JP2016182525A - Ophthalmology imaging apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To improve operation property during setting or switching of an object part of OTC measurement.SOLUTION: An ophthalmology imaging apparatus of an embodiment comprises: an optical system; an image forming part; an optical unit; and a detection part. The optical system divides light output from a first light source into measurement light and reference light, and detects interference light of return light of the measurement light from the eye to be examined and the reference light. The image forming part forms an image based on the detection result by the optical system. The optical unit comprises a lens which can be arranged on an optical path of the measurement light, and changes a focal position of the measurement light to a second site from a first site of the eye to be examined. The detection part detects use or non-use of the optical unit based on an inspection content input by a user.SELECTED DRAWING: Figure 6

Description

  The present invention relates to an ophthalmologic photographing apparatus for obtaining an image of an eye to be examined by using optical coherence tomography (OCT).

  In recent years, OCT that forms an image representing the surface form or internal form of an object to be measured using a light beam from a laser light source or the like has attracted attention. Since OCT has no invasiveness to the human body like X-ray CT, it is expected to be applied particularly in the medical field and the biological field. For example, in the field of ophthalmology, an apparatus for forming an image of the fundus oculi or cornea has been put into practical use.

  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 (measurement 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. Note that this technique is also called a spectral domain.

  In Patent Document 2, a plurality of horizontal two-dimensional tomographic images are formed by scanning (scanning) measurement 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. As 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. In Patent Document 3, 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. And an OCT apparatus for imaging the form of an object to be measured by performing Fourier transform on the obtained image. Such an OCT apparatus is called a swept source type. The swept source type is a kind of Fourier domain type.

  In 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. Prior to the application of OCT, a fundus camera, a slit lamp, an SLO (Scanning Laser Ophthalmoscope), and the like were used as devices for observing the eye to be examined (for example, Patent Document 6, Patent Document 7, and 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 OCT apparatus 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.

  As described above, an ophthalmic observation apparatus using OCT can be applied to observation of various parts of an eye to be examined, and can acquire high-definition images, and thus has been applied to diagnosis of various ophthalmic diseases. . Here, in order to observe various parts of the eye to be examined, an ophthalmologic photographing apparatus capable of OCT measurement of both the fundus and the anterior segment may be used. In such an ophthalmologic photographing apparatus, an attachment (adapter, optical unit) for changing the focal position of the measurement light from the fundus to the anterior eye part is selectively applied (see Patent Document 9). This attachment includes a lens having a predetermined refractive power.

JP 11-325849 A JP 2002-139421 A JP 2007-24677 A JP 2006-153838 A JP 2008-73099 A JP-A-9-276232 JP 2008-259544 A JP 2009-11811 A JP2012-223435A

  By the way, in OCT measurement, fixation is performed to suppress the movement of the eye to be examined. Fixation is performed by presenting a fixation target for gaze the eye to be examined in a predetermined direction. Many ophthalmologic photographing apparatuses incorporate an optical system (fixation optical system) for presenting a fixation target. In an ophthalmologic imaging apparatus capable of OCT measurement, the optical path of measurement light and the optical path of the fixation optical system share a part of each other. For example, a configuration in which the measurement light and the fixation light beam are guided to the eye to be examined through a common objective lens is applied.

  When the attachment is applied to such an ophthalmologic photographing apparatus, the imaging state of the fixation light flux is changed by the lens in the attachment. Then, fixation cannot be performed properly. That is, as the attachment is attached, the imaging position of the light beam for fixation shifts from the retina, so that the subject cannot clearly see the fixation target.

  An object of the present invention is to improve the operability at the time of setting or switching a target part for OCT measurement.

The invention according to claim 1 is an optical system that divides light from the first light source into measurement light and reference light, and detects interference light between the return light of the measurement light and the reference light from the eye to be examined. An image forming unit that forms an image based on a detection result by the optical system, and an optical path of the measurement light, the focus position of the measurement light being changed from the first part to the second part of the eye to be examined An ophthalmologic photographing apparatus having an optical unit including a lens for changing to a lens and a detection unit that detects use or non-use of the optical unit based on examination contents input by a user.
The invention according to claim 2 divides light from the first light source into measurement light and reference light, and detects an interference light between the return light of the measurement light from the eye to be examined and the reference light. An image forming unit that forms an image based on a detection result by the optical system, and an optical path of the measurement light, the focus position of the measurement light being changed from the first part to the second part of the eye to be examined An ophthalmologic photographing apparatus comprising: an optical unit including a lens for changing to: and a detection unit that detects use or non-use of the optical unit based on electronic medical record information of the subject.
A third aspect of the present invention is the ophthalmologic photographing apparatus according to the first or second aspect, wherein the optical system irradiates the subject's eye with the measurement light via an objective lens, and passes through the objective lens. A fixation optical system for presenting a first fixation target to the eye to be examined; the lens included in the optical unit is disposed in an optical path of light from the fixation optical system; A combining member for combining the optical path from the second light source with the optical path of the measurement light, and the light from the second light source guided to the optical path of the measuring light by the combining member through the lens. The image is formed on the fundus of the subject's eye as a fixation target of No. 2.
A fourth aspect of the present invention is the ophthalmologic photographing apparatus according to the third aspect, wherein the second light source is provided outside the optical unit.
The invention according to claim 5 is the ophthalmologic photographing apparatus according to claim 4, wherein the second light source is arranged around the objective lens.
A sixth aspect of the present invention is the ophthalmologic photographing apparatus according to any one of the third to fifth aspects, wherein the optical unit is disposed between the objective lens and the eye to be examined. It is characterized by.

  According to the present invention, it is possible to improve the operability at the time of setting or switching the target site for OCT measurement.

It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an embodiment. It is a schematic block diagram showing an example of composition of an ophthalmology photographing instrument concerning an embodiment. It is the schematic showing an example of a structure of the optical unit which concerns on embodiment. It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an embodiment. It is a schematic block diagram showing an example of composition of an ophthalmology photographing instrument concerning an embodiment.

  An example of an embodiment of an ophthalmologic photographing apparatus according to the present invention will be described in detail with reference to the drawings. The ophthalmologic imaging apparatus according to the embodiment forms a tomographic image or a three-dimensional image of the fundus using OCT. In this specification, images acquired by OCT may be collectively referred to as OCT images. In addition, a measurement operation for forming an OCT image may be referred to as OCT measurement. In addition, it is possible to use suitably the description content of the literature described in this specification as the content of the following embodiment.

  In the following embodiment, a configuration to which Fourier domain type OCT is applied will be described in detail. In particular, the ophthalmologic imaging apparatus according to the embodiment can acquire both the OCT image and the fundus image of the fundus using the spectral domain OCT technique, as in the apparatus disclosed in Patent Document 5.

  By attaching an attachment (optical unit) to the ophthalmologic photographing apparatus for photographing the fundus, the application is changed to photographing the anterior segment. In addition, it is also possible to configure so that the use is changed to fundus photographing by originally attaching an attachment (optical unit) to an ophthalmologic photographing apparatus for photographing the anterior segment. Further, the imaging target part is not limited to the fundus and anterior eye part, and may be an arbitrary part of the eye to be examined, such as a vitreous body or a crystalline lens. Furthermore, it is also possible to prepare attachments (optical units) corresponding to the parts to be imaged and selectively apply them to the ophthalmologic imaging apparatus. It is also possible to configure to automatically use / not use an attachment (optical unit) and / or to select an attachment to be applied. These selection processes are performed based on, for example, the contents of imaging performed in the past, the names of sicknesses and the like.

  The configuration according to the present invention can also be applied to an ophthalmic imaging apparatus using a type other than the spectral domain, for example, a swept source OCT technique. In the following embodiment, an apparatus combining an OCT apparatus and a fundus camera will be described. However, a fundus photographing apparatus other than the fundus camera, for example, an SLO, a slit lamp, an ophthalmic surgical microscope, and the like has a configuration according to this embodiment. It is also possible to combine the OCT apparatus which has. In addition, the configuration according to this embodiment can be incorporated into a single OCT apparatus.

<First Embodiment>
[Constitution]
As shown in FIGS. 1 and 2, the ophthalmologic photographing apparatus 1 includes a fundus camera unit 2, an OCT unit 100, an arithmetic control unit 200, and an optical unit 300 as an attachment. The retinal camera unit 2 has almost the same optical system as a conventional retinal camera. The OCT unit 100 is provided with an optical system for acquiring an OCT image of the fundus. The arithmetic control unit 200 includes a computer that executes various arithmetic processes and control processes. The optical unit 300 is configured to be inserted / retracted with respect to the optical path toward the eye E. The optical unit 300 is retracted from the optical path when performing OCT measurement of the fundus, and is disposed in the optical path when performing OCT measurement of the anterior segment.

[Fundus camera unit]
The fundus camera unit 2 shown in FIG. 1 is provided with an optical system for obtaining a two-dimensional image (fundus image) representing the surface form of the fundus oculi Ef of the eye E to be examined. The fundus image includes an observation image and a captured image. The observation image is, for example, a monochrome moving image formed at a predetermined frame rate using near infrared light. The captured image 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 retinal camera unit 2 is provided with a chin rest and a forehead support 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). The imaging optical system 30 guides the measurement light from the OCT unit 100 to the fundus oculi Ef, and guides the measurement light passing through the fundus oculi Ef (that is, the return light of the measurement light from the fundus oculi Ef) to the OCT unit 100.

  The observation light source 11 of the illumination optical system 10 is constituted by a halogen lamp, for example. 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) can also be used as the observation light source.

  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. Furthermore, 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. When the photographing optical system is focused on the anterior segment, an observation image of the anterior segment of the eye E is displayed.

  The imaging 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. Note that 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. In addition, when similar imaging is performed by illuminating the eye E with infrared light, an infrared captured image is displayed. It is also possible to use an LED as a photographing light source.

  An 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.

  By changing the display position of the fixation target on the screen of the LCD 39, the fixation position of the eye E can be changed. 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.

  Further, the fundus camera unit 2 is provided with an alignment optical system 50 and a focus optical system 60 as in a 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).

  When performing the focus adjustment, 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 cornea 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 branches the optical path for OCT measurement from the optical path for fundus photography. The dichroic mirror 46 reflects light in a wavelength band used for OCT measurement and transmits light for fundus photographing. In this optical path for OCT measurement, 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. It has been.

  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 (measurement light LS) passing through the optical path for OCT measurement. Thereby, the fundus oculi Ef can be scanned with the measurement light LS. The galvano scanner 42 includes, for example, a galvanometer mirror that scans the measurement light LS in the x direction, a galvanometer mirror that scans in the y direction, and a mechanism that drives these independently. Thereby, the measurement light LS can be scanned in an arbitrary direction on the xy plane.

[OCT unit]
An example of the configuration of the OCT unit 100 will be described with reference to FIG. 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 the low-coherence light into reference light and measurement light, and generates interference light by causing the measurement light passing through the fundus oculi Ef and the reference light passing through the reference optical path to generate interference light. It is configured to detect spectral components. This detection result (detection signal) is sent to the arithmetic control unit 200.

  In the case of a swept source type OCT apparatus, 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. In general, for the configuration of the OCT unit 100, 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 that cannot be visually recognized by 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 light output device such as a super luminescent diode (SLD), an LED, or an 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 measurement light LS and the reference light LR.

  The reference light LR is guided by the optical fiber 104 and reaches the 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 measurement 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 measurement 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. Then, the measurement 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 measurement light LS is scattered (including reflection) at various depth positions of the fundus oculi Ef. The backscattered light (return light) of the measurement 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 measurement light LS to interfere with the reference light LR that has passed through the optical fiber 104. 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. Although 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.

  In this embodiment, a Michelson type interferometer is employed, but any type of interferometer such as a Mach-Zehnder type can be appropriately employed. Further, in place of the CCD image sensor, another form of image sensor such as a CMOS (Complementary Metal Oxide Semiconductor) image sensor can be used.

[Calculation control unit]
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.

  As the control of the fundus camera unit 2, 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.

  As control of the OCT unit 100, 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, etc., as in a conventional computer. A computer program for controlling the ophthalmologic photographing 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 photographing apparatus 1 will be described with reference to FIG.

(Control part)
The control system of the ophthalmologic photographing 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 is provided with a main control unit 211 and a storage unit 212.

(Main control unit)
The main control unit 211 performs the various controls described above. In particular, the main control unit 211 controls the focusing drive unit 31A, the optical path length changing unit 41, and the galvano scanner 42 of the fundus camera unit 2, and further the light source unit 101, the optical attenuator 105, and the polarization adjuster 106 of the OCT unit 100. To do.

  The focusing drive unit 31A moves the focusing lens 31 in the optical axis direction. Thereby, the focus position of the photographic optical system 30 is changed. The main control unit 211 can also move an optical system provided in the fundus camera unit 2 in a three-dimensional manner by controlling an optical system drive unit (not shown). 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.

  Further, the main control unit 211 performs processing for writing data into the storage unit 212 and processing for reading data from the storage unit 212.

(Memory part)
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 photographing apparatus 1.

(Image forming part)
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, FFT (Fast Fourier Transform), and the like, 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.

(Image processing unit)
The image processing unit 230 performs various types of image processing and analysis processing on the image formed by the image forming unit 220. For example, the image processing unit 230 executes various correction processes such as image brightness correction and dispersion correction. The image processing unit 230 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. Note that the image data of a three-dimensional image means image data in which pixel positions are defined by a three-dimensional coordinate system. As 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. When displaying an image based on volume data, the image processing unit 230 performs rendering processing (volume rendering, MIP (Maximum Intensity Projection), etc.) on the volume data, and views the image from a specific gaze direction. Image data of a pseudo three-dimensional image is formed. This pseudo three-dimensional image is displayed on a display device such as the display unit 240A.

  It is also possible to form stack data of a plurality of tomographic images as 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 that functions as described above includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, circuit board, and the like. In 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.

(User interface)
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 photographing apparatus 1 or outside. For example, when the fundus camera unit 2 has a housing similar to that of a conventional fundus camera, 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. For example, a device in which a display function and an operation function are integrated, such as a touch panel, can be used. In that case, 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.

[Optical unit]
A configuration example of the optical unit 300 is shown in FIG. The optical unit 300 is disposed on the front side of the objective lens 22, that is, between the objective lens and the eye E when performing OCT measurement of the cornea Ec of the eye E to be examined. The optical unit 300 includes an optical system for projecting a fixation target onto the fundus oculi Ef, in addition to a lens (objective lens 305) for focusing the measurement light LS for OCT measurement on the cornea Ec.

  As another embodiment, when an optical unit is attached to an ophthalmologic photographing apparatus for the cornea (anterior eye part), this optical unit is retracted from the optical path during OCT measurement of the cornea, and during OCT measurement of the fundus. Located in the optical path. In this case, the optical unit includes a lens for focusing the measurement light on the fundus and an optical system for projecting the fixation target onto the fundus.

  In this example, a light source (fixation light source 310) for generating a fixation target is provided outside the optical unit 300. The fixation light source may be provided inside the optical unit. In any case, the fixation light source may be dedicated to fixation or may be used for other functions. For example, the fixation light source outputs at least visible light.

  When a fixation light source is provided outside the optical unit, the fixation light source is used, for example, to project an internal fixation target when performing OCT measurement of the cornea, and an external fixation lamp when performing OCT measurement of the fundus. Used as The fixation light source may have an arbitrary function such as a function for projecting a corneal shape measurement pattern in addition to the function as an external fixation lamp.

  FIG. 5 shows an example in which an external fixation lamp for performing peripheral fixation in the fundus OCT measurement is provided. Peripheral fixation is fixation for performing OCT measurement of the peripheral region of the fundus. FIG. 5 shows an outline of the front surface (surface on the eye E side) of the fundus camera unit 2 (the housing thereof). An objective lens 22 is provided on the front surface of the fundus camera unit 2. The objective lens 22 is accommodated in the lens barrel portion 22A. A light source holding part 23 is provided around the lens barrel part 22A. The light source holding part 23 is provided with a plurality of external fixation lamps 24i (i = 1 to n) for peripheral fixation. Each external fixation lamp 24i is, for example, an LED. In the present example, the plurality of external fixation lamps 24 i are arranged at equal intervals on a circumference centered on the optical axis of the objective lens 22. Control of the external fixation lamp 24i (for example, turning on, turning off, blinking, changing the output light amount, changing the output wavelength, etc.) is executed by the control unit 210.

  The optical unit 300 is disposed in front of the fundus camera unit 2. Light output from any one of the plurality of external fixation lamps 24i (for example, the external fixation lamp arranged at the uppermost position) is used as the fixation light source 310 shown in FIG.

  When a fixation light source is provided inside the optical unit and a configuration in which the optical unit can be retracted from the optical path while being connected to the ophthalmologic photographing apparatus is applied, a light guide means such as an optical fiber is used to fix the optical unit. By guiding the light from the visual light source to the outside of the optical unit, this light can be used for other purposes (for example, an external fixation lamp).

  The example shown in FIG. 4 will be described. The optical unit 300 of this example includes a relay lens 301, a reflection mirror 302, a relay lens 303, a beam splitter 304, and an objective lens 305.

  Light (fixation light LF) output from the fixation light source 310 and incident on the optical unit 300 is guided to the relay lens 301. The relay lenses 301 and 303 function as an optical system for relaying the image of the fixation light source 310 to the beam splitter 304. Specifically, the fixation light LF that has been converted into a parallel light beam by the relay lens 301 is reflected by the reflection mirror 302 and focused on the reflection surface of the beam splitter 304 by the relay lens 303.

  The beam splitter 304 is disposed at a position conjugate with the fundus oculi Ef, for example. The beam splitter 304 combines the optical path of the fixation light LF and the optical path of the measurement light LS. The beam splitter 304 is, for example, a dichroic mirror that reflects visible light (fixation light LF) and transmits infrared light (measurement light LS). Alternatively, the beam splitter 304 may be a half mirror.

  The fixation light LF that has passed through the dichroic mirror 304 is imaged on the fundus by the objective lens 305 and the eyeball optical system of the eye E. Thereby, a fixation target based on the fixation light source 310 is projected onto the fundus oculi Ef.

  On the other hand, the measurement light LS that has passed through the objective lens 22 of the fundus camera unit 2 passes through the beam splitter 304 of the optical unit 300 and is focused on the cornea Ec by the objective lens 305.

[effect]
The effect of the ophthalmologic photographing apparatus 1 will be described.

  The ophthalmologic photographing apparatus 1 includes an optical system, an image forming unit, and an optical unit. The optical system divides light from a first light source (for example, the light source unit 101) into measurement light and reference light, and detects interference light between the return light of the measurement light from the eye to be examined and the reference light. The image forming unit (for example, the image forming unit 220) forms an image based on the detection result of the interference light by the optical system (for example, a detection signal generated by the CCD image sensor 115).

  The optical unit (for example, the optical unit 300) can be disposed in the optical path of the measurement light. The optical unit includes a lens (for example, objective lens 305) for changing the focal position of the measurement light from the first part to the second part of the eye to be examined. The combination of the first part and the second part is arbitrary. For example, the first part is the fundus and the second part is the anterior segment (for example, the cornea). Alternatively, the first part is the anterior segment (eg, cornea) and the second part is the fundus. Furthermore, the optical unit includes a combining member that combines the optical path from the second light source (fixation light source) with the optical path of the measurement light. The combining member may be any beam splitter (eg, dichroic mirror 304, half mirror, etc.). The optical unit forms an image of the light from the second light source guided to the optical path of the measurement light by the combining member on the fundus of the eye to be examined through the lens.

  According to such an ophthalmologic photographing apparatus, when an optical unit is applied, light from the second light source can be imaged on the fundus via the optical unit. Therefore, even if the imaging position of the light beam for fixation from an optical system different from the optical unit is deviated from the retina due to the use of the optical unit, the subject can clearly see the fixation target. it can. Therefore, it is possible to perform fixation properly regardless of use / non-use of the optical unit. The second light source may be constituted by, for example, an LED or a flat panel display (for example, an LCD).

  The first light source can output light including infrared light, and the second light source can output light including visible light. In this case, the composite member may include a dichroic mirror (eg, dichroic mirror 305).

  The second light source may be provided in the optical unit. That is, the optical unit may be configured to project the fixation target on the fundus based on the light from the second light source provided therein. According to this configuration, it is necessary to provide the second light source in the optical unit, but it is not necessary to provide a configuration for guiding light from a light source provided in advance in the ophthalmologic photographing apparatus to the optical unit, for example.

  The second light source may be provided outside the optical unit. That is, the optical unit may be configured to project the fixation target on the fundus based on the light from the second light source provided outside the optical unit. According to this configuration, for example, a light source (which may have a function other than fixation) provided in advance in the ophthalmologic photographing apparatus is used as the second light source for projecting the fixation target onto the fundus when using the optical unit. Can be used as Therefore, the configuration of the optical unit can be simplified.

  When the second light source is provided outside the optical unit, the following configuration can be applied. First, the optical system includes an objective lens (for example, the objective lens 22) and one or more light sources (for example, an external fixation lamp 24i) disposed around the objective lens. Furthermore, the second light source includes any one of the one or more light sources. In this configuration, one of the light sources provided outside the optical unit and around the objective lens of the optical system for OCT measurement projects the fixation target onto the fundus when the optical unit is used. Used as a second light source.

  When the ophthalmologic photographing apparatus has one or more external fixation lamps (for example, the external fixation lamp 24i), the second light source may include any of the one or more external fixation lamps.

  The optical unit may include a relay optical system that relays the image of the second light source to the combining member. According to this configuration, the configuration of the optical unit can be simplified. In the case where this configuration is applied, the second light source may be a point light source substantially.

<Second Embodiment>
In this embodiment, a description will be given of control for switching means for performing fixations depending on whether an attachment (optical unit) is used or not. Hereinafter, the codes used in the first embodiment are applied mutatis mutandis.

[Constitution]
The configuration of the optical system of the ophthalmologic photographing apparatus of this embodiment may be the same as that of the first embodiment (see FIGS. 1, 2 and 5). Also, the optical unit (attachment) may be the same as in the first embodiment (see FIG. 4).

  The control system of the ophthalmologic photographing apparatus of this embodiment has a configuration shown in FIG. 6, for example. The difference from the control system (FIG. 3) of the first embodiment is that the detection unit 250 is provided and the external fixation lamp 24i is clearly shown.

  The external fixation lamp 24i corresponds to a fixation light source (second light source) provided outside the optical unit 300. As described in the first embodiment, the fixation light source provided outside the optical unit 300 is not limited to the external fixation lamp. On the other hand, when a fixation light source is provided in the optical unit 300, the control unit 210 controls the fixation light source (turning on / off, changing the output light amount, changing the output wavelength, etc.).

  The detection unit 250 detects whether or not the optical unit 300 is disposed in the optical path of the measurement light LS. This detection means one or both of detection that the optical unit 300 is disposed in the optical path and detection that the optical unit 300 is not disposed in the optical path. The detection unit 250 includes, for example, a micro switch, a position sensor, and the like.

  When a micro switch is used, the micro switch is disposed at a position where it contacts the optical unit 300 in a state where it is disposed in the optical path of the measurement light LS, for example. The microswitch is “ON” when the optical unit 300 is disposed in the optical path of the measurement light LS, and is “OFF” when the optical unit 300 is retracted from the optical path. The micro switch inputs a signal to the control unit 210 when the micro switch is on. Based on the presence or absence of this signal, the control unit 210 can recognize whether or not the optical unit 300 is disposed in the optical path.

  When a position sensor is used, this position sensor detects, for example, the current position of the optical unit 300 and inputs a signal indicating the detection result to the control unit 210. Based on the content of this signal, the control unit 210 can recognize whether or not the optical unit 300 is arranged in the optical path.

  The ophthalmologic photographing apparatus according to this embodiment includes a fixation optical system for presenting a fixation target to the eye E as in the first embodiment. This fixation optical system includes an LCD 39. 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 passes through the dichroic mirror 46. The light is refracted by the objective lens 22 and imaged on the fundus oculi Ef. When the optical unit 300 is disposed in front of the objective lens 22, the LCD 39 and the cornea Ec are conjugated, so that the subject cannot clearly see the fixation target.

  Operations performed by the control unit 210 will be described. In response to recognizing that the optical unit 300 is disposed in the optical path of the measurement light LS, the control unit 210 controls the light from the external fixation lamp 24i to form an image on the fundus oculi Ef by the optical unit 300. I do. This control includes at least turning on the external fixation lamp 24i. When light is output from the LCD 39 when it is recognized that the optical unit 300 is disposed in the optical path of the measurement light LS, the control unit 210 turns off the LCD 39.

  On the other hand, in response to recognizing that the optical unit 300 is not disposed in the optical path of the measurement light LS, the control unit 210 presents a fixation target using a fixation optical system built in the ophthalmologic photographing apparatus. Take control. This control includes at least displaying the fixation target on the LCD 39. When light is output from the external fixation lamp 24i when it is recognized that the optical unit 300 is not disposed in the optical path of the measurement light LS, the control unit 210 turns off the external fixation lamp 24i. .

[effect]
The effect of the ophthalmologic photographing apparatus of this embodiment will be described.

  The ophthalmologic photographing apparatus of this embodiment has the same effect as that of the first embodiment.

  Further, according to the ophthalmologic photographing apparatus of this embodiment, when an optical unit (for example, the optical unit 300) is used, the light from the second light source (for example, the external fixation lamp 24i) is coupled to the fundus by the optical unit. Control for imaging can be performed. Therefore, when using the optical unit (for example, when shifting from OCT measurement of the fundus to the OCT measurement of the anterior eye), it is not necessary to manually switch means for performing fixation.

  Furthermore, according to the ophthalmologic photographing apparatus of this embodiment, when the optical unit is not used, control for presenting a fixation target can be performed by a fixation optical system built in the apparatus. Therefore, when the optical unit is not used (for example, when shifting from OCT measurement of the anterior segment to OCT measurement of the fundus), it is not necessary to manually switch means for performing fixation.

  Thus, according to the ophthalmologic imaging apparatus of this embodiment, it is possible to improve the operability when setting or switching the target site for OCT measurement.

  In addition, a detection part is not limited to the structure which detects the position and operation | movement of an optical unit. For example, the detection unit may be configured to detect use / non-use of the optical unit based on information input from the outside. Specifically, based on the examination content input by the user (for example, explicitly or implicitly indicating the measurement target site), the detection unit is arranged before the optical unit is arranged in the optical path of the measurement light, or from the optical path. It is possible to recognize the use / non-use of the optical unit before it is retracted. Alternatively, for example, the use / non-use of the optical unit may be recognized by referring to the electronic medical record information (such as past examination contents) of the subject.

<Optical unit>
The optical unit described in the above embodiment can be attached to an ophthalmologic photographing apparatus having an OCT function. This ophthalmologic photographing apparatus has an optical system and an image forming unit. The optical system divides the light from the first light source into measurement light and reference light, and detects interference light between the return light of the measurement light from the eye to be examined and the reference light. The image forming unit forms an image based on the detection result by the optical system.

  This optical unit can be arranged in the optical path of the measurement light. Further, the optical unit includes a lens for changing the focal position of the measurement light from the first part to the second part of the eye to be examined, and a combining member that combines the optical path from the second light source with the optical path of the measurement light. And have. Further, the optical unit is configured to form an image of the light from the second light source guided to the optical path of the measurement light by the combining member on the fundus of the eye to be examined through the lens. The second light source is provided inside or outside the optical unit.

  In the case where the first light source outputs light including infrared light and the second light source outputs light including visible light, the combining member may include a dichroic mirror. The optical unit may include a relay optical system that relays the image of the second light source to the combining member.

  According to such an optical unit, it is possible to perform fixation appropriately regardless of use / nonuse.

[Modification]
The configuration described above is merely an example for favorably implementing the present invention. Therefore, arbitrary modifications (omitted, replacement, addition, etc.) within the scope of the present invention can be made as appropriate.

  In the above embodiment, the fixation target projection position by the optical unit 300 can be changed. For example, it is possible to apply a configuration in which the projection position of the fixation target is changed by using the reflection mirror 302 of the optical unit 300 as a deflection mirror. This deflection mirror is a two-dimensional deflection mirror such as a biaxial galvanometer mirror, and operates under the control of the control unit 210. As another configuration example for changing the projection position of the fixation target, a mechanism for moving the beam splitter 304 can be provided. This mechanism moves the beam splitter 304 along the normal direction of the functional plane of the beam splitter 304 (a plane having an optical path combining / branching function and a plane having a filter function). This mechanism operates under the control of the control unit 210. According to this example, since the fixation position of the eye E can be changed when performing OCT measurement of the cornea, it is possible to facilitate OCT measurement of any part of the cornea (for example, a peripheral part).

  In the above-described embodiment, the focus adjustment of the fixation target projected onto the fundus oculi Ef by the optical unit 300 can be executed. For example, it is possible to apply a configuration for adjusting the focus of the fixation target by providing a mechanism for moving the relay lens 303 (and / or the reflection mirror 302) of the optical unit 300 in the optical axis direction. This mechanism operates under the control of the control unit 210. As an example of this control, the ophthalmologic photographing apparatus 1 obtains a projection state (focus state) of the fixation target by analyzing an image (observation image or the like) of the eye E acquired in real time, and according to the projection state. Thus, the mechanism can be controlled. Further, the ophthalmologic photographing apparatus 1 is configured to display a real-time image of the fundus oculi Ef in a state in which a fixation target is projected, and to control the mechanism according to the content of the operation performed by the user based on this image. It is also possible. According to this example, it is possible to present a suitable fixation target in focus to the eye E.

  The configuration of the optical unit 300 described in the above embodiment is merely an example. For example, regarding the arrangement of the optical elements, the beam splitter 304 does not have to be arranged at a pupil conjugate position.

  In the above embodiment, the optical path length difference between the optical path of the measurement 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. For example, 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. Is possible. Further, 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 measurement light LS. In particular, when the measured object is not a living body part, the optical path length difference can be changed by moving the measured object in the depth direction (z direction).

  A computer program for realizing the above embodiment can be stored in any recording medium readable by a computer. Examples of the recording medium include 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.), and the like. Can be used.

  It is also possible to transmit / receive this program through a network such as the Internet or a LAN.

DESCRIPTION OF SYMBOLS 1 Ophthalmic imaging device 2 Fundus camera unit 22 Objective lens 24i External fixation lamp 39 LCD
100 OCT unit 101 light source unit 200 arithmetic control unit 210 control unit 211 main control unit 212 storage unit 220 image forming unit 230 image processing unit 240A display unit 240B operation unit 300 optical unit 301 relay lens 302 reflection mirror 303 relay lens 304 beam splitter 305 Objective lens 310 Fixation light source E Eye Ec Cornea Ef Fundus LS Measurement light LR Reference light LC Interference light LF Fixation light

Claims (6)

An optical system that divides light from the first light source into measurement light and reference light, and detects interference light between the return light of the measurement light from the eye to be examined and the reference light;
An image forming unit that forms an image based on a detection result by the optical system;
An optical unit that can be arranged in the optical path of the measurement light and includes a lens for changing the focal position of the measurement light from the first part to the second part of the eye to be examined;
An ophthalmologic imaging apparatus comprising: a detection unit that detects use or non-use of the optical unit based on examination contents input by a user. An optical system that divides light from the first light source into measurement light and reference light, and detects interference light between the return light of the measurement light from the eye to be examined and the reference light;
An image forming unit that forms an image based on a detection result by the optical system;
An optical unit that can be arranged in the optical path of the measurement light and includes a lens for changing the focal position of the measurement light from the first part to the second part of the eye to be examined;
An ophthalmologic imaging apparatus comprising: a detection unit that detects use or non-use of the optical unit based on electronic medical record information of the subject. The optical system irradiates the eye to be examined through the objective lens with the measurement light,
A fixation optical system for presenting a first fixation target to the eye to be examined via the objective lens;
The lens included in the optical unit is disposed in an optical path of light from the fixation optical system,
The optical unit includes a synthesis member that synthesizes an optical path from a second light source with an optical path of the measurement light, and the light from the second light source guided to the optical path of the measurement light by the synthesis member is the lens. 3. The ophthalmologic photographing apparatus according to claim 1, wherein an image is formed on the fundus of the eye to be examined as a second fixation target via the lens. The ophthalmologic photographing apparatus according to claim 3, wherein the second light source is provided outside the optical unit. The ophthalmologic photographing apparatus according to claim 4, wherein the second light source is disposed around the objective lens. The ophthalmologic photographing apparatus according to any one of claims 3 to 5, wherein the optical unit is disposed between the objective lens and the eye to be examined.

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