WO2017135278A1

WO2017135278A1 - Tomographic-image image pickup device

Info

Publication number: WO2017135278A1
Application number: PCT/JP2017/003541
Authority: WO
Inventors: 遠藤　雅和; 昌明羽根渕; 康寛古内; 佳史村田; 一並木
Original assignee: 株式会社ニデック
Priority date: 2016-02-02
Filing date: 2017-02-01
Publication date: 2017-08-10
Also published as: JPWO2017135278A1; JP7104516B2

Abstract

The present invention addresses the technical problem of providing a tomographic-image image pickup device that can suitably acquire the structure of an eye under test. Provided is a tomographic-image image pickup device that picks up tomographic images of an eye under test, wherein the device is characterized by being provided with the following: an image pickup means for picking up anterior eye portion tomographic images of the eye under test, from at least two different directions; and a calculation means for synthesizing a plurality of the anterior eye portion tomographic images which were picked up by the image pickup means from at least two different directions, such synthesis carried out on the basis of the positional relationships of the images. Due to this configuration, the structure of the eye under test can be suitably acquired.

Description

Tomographic imaging system

The present disclosure relates to a tomographic imaging apparatus for imaging a tomographic image of an eye to be examined.

Conventionally, an optical coherence tomography (OCT) that acquires an optical coherence tomographic image of a subject is known. A tomographic image capturing apparatus using OCT divides light emitted from a light source into measurement light and reference light, and irradiates the tissue of the subject with the divided measurement light. Then, the tomographic imaging apparatus combines the measurement light reflected by the tissue with the reference light, and acquires information in the depth direction of the tissue from the interference signal of the combined light. The tomographic imaging apparatus generates a tomographic image using the acquired information in the depth direction (see Patent Document 1).

JP2012-223435A

By the way, when the tomographic imaging apparatus was used to photograph the subject's eyes from the front, the measurement light was blocked by the iris, making it difficult to photograph ciliary bodies, chin strips, and the like. As a result, the examiner could not fully grasp the structure of the eye to be examined.

The present disclosure has been made in view of at least one of the problems of the prior art, and provides a tomographic imaging apparatus capable of suitably acquiring the structure of the eye to be examined.

In order to solve the above problems, the present disclosure is characterized by having the following configuration.

(1) A tomographic imaging apparatus for imaging a tomographic image of an eye to be examined, the imaging means for imaging the anterior segment tomographic image of the eye to be examined from two or more different directions, and two or more different directions depending on the imaging means And an arithmetic means for synthesizing a plurality of anterior segment tomographic images taken based on the positional relationship of the images.

It is an optical diagram which shows the optical system of the tomographic imaging apparatus of a present Example. It is a block diagram which shows the control system of a present Example. It is a flowchart which shows the control of a present Example. It is a figure for demonstrating the switching of the imaging | photography direction of a present Example. It is a figure for demonstrating the switching of the imaging | photography direction of a present Example. It is a figure for demonstrating the switching of the imaging | photography direction of a present Example. It is a figure which shows the example of the tomographic image image | photographed by the tomographic image imaging apparatus of a present Example. It is a figure which shows the example of the tomographic image image | photographed by the tomographic image imaging apparatus of a present Example. It is a figure which shows the example of the tomographic image image | photographed by the tomographic image imaging apparatus of a present Example. It is a figure which shows the example of the tomographic image synthesize | combined by the tomographic imaging apparatus of a present Example. It is a figure explaining the example of a change of the method of switching an imaging direction with the tomographic imaging apparatus of a present Example. It is a figure explaining the example of a change of the method of switching an imaging direction with the tomographic imaging apparatus of a present Example. It is a figure explaining the fixation optical system of a present Example.

Embodiments according to the present disclosure will be briefly described based on the drawings. The tomographic imaging apparatus (for example, the tomographic imaging apparatus 1) of the present embodiment mainly includes, for example, an imaging unit (for example, the measurement optical system 100) and a calculation unit (for example, the control unit 70). The imaging unit images the eye to be examined from two or more different directions, for example. The calculation unit synthesizes a plurality of anterior segment tomographic images captured by the imaging unit. For example, the plurality of anterior segment tomographic images are images captured by the imaging unit from two or more different directions. The calculation unit synthesizes a plurality of anterior segment tomographic images based on the positional relationship between the images.

The calculation unit may acquire the structural information of the eye to be examined based on the composite image, for example. The composite image is an image obtained by combining a plurality of anterior ocular segment tomographic images taken from two or more different directions. The structure information may be information such as the position or shape of at least one part of the eye to be examined. As a result, it is easy to obtain structural information regarding a part that is difficult to image from one direction.

The calculation unit calculates a position (for example, postoperative predicted anterior chamber depth) at which the intraocular lens is inserted based on the position of the corneal apex of the eye to be examined and the position of the ciliary body obtained from the structure information. Also good. For example, the calculation unit may calculate the postoperative predicted anterior chamber depth based on the position of the intersection point between the normal of the corneal surface passing through the corneal apex and the plane including the ciliary protrusion in the composite image. . For example, the calculation unit is based on the position of the intersection of the straight line in the measurement optical axis direction (depth direction) in the frontal tomographic image and the line connecting the left and right ciliary protrusions in the synthesized tomogram in the composite image. The postoperative predicted anterior chamber depth may be calculated. The calculation unit may obtain the structure of the eye to be examined by various methods based on the composite image.

The calculation unit may measure the ciliary groove distance based on the composite image. The calculation unit may determine the size of the posterior chamber type phakic intraocular lens (ICL) based on the measured inter-ciliary distance. By acquiring the composite image, the present apparatus can select an appropriate intraocular lens size.

Note that the imaging unit may shoot from the front direction of the subject eye and the oblique direction of the subject eye when photographing the subject eye from two or more different directions. The front direction may be, for example, the fixation direction of the eye to be examined. The oblique direction may be, for example, a direction inclined with respect to the front direction. For example, the imaging unit may image the eye to be examined from a direction inclined by 25 ° to 30 ° with respect to the front direction. The oblique direction may be, for example, a direction inclined to at least one of left and right with respect to the front direction.

Note that the calculation unit may perform noise reduction processing on the anterior segment tomographic image. For example, the calculation unit may perform noise reduction of the anterior segment tomographic image by analyzing a statistic of signal intensity of a plurality of anterior segment tomographic images captured from the same direction. In this case, for example, the imaging unit may capture a plurality of anterior segment tomographic images in each imaging direction.

Note that the arithmetic unit may correct the composite image by correcting the refraction in consideration of the shape of the boundary and the refractive index of the photographed object. For example, the calculation unit may correct the image based on a refractive index of a cornea, a sclera, a crystalline lens, a ciliary body, a chin band, a vitreous body, or the like set in advance. As a result, distortion of the tomographic image is reduced, and more preferable structure information of the eye to be examined can be acquired. As the refractive index of each part, a value obtained in advance by measurement or the like may be used.

In addition, this apparatus may be provided with a fixation guidance part (for example, the 1st fixation optical system 150, the 2nd fixation optical system 10, etc.). The fixation guidance unit guides fixation of the eye to be examined, for example. In this case, the imaging unit may capture the anterior ocular segment tomographic image from two or more different directions by inducing fixation of the eye to be examined by the fixation induction unit. For example, the fixation guidance unit may guide the fixation direction by switching lighting of a plurality of fixation light sources (for example, the light source 151, the light source 11, and the light source 12), or move the fixation light source. The fixation direction may be guided with.

The fixation guidance section may include a presentation distance variable section (for example, the presentation distance variable sections 13 and 14). The presentation distance variable unit changes the presentation distance of the fixation target, for example. In this case, the calculation unit may detect a change in the form of the eye to be inspected caused by a change in the fixation target presentation distance. For example, the calculation unit detects a change in the shape of the eye based on two or more anterior segment tomographic images captured by the imaging unit before and after the presentation distance of the fixation target is changed by the presentation distance variable unit. May be.

Note that the present apparatus may further include an anterior ocular segment observation unit (for example, an observation system 140). The anterior ocular segment observation unit captures, for example, an anterior ocular segment observation image of the eye to be examined. In this case, the imaging unit may capture the anterior ocular segment tomographic image by tracking with reference to the characteristic part of the subject eye detected from the anterior ocular segment observation image.

Note that the imaging unit may include a first interference optical system (for example, the OCT system 110). For example, the first interference optical system captures an anterior tomographic image of the eye to be examined by detecting an interference state between the reflected light of the measurement light irradiated on the eye to be examined and the reference light corresponding to the measurement light. . Further, the imaging unit may include a second interference optical system (for example, the OCT system 210, the OCT system 310, etc.). For example, the second interference optical system captures an anterior tomographic image of the eye to be examined from a direction different from that of the first interference optical system.

Note that the present apparatus may further include a control unit (for example, the control unit 70) that controls the imaging unit. The control unit may change the wavelength band of the measurement light when changing the imaging direction of the imaging unit with respect to the eye to be examined. Note that the control unit may change the polarization state of the measurement light when the imaging direction of the imaging unit with respect to the eye to be examined is changed. Thereby, appropriate imaging can be performed according to the region of the eye to be examined. The control unit may change at least one of the working distance between the imaging unit and the eye to be examined and the light collection position of the imaging unit when switching the imaging direction of the imaging unit with respect to the eye to be examined.

Note that the photographing unit may be equipped with a Shine proof camera. In this case, the imaging unit may capture a tomographic image of the eye to be examined using a Scheimpflug camera. Further, the photographing unit may include an ultrasonic camera. In this case, the imaging unit may capture a tomographic image of the eye to be examined using an ultrasonic camera.

<Example>
Hereinafter, the tomographic imaging apparatus of the present embodiment will be described with reference to the drawings. The tomographic imaging apparatus 1 shown in FIG. 1 mainly includes, for example, a measurement optical system 100 and a second fixation optical system 10. The measurement optical system 100 includes, for example, an optical system for measuring the eye E. For example, the second fixation optical system 10 fixes the eye E to be examined.

<Measurement optical system>
The measurement optical system 100 includes, for example, an OCT system 110, a scanning system 120, a light guide system 130, an observation system 140, a first fixation optical system 150, and the like. For example, the OCT system 110 irradiates the eye E with measurement light and detects an interference signal between the reflected light and the reference light. The OCT system 100 is an optical system of a so-called optical coherence tomography (OCT). The OCT system 110 includes, for example, a light source 111, a coupler (light splitter) 112, a reference system 113, a detection system 115, and the like. The light source 111 emits, for example, low coherent light. The coupler 112 divides the light emitted from the light source 111 into measurement light and reference light. The reference system 113 includes, for example, a reference mirror. For example, the reference system 113 reflects the reference light divided by the coupler 112 and makes it incident on the coupler 112 again. The reference system 113 may be a Michelson type or a Mach-Zehnder type. The detection system 115 detects, for example, an interference state between the measurement light and the reference light. For example, a depth profile (A scan signal) in a predetermined range is acquired by Fourier transform on the interference signal detected by the detection system 115.

As the OCT system 110, for example, Spectral-domain OCT (SD-OCT), Swept-source OCT (SS-OCT), Time-domain OCT (TD-OCT), or the like may be used.

<Scanning system>
The scanning system 120 scans the measurement light from the OCT system 110. The scanning system 120 includes, for example, a galvanometer mirror 121, a galvanometer mirror 122, a drive unit 123, a drive unit 124, and the like. For example, the galvanometer mirror 121 scans the measurement light in the X direction by driving the drive unit 123. For example, the galvanometer mirror 122 scans the measurement light in the Y direction by driving the driving unit 124. Therefore, for example, the scanning system 120 scans the measurement light from the OCT system 100 two-dimensionally.

<Light guide system>
The light guide system 130 guides the measurement light scanned by the scanning system 120 toward the eye E. The light guide system 130 includes, for example, an objective lens 131 and the like.

<Observation system>
The observation system 140 observes the eye E from the direction of the measurement optical axis L1, for example. For example, the observation system 140 is arranged on the measurement optical axis L1 of the measurement optical system 100, and images the eye E from the direction of the measurement optical axis L1. The observation system 140 may include, for example, a light receiving element. The observation system 140 may have, for example, a scanning laser ophthalmoscope (SLO) device configuration (see, for example, Japanese Patent Application Laid-Open No. 2015-66242) or a so-called fundus camera type configuration (special feature). (See Open 2011-10944). Note that the OCT system 110 may also be used as the observation system 140, and a front image may be acquired based on a detection signal from the detection system 115.

<First fixation optical system>
For example, the first fixation optical system 150 fixes the eye E to be examined in the direction of the measurement optical axis L1. For example, the first fixation optical system 150 includes a fixation light source 151 that emits visible light.

Note that the measurement optical system 100 may include a dichroic mirror 101, a dichroic mirror 102, and the like. In the dichroic mirror 101, for example, the measurement optical axis L1 of the measurement optical system 100 and the optical axis L2 of the scanning system 120 are coaxial. In the dichroic mirror 102, for example, the measurement optical axis L1 of the measurement optical system 100 and the optical axis L3 of the first fixation optical system 150 are coaxial.

<Second fixation optical system>
For example, the second fixation optical system 10 fixes the eye E to be examined in an oblique direction. For example, the second fixation optical system 10 causes the eye E to be fixed in an oblique direction by θ with respect to the measurement optical axis L1 of the measurement optical system 100. The second fixation optical system 10 includes, for example, a light source 11 and a light source 12 that emit visible light. For example, the light source 11 and the light source 12 are fixed to the outside of the casing of the device 1.

For example, the light source 11 fixes the eye E with the eye E facing leftward. For example, the emission direction of the fixation light beam emitted from the light source 11 is tilted by θ in the right direction with respect to the measurement optical axis L 1 of the measurement optical system 100. Therefore, when the eye E examinees the light source 11, the fixation direction of the eye E is tilted by θ in the left direction with respect to the measurement optical axis L1.

The light source 12 fixes the eye E, for example, with the eye E facing rightward. For example, the emission direction of the fixation light beam emitted from the light source 12 is inclined to the right by θ with respect to the measurement optical axis L1 of the measurement optical system 100. Therefore, when the subject eye E fixes the light source 12, the fixation direction of the subject eye E is inclined to the right by θ with respect to the measurement optical axis L1.

Note that the angle at which the fixation direction is inclined may be set to an angle at which the ciliary body of the eye to be examined is positioned on the measurement optical axis L1, for example. For example, the second fixation optical system may include the light source 11 and the light source 12 so that θ is in the range of 25 ° to 30 °. Thereby, the tomographic imaging apparatus 1 can arrange the ciliary body in the center of the imaging area of the tomographic image. This angle is such that when the human eye axis length is around 26 mm, the distance between ciliary grooves is around 14 mm, and the eyeball rotation point is located at half the distance of the eye axis length, the ciliary groove is the measurement optical axis. It is an angle for positioning on L1. Of course, the tilt angle in the fixation direction may be changed between the light source 11 and the light source 12.

<Control system>
Next, a control system of the tomographic imaging apparatus 1 will be described with reference to FIG. The tomographic imaging apparatus 1 includes a control unit 70, for example. The control unit 70 is realized by, for example, a CPU (Central Processing Unit) 71, a ROM 72, a RAM 73, and the like. The ROM 72 stores, for example, a program for controlling the operation of acquiring an OCT signal, a program for processing a tomographic image, an initial value, and the like. The RAM 73 temporarily stores various information, for example.

As shown in FIG. 2, the control unit 70 includes, for example, a storage unit (for example, a non-volatile memory) 74, a display unit 75, an operation unit 76, a measurement optical system 100, a second fixation optical system, and the like. Connected. The storage unit 74 is, for example, a non-transitory storage medium that can retain stored contents even when power supply is interrupted. For example, a hard disk drive, a flash ROM, a removable USB memory, or the like can be used as the storage unit 74.

The display unit 75 may be a display mounted on the main body of the apparatus 1 or a display connected to the main body. For example, a display of a personal computer (hereinafter referred to as “PC”) may be used. The display unit 75 displays, for example, a tomographic image acquired by the measurement optical system 110, various operation screens, and the like.

The operation unit 76 receives various operation instructions from the examiner. The operation unit 76 outputs a signal corresponding to the input operation instruction to the CPU 71. For the operation unit 76, for example, at least one of user interfaces such as a mouse, a joystick, a keyboard, and a touch panel may be used.

<Control action>
In the tomographic imaging apparatus 1 having the above-described configuration, an operation when a tomographic image is acquired and analyzed will be described with reference to FIG. In the following example, the tomographic imaging apparatus 1 images the eye E from a plurality of directions by the measurement optical system 100 and synthesizes the acquired tomographic images.

<Step S1: Front shooting>
For example, the control unit 70 controls the first fixation optical system 150 to project a fixation light beam from the direction of the measurement optical axis L1 onto the subject. As shown in FIG. 4A, when the eye to be inspected fixes the fixation light source 151 of the first fixation optical system 150, the eye to be inspected is in a state in which the line of sight is aligned with the measurement optical axis L1. In this case, for example, a corneal apex or a crystalline lens of the eye E is disposed in the center of the imaging region A1 of the measurement optical system 100.

For example, the control unit 70 controls a drive unit (not shown) so that the measurement optical axis L1 is at the center of the pupil of the eye E based on an anterior eye image captured by a camera for observing the anterior eye part (not shown). Align automatically.

When the alignment is completed, the control unit 70 controls the measurement optical system 100 to measure the eye E. For example, the control unit 70 captures a tomographic image of the eye E. For example, the control unit 70 controls driving of the scanning system 120 to scan the eye E with the measurement light. The controller 70 acquires an interference signal based on the measurement light detected by the detection system 115 and the reference light.

For example, as shown in FIG. 5A, the control unit 70 captures a frontal tomographic image 91 obtained by capturing the eye E from the front direction (for example, the fixation direction of the eye to be examined). For example, the control unit 70 stores the captured frontal tomographic image 91 in the storage unit 74 or the like.

When the subject's eye is photographed from the front direction, the normal of the cornea or sclera located in front of the ciliary body or chin band is greatly inclined with respect to the measurement optical axis L1. For this reason, when an attempt is made to photograph the ciliary body or chin band from the front of the eye to be examined, the reflected light from the cornea or sclera is reflected in a direction different from the measurement optical axis L1, and the reflected light cannot be detected well. In many cases (see FIG. 5A). In such a case, the position or structure of the ciliary body or chin band cannot be obtained sufficiently. For this reason, the control part 70 image | photographs on conditions suitable for imaging | photography of a ciliary body or a chin strip in subsequent step S2 and step S3.

<Step S2: First oblique photographing>
When the imaging from the front direction is completed, the control unit 70 images the eye E from a direction different from the front direction. Therefore, for example, the control unit 70 controls the second fixation optical system 10 to switch the fixation direction of the eye E. For example, as illustrated in FIG. 4B, the control unit 70 turns off the fixation light source 151 of the first fixation optical system 150 and turns on the light source 11 of the second fixation optical system 10. When the light source 11 is turned on and the subject fixes the fixation target by the light source 11, the fixation direction of the eye E coincides with the direction of the optical axis L4 of the target luminous flux from the light source 11. Therefore, the fixation direction of the eye E is tilted θ to the left with respect to the measurement optical axis L1. In this case, the right ciliary body of the eye E enters the imaging region A1 of the measurement optical system 100. The controller 70 performs alignment with the anterior eye image as appropriate in a state where the light source 11 is fixed to the eye E, and performs imaging by the measurement optical system 100. For example, as illustrated in FIG. 5B, the control unit 70 acquires a right tomographic image 92 obtained by photographing the eye E from an oblique right direction. For example, the control unit 70 stores the captured right tomographic image 92 in the storage unit 74 or the like.

<Step S3: Second oblique photographing>
For example, the control unit 70 controls the second fixation optical system 10 again to switch the fixation direction of the eye E. For example, as illustrated in FIG. 4C, the control unit 70 turns on the light source 12. When the light source 12 is turned on and the subject fixes the fixation target by the light source 12, the fixation direction of the eye E coincides with the direction of the optical axis L5 of the target luminous flux from the light source 12. Therefore, the fixation direction of the eye E is tilted θ to the right with respect to the measurement optical axis L1. In this case, the ciliary body on the left side of the eye E enters the imaging region A1 of the measurement optical system 100. The control unit 70 performs imaging by the measurement optical system 100 in a state where the light source 12 is fixed to the eye E. For example, as illustrated in FIG. 5C, the control unit 70 acquires a left tomographic image 93 obtained by photographing the eye E from an oblique left direction. For example, the control unit 70 stores the captured left tomographic image 93 in the storage unit 74 or the like.

For example, the measurement light is substantially perpendicular to the cornea or sclera of the eye E by tilting the fixation direction of the subject with respect to the measurement optical axis L1 as in Steps S2 and S3 described above. Since it is incident and heads toward the ciliary body, the ciliary body or the chin strip is suitably photographed.

<Step S4: Image Composition>
As described above, when the tomographic images in a plurality of directions are acquired, the control unit 70 combines the tomographic images photographed from the plurality of directions. For example, the control unit 70 may perform alignment when combining each image using tracking information obtained when the eye to be examined is photographed.

The tracking information is, for example, information obtained from the anterior eye image when the eye E is imaged. For example, the tracking information may be, for example, deviation information of the eye E from the proper alignment position. For example, the control unit 70, based on the tracking information when the front tomographic image 91 is captured and the tracking information when the right tomographic image 92 or the left tomographic image 93 is captured, the position of the eye when each image is captured. May be obtained respectively. Then, the combined position of the images may be determined so that the positions of the eyes of the images match. At this time, for example, the control unit 70 may rotate the left and right tomographic images in consideration of the fixation direction of the eye E. For example, the control unit 70 stores the combined tomographic image (the combined tomographic image 90) in the storage unit 74 or the like.

<Step S5: Image Analysis>
The control unit 70 may analyze the composite tomographic image 90 as shown in FIG. For example, the control unit 70 may predict the ELP (postoperative anterior chamber depth) by analyzing the composite tomographic image 90.

For example, the control unit 70 detects the ciliary protrusions TR and TL from the right tomographic image 92 and the left tomographic image 93, respectively, and a straight line L6 connecting the ciliary protrusions TR and the ciliary protrusions TL; The position of the intersection point i with the perpendicular line V1 passing through the corneal vertex Ca of the frontal tomographic image 91 is obtained. Then, the control unit 70 may predict ELP based on the distance between the corneal vertex Ca and the intersection point i.

The control unit 70 may measure the ciliary interstitial distance (STS: Sulcus to ul sulcus) based on the composite tomographic image 90. The controller 70 may determine the size of the posterior chamber type phakic intraocular lens (ICL) based on the measured ciliary inter-groove distance. The ICL is a lens implanted between the iris and the lens to correct myopia or astigmatism.

As described above, the tomographic imaging apparatus 1 according to the present embodiment can acquire the positional relationship of parts that are difficult to be imaged from one direction by synthesizing tomographic images of the eye E to be inspected from a plurality of directions. That is, the tomographic imaging apparatus 1 of the present embodiment can acquire the positional relationship between a part that appears in an image taken from a certain direction and a part that appears in an image taken from another direction.

For example, the tomographic imaging apparatus 1 captures a ciliary body or a chin band that is difficult to capture from the front direction from an oblique direction, and combines the tomographic image captured from the oblique direction and the tomographic image captured from the front. The position of the ciliary body / chin band with respect to the cornea shape or the entire eyeball can be specified. Thereby, information for selecting an intraocular lens to be inserted into the eye E can be suitably acquired.

In the above description, the tomographic imaging apparatus 1 includes the second fixation optical system 10 and images the eye E from a plurality of directions by switching the fixation direction of the subject. Not exclusively. For example, the eye E may be photographed from a plurality of directions by switching the direction of the measurement optical axis L1 of the measurement optical system 100.

For example, as shown in FIG. 7, the measurement optical system 100 may include a plurality of tomographic imaging systems. For example, the tomographic imaging apparatus 1 may include an OCT system 110, an OCT system 210, and an OCT system 310. For example, the OCT system 110 images the eye E from the direction of the optical axis L1 via the scanning system 120 and the light guide system 130. The OCT system 210 images the eye E from the direction of the optical axis L4 via the scanning system 220 and the light guide system 230, for example. The OCT system 310 images the eye E from the direction of the optical axis L5 via the scanning system 320 and the light guide system 330, for example. As described above, the tomographic imaging apparatus 1 may photograph the eye E from a plurality of directions by including a plurality of tomographic imaging systems having different measurement optical axis directions.

When a plurality of tomographic imaging systems are provided and the subject eye E is photographed simultaneously from a plurality of directions, the positions of the subject eye E at the time of photographing each image coincide with each other, so that the images can be easily combined. For example, the control unit 70 may synthesize an image based on the positional relationship between the imaging regions of each OCT system obtained from the design of the apparatus.

When a plurality of OCT systems are provided, the wavelength band of the OCT system that captures images from the front direction and the OCT system that captures images from an oblique direction may be changed. For example, an OCT system that captures images from the front direction may use a light source having a center wavelength of about 1300 nm, and an OCT system that captures images from an oblique direction may use a light source having a center wavelength of approximately 1700 nm. As a result, it is possible to perform imaging with a light beam suitable for the region to be imaged.

Note that the tomographic imaging apparatus 1 may switch the direction of the measurement optical axis L1 by moving the measurement optical system 100, for example. For example, as shown in FIG. 8, the tomographic imaging apparatus 1 may include a drive unit 50. The drive unit 50 drives the measurement optical system 100, for example. For example, the control unit 70 may control the driving of the driving unit 50 and rotate the measuring optical system 100 so that the optical axis L1 of the measuring optical system 100 rotates θ with respect to the fixation direction of the subject. . Accordingly, the tomographic image photographing apparatus 1 may photograph the eye E from a plurality of directions. In this case, the second fixation optical system 10 may include an external fixation light source 13 that fixes the eye E in a fixed direction regardless of the movement of the measurement optical system 100. The external fixation light source 13 is held by, for example, a base (not shown) of the tomographic imaging apparatus 1 or a face support (not shown) provided on the base for fixing the subject's face. Also good.

In addition, when changing the direction of the measurement optical axis L1, the tomographic imaging apparatus 1 may change the direction of the measurement optical axis L1 on the horizontal plane in order to prevent the measurement light from being blocked by the scissors.

Note that the tomographic imaging apparatus 1 may switch the polarization state of the OCT system 110 between imaging from the front direction and imaging from an oblique direction. In this case, for example, the tomographic imaging apparatus 1 may include the polarization system 116. The polarization system 116 may include, for example, an optical element that splits the measurement light of the OCT system 110 into P waves and S waves.

For example, when photographing the eye E to be examined obliquely, the control unit 70 may divide the measurement light into a P wave and an S wave by a polarization system and irradiate the eye to be examined with the separated P wave. The P wave has a lower reflectance when entering the object from an oblique direction than the S wave. Therefore, by using the P wave as the measurement light, the measurement light can be prevented from being reflected by the cornea or the sclera, and the amount of the measurement light reaching the ciliary body or the chin band can be secured.

Note that the control unit 70 may perform oblique imaging using tracking information in imaging from the front direction. For example, the control unit 70 may perform imaging from an oblique direction when the eye E is positioned at the same position as the imaging position in the front direction. In this case, the control unit 70 may synthesize each tomographic image at a synthesis position determined in advance from the relationship between the imaging region of the measurement optical system 100 and the second fixation optical system 10.

Note that the control unit 70 may capture a plurality of tomographic images while gradually shifting the imaging position from the same direction. For example, when photographing from an oblique direction, the control unit 70 performs photographing a plurality of times while gradually moving the scanning position of the measurement light. As a result, an image whose shooting position is slightly shifted is shot. In this case, the control unit 70 may select and synthesize the one closest to the synthesis position using the tracking information.

In addition, when the timing which image | photographs from each direction differs like a present Example, the tomographic image imaging device 1 image | photographs a tomographic image stably by performing the tracking for the characteristic site | part of the eye E to be examined. Also good. For example, the control unit 70 specifies a characteristic part (for example, an iris pattern, a scleral blood vessel, etc.) of the eye to be examined from the anterior eye part image of the eye to be photographed by the observation system 140, and the position is the anterior eye part. Tracking may be performed by moving the tomographic imaging apparatus 1 so that it is captured at the same position of the image.

Note that the control unit 70 may determine the image synthesis position by edge detection. For example, the control unit 70 may detect the edges of the images, perform matching processing so that the edge shapes of the cornea, sclera, iris, and the like match, and synthesize the images. In addition, for example, the control unit 70 may determine the synthesis position so that the edge of the tomographic image captured from the oblique direction overlaps the ellipse approximated from the edge of the frontal tomographic image. Of course, the iris edges may coincide. The edge detection may use a change in luminance value of adjacent pixels.

Note that the control unit 70 may determine an image combining position using the correlation between the images. For example, image alignment may be performed using a phase only correlation method.

Note that the control unit 70 may use the alignment based on the tracking information described in the above embodiment and the alignment method such as edge detection and phase-only correlation.

The controller 70 may rotate the images in advance in consideration of the fixation direction of the eye E and the inclination of the measurement optical axis L1 in the alignment of the images. For example, in the case of the above embodiment, when the subject is correctly fixing, the right tomographic image 92 is rotated counterclockwise by θ and the left tomographic image is rotated clockwise by θ with respect to the frontal tomographic image 91. is doing. Therefore, for example, the control unit 70 may rotate the right tomographic image 92 by clockwise θ rotation and the left tomographic image 93 by counterclockwise θ rotation.

It should be noted that when images are synthesized, noise reduction processing may be performed on each image in order to visualize parts that are difficult to be imaged, such as ciliary protrusions. For example, the control unit 70 may reduce noise by taking a plurality of images and statistically processing the image information.

Statistic processing includes, for example, addition processing, MAP (Maximum aposteriori) processing, and the like. The MAP process is a process for reducing noise by utilizing the fact that the intensity of an interference signal detected by the OCT system follows a Rice distribution, for example.

By performing noise processing on each tomographic image, the ciliary body image that is easily buried in noise becomes clear and image synthesis processing becomes easier.

The control unit 70 may correct each tomographic image by performing refractive correction based on the shape of the boundary and the refractive index of the imaging region. For example, the control unit 70 may correct the image based on a preset refractive index of the cornea, sclera, crystalline lens, ciliary body, chin band, vitreous body, or the like. Thereby, the control unit 70 may reduce the distortion of the tomographic image.

Note that the control unit 70 may control the working distance of the tomographic imaging apparatus 1, the condensing position of the measurement optical system 100, and the like according to switching of the imaging direction. In this case, for example, the control unit 70 may control the driving unit 50 that moves the measurement optical system 100 according to switching of the photographing direction, or may move, insert, and remove the optical element of the light guide system 130. .

Note that the second fixation optical system may include, for example, a presentation distance variable unit. As shown in FIG. 9, for example, the second fixation optical system 10 may include presentation distance

variable units

13 and 14. The presentation distance variable unit 13 may adjust the presentation distance of the fixation target by the light source 11, for example. The presentation distance variable unit 14 may adjust the presentation distance of the fixation target by the light source 12, for example. The presentation distance variable unit 13 may adjust the presentation distance of the fixation target by moving the light source 11 in the direction of the optical axis L4, for example. The presentation distance variable unit 14 may adjust the presentation distance of the fixation target by moving the light source 12 in the direction of the optical axis L5, for example. In this case, the control unit 70 may control the presentation distance

variable units

13 and 14 to adjust the presentation distance of the fixation target.

Note that the control unit 70 may adjust the presenting distance of the fixation target when the measurement optical system 100 is photographing the eye to be examined. Thereby, the control unit 70 can photograph the change of the ciliary body due to the visual acuity adjustment (Accommodation) of the eye to be examined. For example, the control unit 70 controls the presentation distance

variable units

13 and 14 to capture tomographic images of the eye to be examined when the presentation distance of the

light sources

11 and 12 is increased or decreased. And the control part 70 may detect a change, such as a ciliary body or a chin band, from the change of the tomographic image each image | photographed in each presentation distance. For example, the control unit 70 may detect a change in the ciliary body or the chin band by taking the intensity difference between the tomographic images. The control unit 70 may acquire position information of the ciliary body or the chin band based on the detection result of the change of the ciliary body or the chin band. For example, the control unit 70 may acquire positional information of the ciliary body when the ciliary body contracts or relaxes. In addition, the control unit 70 may change the presentation distance of the fixation target by the presentation distance

variable units

13 and 14 during photographing with the measurement optical system 100, or the measurement optical optics before and after changing the presentation distance. Shooting with the system 100 may be performed. Note that noise reduction as described above may also be performed on an image captured by changing the fixation target presentation distance.

Further, the control unit 70 may acquire a motion contrast by processing a complex OCT signal obtained by Fourier transforming the OCT signal acquired by the OCT system 110, for example. The motion contrast is information indicating the movement of the test object, for example. The control unit 70 may detect the movement of the ciliary body when the presenting distance of the fixation lamp changes by acquiring the motion contrast. As a processing method of the complex OCT signal for obtaining the motion contrast, for example, a method of calculating the intensity difference of the complex OCT signal, a method of calculating the variance of the intensity of the complex OCT signal, and a method of calculating the phase difference of the complex OCT signal , A method of calculating a vector difference of a complex OCT signal, a method of using correlation (or non-correlation) of an OCT signal (correlation mapping, decorrelation mapping), a method of combining motion contrast data obtained thereby, and the like Conceivable.

Of course, the presentation distance variable unit includes, for example, an optical element disposed between the fixation light source (for example, the light sources 11 and 12) and the eye E, and moves the optical element to move the fixation target. The structure which adjusts presentation distance may be sufficient.

Note that the tomographic imaging apparatus 1 may capture a fundus tomographic image of the eye to be examined. In this case, the control unit 70 may align the anterior ocular segment tomographic image and the fundus tomographic image of the eye to be examined. For example, the control unit 70 may align the synthesized tomographic image of the anterior segment tomographic image captured from the front direction and the oblique direction of the eye to be examined and the fundus tomographic image, and synthesize these. Further, the structure information of the eye of the eye E may be acquired based on the alignment information between the anterior segment tomographic image and the fundus tomographic image. The anterior segment tomographic image and the fundus tomographic image may be captured simultaneously or separately.

In the above embodiment, the measurement optical system 110 is provided. However, the present invention is not limited to this, and a configuration in which a Scheimpflug camera, an ultrasonic camera, or the like is provided and a tomographic image of the eye to be examined may be taken.

In the above embodiment, the second fixation optical system 10 may be fixed to the apparatus main body, or may be movably held by an arm or the like provided in the apparatus main body.

In the above embodiment, the second fixation optical system 10 is configured to tilt the fixation direction of the eye to be examined right and left, but is not limited thereto. For example, in the second fixation optical system 10, a light source may be disposed at a position where the eye E is tilted in the vertical direction. In addition, when the subject's eye is photographed from an oblique direction using the measurement optical system, the photographing may be performed while being tilted in the vertical direction.

In the above-described embodiment, the control unit 70 obtains the postoperative predicted anterior chamber depth based on the combined tomographic image obtained by combining the tomographic images captured from a plurality of directions, but is not limited thereto. . For example, the control unit 70 may obtain the postoperative predicted anterior chamber depth based on one tomographic image taken from an oblique direction. In this case, for example, the control unit 70 may obtain the postoperative predicted anterior chamber depth based on a part of the ciliary body and the position of the corneal apex shown in one tomographic image. For example, the control unit 70 may obtain the postoperative anterior chamber depth based on a part of the ciliary body shown in the tomographic image and the tracking information.

DESCRIPTION OF SYMBOLS 1 Tomographic imaging apparatus 10 2nd fixation optical system 70 Control part 100 Measurement optical system 110 OCT system 120 Scanning system 130 Light guide system 140 Observation system 150 1st fixation optical system

Claims

A tomographic imaging apparatus for imaging a tomographic image of an eye to be examined,
Imaging means for imaging the anterior segment tomographic image of the eye to be examined from two or more different directions;
Arithmetic means for synthesizing a plurality of anterior segment tomographic images photographed from two or more different directions by the photographing means based on the positional relationship between the images;
A tomographic imaging apparatus comprising:
2. The tomographic imaging apparatus according to claim 1, wherein the calculation means acquires the structural information of the eye to be examined based on a composite image obtained by combining the plurality of anterior segment tomographic images.
The computing means calculates a postoperative predicted anterior chamber depth at which an intraocular lens is inserted based on the position of the corneal apex of the eye to be examined and the position of the ciliary body obtained from the structure information. The tomographic imaging apparatus according to claim 2.
The computing means calculates the postoperative predicted anterior chamber depth based on the position of the intersection of the normal of the corneal surface passing through the corneal apex and the plane including the ciliary protrusion in the composite image. The tomographic imaging apparatus according to claim 3.
The tomographic imaging apparatus according to any one of claims 2 to 4, wherein the computing means measures a ciliary groove distance based on the composite image.
6. The tomographic imaging apparatus according to claim 5, wherein the computing means determines the size of the posterior chamber type phakic intraocular lens based on the measured ciliary distance.
The tomographic imaging apparatus according to any one of claims 1 to 6, wherein the imaging unit images the eye to be examined from a front direction and a direction inclined at least one of right and left with respect to the front direction. .
8. The tomographic imaging apparatus according to claim 1, wherein the imaging unit images the eye to be examined from a front direction and a direction inclined by 25 ° to 30 ° with respect to the front direction.
The tomographic imaging apparatus according to any one of claims 1 to 8, wherein the calculation means performs noise reduction processing on the anterior segment tomographic image.
The imaging means captures a plurality of anterior segment tomographic images in each imaging direction,
10. The arithmetic means performs noise reduction of the anterior segment tomographic image by analyzing a statistic of signal intensity of a plurality of anterior segment tomographic images taken from the same direction. Tomographic imaging device.
The tomographic imaging apparatus according to any one of claims 2 to 10, wherein the calculation means corrects the composite image by performing a refractive correction in consideration of a boundary shape and a refractive index of a photographed object.
Further comprising a fixation guidance means for guiding fixation of the eye to be examined,
12. The tomographic image photographing apparatus according to claim 1, wherein the photographing unit photographs the anterior segment tomographic image from two or more different directions by guiding fixation of the eye to be examined. .
13. The tomographic imaging apparatus according to claim 12, wherein the fixation guidance means includes a presentation distance varying means for changing a presentation distance of the fixation target.
The calculating means is based on two or more anterior segment tomographic images photographed by the photographing means before and after the presenting distance of the fixation target is changed by the presenting distance varying means. The tomographic imaging apparatus according to claim 13, wherein a change in the shape of the eye to be inspected caused by a change in the tomography is detected.
An anterior ocular segment observation means for capturing an anterior ocular segment observation image of the eye to be examined;
15. The imaging apparatus according to claim 1, wherein the imaging unit captures the tomographic image of the anterior eye by tracking a characteristic part of the eye to be examined detected from the observation image of the anterior eye. Tomographic imaging device.
The imaging means captures an anterior ocular segment tomographic image of the eye to be examined by detecting an interference state between reflected light of the measurement light applied to the eye to be examined and reference light corresponding to the measurement light. The tomographic imaging apparatus according to any one of claims 1 to 15, further comprising one interference optical system.
17. The tomographic imaging apparatus according to claim 16, wherein the imaging unit includes a second interference optical system that captures an anterior ocular segment tomographic image of the eye to be examined from a direction different from the first interference optical system.
Further comprising a control means for controlling the photographing means,
18. The tomographic imaging apparatus according to claim 16, wherein the control unit changes a wavelength band of the measurement light when changing an imaging direction of the imaging unit with respect to the eye to be examined.
Further comprising a control means for controlling the photographing means,
The tomographic imaging apparatus according to claim 16 or 17, wherein the control means changes a polarization state of the measurement light when changing an imaging direction of the imaging means with respect to the eye to be examined.
Further comprising a control means for controlling the photographing means,
The control means changes at least one of a working distance between the imaging means and the eye to be examined and a condensing position of the imaging means when the imaging direction of the imaging means with respect to the eye to be examined is switched. The tomographic imaging apparatus according to any one of claims 1 to 19.
21. The tomographic imaging apparatus according to claim 1, wherein the imaging unit includes a Scheimpflug camera or an ultrasonic camera.
A tomographic imaging apparatus for imaging a tomographic image of an eye to be examined,
An imaging means for imaging an anterior ocular segment tomographic image from a direction inclined left or right with respect to the front direction of the eye to be examined;
Based on the structure information of the eye to be examined obtained from the anterior ocular segment tomographic image, calculation means for calculating a postoperative predicted anterior chamber depth into which an intraocular lens is inserted;
A tomographic imaging apparatus comprising: