position of the first focusing lens and the second focusing lens based on the position specified by the operation on the position specifying image.
- control unit can display an image indicating a position on the moving image corresponding to the position of the second focusing lens when repetitive OCT measurement is performed.
- a desired focus position can be designated for the tomographic image, and the focus position in imaging of the eye to be examined or OCT measurement can be automatically adjusted to the designated position.
- ⁇ Fourth Embodiment> In order to optimize the focus position of OCT measurement in actual inspection, not only the difference between the wavelength of light for imaging (visible light etc.) and the wavelength of light for OCT measurement (near infrared light etc.), It is desirable to pay attention to individual differences in the optical characteristics of the eye to be examined.
- focus adjustment for OCT measurement in consideration of optical characteristics of an eye to be examined will be described. This focus adjustment is performed in two stages, coarse adjustment and fine adjustment. Coarse adjustment is performed using a split index (focus index) or using a measured value of the refractive power of the eye to be examined. The fine adjustment is performed based on the interference sensitivity of the OCT measurement.
- the ophthalmic observation apparatus of this embodiment has the same overall configuration and optical system configuration as those of the first embodiment.
- the configuration of the control system is almost the same as that of the first embodiment.
- the same components as those in the first embodiment will be described using the same reference numerals.
- FIG. 11 shows a configuration example of the control system of the ophthalmic observation apparatus of this embodiment.
- the control unit 210 is provided with a target position acquisition unit 216. Further, the image forming unit 220 is provided with an interference intensity acquisition unit 221.
- the interference intensity acquisition unit 221 acquires the intensity (interference intensity) of the interference signal obtained by the measurement optical system that performs OCT measurement.
- the interference signal is a detection signal output from the CCD image sensor 115 or a signal obtained by performing predetermined signal processing on the detection signal. Examples of this predetermined signal processing include arbitrary signal processing used in the spectral domain OCT or the swept source OCT.
- the interference intensity acquisition unit 221 acquires the interference intensity by detecting the amplitude of the interference signal, for example.
- the interference intensity acquisition unit 221 is an example of an “intensity acquisition unit”.
- a plurality of interference signals are acquired while changing the position of the focusing lens 43 of the measurement optical system.
- the interference intensity acquisition unit 221 determines the intensity of each interference signal.
- the process which acquires a some interference signal is performed as follows, for example.
- the main control unit 211 controls the focusing drive unit 43 to move the focusing lens 43.
- the movement form may be continuous movement or intermittent movement (step movement).
- the main control unit 211 controls the measurement optical system (such as the light source unit 101) and continuously performs OCT measurement a plurality of times while continuously moving the focusing lens 43.
- the main control unit 211 performs OCT measurement on the measurement optical system while the focusing lens 43 is sequentially disposed at the first to Nth positions and the focusing lens 43 is disposed at each position. Let By performing such control, a plurality of interference signals corresponding to a plurality of positions of the focusing lens 43 are obtained.
- the moving range of the focusing lens 43 can be set in advance. That is, a plurality of interference signals can be acquired by performing the OCT measurement a plurality of times while moving the focusing lens 43 within a predetermined range.
- the moving range of the focusing lens 43 includes a position determined in advance by rough adjustment (focus adjustment based on the split index) described later.
- the moving range of the focusing lens 43 is set so that the position (reference position) determined by coarse adjustment is the center.
- the moving range of the focusing lens 43 can be defined by a change in refractive power corresponding to the movement of the focusing lens 43 along the optical axis of the measurement optical system.
- the moving range of the focusing lens 43 is set to a range of ⁇ 3 diopters centered on the reference position.
- the target position acquisition unit 216 acquires the target position of the focusing lens 43 based on the plurality of interference intensities acquired by the interference intensity acquisition unit 221.
- the target position acquisition unit 216 is an example of a “fourth target position acquisition unit”.
- the target position acquisition unit 216 specifies the maximum intensity among the plurality of interference intensities acquired by the interference intensity acquisition unit 221. This process is performed by comparing the interference intensity values. Furthermore, the target position acquisition unit 216 sets the position of the focusing lens 43 corresponding to the specified maximum intensity as the target position. In this process, for example, the position when the interference signal having the maximum intensity is obtained from the positions of the plurality of focusing lenses 43 applied in the above-described plurality of OCT measurements, and this is set as the target position. Is done.
- the processing executed by the target position acquisition unit 216 is not limited to this.
- the target position acquisition unit 216 acquires a change state of the interference intensity accompanying the movement of the focusing lens 43 based on the acquired plurality of interference intensity.
- This process includes, for example, a process of obtaining a curve (continuous value) that smoothly connects a plurality of interference intensity values (discrete values).
- this curve is defined in a coordinate system in which the position of the focusing lens 43 is on the horizontal axis and the interference intensity is on the vertical axis.
- the target position acquisition unit 216 obtains a peak of the interference intensity from the acquired change state of the interference intensity. Then, the target position acquisition unit 216 obtains the position of the focusing lens 43 corresponding to the obtained peak. This position is either one of the plurality of positions of the focusing lens 43 applied in the plurality of OCT measurements, or none of them.
- FIG. 12 illustrates an example of the operation of the ophthalmologic observation apparatus.
- Focus adjustment (rough adjustment) using the split index is performed.
- the rough adjustment may be performed manually or automatically (autofocus).
- the focus adjustment using the split index has been described above.
- the focus adjustment at this stage is performed for both the photographing optical system 30 and the measurement optical system.
- the position of the focusing lens 31 of the photographing optical system 30 is determined using a split index as in a general fundus camera, and the focusing lens 43 is moved to a position corresponding to this position.
- the relationship between the position of the focusing lens 31 and the position of the focusing lens 43 is determined in advance, and information indicating this relationship is stored in the storage unit 212.
- the main control unit 211 acquires a plurality of interference signals while changing the position of the focusing lens 43 of the measurement optical system. This process is executed as described above.
- the interference intensity acquisition unit 221 determines the interference intensity of each of the plurality of interference signals acquired in step 44.
- the target position acquisition unit 216 calculates the target position of the focusing lens 43 based on the plurality of interference intensities acquired in step 45.
- the main control unit 211 controls the focusing drive unit 43 ⁇ / b> A to move the focusing lens 43 to the target position obtained in step 46.
- the main control unit 211 controls the OCT unit 100, the optical path length changing unit 41, the galvano scanner 42, and the like to perform OCT measurement of the fundus oculi Ef.
- the image forming unit 220 forms a tomographic image of the fundus oculi Ef based on the detection signal from the CCD 115.
- the main controller 211 displays the formed tomographic image on the display 240A.
- the main control unit 211 stores the formed tomographic image in the storage unit 212. This OCT measurement is performed in a focus state finely adjusted based on the interference intensity. Therefore, OCT measurement with high sensitivity is possible.
- the main controller 211 controls the illumination optical system 10 (such as the imaging light source 15) and the imaging optical system 30 to acquire a captured image of the fundus oculi Ef.
- the main control unit 211 causes the display unit 240A to display the acquired captured image.
- the main control unit 211 causes the storage unit 212 to store the acquired captured image. Note that this fundus imaging is performed in a suitable focus state adjusted in step 43 based on the split index. This is the end of this operation example.
- the ophthalmic observation apparatus includes a photographing optical system, a measurement optical system, an optical path synthesis unit, a first drive unit, a second drive unit, and a control unit. . Therefore, each of the photographing optical system and the measurement optical system has a focusing lens, and these focusing lenses can be individually controlled. Therefore, it is possible to arrange the first focusing lens at the optimum focus position for acquiring the front image and to arrange the second focusing lens at the optimum focus position for OCT measurement. Thereby, it is possible to perform both the acquisition of the front image of the eye E and the OCT measurement in a suitable focus state.
- the measurement optical system performs optical coherence tomography measurement for acquiring a tomographic image of the fundus oculi Ef.
- the ophthalmic observation apparatus of this embodiment includes a focus optical system 60 (projection optical system) and an interference intensity acquisition unit 221 (intensity acquisition unit).
- the projection optical system projects a split index (focus index) indicating the focus state of the photographing optical system 30 with respect to the fundus oculi Ef onto the fundus oculi Ef.
- the interference intensity acquisition unit 221 acquires the intensity of the interference signal obtained by the measurement optical system.
- the main control unit 211 performs focus drive based on the interference intensity acquired by the interference intensity acquisition unit 221.
- the focus state of the measurement optical system is finely adjusted by controlling the unit 43A.
- control unit 210 can execute the following processing.
- the main control unit 211 controls the focusing optical unit 43A to control the measurement optical system while moving the focusing lens 43, thereby generating a plurality of interference signals corresponding to a plurality of positions of the focusing lens 43. Get it.
- the target position acquisition unit 216 acquires the target position of the focusing lens 43 based on the plurality of interference intensities acquired by the interference intensity acquisition unit 221.
- the main control unit 211 controls the focusing drive unit 43A so as to move the focusing lens 43 to the acquired target position.
- the target position acquisition unit 216 specifies the maximum intensity among the plurality of interference intensities acquired by the interference intensity acquisition unit 221 and adopts the position of the focusing lens 43 corresponding to the specified maximum intensity as the target position. Can do.
- the main control unit 211 can improve the efficiency of fine adjustment by moving the focusing lens 43 within a predetermined range in acquiring a plurality of interference signals.
- This predetermined range may include the position of the focusing lens 43 determined by rough adjustment.
- the center of the predetermined range may be the position of the focusing lens 43 determined by the coarse adjustment.
- the imaging optical system 30 includes an infrared imaging optical system that performs imaging for acquiring a front image of the fundus oculi Ef using infrared light.
- the infrared imaging optical system for example, the optical system described in the first embodiment for illuminating the eye E with observation illumination light and detecting the reflected light is applied.
- the main control unit 211 moves the focusing lens 31 and the focus optical system 60 based on the front image obtained by photographing the fundus oculi Ef on which the split index is projected with the infrared photographing optical system.
- the system 30 is focused, and the measurement optical system is focused (the focusing lens 43 is moved) based on the focusing result.
- the focus state of the measurement optical system can be adjusted based on the interference intensity, it is possible to perform highly sensitive OCT measurement. For example, even when the split index is kicked by the pupil and the coarse adjustment cannot be suitably performed, the OCT measurement can be performed in a favorable focus state. Further, since the coarse adjustment is performed before the fine adjustment, the fine adjustment can be smoothly started.
- the configuration of the ophthalmic observation apparatus according to this modification may be the same as that of the fourth embodiment unless otherwise specified (see FIG. 11).
- the storage unit 212 stores a measurement value of the refractive power of the eye E acquired in advance. This measured value may be acquired by another ophthalmologic apparatus (such as an autorefractometer) or may be acquired by this ophthalmologic observation apparatus.
- the main control unit 211 causes the storage unit 212 to store the measurement value input to the ophthalmic observation apparatus.
- the ophthalmic observation apparatus is provided with a refractive power acquisition unit that acquires the refractive power of the eye to be examined.
- the refractive power acquisition unit has, for example, the configuration described in the first embodiment.
- the main control unit 211 causes the storage unit 212 to store the refractive power acquired by the refractive power acquisition unit.
- the interference intensity acquisition unit 221 acquires the intensity of the interference signal obtained by the measurement optical system, as in the above embodiment.
- the main control unit 211 causes focus adjustment of the imaging optical system 30 and the measurement optical system based on the measurement values stored in the storage unit 212 as coarse adjustment of the focus state.
- the focus adjustment based on the eye refractive power is executed, for example, in the same manner as in the first embodiment. Further, the main control unit 211 performs fine adjustment of the focus state of the measurement optical system by controlling the focusing drive unit 43A based on the interference intensity acquired by the interference intensity acquisition unit 221.
- the focus state of the measurement optical system can be adjusted based on the interference intensity, it is possible to perform highly sensitive OCT measurement. Further, since the coarse adjustment is performed before the fine adjustment, the fine adjustment can be smoothly started. In addition, even when the ophthalmic observation apparatus does not have a function of projecting a focus index such as a split index, or when there is a problem with the function, rough adjustment of the focus state can be performed.
- the optical path length difference between the optical path of the signal light LS and the optical path of the reference light LR is changed by changing the position of the optical path length changing unit 41, but this optical path length difference is changed.
- the method is not limited to this.
- it is possible to change the optical path length difference by disposing a reflection mirror (reference mirror) in the optical path of the reference light and moving the reference mirror in the traveling direction of the reference light to change the optical path length of the reference light.
- the optical path length difference may 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.
- the optical path length difference can be changed by moving the measured object in the depth direction (z direction).
- the computer program for realizing the above embodiment can be stored in an arbitrary recording medium readable by a computer.
- this recording medium for example, a semiconductor memory, 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. Can be used.
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Abstract
Description
また、請求項2に記載の発明は、請求項1に記載の眼科観察装置であって、前記撮影光学系は、被検眼の眼底の正面画像を取得するための撮影を行い、前記計測光学系は、被検眼の眼底の断層像を取得するための光コヒーレンストモグラフィ計測を行い、被検眼の屈折力を取得する屈折力取得部を有し、前記制御部は、取得された屈折力に基づいて、前記第1合焦レンズおよび/または前記第2合焦レンズの目標位置を取得する第1目標位置取得部を含み、取得された目標位置に前記第1合焦レンズおよび/または前記第2合焦レンズを移動させるように、前記第1駆動部および/または前記第2駆動部を制御することを特徴とする。
また、請求項3に記載の発明は、請求項2に記載の眼科観察装置であって、前記撮影光学系は、赤外光を用いて眼底の撮影を行う赤外撮影光学系を含み、前記屈折力取得部は、眼底に対する前記撮影光学系の合焦状態を示す合焦指標を眼底に投影する投影光学系と、合焦指標が投影されている状態の眼底を前記赤外撮影光学系で撮影して得られた正面画像を解析することにより、被検眼の屈折力を求める解析部とを含むことを特徴とする。
また、請求項4に記載の発明は、請求項2または請求項3に記載の眼科観察装置であって、前記制御部は、眼屈折力の値と前記第1合焦レンズの位置とが対応付けられた第1対応情報と、眼屈折力の値と前記第2合焦レンズの位置とが対応付けられた第2対応情報とを予め記憶した記憶部を含み、前記第1目標位置取得部は、前記屈折力取得部により取得された屈折力、前記第1対応情報および前記第2対応情報に基づいて、前記第1合焦レンズおよび前記第2合焦レンズのそれぞれの目標位置を取得することを特徴とする。
また、請求項5に記載の発明は、請求項1に記載の眼科観察装置であって、前記制御部は、前記計測光学系により光コヒーレンストモグラフィ計測が行われたときの前記第2合焦レンズの位置に基づいて、前記第1合焦レンズの目標位置を取得する第2目標位置取得部を含み、取得された目標位置に前記第1合焦レンズを移動させるように前記第1駆動部を制御することを特徴とする。
また、請求項6に記載の発明は、請求項5に記載の眼科観察装置であって、前記計測光学系は、被検眼の実質的に同一の断面に対する光コヒーレンストモグラフィ計測を反復的に行い、前記第2目標位置取得部は、反復的な光コヒーレンストモグラフィ計測により取得された複数の断層像に基づき設定された前記第2合焦レンズの位置に基づいて、前記第1合焦レンズの目標位置の取得を行うことを特徴とする。
また、請求項7に記載の発明は、請求項1に記載の眼科観察装置であって、前記計測光学系による光コヒーレンストモグラフィ計測により取得された断層像を表示する表示部と、表示された断層像中の位置を指定するための操作部とを有し、前記制御部は、前記操作部により指定された位置に基づいて、前記第1合焦レンズおよび/または前記第2合焦レンズの目標位置を取得する第3目標位置取得部を含み、取得された目標位置に前記第1合焦レンズおよび/または前記第2合焦レンズを移動させるように、前記第1駆動部および/または前記第2駆動部を制御することを特徴とする。
また、請求項8に記載の発明は、請求項7に記載の眼科観察装置であって、前記計測光学系は、被検眼の実質的に同一の断面に対する光コヒーレンストモグラフィ計測を反復的に行い、前記表示部は、反復的な光コヒーレンストモグラフィ計測により取得される複数の断層像を動画表示し、前記制御部は、前記操作部により所定の操作がなされたことに対応して当該動画表示を静止画表示に切り替え、前記第3目標位置取得部は、静止画表示された断層像に対して前記操作部により指定された位置に基づいて、前記目標位置の取得を行うことを特徴とする。
また、請求項9に記載の発明は、請求項7に記載の眼科観察装置であって、前記計測光学系は、被検眼の実質的に同一の断面に対する光コヒーレンストモグラフィ計測を反復的に行い、前記表示部は、反復的な光コヒーレンストモグラフィ計測により取得される複数の断層像を動画表示し、かつ、前記操作部による所定の操作により当該動画像に対して移動可能な位置指定用画像を表示し、前記第3目標位置取得部は、前記位置指定用画像に対する操作より指定された位置に基づいて、前記目標位置の取得を行うことを特徴とする。
また、請求項10に記載の発明は、請求項9に記載の眼科観察装置であって、前記制御部は、前記反復的な光コヒーレンストモグラフィ計測が行われているときの前記第2合焦レンズの位置に対応する当該動画像上の位置を示す前記位置指定用画像を表示させることを特徴とする。
また、請求項11に記載の発明は、請求項7~請求項10のいずれか一項に記載の眼科観察装置であって、前記表示部に表示される断層像を解析して、当該断層像において所定の層に相当する層領域を特定する層領域特定部を有し、前記表示部は、特定された層領域を示す層画像を当該断層像に重ねて表示することを特徴とする。
また、請求項12に記載の発明は、請求項1に記載の眼科観察装置であって、前記計測光学系は、被検眼の眼底の断層像を取得するための光コヒーレンストモグラフィ計測を行い、眼底に対する前記撮影光学系の合焦状態を示す合焦指標を眼底に投影する投影光学系と、前記計測光学系により得られた干渉信号の強度を取得する強度取得部とを有し、前記合焦指標に基づく前記撮影光学系および前記計測光学系の合焦が行われた後に、前記制御部は、前記強度取得部により取得された強度に基づいて前記第2駆動部を制御することを特徴とする。
また、請求項13に記載の発明は、請求項12に記載の眼科観察装置であって、前記制御部は、前記第2駆動部を制御して前記第2合焦レンズを移動させつつ前記計測光学系を制御することで、前記第2合焦レンズの複数の位置に対応する複数の干渉信号を取得させ、前記強度取得部により取得された前記複数の干渉信号の強度に基づいて、前記第2合焦レンズの目標位置を取得する第4目標位置取得部を含み、取得された目標位置に前記第2合焦レンズを移動させるように、前記第2駆動部を制御することを特徴とする。
また、請求項14に記載の発明は、請求項13に記載の眼科観察装置であって、前記第4目標位置取得部は、前記複数の干渉信号の強度のうちの最大強度を特定し、特定された最大強度に対応する前記合焦レンズの位置を目標位置とすることを特徴とする。
また、請求項15に記載の発明は、請求項13または請求項14に記載の眼科観察装置であって、前記制御部は、前記複数の干渉信号の取得において、前記第2合焦レンズを所定範囲内にて移動させることを特徴とする。
また、請求項16に記載の発明は、請求項15に記載の眼科観察装置であって、前記所定範囲は、前記合焦指標に基づき事前に決定された前記第2合焦レンズの位置を含むことを特徴とする。
また、請求項17に記載の発明は、請求項16に記載の眼科観察装置であって、前記所定範囲の中心が前記事前に決定された位置であることを特徴とする。
また、請求項18に記載の発明は、請求項12~請求項17のいずれか一項に記載の眼科観察装置であって、前記撮影光学系は、赤外光を用いて被検眼の眼底の正面画像を取得するための撮影を行う赤外撮影光学系を含み、前記制御部は、合焦指標が投影されている状態の眼底を前記赤外撮影光学系で撮影して得られた正面画像に基づき前記第1合焦レンズおよび前記投影光学系を移動させることにより前記撮影光学系の合焦を行い、当該合焦結果に基づいて前記計測光学系の合焦を行うことを特徴とする。
また、請求項19に記載の発明は、請求項1に記載の眼科観察装置であって、前記計測光学系は、被検眼の眼底の断層像を取得するための光コヒーレンストモグラフィ計測を行い、事前に取得された被検眼の屈折力の測定値を記憶する記憶部と、前記計測光学系により得られた干渉信号の強度を取得する強度取得部とを有し、前記測定値に基づく前記撮影光学系および前記計測光学系の合焦が行われた後に、前記制御部は、前記強度取得部により取得された強度に基づいて前記第2駆動部を制御することを特徴とする。
また、請求項20に記載の発明は、請求項19に記載の眼科観察装置であって、被検眼の屈折力を取得する屈折力取得部を有し、前記制御部は、取得された屈折力を前記測定値として前記記憶部に記憶させることを特徴とする。
[構成]
図1および図2に示すように、眼科観察装置1は、眼底カメラユニット2、OCTユニット100および演算制御ユニット200を含んで構成される。眼底カメラユニット2は、従来の眼底カメラとほぼ同様の光学系を含む。OCTユニット100には、眼底のOCT画像を取得するための光学系が設けられている。演算制御ユニット200は、各種の演算処理や制御処理等を実行するコンピュータを含む。
図1に示す眼底カメラユニット2には、被検眼Eの眼底Efの表面形態を表す正面画像(眼底像)を取得するための光学系が設けられている。眼底像には、観察画像や撮影画像などが含まれる。観察画像は、たとえば、近赤外光を用いて所定のフレームレートで形成されるモノクロの動画像である。撮影画像は、たとえば、可視光をフラッシュ発光して得られるカラー画像、または近赤外光若しくは可視光を照明光として用いたモノクロの静止画像であってもよい。眼底カメラユニット2は、これら以外の画像、たとえばフルオレセイン蛍光画像やインドシアニングリーン蛍光画像や自発蛍光画像などを取得可能に構成されていてもよい。
図2を参照しつつOCTユニット100の構成の一例を説明する。OCTユニット100には、眼底EfのOCT画像を取得するための光学系が設けられている。この光学系は、従来のスペクトラルドメインタイプのOCT装置と同様の構成を有する。すなわち、この光学系は、低コヒーレンス光を参照光と信号光に分割し、眼底Efを経由した信号光と参照光路を経由した参照光とを干渉させて干渉光を生成し、この干渉光のスペクトル成分を検出するように構成されている。この検出結果(検出信号)は演算制御ユニット200に送られる。
演算制御ユニット200の構成について説明する。演算制御ユニット200は、CCDイメージセンサ115から入力される検出信号を解析して眼底EfのOCT画像を形成する。そのための演算処理は、従来のスペクトラルドメインタイプのOCT装置と同様である。
眼科観察装置1の制御系の構成について図3を参照しつつ説明する。
眼科観察装置1の制御系は、制御部210を中心に構成される。制御部210は、たとえば、前述のマイクロプロセッサ、RAM、ROM、ハードディスクドライブ、通信インターフェイス等を含んで構成される。制御部210には、主制御部211と、記憶部212と、目標位置取得部213とが設けられている。
主制御部211は前述の各種制御を行う。特に、主制御部211は、眼底カメラユニット2の合焦駆動部31Aおよび43A、光学系駆動部60A、LED61、反射棒駆動部67A、CCD35および38、光路長変更部41、並びにガルバノスキャナ42を制御する。また、主制御部211は、OCTユニット100の光源ユニット101、光減衰器105、偏波調整器106、およびCCDイメージセンサ(単にCCDと呼ぶことがある)115を制御する。
記憶部212は、各種のデータを記憶する。記憶部212に記憶されるデータとしては、たとえば、OCT画像の画像データ、眼底像の画像データ、被検眼情報などがある。被検眼情報は、患者IDや氏名などの被検者に関する情報や、左眼/右眼の識別情報などの被検眼に関する情報を含む。また、記憶部212には、眼科観察装置1を動作させるための各種プログラムやデータが記憶されている。
目標位置取得部213は、被検眼Eの屈折力に基づいて、合焦レンズ31および合焦レンズ43のそれぞれの目標位置を取得する。目標位置取得部213は第1目標位置取得部の一例である。
画像形成部220は、CCDイメージセンサ115からの検出信号に基づいて、眼底Efの断層像の画像データを形成する。この処理には、従来のスペクトラルドメインタイプの光コヒーレンストモグラフィと同様に、ノイズ除去(ノイズ低減)、フィルタ処理、分散補償、FFT(Fast Fourier Transform)などの処理が含まれている。他のタイプのOCT装置の場合、画像形成部220は、そのタイプに応じた公知の処理を実行する。
画像処理部230は、画像形成部220により形成された画像に対して各種の画像処理や解析処理を施す。たとえば、画像処理部230は、画像の輝度補正等の各種補正処理を実行する。また、画像処理部230は、眼底カメラユニット2により得られた画像(眼底像、前眼部像等)に対して各種の画像処理や解析処理を施す。
画像処理部230は解析部231を有する。解析部231は、スプリット指標が投影されている状態の眼底Efを赤外撮影光学系で撮影して得られた正面画像を解析することにより、被検眼Eの屈折力を求める。この正面画像は、たとえば前述の観察画像である。
ユーザインターフェイス240には、表示部240Aと操作部240Bとが含まれる。表示部240Aは、前述した演算制御ユニット200の表示デバイスや表示装置3を含んで構成される。操作部240Bは、前述した演算制御ユニット200の操作デバイスを含んで構成される。操作部240Bには、眼科観察装置1の筐体や外部に設けられた各種のボタンやキーが含まれていてもよい。たとえば眼底カメラユニット2が従来の眼底カメラと同様の筺体を有する場合、操作部240Bは、この筺体に設けられたジョイスティックや操作パネル等を含んでいてもよい。また、表示部240Aは、眼底カメラユニット2の筺体に設けられたタッチパネルなどの各種表示デバイスを含んでいてもよい。
ここで、信号光LSの走査およびOCT画像について説明しておく。
眼科観察装置1の動作について説明する。図5は、眼科観察装置1の動作の一例を表す。
まず、観察照明光で眼底Efを連続照明することにより、眼底Efの観察画像を取得する。観察画像は、連続照明が終了するまでリアルタイムで得られる近赤外動画像である。このとき、LCD39による固視標が被検眼Eに投影される。
更に、被検眼Eには、アライメント光学系50によるアライメント指標と、フォーカス光学系60によるスプリット指標とが投影される。観察画像には、図示しないアライメント指標像と、図4に示すスプリット指標像B1およびB2が描画される。ユーザまたは制御部210は、アライメント指標を用いてアライメント(手動アライメントまたはオートアライメント)を行う。
解析部231は、観察画像(のフレーム)を解析することにより、被検眼Eの屈折力を求める。より詳しく説明すると、解析部231は、観察画像に描画されたスプリット指標像B1およびB2の位置に基づいて、被検眼Eの屈折力を求める。
目標位置取得部213は、ステップ3で取得された被検眼Eの屈折力と、記憶部212に予め記憶された対応情報212aに基づいて、撮影光学系30の合焦レンズ31の目標位置(第1目標位置)と、OCT計測用光学系(計測光学系)の合焦レンズ43の目標位置(第2目標位置)とを求める。
主制御部211は、ステップ4で取得された第1目標位置に合焦レンズ31を移動させるように合焦駆動部31Aを制御する。また、主制御部211は、ステップ4で取得された第2目標位置に合焦レンズ43を移動させるように合焦駆動部43Aを制御する。主制御部211は、この2つの制御を並行して行なってもよいし、一方の制御を行った後に他方の制御を行なってもよい。更に、主制御部211は、合焦レンズ31および43のそれぞれの現在位置を認識可能である。たとえば、各合焦レンズ31および43の位置を検出する位置センサを設けることができる。また、各合焦レンズ31および43に対する制御履歴(たとえば、所定の初期位置に配置されていた状態から現在までの間に各合焦駆動部31Aおよび43Aに送信したパルス信号の内容)を記録する構成を適用することも可能である。主制御部211は、合焦レンズ31を現在位置から第1目標位置まで移動させるための制御信号を合焦駆動部31Aに送信し、合焦レンズ43を現在位置から第2目標位置まで移動させるための制御信号を合焦駆動部43Aに送信する。それにより、合焦レンズ31が第1目標位置に移動され、合焦レンズ43が第2目標位置に移動される。
主制御部211は、OCTユニット100、光路長変更部41、ガルバノスキャナ42等を制御して、眼底EfのOCT計測を実行させる。OCT計測により取得されたデータは、CCD115から検出信号として画像形成部220に送られる。画像形成部220は、この検出信号に基づいて眼底Efの断層像を形成する。主制御部211は、形成された断層像を表示部240Aに表示させる。また、主制御部211は、形成された断層像を記憶部212に記憶させる。
主制御部211は、照明光学系10(撮影光源15等)および撮影光学系30を制御して、眼底Efの撮影画像を取得する。主制御部211は、取得された撮影画像を表示部240Aに表示させる。また、主制御部211は、取得された撮影画像を記憶部212に記憶させる。以上でこの動作例は終了である。
眼科観察装置1の作用および効果について説明する。
この実施形態では、OCT計測における合焦の結果を利用して正面画像取得用の合焦を行うよう構成された眼科観察装置について説明する。たとえば眼底の検査では、被検眼の縮瞳を考慮して、OCT計測の後に可視光による撮影が行われるのが一般的である。この実施形態はこのような流れで行われる検査において有効である。
この実施形態の眼科観察装置は、第1の実施形態と同様の全体構成および光学系の構成を有する。制御系の構成についても第1の実施形態とほぼ同様である。以下、第1の実施形態と同様の構成部分については同じ符号を用いて説明する。
この実施形態の眼科観察装置の動作について説明する。図7は、眼科観察装置の動作の一例を表す。
第1の実施形態と同様に、観察画像の取得が開始され、かつ、被検眼Eの固視が行われる。
第1の実施形態と同様に、被検眼Eにアライメント指標とスプリット指標とが投影される。そして、アライメント指標を用いたアライメントと、スプリット指標を用いたフォーカス調整とが実行される。このフォーカス調整は、撮影光学系および計測光学系の双方について行われる。
主制御部211は、OCTユニット100、光路長変更部41、ガルバノスキャナ42等を制御して、眼底EfのOCT計測を開始する。このOCT計測は、眼底Efの実質的に同一の断面に対して反復的に行われる。すなわち、このOCT計測は、OCT動画像を取得するための動作モードで行われる。
ユーザまたは眼科観察装置は、OCT動画像を用いた詳細なフォーカス調整を行う。
ステップ14の詳細なフォーカス調整が完了したことを受けて、またはユーザによる所定の操作を受けて、主制御部211は、OCTユニット100、光路長変更部41、ガルバノスキャナ42等を制御して、眼底EfのOCT計測を行う。このOCT計測は、予め設定されたスキャンモードで実行される。それにより、診断に供される断層像が取得される。
OCT計測が終了したことを受けて、またはユーザによる所定の操作を受けて、目標位置取得部214は、ステップ15のOCT計測で適用された合焦レンズ43の位置、つまりステップ14のフォーカス調整で設定された合焦レンズ43の位置に基づいて、撮影光学系の合焦レンズ31の目標位置を求める。
主制御部211は、ステップ16で取得された目標位置に合焦レンズ31を移動させるように合焦駆動部31Aを制御する。
主制御部211は、照明光学系10(撮影光源15等)および撮影光学系を制御して、眼底Efの撮影画像を取得する。主制御部211は、取得された撮影画像を表示部240Aに表示させる。また、主制御部211は、取得された撮影画像を記憶部212に記憶させる。以上でこの動作例は終了である。
この実施形態の眼科観察装置の作用および効果について説明する。
この実施形態では、OCT画像に基づいて撮影光学系や計測光学系のフォーカス調整を行うためのユーザインターフェイスについて説明する。
この実施形態の眼科観察装置は、第1の実施形態と同様の全体構成および光学系の構成を有する。制御系の構成についても第1の実施形態とほぼ同様である。以下、第1の実施形態と同様の構成部分については同じ符号を用いて説明する。
図9を参照しつつ第1の処理例を説明する。この処理例は、OCT動画像をフリーズ(静止画表示)させてフォーカス位置を指定するものである。
主制御部211は、OCTユニット100、光路長変更部41、ガルバノスキャナ42等を制御し、被検眼E(眼底Ef)の実質的に同一の断面に対するOCT計測を反復的に行わせる。主制御部211は、この反復的なOCT計測により取得される複数の断層像に基づき、表示部240AにOCT動画像をリアルタイムで表示させる。
主制御部211は、操作部240Bにより所定の操作(静止画表示を指示する操作)がなされたことに対応し、断層像の表示モードを動画表示から静止画表示に切り替える。
ユーザは、操作部240Bを操作し、静止画表示された断層像における所望の位置を指定する。この指定位置は、たとえば、断層像に描画された眼底Efの所望の組織を示す位置である。
目標位置取得部215は、ステップ23で断層像に指定された位置に基づいて、合焦レンズ31の目標位置(第1目標位置)および/または合焦レンズ43の目標位置(第2目標位置)を求める。
ステップ24で第1目標位置が取得された場合、主制御部211は、合焦駆動部31Aを制御して合焦レンズ31を第1目標位置に移動させる。また、ステップ24で第2目標位置が取得された場合、主制御部211は、合焦駆動部43Aを制御して合焦レンズ43を第2目標位置に移動させる。
主制御部211は、OCTユニット100、光路長変更部41、ガルバノスキャナ42等を制御して、眼底EfのOCT計測を実行させる。画像形成部220は、CCD115からの検出信号に基づいて眼底Efの断層像を形成する。主制御部211は、形成された断層像を表示部240Aに表示させる。また、主制御部211は、形成された断層像を記憶部212に記憶させる。
主制御部211は、照明光学系10(撮影光源15等)および撮影光学系30を制御して、眼底Efの撮影画像を取得する。主制御部211は、取得された撮影画像を表示部240Aに表示させる。また、主制御部211は、取得された撮影画像を記憶部212に記憶させる。以上でこの動作例は終了である。
図10を参照しつつ第2の処理例を説明する。この処理例は、OCT動画像上に表示された位置指定用画像を所望の位置に移動させることによってフォーカス位置を指定するものである。
主制御部211は、OCTユニット100、光路長変更部41、ガルバノスキャナ42等を制御し、被検眼E(眼底Ef)の実質的に同一の断面に対するOCT計測を反復的に行わせる。主制御部211は、この反復的なOCT計測により取得される複数の断層像に基づき、表示部240AにOCT動画像をリアルタイムで表示させる。
主制御部211は、ステップ31の反復的なOCT計測が行われているときのフォーカス位置(つまり合焦レンズ43の位置)に対応するOCT動画像上の位置に、所定の位置指定用画像を表示させる。
ユーザは、操作部240Bを操作することで、位置指定用画像を所望の位置に移動させる。この所望の位置は、たとえば、断層像に描画された眼底Efの所望の組織を示す位置である。
目標位置取得部215は、ステップ33で移動された後の位置指定用画像の位置に基づいて、合焦レンズ31の目標位置(第1目標位置)および/または合焦レンズ43の目標位置(第2目標位置)を求める。
ステップ34で第1目標位置が取得された場合、主制御部211は、合焦駆動部31Aを制御して合焦レンズ31を第1目標位置に移動させる。また、ステップ34で第2目標位置が取得された場合、主制御部211は、合焦駆動部43Aを制御して合焦レンズ43を第2目標位置に移動させる。
主制御部211は、OCTユニット100、光路長変更部41、ガルバノスキャナ42等を制御して、眼底EfのOCT計測を実行させる。画像形成部220は、CCD115からの検出信号に基づいて眼底Efの断層像を形成する。主制御部211は、形成された断層像を表示部240Aに表示させる。また、主制御部211は、形成された断層像を記憶部212に記憶させる。
主制御部211は、照明光学系10(撮影光源15等)および撮影光学系30を制御して、眼底Efの撮影画像を取得する。主制御部211は、取得された撮影画像を表示部240Aに表示させる。また、主制御部211は、取得された撮影画像を記憶部212に記憶させる。以上でこの動作例は終了である。
上記した第1および第2の処理例において、次のような処理を行うことが可能である。まず、層領域特定部232が、表示部240Aに表示される断層像(OCT動画像を構成する静止画像)を解析し、この断層像において所定の層に相当する層領域を特定する。この層領域は、層構造をなす眼底Efの所定の層組織の少なくとも1つに相当する画像領域である。なお、眼底Efの層組織には、内境界膜、神経線維層、神経節細胞層、内網状層、内顆粒層、外網状層、外顆粒層、外境界膜、視細胞層、網膜色素上皮層、脈絡膜、強膜などがある。
この実施形態の眼科観察装置の作用および効果について説明する。
実際の検査においてOCT計測のフォーカス位置を最適化するには、撮影用の光の波長(可視光等)と、OCT計測用の光の波長(近赤外光等)との相違だけでなく、被検眼の光学特性の個人差にも着目することが望ましい。この実施形態では、被検眼の光学特性を考慮したOCT計測用のフォーカス調整について説明する。このフォーカス調整は、粗調整と微調整の2段階で行われる。粗調整は、スプリット指標(合焦指標)を用いて、或いは被検眼の屈折力の測定値を用いて、行われる。微調整は、OCT計測の干渉感度に基づいて行われる。
この実施形態の眼科観察装置は、第1の実施形態と同様の全体構成および光学系の構成を有する。制御系の構成についても第1の実施形態とほぼ同様である。以下、第1の実施形態と同様の構成部分については同じ符号を用いて説明する。
この実施形態の眼科観察装置の動作について説明する。図12は、眼科観察装置の動作の一例を表す。
第1の実施形態と同様に、観察画像の取得が開始され、かつ、被検眼Eの固視が行われる。
第1の実施形態と同様に、被検眼Eにアライメント指標とスプリット指標とが投影される。そして、アライメント指標を用いたアライメントが実行される。
スプリット指標を用いたフォーカス調整(粗調整)を行なう。粗調整は、手動で行なってもよいし、自動(オートフォーカス)で行なってもよい。スプリット指標を用いたフォーカス調整については前述した。
主制御部211は、計測光学系の合焦レンズ43の位置を変更しつつ複数の干渉信号を取得する。この処理は前述の要領で実行される。
干渉強度取得部221は、ステップ44で取得された複数の干渉信号のそれぞれの干渉強度を求める。
目標位置取得部216は、ステップ45で取得された複数の干渉強度に基づいて、合焦レンズ43の目標位置を求める。
主制御部211は、合焦駆動部43Aを制御し、ステップ46で得られた目標位置に合焦レンズ43を移動させる。
主制御部211は、OCTユニット100、光路長変更部41、ガルバノスキャナ42等を制御して、眼底EfのOCT計測を実行させる。画像形成部220は、CCD115からの検出信号に基づいて眼底Efの断層像を形成する。主制御部211は、形成された断層像を表示部240Aに表示させる。また、主制御部211は、形成された断層像を記憶部212に記憶させる。なお、このOCT計測は、干渉強度に基づいて微調整されたフォーカス状態にて行われる。よって、高感度でのOCT計測が可能である。
主制御部211は、照明光学系10(撮影光源15等)および撮影光学系30を制御して、眼底Efの撮影画像を取得する。主制御部211は、取得された撮影画像を表示部240Aに表示させる。また、主制御部211は、取得された撮影画像を記憶部212に記憶させる。なお、この眼底撮影は、ステップ43でスプリット指標に基づき調整された好適なフォーカス状態にて実行される。以上でこの動作例は終了である。
この実施形態の眼科観察装置の作用および効果について説明する。
この実施形態の変形例を説明する。
以上に説明した構成は、この発明を好適に実施するための一例に過ぎない。よって、この発明の要旨の範囲内における任意の変形(省略、置換、付加等)を適宜に施すことが可能である。また、以上の実施形態に記載された各種の構成を任意に組み合わせることが可能である。
2 眼底カメラユニット
10 照明光学系
30 撮影光学系
31 合焦レンズ
31A 合焦駆動部
41 光路長変更部
42 ガルバノスキャナ
43 合焦レンズ
43A 合焦駆動部
60 フォーカス光学系
60A 光学系駆動部
100 OCTユニット
200 演算制御ユニット
210 制御部
211 主制御部
212 記憶部
212a 対応情報
213、214、215、216 目標位置取得部
220 画像形成部
221 干渉強度取得部
230 画像処理部
231 解析部
232 層領域特定部
240A 表示部
240B 操作部
E 被検眼
Ef 眼底
Claims (20)
- 第1合焦レンズを含み、被検眼の正面画像を取得するための撮影を行う撮影光学系と、
第2合焦レンズを含み、被検眼の断層像を取得するための光コヒーレンストモグラフィ計測を行う計測光学系と、
前記第1合焦レンズおよび前記第2合焦レンズよりも被検眼側の位置において前記撮影光学系の光路と前記計測光学系の光路とを合成する光路合成部と、
前記撮影光学系の光軸に沿って前記第1合焦レンズを移動するための第1駆動部と、
前記計測光学系の光軸に沿って前記第2合焦レンズを移動するための第2駆動部と、
前記第1駆動部および前記第2駆動部をそれぞれ制御する制御部と
を有する眼科観察装置。 - 前記撮影光学系は、被検眼の眼底の正面画像を取得するための撮影を行い、
前記計測光学系は、被検眼の眼底の断層像を取得するための光コヒーレンストモグラフィ計測を行い、
被検眼の屈折力を取得する屈折力取得部を有し、
前記制御部は、
取得された屈折力に基づいて、前記第1合焦レンズおよび/または前記第2合焦レンズの目標位置を取得する第1目標位置取得部を含み、
取得された目標位置に前記第1合焦レンズおよび/または前記第2合焦レンズを移動させるように、前記第1駆動部および/または前記第2駆動部を制御する
ことを特徴とする請求項1に記載の眼科観察装置。 - 前記撮影光学系は、赤外光を用いて眼底の撮影を行う赤外撮影光学系を含み、
前記屈折力取得部は、
眼底に対する前記撮影光学系の合焦状態を示す合焦指標を眼底に投影する投影光学系と、
合焦指標が投影されている状態の眼底を前記赤外撮影光学系で撮影して得られた正面画像を解析することにより、被検眼の屈折力を求める解析部と
を含む
ことを特徴とする請求項2に記載の眼科観察装置。 - 前記制御部は、眼屈折力の値と前記第1合焦レンズの位置とが対応付けられた第1対応情報と、眼屈折力の値と前記第2合焦レンズの位置とが対応付けられた第2対応情報とを予め記憶した記憶部を含み、
前記第1目標位置取得部は、前記屈折力取得部により取得された屈折力、前記第1対応情報および前記第2対応情報に基づいて、前記第1合焦レンズおよび前記第2合焦レンズのそれぞれの目標位置を取得する
ことを特徴とする請求項2または請求項3に記載の眼科観察装置。 - 前記制御部は、
前記計測光学系により光コヒーレンストモグラフィ計測が行われたときの前記第2合焦レンズの位置に基づいて、前記第1合焦レンズの目標位置を取得する第2目標位置取得部を含み、
取得された目標位置に前記第1合焦レンズを移動させるように前記第1駆動部を制御する
ことを特徴とする請求項1に記載の眼科観察装置。 - 前記計測光学系は、被検眼の実質的に同一の断面に対する光コヒーレンストモグラフィ計測を反復的に行い、
前記第2目標位置取得部は、反復的な光コヒーレンストモグラフィ計測により取得された複数の断層像に基づき設定された前記第2合焦レンズの位置に基づいて、前記第1合焦レンズの目標位置の取得を行う
ことを特徴とする請求項5に記載の眼科観察装置。 - 前記計測光学系による光コヒーレンストモグラフィ計測により取得された断層像を表示する表示部と、
表示された断層像中の位置を指定するための操作部と
を有し、
前記制御部は、
前記操作部により指定された位置に基づいて、前記第1合焦レンズおよび/または前記第2合焦レンズの目標位置を取得する第3目標位置取得部を含み、
取得された目標位置に前記第1合焦レンズおよび/または前記第2合焦レンズを移動させるように、前記第1駆動部および/または前記第2駆動部を制御する
ことを特徴とする請求項1に記載の眼科観察装置。 - 前記計測光学系は、被検眼の実質的に同一の断面に対する光コヒーレンストモグラフィ計測を反復的に行い、
前記表示部は、反復的な光コヒーレンストモグラフィ計測により取得される複数の断層像を動画表示し、
前記制御部は、前記操作部により所定の操作がなされたことに対応して当該動画表示を静止画表示に切り替え、
前記第3目標位置取得部は、静止画表示された断層像に対して前記操作部により指定された位置に基づいて、前記目標位置の取得を行う
ことを特徴とする請求項7に記載の眼科観察装置。 - 前記計測光学系は、被検眼の実質的に同一の断面に対する光コヒーレンストモグラフィ計測を反復的に行い、
前記表示部は、反復的な光コヒーレンストモグラフィ計測により取得される複数の断層像を動画表示し、かつ、前記操作部による所定の操作により当該動画像に対して移動可能な位置指定用画像を表示し、
前記第3目標位置取得部は、前記位置指定用画像に対する操作より指定された位置に基づいて、前記目標位置の取得を行う
ことを特徴とする請求項7に記載の眼科観察装置。 - 前記制御部は、前記反復的な光コヒーレンストモグラフィ計測が行われているときの前記第2合焦レンズの位置に対応する当該動画像上の位置を示す前記位置指定用画像を表示させることを特徴とする請求項9に記載の眼科観察装置。
- 前記表示部に表示される断層像を解析して、当該断層像において所定の層に相当する層領域を特定する層領域特定部を有し、
前記表示部は、特定された層領域を示す層画像を当該断層像に重ねて表示する
ことを特徴とする請求項7~請求項10のいずれか一項に記載の眼科観察装置。 - 前記計測光学系は、被検眼の眼底の断層像を取得するための光コヒーレンストモグラフィ計測を行い、
眼底に対する前記撮影光学系の合焦状態を示す合焦指標を眼底に投影する投影光学系と、
前記計測光学系により得られた干渉信号の強度を取得する強度取得部と
を有し、
前記合焦指標に基づく前記撮影光学系および前記計測光学系の合焦が行われた後に、前記制御部は、前記強度取得部により取得された強度に基づいて前記第2駆動部を制御する
ことを特徴とする請求項1に記載の眼科観察装置。 - 前記制御部は、
前記第2駆動部を制御して前記第2合焦レンズを移動させつつ前記計測光学系を制御することで、前記第2合焦レンズの複数の位置に対応する複数の干渉信号を取得させ、
前記強度取得部により取得された前記複数の干渉信号の強度に基づいて、前記第2合焦レンズの目標位置を取得する第4目標位置取得部を含み、
取得された目標位置に前記第2合焦レンズを移動させるように、前記第2駆動部を制御する
ことを特徴とする請求項12に記載の眼科観察装置。 - 前記第4目標位置取得部は、前記複数の干渉信号の強度のうちの最大強度を特定し、特定された最大強度に対応する前記合焦レンズの位置を目標位置とすることを特徴とする請求項13に記載の眼科観察装置。
- 前記制御部は、前記複数の干渉信号の取得において、前記第2合焦レンズを所定範囲内にて移動させることを特徴とする請求項13または請求項14に記載の眼科観察装置。
- 前記所定範囲は、前記合焦指標に基づき事前に決定された前記第2合焦レンズの位置を含むことを特徴とする請求項15に記載の眼科観察装置。
- 前記所定範囲の中心が前記事前に決定された位置であることを特徴とする請求項16に記載の眼科観察装置。
- 前記撮影光学系は、赤外光を用いて被検眼の眼底の正面画像を取得するための撮影を行う赤外撮影光学系を含み、
前記制御部は、合焦指標が投影されている状態の眼底を前記赤外撮影光学系で撮影して得られた正面画像に基づき前記第1合焦レンズおよび前記投影光学系を移動させることにより前記撮影光学系の合焦を行い、当該合焦結果に基づいて前記計測光学系の合焦を行う
ことを特徴とする請求項12~請求項17のいずれか一項に記載の眼科観察装置。 - 前記計測光学系は、被検眼の眼底の断層像を取得するための光コヒーレンストモグラフィ計測を行い、
事前に取得された被検眼の屈折力の測定値を記憶する記憶部と、
前記計測光学系により得られた干渉信号の強度を取得する強度取得部と
を有し、
前記測定値に基づく前記撮影光学系および前記計測光学系の合焦が行われた後に、前記制御部は、前記強度取得部により取得された強度に基づいて前記第2駆動部を制御する
ことを特徴とする請求項1に記載の眼科観察装置。 - 被検眼の屈折力を取得する屈折力取得部を有し、
前記制御部は、取得された屈折力を前記測定値として前記記憶部に記憶させる
ことを特徴とする請求項19に記載の眼科観察装置。
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