Source: https://patents.google.com/patent/US7980696B1/en
Timestamp: 2019-02-18 03:17:57
Document Index: 99545144

Matched Legal Cases: ['art 61', 'art 23', 'art 23', 'art 23', 'art 23', 'art 23', 'art 23', 'art 23', 'art 23', 'art 23', 'art 70', 'art 70', 'art 23', 'art 70', 'art 70', 'art 70', 'art 70', 'art 61', 'art 61', 'art 64', 'art 70', 'art 70', 'art) 72', 'art 74', 'art 70', 'art 70', 'art 70', 'art 70', 'art 70', 'art 70', 'art 70', 'art 70', 'art 70', 'art 70', 'art 70', 'art 70', 'art 70', 'art 70']

US7980696B1 - Ophthalmic photographing apparatus - Google Patents
US7980696B1
US7980696B1 US13/009,940 US201113009940A US7980696B1 US 7980696 B1 US7980696 B1 US 7980696B1 US 201113009940 A US201113009940 A US 201113009940A US 7980696 B1 US7980696 B1 US 7980696B1
US13/009,940
US20110176111A1 (en
2010-01-21 Priority to JP2010011366A priority Critical patent/JP5545630B2/en
2010-01-21 Priority to JP2010-011366 priority
2010-01-21 Priority to JP2010011355A priority patent/JP5545629B2/en
2010-01-21 Priority to JP2010-011355 priority
2011-01-20 Assigned to NIDEK CO., LTD. reassignment NIDEK CO., LTD. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: ABE, YUKIO, Furuuchi, Yasuhiro, MURATA, TOSHIO, NAKANISHI, HIROYOSHI, TAKI, SEIJI
2011-07-19 Publication of US7980696B1 publication Critical patent/US7980696B1/en
2011-07-21 Publication of US20110176111A1 publication Critical patent/US20110176111A1/en
An ophthalmic photographing apparatus includes: an interference optical system including a splitter that splits light, emitted from a measurement light source, into measurement light and reference light, and synthesizing the measurement light reflected on an eye with the reference light to guide the synthesized light to a detector; a driving part that moves an optical member arranged in the optical path to adjust an optical-path difference between the measurement light and the reference light; an image obtaining part that obtains a tomographic image of a fundus or an anterior segment based on a light receiving signal output from the detector; and a driving control unit that controls driving of the driving part to locate the optical member in a predetermined position corresponding to either a photographing mode for photographing the tomographic image of the fundus or a photographing mode for photographing the tomographic image of the anterior segment.
This application is based on Japanese Patent Applications No. 2010-011355 and No. 2010-011366 filed with the Japan Patent Office on Jan. 21, 2010, the entire content of which is hereby incorporated by reference.
There is known an ophthalmic photographing apparatus (Optical Coherence Tomography: OCT) which has an interference optical system and photographs a tomographic image of a fundus. The interference optical system of this apparatus splits light emitted from a light source into measurement light and reference light. This interference optical system then guides the measurement light to a predetermined region of an examinee's eye, while guiding the reference light to a reference optical system. Subsequently, the interference optical system synthesizes the measurement light, reflected on the predetermined region of the examinee's eye, with the reference light, to obtain interference light, and thereafter makes a light receiving device receive this interference light. In such an apparatus, an optical member for changing an optical path length is moved in an optical-axis direction. This can adjust an optical-path difference between the measurement light and the reference light in accordance with a difference in ocular axial length (refer to JP-A-2008-29467).
It is to be noted that a dichroic mirror 40 is used as a light splitting member. The dichroic mirror 40 has a characteristic of reflecting measurement light (e.g., λ=about 840 nm) emitted from a measurement light source 27 provided in the OCT optical system 200, while being transmitted by laser light (light with a different wavelength from that of the light source 27, e.g., λ=about 780 nm) emitted from a light emitting part 61 provided in the SLO optical system 300. The dichroic mirror 40 makes a measurement optical axis L2 of the OCT optical system 200 and a measurement optical axis L1 of the SLO optical system 300 be the same axial.
The OCT light source 27 emits low coherent light. As the OCT light source 27, there is for example used a light source that emits light with a central wavelength of 840 nm and a band width of 50 nm (e.g., SLD light source). A fiber coupler 26 serves as a light splitting member as well as a light coupling member. The light emitted from the OCT light source 27 passes through an optical fiber 38 a as a guiding optical path, and is thereafter split by the coupler 26 into reference light and measurement light. The measurement light travels toward the eye E via an optical fiber 38 b, while the reference light travels toward a reference mirror 31 via an optical fiber 38 c.
In an optical path for emitting the measurement light toward the eye E, an end 39 b of the optical fiber 38 b, a collimator lens 22, a focusing lens 24 and a scanning part 23 are arranged. The focusing lens 24 is movable in the optical-axis direction in line with a refraction error of the eye E for adjustment of a focus on the fundus. The scanning part 23 is capable of scanning the fundus in XY directions with the measurement light. This scanning part 23 includes two galvanometer mirrors, and is operated by driving of a scanning driving mechanism 51. The dichroic mirror 40 and an objective lens 10 serve as a light guiding optical system for guiding OCT measurement light from the OCT optical system 200 to the fundus. It is to be noted that the scanning part 23 of the present embodiment arbitrarily adjusts a reflection angle of the measurement light by means of the two galvanometer mirrors. Hence a direction of scanning by means of the measurement light on the fundus is arbitrarily set. A tomographic image in an arbitrary area of the fundus is thus obtained. It is to be noted that the end 39 b of the optical fiber 38 b is arranged in a position conjugate with the fundus of the eye E. Further, the two galvanometer mirrors of the scanning part 23 are arranged in a position substantially conjugate with a pupil of the eye E.
The measurement light emitted from the end 39 b of the optical fiber 38 b is collimated by the collimator lens 22, and thereafter reaches the scanning part 23 via the focusing lens 24. In this scanning part 23, the two galvanometer mirrors are driven, to change a reflecting direction of the measurement light. The measurement light reflected on the scanning part 23 is reflected on the dichroic mirror 40, and thereafter collected in the fundus via a dichroic mirror 91 and the objective lens 10.
The measurement light reflected on the fundus passes through the objective lens 10 and the dichroic mirror 91, and is thereafter reflected on the dichroic mirror 40, to travel toward the OCT optical system 200. Further, the measurement light is incident on the end 39 b of the optical fiber 38 b via the two galvanometer mirrors of the scanning part 23, the focusing lens 24 and the collimator lens 22. The measurement light incident on the end 39 b reaches an end 84 a of an optical fiber 38 d via the optical fiber 38 b, the fiber coupler 26 and the optical fiber 38 d.
Meanwhile, in an optical path for emitting reference light toward the reference mirror 31 (reference optical path), an end 39 c of the optical fiber 38 c, a collimator lens 29 and the reference mirror 31 are arranged. The reference mirror 31 is configured to be movable in the optical-axis direction by a reference mirror driving mechanism 50. This allows the reference mirror 31 to change an optical path length of the reference light.
The reference light emitted from the end 39 c of the optical fiber 38 c is made to be a parallel light flux by the collimator lens 29 and reflected on the reference mirror 31, and is thereafter collected by the collimator lens 29, to be incident on the end 39 c of the optical fiber 38 c. The reference light incident on the end 39 c reaches the coupler 26 via the optical fiber 38 c.
The reference light generated as described above and the fundus reflected light obtained by reflection of the measurement light on the fundus are synthesized in the coupler 26, to become interference light. The interference light is emitted from the end 84 a through the optical fiber 38 d.
The light emitted from the end 84 a is made to be parallel light in the collimator lens 80, and thereafter split in the grating 81 into each frequency component (each wavelength component). The split light is then collected on the light receiving surface of the light receiving device 83 via the condenser lens 82. Thereby, spectrum information with interference fringes is recorded in the light receiving device 83. The spectrum information (light receiving signal) is then input into a control part 70. The control part 70 can analyze the spectrum information by use of Fourier transformation, to measure information (A-scan signal) in the depth direction of the eye. Using the scanning part 23, the control part 70 can scan the fundus in a predetermined transverse direction with the measurement light, to obtain a tomographic image. For example, the control part 70 can scan the fundus in the X-direction or the Y-direction with the measurement light, to obtain a tomographic image in an X-Z plane or a Y-Z plane (it is to be noted that in the present embodiment, such a method for one-dimensionally scanning the fundus with the measurement light to obtain a tomographic image is referred to as B-scan). In addition, the obtained tomographic image is stored in a memory 72 connected to the control part 70. Further, the control part 70 can two-dimensionally scan the fundus in the XY directions with the measurement light, to obtain a three-dimensional image of the fundus.
The light emitting part 61 has a first light source (SLO light source) 61 a, a second light source (fixation optical system) 61 b, a mirror 69, and a dichroic mirror 101. The first light source 61 a emits light with a wavelength in the infrared region (e.g., λ=780 nm), and the second light source 61 b emits light with a wavelength in a visible region (e.g., λ=630 nm). It is to be noted that as the first light source 61 a and the second light source 61 b, a light source is used which emits light with high luminance and high directivity (such as a laser diode light source or an SLD light source). Infrared light emitted from the first light source 61 a passes through the dichroic mirror 101, and travels to a beam splitter 62 through a collimator lens 65. Visible light emitted from the second light source 61 b is bent by the mirror 69, and thereafter reflected on the dichroic minor 101. This visible light then travels along the same axis as that of the infrared light emitted from the first light source 61 a. The first light source 61 a is used for obtaining a fundus front image for observation. Meanwhile, the second light source 61 b is used for guiding the sight direction of the eye.
Herein, laser light (measurement light or fixation light) emitted from the light emitting part 61 transmits the beam splitter 62 via the collimator lens 65, and thereafter passes through the focusing lens 63. Subsequently, this laser light reaches the scanning part 64. By driving of the galvanometer mirror and the polygon mirror, the reflecting direction of this laser light is changed. The reflected laser light transmits the dichroic mirror 40, and is thereafter collected in the fundus via the dichroic minor 91 and the objective lens 10.
FIG. 5 is an optical side view explaining an internal configuration of the adaptor 500. The adaptor 500 has a lens system 510 and a flat plate 515. The lens system 510 serves to shift the focal position to the apparatus side so as to be located on the anterior segment. The flat plate 515 is formed with a mirror surface (light reflective member) 515 a for detecting the mounted state (refer to front view of FIG. 6).
It is to be noted that in the present embodiment, in the case of photographing the anterior-segment tomographic image, the focusing lens 24 is moved to a predetermined position in a plus-diopter direction (e.g., position of +10D). Thereby, the focal position of the measurement light emitted from the OCT optical system 200 is moved to the apparatus side. That is, mounting of the adaptor 500 and positional adjustment of the focusing lens 24 to the foregoing plus side bring the apparatus into the state of being capable of adjusting the focus of the measurement light on the anterior segment. It is to be noted that at the time of photographing, focusing on the anterior segment is performed after the working distance (front-back distance) of the apparatus to the eye E has been adjusted.
It is to be noted that the control part 70 is connected to the display monitor 75, and controls a display image thereof. Further, the control part 70 is connected with a memory (storing part) 72, an operating part 74 for performing a variety of operations, the scanning driving mechanism 51, the scanning driving mechanism 52, the reference mirror driving mechanism 50, a first driving mechanism 63 a for moving the focusing lens 63 in the optical-axis direction, a second driving mechanism 24 a for moving the focusing lens 24 in the optical-axis direction, and the like. It is to be noted that as the monitor 75, two monitors, i.e., a monitor for alignment observation and a monitor for photographed image observation, may be used or one shared monitor may naturally be used.
In the ophthalmic photographing apparatus of the present embodiment, at least two among the infrared light sources 151 each serve also as a light source for detection which emits a detection light flux toward the mirror surface 515 a. Further, the photographing device 97 also serves as a light receiving device for detection which receives a reflection light flux from the mirror surface 515 a. The control part 70 determines the mounted state of the adaptor 500 based on the light receiving signal output from the photographing device 97.
FIG. 7 is a view explaining a function of the mirror surface 515 a provided in the adaptor 500. In the case of the adaptor 500 being mounted, light emitted from two light sources arranged diagonally downward right and diagonally downward left, among the infrared light sources 151, pass through an opening (hole) 517 formed in the adaptor 500, and are reflected by the two mirror surfaces 515 a. The reflected light passes through part of the lens system 510 and the objective lens 10, and is reflected by the dichroic mirror 91. Thereafter, the light is received by the two-dimensional photographing device 97 via the image forming lens 95. This leads to formation of rasters (reflected images) KR and KL (detection signal, mode switching signal) on the photographing device 97 by means of the two mirror surfaces 515 a.
In the case of the adaptor 500 being properly mounted, as shown in FIG. 8A, the rasters KR and KL are both detected in predetermined positions inside the frames FR and FL. In the case of the adaptor 500 being mounted in a slanted state, the mirror surface 515 a is slanted with respect to a proper position. For this reason, as shown in FIG. 8B, at least either the raster KR or KL is detected in a position off the foregoing predetermined position, though inside the frame FR or FL. In the case of the adaptor 500 being not mounted, as shown in FIG. 8C, the rasters KR and KL are both detected in positions off the frames FR and FL (or detected nowhere).
It is to be noted that an installation position and a reflection angle of the mirror surface 515 a are preferably set such that the rasters KR and KL at the time of the adaptor 500 being mounted are formed on the ends of the photographing surface of the photographing device 97. This is for preventing erroneous detection of a cornea raster formed by the infrared light source 151 as the rasters KR and KL. On top of this, the sizes of the rasters KR and KL are preferably set so as to be larger than the cornea raster formed by the infrared light source 151. This can avoid the erroneous detection in the image processing. Further, the shape of the mirror surface 515 a is not limited to circular, but may be linear, rectangular, or the like.
Further, in the above configuration, the lens system 510 of the adaptor 500 may be a zooming optical system capable of changing a photographing scaling factor. Moreover, in the case of the mirror surface 515 a as described above being provided in the adaptor 500 having the zooming optical system, the detected positions of the rasters KR and KL on the photographing device 97 are moved in accordance with a change in zoom scaling factor. Therefore, the control part 70 may determine whether or not the zoom scaling factor to be changed is proper based on the positions of the rasters KR and KL.
Next, an overall operation of the present apparatus will be described. The control part 70 controls driving of the OCT optical system 200 and the SLO optical system 300, to obtain an OCT image or a front image (SLO image). The control part 70 then occasionally updates the OCT image and the front image on the monitor 75 (refer to FIGS. 10 and 11)<
Next, the second photographing mode will be described. In the case of executing the second photographing mode, the examiner mounts the adaptor 500 in the inspection window 160. The control part 70 determines the properness of the mounted state of the adaptor 500 as described above. When determining that mounting is proper, the control part 70 switches the photographing mode from the first photographing mode (fundus photographing mode) to the second photographing mode (anterior-segment photographing mode). That is, the control part 70 outputs driving command signals, corresponding to the second photographing mode for controlling driving of the driving mechanism 50, the first driving mechanism 63 a and the second driving mechanism 24 a, to these mechanisms. Thereby, the driving mechanism 50, the first driving mechanism 63 a and the second driving mechanism 24 a bring the optical arrangements of the OCT optical system 200 and the SLO optical system 300 to predetermined arrangements corresponding to the second photographing mode. That is, the positions of the respective optical members are automatically adjusted.
It is to be noted that in the above description, the optical path length of the reference light is changed for adjusting the optical-path difference between the measurement light and the reference light. However, this is not restrictive, and the optical path length of the measurement light may be changed. For example, the collimator lens 22 and the end of the optical fiber 39 b may be moved in the optical-axis direction.
Concerning the OCT optical system 200, the control part 70 controls driving of the second driving mechanism 24 a, to locate the focusing lens 24 in the predetermined position corresponding to the second photographing mode. When the focusing lens 24 reaches the predetermined position, the control part 70 stops and prohibits driving of the second driving mechanism 24 a.
Further, concerning the SLO optical system 300, the control part 70 controls driving of the first driving mechanism 63 a, and moves the focusing lens 63 to the predetermined position corresponding to the second photographing mode in a similar manner to the OCT optical system 200. It is to be noted that the technique for setting the movement position of the focusing lens 63 is similar to the case of the OCT optical system 200 above, and the description thereof is thus omitted.
Subsequently, the control part 70 selectably displays respective scanning patterns for anterior-segment photographing (e.g., cornea line scan, cornea cross scan, and corner line scan), prepared in plurality in accordance with photographed regions. Further, the control part 70 switches the display unit of the scanning range from an angle-of-view unit (e.g., 40°) to a distance unit (e.g., 6.0 mm). Moreover, the control part 70 makes a display indicating prohibition of the movement of the respective focusing lenses 24 and 63, while prohibiting driving of the first driving mechanism 63 a and the second driving mechanism 24 a, to actually prohibit movement of each of the lenses. This can fix the positions of the lenses 24 and 63 to the predetermined positions.
In the case of switching the photographing mode to the first photographing mode, the control part 70 outputs driving command signals, corresponding to the first photographing mode for controlling driving of the driving mechanism 50, the first driving mechanism 63 a and the second driving mechanism 24 a, to these mechanisms. Thereby, the driving mechanism 50, the first driving mechanism 63 a and the second driving mechanism 24 a bring the optical arrangements of the OCT optical system 200 and the SLO optical system 300 to arrangements corresponding to the first photographing mode. That is, the positions of the respective optical members are automatically adjusted. With this adjustment, the reference mirror 31 and the respective focusing lenses 24 and 63 are moved to predetermined original point positions.
1. An ophthalmic photographing apparatus for photographing a tomographic image of an eye, comprising:
2. The ophthalmic photographing apparatus according to claim 1, wherein the predetermined position is a position where the anterior-segment tomographic image is obtainable by the image obtaining part in the state that a distance between the eye and the apparatus has been adjusted so as to focus the measurement light to the anterior segment.
3. The ophthalmic photographing apparatus according to claim 1, further comprising:
a second driving part that moves, in the optical-axis direction, a focusing lens arranged in the measurement optical path for adjusting a focus on the fundus,
4. The ophthalmic photographing apparatus according to claim 1, wherein the interference optical system is one of a spectral domain OCT optical system and a swept source OCT optical system.
5. The ophthalmic photographing apparatus according to claim 1, wherein the interference optical system comprises an optical scanner that is arranged in the measurement optical path and scans the eye with the measurement light.
6. The ophthalmic photographing apparatus according to claim 1, further comprising:
an inspection window that can be mounted with an adaptor having a lens system for moving a focal position of the measurement light from the fundus to the anterior segment.
7. The ophthalmic photographing apparatus according to claim 6, wherein the predetermined position is a position where it is possible to avoid obtainment of a tomographic image of the lens system by light obtained by synthesizing the reflected light, which is obtained by reflection of the measurement light on the lens system, with the reference light.
8. The ophthalmic photographing apparatus according to claim 6, further comprising:
a sensor for detecting a mounted state of the adaptor in the inspection window; and
an alarm that notifies a result of detection made by the sensor.
9. The ophthalmic photographing apparatus according to claim 8, wherein the sensor detects whether or not the adaptor is properly mounted in the inspection window.
10. The ophthalmic photographing apparatus according to claim 8, wherein
the adaptor is provided with an optical reflector,
the sensor has a detection light source that emits detection light toward the optical reflector, and a detection light receiving device that receives reflected light from the optical reflector, and
11. The ophthalmic photographing apparatus according to claim 10, further comprising:
an anterior-segment observing optical system that has a two-dimensional light receiving device for observing an anterior-segment image of an examinee's eye,
12. The ophthalmic photographing apparatus according to claim 11, further comprising:
an anterior-segment light source for projecting an alignment target to the anterior segment or illuminating the anterior segment,
13. The ophthalmic photographing apparatus according to claim 11, wherein the sensor detects a reflected image obtained by reflection of the detection light on the optical reflector based on the light receiving signal output from the two-dimensional light receiving device, and determines whether or not the adaptor is properly mounted based on whether or not a position of the detected reflected image is a predetermined position.
14. The ophthalmic photographing apparatus according to claim 8, wherein the driving control unit switches the photographing mode from the fundus photographing mode to the anterior segment photographing mode based on a detection signal output from the sensor.
US13/009,940 2010-01-21 2011-01-20 Ophthalmic photographing apparatus Active US7980696B1 (en)
JP2010011366A JP5545630B2 (en) 2010-01-21 2010-01-21 Ophthalmic imaging apparatus
JP2010-011366 2010-01-21
JP2010011355A JP5545629B2 (en) 2010-01-21 2010-01-21 Ophthalmic imaging apparatus
JP2010-011355 2010-01-21
US7980696B1 true US7980696B1 (en) 2011-07-19
US20110176111A1 US20110176111A1 (en) 2011-07-21
US13/009,940 Active US7980696B1 (en) 2010-01-21 2011-01-20 Ophthalmic photographing apparatus
US20110051087A1 (en) * 2009-09-01 2011-03-03 Canon Kabushiki Kaisha Fundus camera
CN103222849A (en) * 2012-01-26 2013-07-31 佳能株式会社 Ophthalmologic apparatus, and control method therefore
CN103251376A (en) * 2012-02-15 2013-08-21 佳能株式会社 Ophthalmic apparatus and method for controlling ophthalmic apparatus
US20130258282A1 (en) * 2012-03-30 2013-10-03 Canon Kabushiki Kaisha Ophthalmologic apparatus
CN103356161A (en) * 2012-03-30 2013-10-23 佳能株式会社 Optical coherence tomography imaging apparatus and method for controlling the same
US20130286348A1 (en) * 2012-04-03 2013-10-31 Canon Kabushiki Kaisha Optical coherence tomography apparatus, control method, and program
US20140016095A1 (en) * 2011-03-31 2014-01-16 Canon Kabushiki Kaisha Ophthalmologic apparatus
US20140063507A1 (en) * 2012-08-30 2014-03-06 Canon Kabushiki Kaisha Optical coherence tomographic imaging apparatus and control method thereof
CN103767677A (en) * 2012-10-17 2014-05-07 佳能株式会社 Ophthalmologic imaging method and imaging apparatus
US20140132919A1 (en) * 2012-11-09 2014-05-15 Canon Kabushiki Kaisha Ophthalmologic photographing apparatus
CN103799962A (en) * 2012-11-01 2014-05-21 佳能株式会社 Ophthalmic apparatus, imaging control apparatus, and imaging control method
US20140192323A1 (en) * 2011-03-31 2014-07-10 The Yoshida Dental Mfg. Co., Ltd. Control device, control method and control program for optical coherence tomographic image-generating apparatuses
US9125598B2 (en) 2012-04-03 2015-09-08 Canon Kabushiki Kaisha Optical coherence tomography apparatus, control method, and computer-readable storage medium
US10076243B2 (en) 2015-05-01 2018-09-18 Nidek Co., Ltd. Ophthalmic imaging device
DE3335386A1 (en) * 1983-09-29 1985-04-11 Siemens Ag Circuit for CSD coding of a number represented in two's complement binary
JP6007527B2 (en) * 2012-03-13 2016-10-12 株式会社ニデック Fundus imaging apparatus
JP6007549B2 (en) * 2012-03-30 2016-10-12 株式会社ニデック Fundus imaging apparatus
JP6224910B2 (en) * 2013-04-17 2017-11-01 キヤノン株式会社 Ophthalmic imaging apparatus, a control method, and program
CN104337498B (en) 2013-08-07 2016-08-31 卡尔蔡司医疗技术公司 Optical coherence tomography
JP6277748B2 (en) * 2014-02-03 2018-02-14 株式会社ニデック Fundus imaging apparatus and a wide-angle lens attachment
JP2016123467A (en) * 2014-12-26 2016-07-11 株式会社ニデック Fundus oculus photographing apparatus and wide-angle lens attachment
US20100014089A1 (en) 2008-07-04 2010-01-21 Nidek Co., Ltd. Optical tomographic image photographing apparatus
JP3870211B2 (en) * 2004-12-28 2007-01-17 キヤノン株式会社 Fundus camera
EP2359743B1 (en) * 2007-07-24 2012-12-05 SIS AG, Surgical Instrument Systems Ophthalmologic measuring device and measuring method
JP4659858B2 (en) 2008-06-30 2011-03-30 シャープ株式会社 Image forming apparatus, a program, and a recording medium
US8147064B2 (en) * 2009-09-01 2012-04-03 Canon Kabushiki Kaisha Fundus camera
US9565999B2 (en) * 2011-03-31 2017-02-14 Canon Kabushiki Kaisha Ophthalmologic apparatus
US9084562B2 (en) * 2011-03-31 2015-07-21 The Yoshida Dental Mfg. Co., Ltd. Control device, control method and control program for optical coherence tomographic image-generating apparatuses
CN103222849B (en) * 2012-01-26 2015-11-18 佳能株式会社 The ophthalmic apparatus and a control method
CN103222852B (en) * 2012-01-26 2015-09-23 佳能株式会社 Optical coherence tomographic imaging apparatus
US9398850B2 (en) 2012-02-15 2016-07-26 Canon Kabushiki Kaisha Ophthalmic apparatus, method for controlling ophthalmic apparatus, and storage medium
CN103251376B (en) * 2012-02-15 2016-03-30 佳能株式会社 The ophthalmic apparatus and a method for controlling an ophthalmic device
CN103356161B (en) * 2012-03-30 2016-08-03 佳能株式会社 Optical coherence tomography apparatus and a control method
US9186057B2 (en) * 2012-08-30 2015-11-17 Canon Kabushiki Kaisha Optical coherence tomographic imaging apparatus and control method thereof
US9615741B2 (en) 2012-10-17 2017-04-11 Canon Kabushiki Kaisha Ophthalmologic imaging method, imaging apparatus, and non-transitory tangible medium
EP2347701A1 (en) 2011-07-27
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:TAKI, SEIJI;ABE, YUKIO;NAKANISHI, HIROYOSHI;AND OTHERS;REEL/FRAME:025665/0508