JP2020156622A - Ophthalmologic apparatus - Google Patents

Abstract

To provide an ophthalmologic apparatus capable of shortening the time for imaging and measurement while securing precision and accuracy of the imaging and the measurement.SOLUTION: An ophthalmologic apparatus for optically acquiring data on an eye to be examined includes: a data acquisition unit 250 having an optical system which collects OCT data by projecting at least part of the light from a light source onto an eye to be examined as a measurement light, and applying optical coherence tomography scanning to a three-dimensional region of the eye to be examined, a data processing unit 230 for specifying a transmission position where the measurement light transmits the anterior eye part of the eye to be examined based on the arrangement of the optical system; and a display control unit 2102 for causing display means to display an image showing the transmission position specified by the data processing unit 230 by superimposing it on an image of the eye to be examined.SELECTED DRAWING: Figure 3B

Description

The present invention relates to an ophthalmic apparatus.

In ophthalmic practice, a device for obtaining an image of an eye to be inspected (ophthalmic imaging device) and a device for measuring the characteristics of the eye to be inspected (ophthalmology measuring device) are used.

Examples of ophthalmologic imaging devices include an optical coherence tomography that obtains data using optical coherence tomography (OCT), a fundus camera that photographs the fundus, and a fundus image by laser scanning using a confocal optical system. There is a scanning laser ophthalmoscope (SLO) and the like. Patent Document 1 discloses an ophthalmologic observation system that acquires a three-dimensional tomographic image of a subject's eye by OCT.

Examples of ophthalmic measuring devices include an ophthalmic refraction tester (refractometer) that measures the refraction characteristics of the eye to be inspected, a wavefront analyzer that obtains aberration data of the eye to be inspected using a Hartmann-Shack sensor, a corneal apex and a central retinal fossa. There is an axial length measuring device that measures the distance between them (axial length).

The ophthalmic apparatus illustrated above projects light toward the fundus of the eye to be inspected and obtains data based on the return light. Therefore, when the intermediate translucent body (lens, vitreous, etc.) is opaque, such as in a cataract eye, the projected light and the return light are affected by the opacity, and imaging and measurement may not be suitable.

Further, the light source of the optical interference tomographic meter for which data is obtained by using OCT emits light in a wavelength band in the near infrared region, for example. Therefore, the examiner cannot visually recognize the light (measurement light) projected from the light source toward the eye to be inspected through an optical system having a mirror, a lens, or the like, and the measurement light passes through the anterior segment of the eye to be inspected. The transmission position cannot be confirmed. Further, the examiner cannot confirm the transmission position through which the measurement light passes through the anterior segment of the eye to be inspected even when a display unit such as a display is used. Therefore, even if the examiner can confirm the opaque region existing in the intermediate translucent body of the eye to be inspected, it is difficult for the examiner to transmit the measurement light to the anterior segment of the eye to be inspected while avoiding the opaque region. .. That is, the examiner can acquire an accurate photographed image of the anterior segment and fundus of the eye to be inspected only after operating the optical interference tomography and confirming the captured image after photographing the anterior segment and fundus of the eye to be inspected. Notice that it wasn't there. Even when the examiner re-operates the optical interference tomography and re-photographs the eye to be inspected, the examiner cannot confirm the transmission position through which the measured light passes through the anterior segment of the eye to be inspected, so that the examiner acquires an accurate photographed image again. It may not be possible. Therefore, in an ophthalmic apparatus that projects measurement light onto an eye to be inspected and optically acquires data of the eye to be inspected, it is desired to shorten the time for taking and measuring while ensuring the accuracy and accuracy of taking and measuring. There is.

Japanese Unexamined Patent Publication No. 2012-75640

The present invention has been made to solve the above problems, and an object of the present invention is to provide an ophthalmic apparatus capable of shortening the time for imaging and measurement while ensuring the accuracy and accuracy of imaging and measurement. To do.

The subject is an ophthalmic apparatus that optically acquires data of an eye to be inspected, and projects at least a part of the light from the light source as measurement light onto the eye to be inspected and optical coherence stromography in a three-dimensional region of the eye to be inspected. A data acquisition unit having an optical system for collecting OCT data by applying a scan, and a data processing unit for specifying a transmission position through which the measurement light passes through the anterior segment of the eye to be inspected based on the arrangement of the optical system. The ophthalmic apparatus according to the present invention comprises a display control unit that superimposes an image representing the transmission position specified by the data processing unit on the image of the eye to be inspected and displays it on a display means. Will be done.

According to the ophthalmic apparatus according to the present invention, the data processing unit specifies a transmission position through which the measurement light passes through the anterior segment of the eye to be inspected based on the arrangement of the optical system for collecting OCT data. Then, the display control unit superimposes an image representing the transmission position specified by the data processing unit on the image of the eye to be inspected and causes the display means to display the image. Therefore, the examiner can confirm the transmission position through which the measurement light passes through the anterior segment of the eye to be inspected by visually recognizing the display means. Therefore, the examiner can set the transmission position through which the measurement light passes through the anterior segment of the eye to be inspected to the intended position, and the measurement light is incident inside the eye to be inspected through the transmission position to cause the data of the eye to be inspected. Can be obtained. As a result, it is possible to shorten the shooting and measuring time while ensuring the accuracy and accuracy of shooting and measuring.

In the ophthalmic apparatus according to the present invention, preferably, the display control unit superimposes an image representing the transmission position specified by the data processing unit on the image of the anterior eye portion and causes the display means to display the image. And.

According to the ophthalmic apparatus according to the present invention, the examiner visually recognizes the display means to visually recognize the image of the anterior segment of the eye to be inspected displayed on the display means, and the measurement light passing through the anterior segment of the eye. You can check the transmission position of. Therefore, the transmission position through which the measurement light passes through the anterior segment of the eye to be inspected can be reliably set at the intended position, and the measurement light is incident inside the eye to be inspected through the transmission position to obtain more data of the eye to be inspected. You can definitely get it.

In the ophthalmologic apparatus according to the present invention, preferably, the data processing unit specifies the projection direction of the measurement light based on the arrangement of the optical system, and the measurement light is generated based on the transmission position and the projection direction. The reaching position to reach the fundus of the eye to be inspected is further specified, and the display control unit further superimposes an image representing the reaching position specified by the data processing unit on the image of the fundus and causes the display means to display the image. It is characterized by that.

According to the ophthalmic apparatus according to the present invention, the data processing unit specifies the projection direction of the measurement light based on the arrangement of the optical system for collecting the OCT data, and is based on the transmission position of the measurement light and the projection direction of the measurement light. The arrival position where the measurement light reaches the fundus of the eye to be inspected is specified. Then, the display control unit superimposes an image representing the arrival position specified by the data processing unit on the image of the fundus and causes the display means to further display the image. Therefore, the examiner can confirm the arrival position at which the measurement light reaches the fundus of the eye to be inspected in the image of the fundus by visually recognizing the display means. Therefore, the examiner can confirm the arrival position at which the measurement light reaches the fundus of the eye to be inspected while setting the transmission position through which the measurement light passes through the anterior segment of the eye to be inspected to the intended position. As a result, it is possible to shorten the time required for taking an image of the fundus while ensuring accuracy and accuracy.

In the ophthalmic apparatus according to the present invention, preferably, the display control unit superimposes an image representing the arrival position specified by the data processing unit on the three-dimensional scan image of the fundus acquired by the data acquisition unit. It is characterized in that it is further displayed by the display means.

According to the ophthalmic apparatus according to the present invention, the examiner can confirm the reaching position where the measurement light reaches the fundus of the eye to be inspected in the three-dimensional scan image of the fundus by visually recognizing the display means. As a result, it is possible to shorten the time required for capturing a three-dimensional scan image of the fundus while ensuring accuracy and accuracy.

In the ophthalmic apparatus according to the present invention, preferably, the display control unit superimposes an image showing a locus of the arrival position specified by the data processing unit by the optical coherence tomography scan on the image of the fundus and displays the display. It is characterized in that it is displayed by means.

According to the ophthalmologic apparatus according to the present invention, by visually recognizing the display means, the examiner can obtain an image of the fundus or the fundus of the fundus by visually recognizing the locus of the reaching position where the measurement light reaches the fundus of the eye to be inspected. It can be confirmed in the B scan image of the above and the three-dimensional scan image of the fundus. As a result, it is possible to shorten the time for the OCT scan in the three-dimensional region of the fundus of the eye to be inspected while ensuring the accuracy and accuracy.

In the ophthalmic apparatus according to the present invention, preferably, the data processing unit analyzes the OCT data to further identify the opaque region of the anterior ocular region, and the display control unit is specified by the data processing unit. It is characterized in that an image showing the turbid region is superimposed on the image of the eye to be inspected and further displayed on the display means.

According to the ophthalmic apparatus according to the present invention, the examiner can easily grasp the opaque region in the anterior segment of the eye to be inspected by visually recognizing the display means, and the measurement light is the anterior segment of the eye to be inspected. It is possible to set the position to avoid the turbid region while checking the transmission position through which the light is transmitted. As a result, the accuracy and accuracy of shooting and measurement can be improved, and the time for shooting and measurement can be shortened.

According to the present invention, it is possible to provide an ophthalmic apparatus capable of shortening the time for imaging and measurement while ensuring the accuracy and accuracy of imaging and measurement.

It is the schematic which shows an example of the structure of the ophthalmic apparatus which concerns on embodiment of this invention. It is the schematic which shows an example of the structure of the OCT unit of this embodiment. It is the schematic which shows an example of the structure of the arithmetic control unit of this embodiment. It is the schematic which shows an example of the structure of the arithmetic control unit of this embodiment. It is a front view which shows an example of the ophthalmic apparatus which concerns on this embodiment. It is a side view which shows an example of the ophthalmic apparatus which concerns on this embodiment. It is a top view which shows the positional relationship between an eye to be examined and an anterior eye camera. It is a side view which shows the positional relationship between an eye under test and an anterior eye camera. It is a flowchart explaining an example of operation of the ophthalmic apparatus which concerns on this embodiment. FIG. 5 is a schematic view showing a state in which an image showing a transmission position of measurement light is superimposed on an image of the anterior segment and displayed on the display unit. It is a schematic diagram which shows the state which the image which shows the arrival position of the measurement light is superposed on the image of the fundus, and is displayed on the display part. It is a schematic diagram which shows the state which the image which shows the arrival position of the measurement light is superposed on the 3D scan image of the fundus, and is displayed on the display part. It is a flowchart explaining the modification of the operation of the ophthalmic apparatus which concerns on this embodiment. It is a schematic diagram which shows the state which the image which shows the transmission position of the measurement light, and the image which shows an opaque region is superposed on the image of the anterior segment part, and is displayed on the display part. It is a schematic diagram which shows the state which the image which shows the arrival position of the measurement light and the image which shows the opaque area are superposed on the image of the fundus, and is displayed on the display part. It is a schematic diagram which shows the state which the image which shows the arrival position of the measurement light and the image which shows the opaque region are superposed on the three-dimensional scan image of the fundus, and is displayed on the display part.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the drawings.
Since the embodiments described below are suitable specific examples of the present invention, various technically preferable limitations are attached, but the scope of the present invention particularly limits the present invention in the following description. Unless otherwise stated, the present invention is not limited to these aspects. Further, in each drawing, the same components are designated by the same reference numerals, and detailed description thereof will be omitted as appropriate.

The ophthalmic apparatus according to the embodiment is used to optically acquire data of the eye to be inspected (that is, using light and using optical technology). In particular, the ophthalmic apparatus according to the embodiment can acquire data of the eye to be inspected by injecting light into the eye through the pupil of the eye to be inspected.

Such an ophthalmic apparatus includes, for example, at least one of an imaging function and a measuring function. Examples of ophthalmic devices having an imaging function include an optical interference tomogram, a fundus camera, and a scanning laser ophthalmoscope. Examples of ophthalmic devices having a measuring function include an axial length measuring device, an ocular refraction testing device, a wavefront analyzer, a microperimeter, and a perimeter.

In the following examples, an ophthalmologic imaging apparatus in which a Swept source OCT and a fundus camera are combined will be described, but the embodiment is not limited thereto. The type of OCT is not limited to Swept Source OCT, and may be, for example, Spectral Domain OCT.

The swept source OCT divides the light from the variable wavelength light source into the measurement light and the reference light, superimposes the return light of the measurement light from the test object on the reference light to generate interference light, and balances this interference light. This is a method of forming an image by detecting with an optical detector such as a dophotonode and performing Fourier transform or the like on the detection data collected according to the sweep of the wavelength and the scanning of the measurement light.

Spectral domain OCT divides the light from the low coherence light source into measurement light and reference light, and superimposes the return light of the measurement light from the subject with the reference light to generate interference light, and the spectrum of this interference light. This is a method in which the distribution is detected by a spectroscope and the detected spectral distribution is subjected to Fourier transform or the like to form an image.

As described above, Swept Source OCT is an OCT method for acquiring a spectral distribution by time division, and Spectral Domain OCT is an OCT method for acquiring a spectral distribution by spatial division. The OCT method that can be used in the embodiment is not limited to these, and it is also possible to adopt an embodiment that uses an arbitrary OCT method (for example, time domain OCT) different from these.

In the present specification, unless otherwise specified, "image data" and "image" based on the "image data" are not distinguished. In addition, unless otherwise specified, the site or tissue of the eye to be inspected is not distinguished from the image showing it.

[Constitution]
FIG. 1 is a schematic view showing an example of the configuration of an ophthalmic apparatus according to an embodiment of the present invention.
The exemplary ophthalmic apparatus 1 shown in FIG. 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200. The fundus camera unit 2 is provided with an optical system and mechanism for acquiring a front image of the eye E to be inspected, and an optical system and mechanism for executing OCT. The OCT unit 100 is provided with an optical system and a mechanism for executing OCT. The arithmetic control unit 200 includes one or more processors configured to perform various processes (calculations, controls, etc.). Further, the ophthalmic apparatus 1 includes two anterior segment cameras 300 for photographing the anterior segment from two directions.

The fundus camera unit 2 is provided with a chin rest and a forehead pad for supporting the face of the subject. The chin rest and forehead rest correspond to the support portion 440 shown in FIGS. 4A and 4B. The base 410 stores a drive system such as an optical system drive unit and an arithmetic control circuit. The optical system is housed in the housing 420 provided on the base 410. The objective lens 22 is housed in the lens accommodating portion 430 provided so as to project from the front surface of the housing 420.

Further, the ophthalmic apparatus 1 includes a lens unit for switching a site to which OCT is applied. Specifically, the ophthalmic apparatus 1 includes an anterior segment OCT attachment 400 for applying OCT to the anterior segment. The anterior segment OCT attachment 400 may be configured in the same manner as the optical unit disclosed in Japanese Patent Application Laid-Open No. 2015-160103, for example.

As shown in FIG. 1, the anterior segment OCT attachment 400 can be arranged between the objective lens 22 and the eye E to be inspected. When the anterior segment OCT attachment 400 is located in the optical path, the ophthalmic apparatus 1 is capable of applying an OCT scan to the anterior segment. On the other hand, when the anterior segment OCT attachment 400 is retracted from the optical path, the ophthalmic apparatus 1 can apply the OCT scan to the posterior segment. The movement of the anterior segment OCT attachment 400 is performed manually or automatically.

In another embodiment, the OCT scan can be applied to the posterior segment of the eye when the attachment is placed in the optical path, and the OCT scan can be applied to the anterior segment of the eye when the attachment is retracted from the optical path. You can. Further, the measurement site that can be switched by the attachment is not limited to the posterior eye portion and the anterior eye portion, and may be any region of the eye. The configuration for switching the site to which the OCT scan is applied is not limited to such an attachment. For example, a configuration including a lens that can move along the optical path or a lens that can be inserted into and removed from the optical path. It is also possible to adopt a configuration provided with.

In this embodiment, the "processor" is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, a SPLD (Simple Program)). It means a circuit such as Programmable Logic Device) and FPGA (Field Programmable Gate Array). The processor realizes the function according to the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example.

[Fundus camera unit 2]
The fundus camera unit 2 is provided with an optical system for photographing the fundus Ef of the eye to be inspected E. The acquired digital image of the fundus Ef (called a fundus image, a fundus photograph, etc.) is generally a front image such as an observation image, a photographed image, or the like. The observed image is obtained by photographing a moving image using near infrared light. The captured image is a still image using flash light in the visible region.

The fundus camera unit 2 includes an illumination optical system 10 and a photographing optical system 30. The illumination optical system 10 irradiates the eye E to be inspected with illumination light. The photographing optical system 30 detects the return light of the illumination light applied to the eye E to be inspected. The measurement light from the OCT unit 100 is guided to the eye E to be inspected through the optical path in the fundus camera unit 2. The return light of the measurement light projected on the eye E (for example, fundus Ef) is guided to the OCT unit 100 through the same optical path in the fundus camera unit 2.

The light (observation illumination light) output from the observation light source 11 of the illumination optical system 10 is reflected by the concave mirror 12, passes through the condenser lens 13, passes through the visible cut filter 14, and becomes near-infrared light. Further, the observation illumination light is once focused in the vicinity of the photographing light source 15, reflected by the mirror 16, and passed through the relay lens system 17, the relay lens 18, the diaphragm 19, and the relay lens system 20 to the perforated mirror 21. Be guided. Then, the observation illumination light is reflected at the peripheral portion of the perforated mirror 21 (the region around the perforated portion), passes through the dichroic mirror 46, is refracted by the objective lens 22, and illuminates the eye E (fundus Ef) to be inspected. To do. The return light of the observation illumination light from the eye E to be inspected 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, and passes through the dichroic mirror 55. , It is reflected by the mirror 32 via the photographing focusing lens 31. Further, this return light passes through the half mirror 33A, is reflected by the dichroic mirror 33, and is imaged on the light receiving surface of the image sensor 35 by the imaging lens 34. The image sensor 35 detects the return light at a predetermined frame rate. The focus of the photographing optical system 30 is adjusted so as to match the fundus Ef or the anterior segment of the eye.

The light output from the photographing light source 15 (photographing illumination light) is applied to the fundus Ef through the same path as the observation illumination light. The return light of the photographing illumination light from the eye E to be examined is guided to the dichroic mirror 33 through the same path as the return light of the observation illumination light, passes through the dichroic mirror 33, is reflected by the mirror 36, and is reflected by the imaging lens 37. An image is formed on the light receiving surface of the image sensor 38.

The liquid crystal display (LCD) 39 displays a fixation target (fixation target image). A part of the light flux output from the LCD 39 is reflected by the half mirror 33A, reflected by the mirror 32, passes through the photographing focusing lens 31 and the dichroic mirror 55, and passes through the hole portion of the perforated mirror 21. The luminous flux that has passed through the hole of the perforated mirror 21 passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus Ef. The fixation target is typically used to guide and fix the line of sight. The direction in which the line of sight of the eye E to be examined is guided (and fixed), that is, the direction in which the fixation of the eye E to be examined is promoted is called the fixation position.

The fixation position can be changed by changing the display position of the fixation target image on the screen of the LCD 39. As an example of the fixation position, the fixation position for acquiring an image centered on the macula, the fixation position for acquiring an image centered on the optic nerve head, and the position between the macula and the optic nerve head ( There are a fixation position for acquiring an image centered on the fundus (center of the fundus) and a fixation position for acquiring an image of a portion (peripheral part of the fundus) far away from the macula.

A graphical user interface (GUI) or the like for designating at least one of such typical fixation positions can be provided. In addition, a GUI or the like for manually moving the fixation position (display position of the fixation target) can be provided. It is also possible to apply a configuration that automatically sets the fixation position.

The configuration for presenting the fixation target whose fixation position can be changed to the eye E to be examined is not limited to a display device such as an LCD. For example, a device (fixation matrix) in which a plurality of light emitting units (light emitting diodes and the like) are arranged in a matrix can be adopted instead of the display device. In this case, the fixation position of the eye E to be inspected by the fixation target can be changed by selectively lighting the plurality of light emitting units. As another example, a device having one or more movable light emitting units can generate an fixation target whose fixation position can be changed.

The alignment optical system 50 generates an alignment index used for alignment of the optical system with respect to the eye E to be inspected. The alignment light output from the light emitting diode (LED) 51 passes through the diaphragm 52, the diaphragm 53, and the relay lens 54, is reflected by the dichroic mirror 55, passes through the hole portion of the perforated mirror 21, and passes through the dichroic mirror 46. It is transmitted and projected onto the eye E to be inspected through the objective lens 22. The return light of the alignment light from the eye E to be inspected is guided to the image sensor 35 through the same path as the return light of the observation illumination light. Manual alignment or auto alignment can be executed based on the received light image (alignment index image).

The alignment method applicable to the embodiment is not limited to the method using such an alignment index, and a method using the anterior segment camera 300 (described later) or projecting light from an oblique direction onto the cornea. Any known method may be used, such as a method using an optical camera configured to detect the reflected light from the cornea in the opposite direction.

The focus optical system 60 generates a split index used for focus adjustment with respect to the eye E to be inspected. The focus optical system 60 is moved along the optical path (illumination optical path) of the illumination optical system 10 in conjunction with the movement of the imaging focusing lens 31 along the optical path (photographing optical path) of the photographing optical system 30. The reflection rod 67 is inserted and removed from the illumination optical path. When adjusting the focus, the reflecting surface of the reflecting rod 67 is inclined and arranged in the illumination optical path. The focus light output from the LED 61 passes through the relay lens 62, is separated into two light beams by the split index plate 63, passes through the two-hole diaphragm 64, is reflected by the mirror 65, and is reflected by the condensing lens 66. It is once imaged on the reflecting surface of the lens and reflected. Further, the focus light is reflected by the perforated mirror 21 via the relay lens 20, passes through the dichroic mirror 46, and is projected onto the eye E to be inspected via the objective lens 22. The return light (reflected light from the fundus, etc.) of the focus light from the eye E to be inspected is guided to the image sensor 35 through the same path as the return light of the alignment light. Manual focusing or auto focusing can be executed based on the received light image (split index image).

The diopter correction lenses 70 and 71 can be selectively inserted into the photographing optical path between the perforated mirror 21 and the dichroic mirror 55. The diopter correction lens 70 is a plus lens (convex lens) for correcting high-intensity hyperopia. The diopter correction lens 71 is a minus lens (concave lens) for correcting high myopia.

The dichroic mirror 46 synthesizes a fundus photography optical path and an OCT optical path (measurement arm). The dichroic mirror 46 reflects light in the wavelength band used for OCT and transmits light for fundus photography. The measuring arm is provided with a collimator lens unit 40, a retroreflector 41, a dispersion compensation member 42, an OCT focusing lens 43, an optical scanner 44, and a relay lens 45 in this order from the OCT unit 100 side.

The retroreflector 41 is made movable along the optical path of the measurement light LS incident on the retroreflector 41, whereby the length of the measurement arm is changed. The change in the measurement arm length is used, for example, for correcting the optical path length according to the axial length and adjusting the interference state.

The dispersion compensating member 42 together with the dispersion compensating member 113 (described later) arranged on the reference arm
It acts to match the dispersion characteristics of the measurement light LS and the dispersion characteristics of the reference light LR.

The OCT focusing lens 43 is moved along the measuring arm in order to adjust the focus of the measuring arm. The movement of the photographing focusing lens 31, the movement of the focus optical system 60, and the movement of the OCT focusing lens 43 can be controlled in a coordinated manner.

The optical scanner 44 is substantially located at a position optically conjugate with the pupil of the eye E to be inspected. The optical scanner 44 deflects the measurement light LS guided by the measurement arm. The optical scanner 44 is, for example, a galvano scanner capable of two-dimensional scanning. Typically, the optical scanner 44 is a one-dimensional scanner (x-scanner) for deflecting the measurement light in the ± x direction and a one-dimensional scanner (y-scanner) for deflecting the measurement light in the ± y direction. And, including. In this case, for example, one of these one-dimensional scanners is arranged at a position optically conjugate with the pupil, or a position optically conjugate with the pupil is arranged between these one-dimensional scanners.

[OCT unit 100]
FIG. 2 is a schematic view showing an example of the configuration of the OCT unit of the present embodiment.
The exemplary OCT unit 100 shown in FIG. 2 is provided with an optical system for performing Swept Source OCT. This optical system includes an interference optical system. This interference optical system divides the light from the variable wavelength light source into measurement light and reference light, and superimposes the return light of the measurement light projected on the eye E to be examined and the reference light passing through the reference optical path to cause interference light. Is generated and this interference light is detected. The data (detection signal) obtained by the detection of the interference light is a signal representing the spectrum of the interference light and is sent to the arithmetic control unit 200.

The light source unit 101 includes, for example, a near-infrared wavelength tunable laser that changes the wavelength of emitted light at high speed. The light L0 output from the light source unit 101 is guided to the polarization controller 103 by the optical fiber 102. As a result, the polarization state of the light L0 is adjusted. Further, the optical L0 is guided by the optical fiber 104 to the fiber coupler 105 and divided into the measurement optical LS and the reference optical LR. The optical path of the measurement light LS is called a measurement arm or the like, and the optical path of the reference light LR is called a reference arm or the like.

The reference light LR generated by the fiber coupler 105 is guided by the optical fiber 110 to the collimator 111, converted into a parallel light flux, and guided to the retroreflector 114 via the optical path length correction member 112 and the dispersion compensation member 113. The optical path length correction member 112 acts to match the optical path length of the reference light LR with the optical path length of the measurement light LS. The dispersion compensating member 113, together with the dispersion compensating member 42 arranged on the measurement arm, acts to match the dispersion characteristics between the reference light LR and the measurement light LS. The retroreflector 114 is movable along the optical path of the reference light LR incident on it. As a result, the length of the reference arm is changed. The change of the reference arm length is used, for example, for correcting the optical path length according to the axial length and adjusting the interference state.

The reference light LR that has passed through the retro-reflector 114 is converted from a parallel luminous flux to a focused luminous flux by a collimator 116 via a dispersion compensating member 113 and an optical path length correcting member 112, and is incident on the optical fiber 117. The reference light LR incident on the optical fiber 117 is guided by the polarization controller 118 to adjust the polarization state, is guided to the attenuator 120 through the optical fiber 119 to adjust the amount of light, and is guided to the fiber coupler 122 through the optical fiber 121. ..

On the other hand, the measurement optical LS generated by the fiber coupler 105 is guided to the collimator lens unit 40 through the optical fiber 127 and converted into a parallel light beam, and is converted into a parallel light beam, and the retroreflector 41, the dispersion compensation member 42, the OCT focusing lens 43, and the optical scanner 44. , And is reflected by the dichroic mirror 46 via the relay lens 45, refracted by the objective lens 22, and projected onto the eye E to be inspected. The measurement light LS is scattered and reflected at various depth positions of the eye E to be inspected. The return light from the eye E to be inspected of the measurement light LS travels in the opposite direction on the measurement arm, is guided to the fiber coupler 105, and reaches the fiber coupler 122 via the optical fiber 128.

The fiber coupler 122 superimposes the measurement light LS incidented via the optical fiber 128 and the reference light LR incidented via the optical fiber 121 to generate interference light. The fiber coupler 122 generates a pair of interference light LCs by branching the generated interference light at a predetermined branching ratio (for example, 1: 1). The pair of interference light LCs are guided to the detector 125 through optical fibers 123 and 124, respectively.

The detector 125 includes, for example, a balanced photodiode. The balanced photodiode includes a pair of photodetectors that detect each pair of interference light LCs, and outputs the difference between the pair of detection signals obtained by these. The detector 125 sends this output (detection signal such as a difference signal) to the data acquisition system (DAQ) 130.

A clock KC is supplied to the data acquisition system 130 from the light source unit 101. The clock KC is generated in the light source unit 101 in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the tunable light source. The light source unit 101, for example, branches the light L0 of each output wavelength to generate two branched lights, optically delays one of the branched lights, synthesizes the branched lights, and produces the obtained combined light. It is detected and a clock KC is generated based on the detected signal. The data acquisition system 130 executes sampling of the detection signal (difference signal) input from the detector 125 based on the clock KC. The data collection system 130 sends the data obtained by this sampling to the arithmetic control unit 200.

In this example, both an element for changing the measurement arm length (for example, the retroreflector 41) and an element for changing the reference arm length (for example, the retroreflector 114 or the reference mirror) are provided. However, only one of these elements may be provided. Further, the elements for changing the difference (optical path length difference) between the measurement arm length and the reference arm length are not limited to these, and any element (optical member, mechanism, etc.) can be adopted. ..

[Calculation control unit 200]
3A and 3B are schematic views showing an example of the configuration of the arithmetic control unit of the present embodiment.
The arithmetic control unit 200 controls each part of the ophthalmic apparatus 1. In addition, the arithmetic control unit 200 executes various arithmetic processes. For example, the arithmetic control unit 200 performs signal processing such as Fourier transform on the spectral distribution based on the sampling data group obtained by the data acquisition system 130 for each series of wavelength scans (for each A line). Form a reflection intensity profile in the line. Further, the arithmetic control unit 200 forms image data by imaging the reflection intensity profile of each A line. The arithmetic processing for that purpose is the same as that of the conventional Swept source OCT.

The arithmetic control unit 200 includes, for example, a processor, a RAM (Random Access Memory), a ROM (Read Only Memory), a hard disk drive, a communication interface, and the like. Various computer programs are stored in a storage device such as a hard disk drive. The arithmetic control unit 200 may include an operation device, an input device, a display device, and the like.

[User Interface 240]
The user interface 240 includes a display unit 241 and an operation unit 242. The display unit 241 of the present embodiment is an example of the "display means" of the present invention. The display unit 241 includes a display device 3. The operation unit 242 includes various operation devices and input devices. The user interface 240 may include a device such as a touch panel in which a display function and an operation function are integrated. It is also possible to build embodiments that do not include at least part of the user interface 240. For example, the display device may be an external device connected to the ophthalmologic imaging device.

[Front eye camera 300]
FIG. 4A is a front view showing an example of the ophthalmic apparatus according to the present embodiment.
FIG. 4B is a side view showing an example of the ophthalmic apparatus according to the present embodiment.
The anterior segment camera 300 captures the anterior segment of the eye E to be inspected from two or more different directions. The anterior segment camera 300 includes an image sensor such as a CCD image sensor or a CMOS image sensor. In this embodiment, two anterior segment cameras 300 are provided on the surface of the fundus camera unit 2 on the subject side (see the anterior segment cameras 300A and 300B shown in FIG. 4A). As shown in FIGS. 1 and 4A, the anterior segment cameras 300A and 300B are provided at positions deviating from the optical path passing through the objective lens 22. Hereinafter, one or both of the anterior segment cameras 300A and 300B may be indicated by reference numeral 300.

In this embodiment, two anterior segment cameras 300A and 300B are provided, but typically, the number of anterior segment cameras may be any number of 2 or more. Considering the arithmetic processing described later, a configuration capable of photographing the anterior segment from two different directions is sufficient (but not limited to this). Further, one or more movable anterior segment cameras 300 may be provided.

In this embodiment, the anterior segment camera 300 is provided separately from the illumination optical system 10 and the photographing optical system 30, but at least the anterior segment imaging can be performed using the photographing optical system 30. That is, one of the two or more anterior segment cameras may include the photographing optical system 30. The anterior segment camera 300 according to this embodiment may be capable of photographing the anterior segment from two (or more) different directions.

A configuration for illuminating the anterior segment of the eye may be provided. The anterior segment illumination means includes, for example, one or more light sources. Typically, at least one light source (eg, an infrared light source) can be provided in the vicinity of each of the two or more front eye cameras.

Two or more anterior segment cameras can image the anterior segment substantially simultaneously from two or more different directions. "Substantially at the same time" means that, in addition to the case where the shooting timings by two or more anterior eye cameras are simultaneous, for example, the case where the shooting timing is shifted to the extent that the eye movement can be ignored is allowed. Shown. By such substantially simultaneous imaging, it becomes possible to acquire an image when the eye E to be inspected is in substantially the same position and orientation with two or more anterior eye cameras.

Shooting with two or more front eye cameras may be moving image shooting or still image shooting. In the case of moving image shooting, it is possible to realize substantially simultaneous front eye shooting as described above by controlling the shooting start timing to be adjusted, and controlling the frame rate and the shooting timing of each frame. .. On the other hand, in the case of still image shooting, this can be realized by controlling the shooting timing to be adjusted.

[Control system]
An example of the configuration of the control system (processing system) of the ophthalmic apparatus 1 is shown in FIGS. 3A and 3B. The control unit 210, the image forming unit 220, and the data processing unit 230 are provided in, for example, the arithmetic control unit 200.

[Control unit 210]
The control unit 210 includes a processor and controls each unit of the ophthalmic apparatus 1. The control unit 210 includes a main control unit 211 and a storage unit 212.

[Main control unit 211]
The main control unit 211 includes a processor and controls each element of the ophthalmic apparatus 1 (including the element shown in FIGS. 1 to 3B). The main control unit 211 is realized by the cooperation of the hardware including the circuit and the control software.

The photographing focusing lens 31 arranged in the photographing optical path and the focusing optical system 60 arranged in the illumination optical path are moved by a photographing focusing drive unit (not shown) under the control of the main control unit 211. The retroreflector 41 provided on the measuring arm is moved by the retroreflector (RR) drive unit 41A under the control of the main control unit 211. The OCT focusing lens 43 arranged on the measuring arm is moved by the OCT focusing driving unit 43A under the control of the main control unit 211. The optical scanner 44 provided on the measuring arm operates under the control of the main control unit 211. The retroreflector 114 arranged on the reference arm is moved by the retroreflector (RR) drive unit 114A under the control of the main control unit 211. Each of the mechanisms exemplified herein typically includes an actuator such as a pulse motor that operates under the control of the main control unit 211.

The moving mechanism 150, for example, moves at least the fundus camera unit 2 three-dimensionally. In a typical example, the moving mechanism 150 includes an x stage that can move in the ± x direction (horizontal direction), an x moving mechanism that moves the x stage, and a y stage that can move in the ± y direction (vertical direction). , The y-moving mechanism that moves the y-stage, the z-stage that can move in the ± z direction (depth direction), and the z-moving mechanism that moves the z-stage are included. Each of these moving mechanisms includes an actuator such as a pulse motor that operates under the control of the main control unit 211.

[Storage 212]
The storage unit 212 stores various types of data. The data stored in the storage unit 212 includes, for example, image data of an OCT image, image data of a fundus image, eye information to be inspected, and the like. The eye test information includes subject information such as patient ID and name, left eye / right eye identification information, electronic medical record information, and the like.

Aberration information (not shown) is stored in advance in the storage unit 212. In the aberration information, information on the distortion aberration generated in the captured image due to the influence of the optical system mounted on each front eye camera 300 is recorded. Here, the optical system mounted on the anterior segment camera 300 includes an optical element such as a lens that generates distortion. Aberration information can be said to be a parameter that quantifies the distortion given to the captured image by these optical elements.

An example of a method of generating aberration information will be described. The following measurements are performed for each anterior segment camera 300 in consideration of the instrumental error (difference in distortion) of the anterior segment camera 300. The worker prepares a predetermined reference point. The reference point is a photographing target used for detecting distortion. The operator takes a plurality of times while changing the relative position between the reference point and the anterior segment camera 300. As a result, a plurality of captured images of reference points taken from different directions can be obtained. The operator generates aberration information of the anterior segment camera 300 by analyzing the acquired plurality of captured images with a computer. The computer that performs this analysis process may be the data processing unit 230, or any other computer (inspection computer before product shipment, maintenance computer, etc.).

The analysis process for generating aberration information includes, for example, the following steps:
Extraction process to extract the image area corresponding to the reference point from each captured image;
Distribution state calculation process for calculating the distribution state (coordinates) of the image area corresponding to the reference point in each captured image;
Distortion calculation step for calculating parameters representing distortion based on the obtained distribution state;
A correction coefficient calculation step of calculating a coefficient for correcting distortion based on the obtained parameters.

The parameters related to the distortion given to the image by the optical system include the principal point distance, the principal point position (vertical direction, horizontal direction), lens distortion (radiation direction, tangential direction), and the like. The aberration information is configured as information (for example, table information) in which the identification information of each anterior segment camera 300 and the correction coefficient corresponding thereto are associated with each other. The aberration information generated in this way is stored in the storage unit 212 by the main control unit 211. The generation of such aberration information and the aberration correction based on the same are called camera calibration and the like.

[Image forming unit 220]
The image forming unit 220 forms OCT image data based on the data collected by the data collecting system 130. The image forming unit 220 includes a processor. The image forming unit 220 is realized by the cooperation of the hardware including the circuit and the image forming software.

The image forming unit 220 forms the cross-sectional image data based on the data collected by the data collecting system 130. This processing includes signal processing such as noise removal (noise reduction), filtering, and fast Fourier transform (FFT), as in the conventional Swept Source OCT.

The image data formed by the image forming unit 220 is a group of images formed by imaging reflection intensity profiles in a plurality of A lines (scan lines along the z direction) arranged in an area to which an OCT scan is applied. A data set containing image data (a group of A-scan image data).

The image data formed by the image forming unit 220 is, for example, one or more B-scan image data or stack data formed by embedding a plurality of B-scan image data in a single three-dimensional coordinate system. The image forming unit 220 can also perform voxelization processing on the stack data to construct volume data (voxel data). The stack data and volume data are typical examples of 3D scanned image data represented by a 3D coordinate system.

The image forming unit 220 can process the three-dimensional scanned image data. For example, the image forming unit 220 can construct new image data by applying rendering to the three-dimensional scanned image data. Rendering methods include volume rendering, maximum value projection (MIP), minimum value projection (MinIP), surface rendering, and multi-section reconstruction (MPR). Further, the image forming unit 220 can project the three-dimensional scanned image data in the z direction (A-line direction, depth direction) to construct the projection data. Further, the image forming unit 220 can construct a shadow gram by projecting a part of the three-dimensional scanned image data in the z direction. It should be noted that a part of the three-dimensional scanned image data projected to construct the shadow gram is set by using, for example, segmentation.

[Data processing unit 230]
The data processing unit 230 executes various data processing. For example, the data processing unit 230 can apply image processing or analysis processing to OCT image data, or apply image processing or analysis processing to observation image data or captured image data. The data processing unit 230 includes, for example, at least one of a processor and a dedicated circuit board.

[Data acquisition unit 250]
Hereinafter, FIG. 3B will be referred to. The data acquisition unit 250 is configured to optically acquire the data of the eye E to be inspected. In particular, the data acquisition unit 250 can project light onto the fundus Ef and acquire the data of the eye E to be inspected based on the return light. The data acquisition unit 250 can acquire image data by applying OCT to the eye E to be inspected. The data acquisition unit 250 includes an element group that constitutes a measurement arm provided in the fundus camera unit 2, an element group provided in the OCT unit 100, and an image forming unit 220. In another example, the data acquisition unit 250 may include a configuration for acquiring a fundus image (illumination optical system 10, photographing optical system 30, etc.).

The data acquisition unit 250 of this example also functions as an OCT unit having an anterior segment OCT optical system that collects OCT data by applying an OCT scan to a three-dimensional region of the anterior segment of the eye E to be inspected. When the data acquisition unit 250 is used as the OCT unit, the anterior segment OCT attachment 400 is inserted into the optical path. When the data acquisition unit 250 projects light onto the fundus Ef to acquire the data of the eye to be inspected E, the anterior segment OCT attachment 400 is retracted from the optical path.

As described above, in this example, both anterior segment OCT and fundus OCT can be performed, but the embodiment is not limited to this. For example, the ophthalmologic apparatus according to the embodiment can be used instead of the fundus OCT or in addition to the fundus OCT, such as fundus photography (fundus camera, SLO), axial length measurement, ocular refractive error measurement, and eyeball aberration measurement (wavefront analyzer). , Visual field examination (microperimeter, perimeter) may be feasible.

Further, in this example, an optical system for projecting light onto the fundus Ef to acquire data of the eye E to be inspected (data acquisition optical system included in the data acquisition unit 250) and an optical system for the anterior segment OCT. (Foreground OCT optical system) includes a common scanning optical system. This common scanning optical system includes a group of elements constituting the measurement arm provided in the fundus camera unit 2 and a group of elements provided in the OCT unit 100. In other embodiments, it is not necessary to adopt such a configuration, and for example, the data acquisition optical system and the anterior segment OCT optical system may be provided separately.

[Alignment system 260]
The alignment system 260 includes an element for aligning the data acquisition optical system. The alignment system 260 may include an alignment optical system 50 for projecting an alignment index onto the eye E to be inspected (first configuration). Further, the alignment system 260 includes two front eye cameras 300 and a position information acquisition unit 231 (described later) that obtains a three-dimensional position of the eye E to be inspected from two front eye images acquired substantially at the same time by these cameras. May include (second configuration). Further, the alignment system 260 may include an optical projection system, a light receiving system, and a processor for obtaining the position of the eye E to be inspected from the output from the light receiving system for performing alignment using an optical lever (No. 1). Configuration of 3).

The ophthalmic apparatus 1 according to this embodiment includes both the first configuration and the second configuration of these first to third configurations, but any one of the first to third configurations. One, any two or three may be provided. Alternatively, the alignment system 260 may include configurations other than the first to third configurations. That is, the alignment method performed by the alignment system 260 is arbitrary.

[Example of control unit 210]
The control unit 210 illustrated in FIG. 3B includes a drive control unit 2101 and a display control unit 2102. The drive control unit 2101 controls the moving mechanism 150. The display control unit 2102 controls the user interface 240 (display unit 241). The drive control unit 2101 and the display control unit 2102 are included in the main control unit 211 shown in FIG. 3A.

[Example of data processing unit 230]
The data processing unit 230 illustrated in FIG. 3B includes a position information acquisition unit 231, a determination unit 232, a turbidity area identification unit 233, a movement target determination unit 234, a transmission position identification unit 236, and a arrival position identification unit 237. And, including.

[Location information acquisition unit 231]
The position information acquisition unit 231 analyzes the two anterior segment images acquired by the two anterior segment cameras 300 photographing the anterior segment of the eye E to be inspected substantially at the same time. The dimensional position can be obtained. An example of the process executed by the position information acquisition unit 231 will be described below.

First, the position information acquisition unit 231 can correct the distortion of the captured image obtained by the front eye unit camera 300 based on the aberration information stored in the storage unit 212. This correction can be performed, for example, by a known image processing technique based on a correction coefficient for correcting distortion. In addition, when the distortion that the optical system of the anterior segment camera 300 gives to the captured image is sufficiently small, the aberration information and the correction using the aberration information may not be necessary.

Next, the position information acquisition unit 231 can specify an image region (pupil region) corresponding to the pupil of the eye E to be inspected based on the distribution of pixel values (for example, luminance value) of the captured image. Since the pupil is generally expressed with lower brightness than other parts, it is possible to identify the pupil region by searching the low-luminance image region. At this time, the pupil region may be specified in consideration of the shape of the pupil. For example, the pupil region can be specified by searching for a substantially circular and low-luminance image region.

Subsequently, the position information acquisition unit 231 can specify the central position of the specified pupil region. Utilizing the fact that the pupil is substantially circular as described above, the position information acquisition unit 231 performs, for example, a process of specifying the contour of the pupil region and a process of obtaining an approximate ellipse (or an approximate circle) of the contour. The process of specifying the center position of the approximate ellipse (or approximate circle) is included. The center position of the approximate ellipse (or approximate circle) thus identified is used as the pupil center of the eye E to be inspected. As another example of the process of finding the center of the pupil, the position information acquisition unit 231 can find the center of gravity of the pupil region and set it at the center of the pupil.

The position information acquisition unit 231 is based on the position (and imaging magnification) of the anterior segment camera 300 and the position of the pupil center in the two captured images identified in the previous stage processing, and the pupil center of the eye E to be inspected. The three-dimensional position of can be obtained.

FIG. 5A is a top view showing the positional relationship between the eye to be inspected and the anterior segment camera.
FIG. 5B is a side view showing the positional relationship between the eye to be inspected and the anterior segment camera.
The distance (baseline length) between the anterior segment camera 300A and the anterior segment camera 300B is represented by "B". The distance (imaging distance) between the baselines of the anterior segment cameras 300A and 300B and the pupil center P of the eye E to be inspected is represented by "H". The distance (screen distance) between the anterior segment camera 300A and its screen plane is represented by "f".

In such an arrangement state, the resolution of the images captured by the anterior segment cameras 300A and 300B is expressed by the following equation. Here, Δp represents the pixel resolution.

Resolution in the xy direction (planar resolution): Δxy = H × Δp / f
Resolution in the z direction (depth resolution): Δz = H × H × Δp / (B × f)

The position information acquisition unit 231 is arranged as shown in FIGS. 5A and 5B with respect to, for example, the positions (known) of the anterior segment cameras 300A and 300B and the positions corresponding to the pupil center P in the two captured images. By applying a known trigonometry in consideration of the relationship, the three-dimensional position of the pupil center P can be calculated.

Even when a feature point other than the center of the pupil is applied, the position information acquisition unit 231 applies the same processing as above, so that the feature point is three-dimensionally based on the distribution of pixel values of the captured image. It is possible to find the position.

The position information acquired by the position information acquisition unit 231 (for example, information indicating the three-dimensional position of the center of the pupil) is sent to the control unit 210. The drive control unit 2101 applies the alignment control based on this position information to the moving mechanism 150. This alignment control is an example of the above-mentioned auto alignment.

[Judgment unit 232]
As described above, the data acquisition unit 250 projects light on the fundus Ef and acquires the data of the eye E to be inspected based on the return light. The determination unit 232 determines whether or not to apply the three-dimensional OCT scan to the anterior segment of the eye E to be inspected based on the data acquired by the data acquisition unit 250. Typically, after the above-mentioned auto-alignment is performed, the data acquisition unit 250 acquires the data, and the determination unit 232 makes a determination.

The data acquired by the data acquisition unit 250 of this example is, for example, OCT data. An example of OCT data is A-scan image data for axial length measurement or imaging. In this case, the determination unit 232 determines, for example, whether or not the brightness of the A-scan image data exceeds a predetermined threshold value. Typically, it is determined whether or not the statistical value (for example, sum, average, maximum value) of the brightness value of the pixel group included in the A-scan image data exceeds the threshold value. If this statistical value does not exceed the threshold value, it is suggested that the measurement light LS and / or its return light has passed through the turbid portion in the eye E to be inspected. In this threshold value processing, for example, a threshold value set by default or a threshold value set according to A-scan image data or the like is used.

Even when the data acquisition unit 250 acquires other types of data, if the light to be projected on the fundus Ef and / or its return light passes through the opaque portion in the eye E to be inspected, the acquired data Information (eg, brightness) indicating the intensity of the light is reduced. The determination unit 232 can make a similar determination based on the strength of the data acquired by the data acquisition unit 250.

[Muddy area identification unit 233]
The turbid region identification unit 233 identifies the opaque region of the anterior segment of the eye by analyzing the OCT data collected by the three-dimensional OCT scan of the anterior segment of the eye E to be examined. The opaque region is an image region corresponding to the opacity inside the eye E to be inspected. The opaque region corresponds to the opacity of the intermediate translucent body as seen in cataract eyes.

For example, the turbid region identification unit 233 analyzes a three-dimensional OCT image of the anterior segment of the eye or a projection image (or shadowgram) based on the three-dimensional OCT image. The turbid region specifying unit 233 can obtain the distribution of pixel values (for example, luminance values) of such an OCT image, and can specify the turbid region based on this distribution. The opaque portion is projected like a shadow on the OCT image of the anterior segment of the eye. The turbid region identification unit 233 identifies pixels whose brightness value is equal to or less than a predetermined threshold value by applying a threshold value processing related to brightness to an OCT image. The pixel group specified by this is set in the turbid region. In this threshold value processing, for example, a default set threshold value or a threshold value set according to an OCT image or the like is used.

[Movement target determination unit 234]
The movement target determination unit 234 determines the movement target of the data acquisition optical system included in the data acquisition unit 250 based on the turbidity region specified by the turbidity region identification unit 233. The determined moving target is used for alignment of the data acquisition optical system.

For example, an image representing the anterior segment of the eye E to be inspected and an opaque region (information indicating its position / distribution) specified by the turbid region identification unit 233 are input to the movement target determination unit 234. The images representing the anterior segment include, for example, OCT data subjected to processing by the turbid region identification unit 233, an image obtained by processing the OCT data (for example, a projection image, a shadow gram), and a fundus camera unit 2. An anterior segment image acquired by, an anterior segment image acquired by the anterior segment camera 300, and an image obtained by processing two anterior segment images acquired by two anterior segment cameras 300. (For example, a front image) may be used.

When the image representing the anterior segment is neither the OCT data subjected to the processing by the turbid region identification unit 233 nor the processed image of the OCT data, the data processing unit 230 uses the image representing the anterior segment and the OCT. Registration with the data (or its processed image) can be performed. The registration may be, for example, image matching using feature points. According to the registration, the position (distribution) of the opaque region in the image representing the anterior segment can be obtained.

When the image representing the anterior segment is the OCT data subjected to the processing by the turbid region identification unit 233, or the processed image of the OCT data, the image representing the anterior segment and the opaque region are used. There is a trivial correspondence between the two, so there is no need to apply registration.

The movement target determination unit 234 can determine the movement target of the data acquisition optical system so as to pass through a position different from the turbid region in the image representing the anterior segment of the eye. That is, the movement target determination unit 234 can determine the movement target of the data acquisition optical system so that the measurement light LS projected by the data acquisition unit 250 is guided while avoiding turbidity in the eye E to be inspected.

The movement target determination unit 234 can determine the movement target of the data acquisition optical system in consideration of the beam diameter of the measurement light LS. For example, the movement target determination unit 234 can determine the movement target of the data acquisition optical system so that the entire beam cross section of the measurement light LS passes through the non-turbid portion.

In order to reduce speckle noise mixed in the image, the control unit 210 can control the optical scanner 44 so as to change the deflection direction of the measurement light LS with time. In this case, the movement target determination unit 234 can determine the movement target of the data acquisition optical system in consideration of the change in the passing position of the measurement light LS. For example, the movement target determination unit 234 may determine the movement target of the data acquisition optical system so that the change range of the passing position of the measurement light LS at a predetermined depth position in the eye E to be inspected does not overlap with the turbid region. it can. Typically, since the optical scanner 44 is arranged at a position optically conjugate with the pupil of the eye E to be inspected, the passage of the measurement light LS at a position relatively far from the pupil (for example, the rear surface of the crystalline lens). The movement target of the data acquisition optical system can be determined so that the change range of the position does not overlap with the turbid region. The distance between the pupil and the predetermined location may be, for example, a value obtained by measuring the eye E to be inspected or a value obtained from model eye data.

The movement target determined by the movement target determination unit 234 is, for example, information including at least the x-coordinate and the y-coordinate. The determined movement target is sent to the control unit 210.

When the alignment of the data acquisition optical system is automatically corrected, the drive control unit 2101 can control the movement mechanism 150 based on the movement target obtained by the movement target determination unit 234. For example, the drive control unit 2101 can control the movement mechanism 150 so that the data acquisition optical system is moved to a position corresponding to the x-coordinate and the y-coordinate included in the movement target.

When the alignment of the data acquisition optical system is manually corrected, the display control unit 2102 can display, for example, an image representing the anterior eye portion described above on the display unit 241. The display control unit 2102 can display an alignment index image together with an image representing the anterior segment of the eye. The operation unit 242 is used for the user to perform an alignment operation of the data acquisition optical system. The drive control unit 2101 can control the movement mechanism 150 based on the signal input from the operation unit 242. Thereby, the user can move the data acquisition optical system to a desired position.

When the alignment is manually corrected, the display control unit 2102 may display the information for the alignment operation (alignment support information) on the display unit 241 based on the movement target obtained by the movement target determination unit 234. it can. The alignment support information may include, for example, information indicating a position corresponding to a movement target, which is displayed together with an image representing the anterior segment of the eye. Alternatively, the alignment support information includes information indicating the operation direction (movement direction) and / or the operation amount (movement amount), such as an arrow image from the current position of the data acquisition optical system to the position corresponding to the movement target. May include. Such alignment support information is generated based on, for example, the x-coordinate and the y-coordinate included in the movement target.

[Transmission position identification unit 236]
The transmission position specifying unit 236 identifies the transmission position through which the measurement light LS passes through the anterior segment of the eye E to be inspected, based on the arrangement of at least one of the data acquisition optical system and the OCT optical system. The OCT optical system is an optical system that projects measurement light LS onto the eye E to be inspected and applies an OCT scan to a three-dimensional region of the eye E to be inspected to acquire OCT data. That is, the transmission position specifying unit 236 specifies the transmission position through which the measurement light LS passes through or passes through the cornea, the pupil, or the crystalline lens when it enters the inside of the eye E through the pupil of the eye E. The transmission position is an image position corresponding to a position where the measurement light LS transmits through the anterior segment of the eye E to be inspected.

For example, information regarding the arrangement of the alignment system 260 is input to the transmission position specifying unit 236. The information regarding the arrangement of the alignment system 260 may include information regarding the arrangement of the alignment optical system 50 for projecting the alignment index onto the eye E to be inspected. Further, the information regarding the arrangement of the alignment system 260 may include information regarding the arrangement of the data acquisition optical system. Further, the information regarding the arrangement of the alignment system 260 is acquired by the position information acquisition unit 231 that obtains the three-dimensional position of the eye E to be inspected from the two anterior segment images acquired substantially at the same time by the two anterior segment cameras 300. It may include the position information of the eye E to be inspected. Further, the information regarding the arrangement of the alignment system 260 may include information regarding the arrangement of the light projection system and the light receiving system for performing alignment using the optical alignment. Further, the information regarding the arrangement of the alignment system 260 may include information regarding the alignment control executed based on the position information of the eye E to be inspected acquired by the position information acquisition unit 231. The transmission position specifying unit 236 specifies at least the x-coordinate and the y-coordinate of the transmission position through which the measurement light LS passes through the anterior segment of the eye E to be inspected.

The display control unit 2102 can display the image representing the anterior segment described above with respect to the movement target determination unit 234 on the display unit 241. The display control unit 2102 superimposes an image showing the transmission position of the measurement light LS in the anterior segment of the eye E to be inspected identified by the transmission position specifying unit 236 on the image of the anterior segment (an image representing the anterior segment). It is displayed on the display unit 241. For example, the display control unit 2102 superimposes an image showing the transmission position of the measurement light LS on the front image of the anterior segment obtained by processing the two anterior segment images acquired by the two anterior segment cameras 300. Is displayed on the display unit 241. The image of the anterior segment in which the image showing the transmission position of the measurement light LS is superimposed and displayed on the display unit 241 is not limited to the front image by the two anterior segment cameras 300, and is not limited to a transillumination image or an OCT tomographic image. It may be an OCT front image or the like.

[Arrival position identification unit 237]
The arrival position specifying unit 237 specifies the projection direction of the measurement light LS projected on the eye E to be inspected based on the arrangement of at least one of the data acquisition optical system and the OCT optical system. Further, the arrival position specifying unit 237 generates the measurement light LS based on the transmission position of the measurement light LS specified by the transmission position identification unit 236 and the projection direction of the measurement light LS specified by the arrival position identification unit 237. The arrival position of the eye E to reach the fundus Ef is specified. The arrival position is an image position corresponding to the position where the measurement light LS reaches the fundus Ef of the eye E to be inspected.

For example, information regarding the arrangement of the OCT optical system is input to the arrival position specifying unit 237. The information regarding the arrangement of the OCT optical system includes, for example, information regarding the angle of the optical scanner 44. As a result, the arrival position specifying unit 237 specifies the projection direction of the measurement light LS projected on the eye E to be inspected, for example, the angle between the optical axis of the objective lens 22 and the traveling direction of the measurement light LS. Then, for example, the arrival position specifying unit 237 is based on the transmission position of the measurement light LS specified by the transmission position specifying unit 236 and the angle between the optical axis of the objective lens 22 and the traveling direction of the measurement light LS. Then, the arrival position where the measurement light LS reaches the fundus Ef of the eye E to be inspected is specified.

The display control unit 2102 can display an image representing the fundus Ef of the eye E to be inspected on the display unit 241. The display control unit 2102 superimposes an image showing the arrival position of the measurement light LS on the fundus Ef of the eye to be inspected E specified by the arrival position specifying unit 237 on the image of the fundus Ef (an image expressing the fundus Ef of the eye to be inspected E). Is displayed on the display unit 241. For example, the display control unit 2102 superimposes an image showing the arrival position of the measurement light LS on the front image of the fundus Ef obtained by photographing using near infrared light, and causes the display unit 241 to display the image. The image of the fundus Ef on which the image showing the arrival position of the measurement light LS is superimposed and displayed on the display unit 241 is not limited to the front image by the near infrared light, and may be a three-dimensional scan image or the like. The three-dimensional scanned image is as described above with respect to the image forming unit 220.

When the axial length data or the corneal curve data is stored in the storage unit 212 as the subject information, the arrival position specifying unit 237 is based on the axial length data or the corneal curve data stored in the storage unit 212. The eye model may be modified. Alternatively, the axial length data and the corneal curve data may be stored in the storage unit 212 as a table set according to, for example, age. As a result, the arrival position specifying unit 237 can more accurately identify the arrival position at which the measurement light LS reaches the fundus Ef of the eye E to be inspected. Then, the display control unit 2102 can superimpose an image showing the arrival position of the measurement light LS on the three-dimensional scan image modified according to, for example, the age of the subject.

[motion]
FIG. 6 is a flowchart illustrating an example of the operation of the ophthalmic apparatus according to the present embodiment.
FIG. 7 is a schematic view showing a state in which an image showing the transmission position of the measurement light is superimposed on the image of the front eye portion and displayed on the display portion.
FIG. 8 is a schematic view showing a state in which an image showing the arrival position of the measurement light is superimposed on the image of the fundus and displayed on the display unit.
FIG. 9 is a schematic view showing a state in which an image showing the arrival position of the measurement light is superimposed on the three-dimensional scan image of the fundus and displayed on the display unit.

(S1: Start alignment)
An example of the operation of the ophthalmic apparatus 1 according to this embodiment will be described.
First, the alignment of the data acquisition optical system using the alignment system 260 is started.
This alignment may be manual alignment, but is typically auto alignment.

The auto alignment can be executed by using, for example, the anterior segment camera 300, the position information acquisition unit 231 and the drive control unit 2101 (stereo camera method). Alternatively, the auto alignment may be any one of alignment using an alignment index generated by the alignment optical system 50, alignment using an optical alignment, alignment using a Pulkinye image, and alignment by another method. ..

(S2: Alignment completed)
The alignment in step S1 is completed when the alignment of the data acquisition optical system with respect to the eye E to be examined falls within a predetermined allowable range.

For example, according to the auto-alignment of the stereo camera method in this embodiment, the optical axis of the data acquisition optical system is substantially aligned with the center of the pupil of the eye E to be inspected (alignment in the xy direction), and the data is aligned with the eye E to be inspected. The distance to the acquisition optical system (eg, the objective lens 22) is approximately matched to a given working distance (alignment in the z direction).

Upon completion of the alignment, known tracking for moving the data acquisition optical system in accordance with the movement of the eye E to be inspected may be started.

(S3: Project light toward the fundus to acquire data)
Upon completing the alignment, the control unit 210 causes the data acquisition unit 250 to acquire data. The data acquisition unit 250 of this example projects the measurement light LS toward the fundus Ef of the eye E to be inspected, detects the interference light LC generated by superimposing the return light and the reference light LR, and detects a data acquisition system. At least one of A scan image data, B scan image data, and three-dimensional scan image data is formed from the data collected by 130.

(S4: Specify the transmission position of the measurement light)
When the alignment is completed and the measurement light LS is projected onto the eye E to be inspected, the transmission position specifying unit 236 receives the measurement light LS from the eye E to be inspected based on the arrangement of at least one of the data acquisition optical system and the OCT optical system. Identify the transmission position that penetrates the anterior segment of the eye. For example, information regarding the result of auto alignment by the alignment system 260 is input to the transmission position specifying unit 236. Examples of the information regarding the result of the auto alignment include information regarding the alignment in the xy direction (x coordinate and y coordinate). In this case, the transmission position specifying unit 236 specifies the transmission position through which the measurement light LS passes through the anterior segment of the eye E to be inspected, based on the information (x coordinate and y coordinate) regarding the alignment in the xy direction.

(S5: An image showing the transmission position of the measurement light is displayed overlaid on the image of the anterior segment of the eye)
Subsequently, the display control unit 2102 causes the display unit 241 to superimpose an image showing the transmission position of the measurement light LS in the anterior segment of the eye E to be inspected identified by the transmission position specifying unit 236 on the image of the anterior segment. .. For example, as shown in FIG. 7, the display control unit 2102 displays an image TP representing the transmission position of the measurement light LS in the anterior eye portion Ea of the eye to be inspected E specified by the transmission position specifying unit 236, in the eye E. The OCT front image (projection image, etc.) 700 of the anterior segment Ea is superimposed and displayed on the display unit 241. More preferably, the image TP representing the transmission position of the measurement light LS is a circular image having a diameter of about 0.5 mm or more and about 2 mm or less in the anterior segment Ea of the eye E to be inspected.

(S6: Specify the arrival position of the measurement light)
Subsequently, the arrival position specifying unit 237 specifies the projection direction of the measurement light LS projected on the eye E based on the arrangement of at least one of the data acquisition optical system and the OCT optical system, and the transmission position specifying unit 236 determines the projection direction. Based on the transmission position of the specified measurement light LS and the projection direction of the measurement light LS specified by the arrival position specifying unit 237, the arrival position at which the measurement light LS reaches the fundus Ef of the eye E to be inspected is specified. For example, information regarding the angle of the optical scanner 44 is input to the arrival position specifying unit 237. In this case, the arrival position specifying unit 237 specifies the angle between the optical axis of the objective lens 22 and the traveling direction of the measurement light LS based on the information regarding the angle of the optical scanner 44, and the transmission position specifying unit 236. Reaching the measurement light LS to reach the fundus Ef of the eye E to be inspected based on the transmission position of the measurement light LS specified by the above and the angle between the optical axis of the objective lens 22 and the traveling direction of the measurement light LS. Identify the location.

(S7: An image showing the arrival position of the measurement light is superimposed on the image of the fundus).
Subsequently, the display control unit 2102 causes the display unit 241 to superimpose an image showing the arrival position of the measurement light LS on the fundus Ef of the eye to be inspected E specified by the arrival position specifying unit 237 on the image of the fundus Ef. For example, as shown in FIG. 8, the display control unit 2102 displays an image RP representing the arrival position of the measurement light LS in the fundus Ef of the eye to be inspected E specified by the arrival position specifying unit 237 in the fundus camera unit 2 (or fundus camera unit 2 (or). , Another fundus imaging device) is superimposed on the fundus image 500 and displayed on the display unit 241. More preferably, the image RP representing the arrival position of the measurement light LS is a circular image having a diameter of about 0.5 mm or more and about 2 mm or less in the fundus Ef of the eye E to be inspected.

Further, the display control unit 2102 superimposes the image RPT representing the locus of the arrival position of the measurement light LS in the fundus Ef of the eye to be inspected E specified by the arrival position identification unit 237 by the OCT scan on the fundus image 500, and displays the display unit 241. To display. As shown in FIG. 8, the image RPT representing the locus of the arrival position of the measurement light LS by the OCT scan is represented by a broken line or a dotted line.

More preferably, the display control unit 2102 superimposes the image TP representing the transmission position of the measurement light LS on the OCT front image 700 of the anterior eye portion Ea of the eye E to be examined and displays it on the display unit 241 substantially at the same time. The image RP representing the arrival position of the measurement light LS is superimposed on the fundus image 500 and displayed on the display unit 241. That is, the display control unit 2102 causes the display unit 241 to display the image shown in FIG. 7 and the image shown in FIG. 8 substantially at the same time. As a result, the examiner visually recognizes the display unit 241 to display the transmission position of the measurement light LS in the anterior eye portion Ea of the eye to be inspected E and the measurement light LS in the fundus Ef of the eye to be inspected E substantially simultaneously. The arrival position can be confirmed in the OCT front image 700 in which the image TP representing the transmission position is superimposed and the fundus image 500 in which the image RP indicating the arrival position is superimposed and displayed.

Further, in step S7, the image of the fundus Ef of the eye to be inspected E displayed on the display unit 241 is not limited to the fundus image 500 acquired by the fundus camera unit 2. For example, as shown in FIG. 9, the display control unit 2102 forms an image RP representing the arrival position of the measurement light LS in the fundus Ef of the eye E to be inspected specified by the arrival position specifying unit 237 by the image forming unit 220. The 3D scan image 500B represented by the 3D coordinate system may be superimposed and displayed on the display unit 241. The three-dimensional scan image 500B shown in FIG. 9 is generated based on an eyeball model based on the axial length data and the corneal curve data stored in the storage unit 212 and the fundus image acquired by the fundus camera unit 2, for example. It is an image in which the fundus model and the fundus model are combined.

In the example of the image shown in FIG. 9, the B scan image 500A of the fundus Ef acquired by the fundus OCT of the OCT unit 100 is displayed. By confirming the B scan image 500A, the examiner can confirm whether or not the measurement light LS has reached the fundus Ef of the eye E to be inspected. Further, in the example of the image shown in FIG. 9, the B scan image 500C of the anterior segment acquired by the anterior segment OCT of the OCT unit 100 is displayed in the upper right of the three-dimensional scan image 500B. By confirming the image 501C representing the measurement light LS displayed on the B scan image 500C of the anterior eye portion, the examiner confirms the state in which the measurement light LS is transmitted through the cornea, pupil, and crystalline lens of the eye E to be inspected. can do. The B-scan image 500A of the fundus Ef and the B-scan image 500C of the anterior segment of the eye do not have to be images acquired substantially at the same time. For example, the B-scan image 500C of the anterior segment of the eye may be an image acquired in advance and stored in the storage unit 212.

Also in this case, the display control unit 2102 converts the image RPT representing the locus of the arrival position of the measurement light LS in the fundus Ef of the eye to be inspected E specified by the arrival position identification unit 237 by the OCT scan into the three-dimensional scan image 500B. It can be superimposed and displayed on the display unit 241. Also in this case, as shown in FIG. 9, the image RPT representing the locus of the arrival position of the measurement light LS by the OCT scan is represented by a broken line or a dotted line.

More preferably, the display control unit 2102 superimposes the image TP representing the transmission position of the measurement light LS on the OCT front image 700 of the anterior eye portion Ea of the eye E to be examined and displays it on the display unit 241 substantially at the same time. An image RP representing the arrival position of the measurement light LS is superimposed on at least one of the fundus image 500 and the three-dimensional scan image 500B and displayed on the display unit 241. As a result, the examiner visually recognizes the display unit 241 to display the transmission position of the measurement light LS in the anterior eye portion Ea of the eye to be inspected E and the measurement light LS in the fundus Ef of the eye to be inspected E substantially simultaneously. The arrival position is determined by at least one of the OCT front image 700 in which the image TP representing the transmission position is superimposed and the fundus image 500 and the three-dimensional scan image 500B in which the image RP indicating the arrival position is superimposed. You can check.

(S8: Determine the movement target of the data acquisition optical system)
The movement target determination unit 234 determines the transmission position of the measurement light LS in the anterior segment Ea of the eye E to be inspected identified in step S4 and the arrival position of the measurement light LS in the fundus Ef of the eye E to be inspected identified in step S6. Based on, the movement target of the data acquisition optical system is determined.

The movement target determination unit 234 determines the movement target so that the optical axis (measurement light LS) of the data acquisition optical system passes through a position different from the turbid region, for example. As described above, the beam diameter of the measurement light LS and / or the deflection range of the measurement light LS for reducing speckle noise may be taken into consideration in determining the movement target.

The display control unit 2102 can display the information indicating the determined movement target on the display unit 241 together with the image representing the anterior eye portion.

In the operation of the ophthalmic apparatus 1 in the flowchart shown in FIG. 6, the movement target determination unit 234 automatically corrects the alignment of the data acquisition optical system. However, the alignment of the data acquisition optical system is not limited to automatic, and may be manually corrected. That is, the examiner visually recognizes the display unit 241 and displays the OCT front image 700 on which the image TP representing the transmission position is superimposed, and the fundus image 500 and the three-dimensional scan on which the image RP indicating the arrival position is superimposed. The operation of correcting the alignment of the data acquisition optical system may be performed using the operation unit 242 with reference to at least one of the images 500B.

(S9: Move the data acquisition optical system)
The drive control unit 2101 controls the movement mechanism 150 to move the optical axis of the data acquisition optical system to the position (x coordinate, y coordinate) indicated by the movement target determined in step S8.

(S10: Light is projected toward the fundus to acquire data)
When the movement of the data acquisition optical system in step S9 is completed, the control unit 210 causes the data acquisition unit 250 to acquire data. Alternatively, upon the detection of the completion of the alignment correction by the ophthalmic apparatus 1, the control unit 210 causes the data acquisition unit 250 to acquire the data. The data acquisition unit 250 of this example projects the measurement light LS toward the fundus Ef of the eye E to be inspected, detects the interference light LC generated by superimposing the return light and the reference light LR, and detects the interference light LC, and is a data acquisition system. OCT image data is formed from the data collected by 130.

For example, the OCT image data is A scan OCT image data, and the data processing unit 230 calculates the cornea-retinal distance from the A scan OCT image data. This corneal-retinal distance can be referred to as an approximation of the axial length. In another example, the OCT image data is B-scan image data or three-dimensional scan image data.

The data acquisition performed in step S10 is not limited to OCT, for example, fundus photography (fundus camera, SLO), ocular refraction test, ocular aberration measurement (wavefront analyzer), or visual field test (microperimeter, perimeter). It may be. This completes the operation illustrated in FIG.

[Modification example]
FIG. 10 is a flowchart illustrating a modified example of the operation of the ophthalmic apparatus according to the present embodiment.
FIG. 11 is a schematic view showing a state in which an image showing the transmission position of the measurement light and an image showing the turbid region are displayed on the display unit overlaid on the image of the front eye portion.
FIG. 12 is a schematic view showing a state in which an image showing the arrival position of the measurement light and an image showing the turbid region are superimposed on the image of the fundus and displayed on the display unit.
FIG. 13 is a schematic view showing a state in which an image showing the arrival position of the measurement light and an image showing the turbid region are superimposed on the three-dimensional scan image of the fundus and displayed on the display unit.

(S21-S27)
A modified example of the operation of the ophthalmic apparatus 1 according to this embodiment will be described.
First, steps S21 to S27 are executed in the same manner as in steps S1 to S7 of FIG. 6, respectively.

(S28: 3D OCT is applied to the anterior segment of the eye)
Subsequently, the anterior segment OCT attachment 400 is inserted between the objective lens 22 and the eye E to be inspected. The control unit 210 controls the data acquisition unit 250 so as to apply the three-dimensional OCT to the anterior eye portion of the eye E to be inspected.

The data acquisition unit 250 (image forming unit 220) can form an image (projection image, shadow gram, etc.) expressing the anterior segment from the three-dimensional OCT image data obtained by the three-dimensional OCT of the anterior segment. it can.

In addition to the anterior segment OCT, it is also possible to acquire an image expressing the anterior segment by using the fundus camera unit 2, the anterior segment camera 300, and the like.

(S29: Identify the turbid area in the front image)
The turbid region identification unit 233 analyzes the three-dimensional OCT image data (or an image representing the anterior segment based on the image) acquired in step S28 to identify the turbid region of the anterior segment.

The display control unit 2102 superimposes the information indicating the turbidity region specified by the turbidity region identification unit 233 on the image of the anterior eye portion and the image showing the transmission position of the measurement light LS in the anterior eye portion of the eye E to be inspected. It can be displayed on 241. For example, as shown in FIG. 11, the display control unit 2102 displays an image 710 representing the turbidity region specified by the turbidity region identification unit 233 on the anterior eye portion Ea of the eye E to be inspected specified by the transmission position identification unit 236. The image TP showing the transmission position of the measurement light LS in the above image and the OCT front image (projection image or the like) 700 of the anterior eye portion Ea of the eye E to be inspected are superimposed and displayed on the display unit 241.

Further, the display control unit 2102 superimposes the information indicating the turbidity region specified by the turbidity region identification unit 233 on the image of the fundus Ef and the image showing the arrival position of the measurement light LS in the fundus Ef of the eye E to be inspected. It can be displayed on 241. For example, as shown in FIG. 12, the display control unit 2102 measures the image 510 representing the turbidity region specified by the turbidity region identification unit 233 on the fundus Ef of the eye E to be inspected specified by the arrival position identification unit 237. The image RP showing the arrival position of the optical LS and the fundus image 500 acquired by the fundus camera unit 2 (or another fundus photography device) are superimposed and displayed on the display unit 241. The image 510 representing the turbid region in FIG. 12 is an image of the region affected by the image 710 representing the turbid region in FIG. That is, the image 510 representing the turbid region in FIG. 12 corresponds to the image 710 representing the turbid region in FIG.

Further, the display control unit 2102 superimposes the image RPT representing the locus of the arrival position of the measurement light LS in the fundus Ef of the eye to be inspected E specified by the arrival position identification unit 237 by the OCT scan on the fundus image 500, and displays the display unit 241. To display. As shown in FIG. 12, the image RPT representing the locus of the arrival position of the measurement light LS by the OCT scan is represented by a broken line or a dotted line.

More preferably, the display control unit 2102 displays the image 710 representing the opaque region on the display unit 241 by superimposing the image TP representing the transmission position of the measurement light LS and the OCT front image 700 of the anterior eye portion Ea of the eye E to be inspected. At substantially the same time as the timing of the operation, the image 510 representing the opaque region is displayed on the display unit 241 overlaid on the image RP and the fundus image 500 showing the arrival position of the measurement light LS. That is, the display control unit 2102 causes the display unit 241 to display the image shown in FIG. 11 and the image shown in FIG. 12 substantially at the same time. As a result, the examiner visually recognizes the display unit 241 to measure the transmission position and turbid region of the measurement light LS in the anterior eye portion Ea of the eye E to be inspected and the measurement in the fundus Ef of the eye E to be inspected substantially at the same time. An OCT front image 700 in which an image TP representing a transmission position and an image 710 representing a turbid region are superimposed and displayed on the arrival position and turbid region of the optical LS, and an image RP representing the arrival position and an image 510 representing the turbid region are displayed. It can be confirmed in the fundus image 500 displayed on top of each other.

Further, for example, as shown in FIG. 13, the display control unit 2102 displays an image 510B representing the turbidity region specified by the turbidity region identification unit 233 on the fundus Ef of the eye E to be inspected specified by the arrival position identification unit 237. The image RP representing the arrival position of the measurement light LS and the three-dimensional scan image 500B represented by the three-dimensional coordinate system formed by the image forming unit 220 may be superimposed and displayed on the display unit 241. The three-dimensional scanned image 500B is as described above with respect to FIG. The B-scan image 500A of the fundus Ef and the B-scan image 500C of the anterior segment shown in FIG. 13 are as described above with respect to FIG. Image 510B representing the turbid region in FIG. 13 is an image of the region affected by image 710 representing the turbid region in FIG. That is, the image 510B representing the turbid region in FIG. 13 corresponds to the image 710 representing the turbid region in FIG.

Also in this case, the display control unit 2102 converts the image RPT representing the locus of the arrival position of the measurement light LS in the fundus Ef of the eye to be inspected E specified by the arrival position identification unit 237 by the OCT scan into the three-dimensional scan image 500B. It can be superimposed and displayed on the display unit 241. Also in this case, as shown in FIG. 13, the image RPT representing the locus of the arrival position of the measurement light LS by the OCT scan is represented by a broken line or a dotted line.

The display control unit 2102 superimposes the image 710 representing the opaque region on the image TP showing the transmission position of the measurement light LS and the OCT front image 700 of the anterior eye portion Ea of the eye E to be inspected, and displays the image 710 on the display unit 241. At the same time, the images 510 and 510B representing the opaque region are superimposed on at least one of the fundus image 500 and the three-dimensional scanned image 500B and displayed on the display unit 241. As a result, the examiner visually recognizes the display unit 241 to measure the transmission position and opaque region of the measurement light LS in the anterior eye portion Ea of the eye E to be inspected and the measurement in the fundus Ef of the eye E to be inspected substantially at the same time. An OCT front image 700 in which an image TP representing a transmission position and an image 710 representing a turbid region are superimposed and displayed on the arrival position and turbid region of the optical LS, an image RP representing the arrival position, and an image 510 representing the turbid region. It can be confirmed in at least one of the fundus image 500 and the three-dimensional scanned image 500B on which 510B is superimposed.

(S30: Determine the movement target of the data acquisition optical system)
The movement target determination unit 234 moves the data acquisition optical system based on the transmission position of the measurement light LS in the anterior eye portion Ea of the eye E to be inspected identified in step S24 and the turbid region identified in step S29. Set goals.

The movement target determination unit 234 determines the movement target so that the optical axis (measurement light LS) of the data acquisition optical system passes through a position different from the turbid region. As described above, the beam diameter of the measurement light LS and / or the deflection range of the measurement light LS for reducing speckle noise may be taken into consideration in determining the movement target.

The display control unit 2102 can display the information indicating the determined movement target on the display unit 241 together with the image representing the anterior eye portion and / or the information indicating the turbid region.

In the operation of the ophthalmic apparatus 1 in the flowchart shown in FIG. 10, the movement target determination unit 234 automatically corrects the alignment of the data acquisition optical system. However, the alignment of the data acquisition optical system is not limited to automatic, and may be manually corrected. That is, the examiner visually recognizes the display unit 241 and displays the OCT front image 700 in which the image TP representing the transmission position and the image 710 representing the turbid region are superimposed and displayed, and the image RP representing the arrival position and the image representing the turbid region. The operation unit 242 may be used to correct the alignment of the data acquisition optical system while referring to at least one of the fundus image 500 and the three-dimensional scan image 500B on which 510 and 510B are superimposed.

(S31: Move the data acquisition optical system)
The drive control unit 2101 controls the movement mechanism 150 to move the optical axis of the data acquisition optical system to the position (x coordinate, y coordinate) indicated by the movement target determined in step S30.

(S32: Light is projected toward the fundus to acquire data)
When the movement of the data acquisition optical system in step S31 is completed, the control unit 210 causes the data acquisition unit 250 to acquire data in the same manner as in step S10 of FIG. Alternatively, upon the detection of the completion of the alignment correction by the ophthalmic apparatus 1, the control unit 210 causes the data acquisition unit 250 to acquire data in the same manner as in step S10 of FIG. This completes the operation illustrated in FIG.

[effect]
According to the ophthalmic apparatus 1 according to the present embodiment, the data processing unit 230 specifies a transmission position through which the measurement light LS passes through the anterior eye portion Ea of the eye E to be inspected based on the arrangement of the optical system for collecting OCT data. .. Then, the display control unit 2102 superimposes the image TP representing the transmission position specified by the data processing unit 230 on the image of the eye E to be inspected and causes the display unit 241 to display the image TP. Therefore, the examiner can confirm the transmission position through which the measurement light LS passes through the anterior eye portion Ea of the eye E to be inspected by visually recognizing the display unit 241. Therefore, the examiner can set the transmission position through which the measurement light LS passes through the anterior segment Ea of the eye E to be examined at an intended position, and causes the measurement light LS to enter the inside of the eye E through the transmission position. The data of the eye E to be inspected can be acquired. As a result, it is possible to shorten the shooting and measuring time while ensuring the accuracy and accuracy of shooting and measuring.

Further, the examiner visually recognizes the image 700 of the anterior eye portion Ea of the eye to be inspected E displayed on the display unit 241 while visually recognizing the measurement light LS passing through the anterior eye portion Ea. The transmission position can be confirmed. Therefore, the transmission position through which the measurement light LS passes through the anterior segment Ea of the eye E to be inspected can be reliably set at the intended position, and the measurement light LS is incident on the inside of the eye E to be inspected through the transmission position to be covered. The data of optometry E can be acquired more reliably.

Further, the data processing unit 230 specifies the projection direction of the measurement light LS based on the arrangement of the optical system for collecting OCT data, and the measurement light LS is based on the transmission position of the measurement light LS and the projection direction of the measurement light LS. Identify the arrival position of the eye E to be examined to reach the fundus Ef. Then, the display control unit 2102 superimposes the image RP representing the arrival position specified by the data processing unit 230 on the image 500 of the fundus Ef and causes the display unit 241 to further display the image RP. Therefore, the examiner can confirm the arrival position at which the measurement light LS reaches the fundus Ef of the fundus Ef in the image 500 of the fundus Ef by visually recognizing the display unit 241. Therefore, the examiner confirms the arrival position at which the measurement light LS reaches the fundus Ef of the eye E to be inspected E while setting the transmission position through which the anterior eye portion Ea of the eye to be inspected E is transmitted to the intended position. be able to. As a result, it is possible to shorten the time required for capturing the image 500 of the fundus Ef while ensuring the accuracy and accuracy.

In addition, the examiner can confirm the arrival position at which the measurement light LS reaches the fundus Ef of the eye fundus E in the three-dimensional scan image 500B of the fundus Ef by visually recognizing the display unit 241. As a result, it is possible to shorten the time required for capturing the three-dimensional scan image 500B of the fundus Ef while ensuring accuracy and accuracy.

By visually recognizing the display unit 241, the examiner can obtain the locus of the measurement light LS reaching the fundus Ef of the eye to be inspected E by the optical coherence stomography scan in the image 500 of the fundus Ef and the three dimensions of the fundus Ef. It can be confirmed in the scanned image 500B. As a result, it is possible to shorten the time for the OCT scan in the three-dimensional region of the fundus Ef of the eye E to be inspected while ensuring the accuracy and accuracy.

Further, the examiner can easily grasp the opaque region in the anterior segment Ea of the eye E to be inspected by visually recognizing the display unit 241 and the measurement light LS transmits the anterior segment Ea of the eye E to be inspected. It is possible to set the position to avoid the turbid area while confirming the transmission position. As a result, the accuracy and accuracy of shooting and measurement can be improved, and the time for shooting and measurement can be shortened.

The embodiment of the present invention has been described above. However, the present invention is not limited to the above embodiment, and various modifications can be made without departing from the scope of claims. The configuration of the above embodiment may be partially omitted or may be arbitrarily combined so as to be different from the above.

1: Ophthalmology device, 2: Fundus camera unit, 3: Display device, 10: Illumination optics, 11: Observation light source, 12: Concave mirror, 13: Condensing lens, 14: Visible cut filter, 15: Imaging light source, 16: Mirror, 17: Relay lens system, 18: Relay lens, 19: Aperture, 20: Relay lens, 21: Perforated mirror, 22: Objective lens, 30: Shooting optical system, 31: Shooting focusing lens, 32: Mirror, 33: Dycroic mirror, 33A: Half mirror, 34: Imaging lens, 35: Image sensor, 36: Mirror, 37: Imaging lens, 38: Image sensor, 39: LCD, 40: Collimator lens unit, 41: Retro reflector , 41A: Litro reflector drive unit, 42: Dispersion compensation member, 43: OCT focusing lens, 43A: OCT focusing drive unit, 44: Optical scanner, 45: Relay lens, 46: Dicroic mirror, 50: Alignment optical system, 51: Light emitting diode, 52, 53: Aperture, 54: Relay lens, 55: Dycroic mirror, 60: Focus optical system, 61: LED, 62: Relay lens, 63: Split indicator plate, 64: Two-hole aperture, 65: Mirror, 66: Condensing lens, 67: Reflector, 70, 71: Diopter correction lens, 100: OCT unit, 101: Light source unit, 102: Optical fiber, 103: Polarization controller, 104: Optical fiber, 105: Fiber coupler, 110: Optical fiber, 111: Collimator, 112: Optical path length correction member, 113: Dispersion compensation member, 114: Retro reflector, 114A: Retro reflector drive unit, 116: Collimator, 117: Optical fiber, 118: Polarization Controller, 119: Optical fiber, 120: Attenuator, 121: Optical fiber, 122: Fiber coupler, 123, 124: Optical fiber, 125: Detector, 127, 128: Optical fiber, 130: Data acquisition system, 150: Mobile mechanism , 200: Arithmetic control unit, 210: Control unit, 211: Main control unit, 212: Storage unit, 220: Image forming unit, 230: Data processing unit, 231: Position information acquisition unit, 232: Judgment unit, 233: Turbidity Area identification unit, 234: Movement target determination unit, 236: Transmission position identification unit, 237: Arrival position identification unit, 240: User -Interface, 241: Display, 242: Operation, 250: Data acquisition, 260: Alignment system, 300: Anterior camera, 300A, 300B: Anterior camera, 400: Anterior OCT attachment, 410 : Base, 420: Housing, 430: Lens housing, 440: Support, 500: Eye fundus image, 500A: B scan image, 500B: Three-dimensional scan image, 500C: B scan image, 501C: Image showing measurement light , 510, 510B: Image showing opaque area, 700: OCT front image, 710: Image showing turbid area, 2101: Drive control unit, 2102: Display control unit, E: Eye to be examined, Ea: Anterior eye, Ef: Fundus, KC: Clock, L0: Light, LC: Interference light, LR: Reference light, LS: Measurement light, P: Eye center, RP: Image showing arrival position, RPT: Image showing locus, TP: Transmission position Representing image

Claims (6)

An ophthalmic device that optically acquires data on the eye to be inspected.
A data acquisition unit having an optical system that projects at least a part of the light from the light source as measurement light onto the eye to be inspected and applies an optical coherence stromography scan to the three-dimensional region of the eye to be inspected to collect OCT data.
A data processing unit that specifies a transmission position at which the measurement light passes through the anterior segment of the eye to be inspected based on the arrangement of the optical system.
A display control unit that superimposes an image representing the transmission position specified by the data processing unit on the image of the eye to be inspected and displays it on the display means.
An ophthalmic device characterized by being equipped with. The ophthalmic apparatus according to claim 1, wherein the display control unit superimposes an image representing the transmission position specified by the data processing unit on the image of the anterior eye portion and causes the display means to display the image. The data processing unit specifies the projection direction of the measurement light based on the arrangement of the optical system, and determines the arrival position at which the measurement light reaches the fundus of the eye to be inspected based on the transmission position and the projection direction. Further identify
The ophthalmic apparatus according to claim 2, wherein the display control unit superimposes an image representing the arrival position specified by the data processing unit on the image of the fundus and further displays it on the display means. The display control unit is characterized in that an image representing the arrival position specified by the data processing unit is superimposed on the three-dimensional scan image of the fundus acquired by the data acquisition unit and further displayed on the display means. The ophthalmologic apparatus according to claim 3. The display control unit is characterized in that an image showing a locus of the arrival position specified by the data processing unit by the optical coherence tomography scan is superimposed on the image of the fundus and displayed on the display means. 3 or 4 ophthalmic apparatus. The data processing unit analyzes the OCT data to further identify the opaque region of the anterior segment of the eye.
Any one of claims 1 to 5, wherein the display control unit superimposes an image representing the turbid region specified by the data processing unit on the image of the eye to be inspected and causes the display means to further display the image. The ophthalmic device described in the section.

Images