Office Action 1: Non-Final Rejection (2024-11-15)
Rejection types: 103 - Obviousness, 112 - Written Description/Enablement

CLAIMS:
Claims

1\. An apparatus suitable for optical coherence tomography, OCT, scanning comprising:means for providing a first signal;
means for providing a reference signal;
a photonics integrated circuit comprising (i) means for receiving a reflected first signal, reflected from a subject;
(ii) means for coupling the reflected first signal to the reference signal to provide an interference signal, and
(iii) a variable delay for varying an optical path length of one of the reference signal and the first signal to match the optical path length of the reference signal to an optical path length of the reflected first signal, wherein the variable delay comprises at least one binary switch for selecting between paths of different lengths; and means for analyzing the interference signal.

2\. The apparatus of claim 1, wherein the variable delay comprises a series of binary switches and path elements of different selectable lengths.

3\. The apparatus of claim 2, wherein the path elements are of length L, 2L, etc. up to 2NL,
where N is an integer.
4\. The apparatus of claim 3, wherein the variable delay is a binary delay implementing a delay,SVG {EMBED HERE} 0.1570.217
in steps of L, of 0 to (2x2NL.

5\. The apparatus of claim 2, 3 or 4, wherein the variable delay has N delay path elements and
N+1 binary switches, one binary switch before each delay path element, to selectively switch between a direct path or the delay path element, and one binary switch at the output to selectively switch from the direct path or the final delay path element to an output of the variable delay.

6\. The apparatus of any one of claims 2 to 5, wherein the switches are two-way multiplexing or
demultiplexing switches.

7\. The apparatus of any one of the preceding claims, wherein the variable delay acts on the reference signal.

8\. The apparatus of any one of the preceding claims, wherein one of the paths of different lengths includes a tunable labyrinth with integrated phase shifter.

9\. The apparatus of any one claims 1 to 8, wherein the means for providing the first signal is a broadband light source and the means for analyzing the interference signal is a spectrometer.

10\. The apparatus of claim 9, wherein the spectrometer is implemented as one of an arrayed waveguide grating, AWG, a ring bus, a ring fan-out, a binary asymmetric Mach-Zehnder interferometer, AMZI, or an AMZI fan out.

11\. The apparatus of any one of claims 1 to 8, wherein the means for providing the first signal is a swept laser source and the means for analyzing the interference signal is a point photodetector.

12\. The apparatus of any one of the preceding claims, wherein the means for providing the reference signal is a beam-splitter, wherein the beam-splitter beam-splits the first signal.

13\. The apparatus of any one of the preceding claims, wherein the means for coupling is a 2 x 2 coupler, wherein the 2 x 2 coupler is one of a directional coupler, a multimode interferometer or a Mach-Zender interferometer.

14\. The apparatus of any one of the preceding claims, wherein the photonic integrated circuit comprises a first path for guiding the first signal to a set of imaging optics to the subject and for guiding reflected light from the subject back from through the set of imaging optics to the means for coupling and a second path for guiding the reference signal to a reflector and back to the means for coupling.

15\. The apparatus of claim 14, wherein the first and second paths comprise polarization- maintaining fibres for maintaining polarization of the first signal and the reference signal
respectively.

16\. The apparatus of any one of the preceding claims, wherein the means for remote viewing of the analyzed interference signal is an output image processor and the means for remote control of the variable delay is an on-chip control unit.

17\. A method suitable for performing an optical coherence tomography, OCT, scan comprising:providing a first signal provided by a light source;
providing a reference signal;
reflecting the first signal from a subject and coupling the reflected first signal to the reference signal to provide an interference signal;
adjusting a delay of one of the reference signal and the first signal by a variable delay to match an optical path length of the reference signal to an optical path length of the reflected first signal, wherein the step of adjusting comprises selecting between paths of different
lengths; andanalyzing the interference signal.

18\. The method of claim 17, comprising automatically selecting between the paths of different lengths until an interference peak is identified in the interference signal.

19\. The method of claim 18, comprising performing image recognition on the interference signal to identify the interference peak. 5 10 15 20 25 30 35

OFFICE ACTION:
DETAILED ACTION
Notice of Pre-AIA  or AIA  Status
The present application, filed on or after March 16, 2013, is being examined under the first inventor to file provisions of the AIA .
Claim Rejections - 35 USC § 112
The following is a quotation of 35 U.S.C. 112(b):
(b)  CONCLUSION.—The specification shall conclude with one or more claims particularly pointing out and distinctly claiming the subject matter which the inventor or a joint inventor regards as the invention.
The following is a quotation of 35 U.S.C. 112 (pre-AIA ), second paragraph:
The specification shall conclude with one or more claims particularly pointing out and distinctly claiming the subject matter which the applicant regards as his invention.
Claims 1, 4-19 are rejected under 35 U.S.C. 112(b) or 35 U.S.C. 112 (pre-AIA ), second paragraph, as being indefinite for failing to particularly point out and distinctly claim the subject matter which the inventor or a joint inventor (or for applications subject to pre-AIA  35 U.S.C. 112, the applicant), regards as the invention.
Claim 14 recites the limitation the reflected first signal.  There is insufficient antecedent basis for this limitation in the claim.
Claim 16 recites the limitation the analyzed interference signal.  There is insufficient antecedent basis for this limitation in the claim.
Claim 17 recites the limitation the path elements.  There is insufficient antecedent basis for this limitation in the claim.
Claim 18 recites the limitation the reflected first signal.  There is insufficient antecedent basis for this limitation in the claim.  Claim 19 is rejected for the same reasons because they depend on claim 18.
Regarding claim 1, the phrase etc. renders the claim(s) indefinite because the claim(s) include(s) elements not actually disclosed (those encompassed by etc.), thereby rendering the scope of the claim(s) unascertainable.  See MPEP § 2173.05(d).
Claims 4-16 are rejected for the same reasons because they depend on claim 1.
Regarding claim 17, the phrase etc. renders the claim(s) indefinite because the claim(s) include(s) elements not actually disclosed (those encompassed by etc.), thereby rendering the scope of the claim(s) unascertainable.  See MPEP § 2173.05(d).
Claim Rejections - 35 USC § 103
In the event the determination of the status of the application as subject to AIA  35 U.S.C. 102 and 103 (or as subject to pre-AIA  35 U.S.C. 102 and 103) is incorrect, any correction of the statutory basis (i.e., changing from AIA  to pre-AIA ) for the rejection will not be considered a new ground of rejection if the prior art relied upon, and the rationale supporting the rejection, would be the same under either status.
The following is a quotation of 35 U.S.C. 103 which forms the basis for all obviousness rejections set forth in this Office action:
A patent for a claimed invention may not be obtained, notwithstanding that the claimed invention is not identically disclosed as set forth in section 102, if the differences between the claimed invention and the prior art are such that the claimed invention as a whole would have been obvious before the effective filing date of the claimed invention to a person having ordinary skill in the art to which the claimed invention pertains. Patentability shall not be negated by the manner in which the invention was made.
Claim(s) 1, 4-5, 7-9, 12-17 are rejected under 35 U.S.C. 103 as being unpatentable over Swanson et al (Pub. No.:  US 2014/0376000) in view of Hu et al (Pub. No.:  US 2017/0227399).
Regarding claims 1, 4-5, 7-9, 12-15, Swanson et al disclose an apparatus suitable for optical coherence tomography scanning of a subject, the apparatus comprising:
at least one source for providing a first signal and a reference signal [see claims 1, 12] by disclosing a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal [se claim 1];
a photonics integrated circuit [see claim 12, 0006] comprising:
a first path (sample path) for receiving a reflected first signal, reflected from the subject [see claim 12, fig 2] by disclosing a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal [see claim 12];
a second path for coupling the reflected first signal to the reference signal (from the reference path) to provide an interference signal [see claim 12, fig 2] by disclosing a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal [see claim 12];
a variable delay (via an on-chip path delay unit, 0065) for varying an optical path length of one of the reference signal and the first signal to match the optical path length of the reference signal to an optical path length of the reflected first signal [see 0014, 0044, 0065, 0074-0075, 0093, figs 6, 8, 15];
a detector for analyzing and detecting the interference signal [see claim 12, 0006, 0044 and figs 2, 18-22] by disclosing a detection system that detects the interference signal from which a ranging or longitudinal reflectance imaging of a sample positioned in the sample arm may be generated [see claim 12].
Swanson et al don’t mention path elements of L, 2L, etc. up to 2NL, where N is an integer and wherein the variable delay is a binary delay implementing a delay, in steps of L, of 0 to (2x2N-1)L.
Nonetheless, Hu et al disclose a series of binary switches path elements of L, 2L, etc. up to 2NL, where N is an integer and wherein the variable delay is a binary delay implementing a delay, in steps of L, of 0 to (2x2N-1)L [see claims 2-7, 0087-0094, abstract, 0008, 0023, 0029, 0037] by disclosing a cascade of optical switches to increase the tuning range (also referred to as the dynamic range) of optical path length differences and increasing the optical path length differences can increase the resolution of the spectrometer [see 0043].
Therefore, it is obvious to one skilled in the art at the time the invention was filed and would have been motivated to combine Swanson et al and Hu et al by using a series of binary switches path elements of L, 2L, etc. up to 2NL, where N is an integer and wherein the variable delay is a binary delay implementing a delay, in steps of L, of 0 to (2x2N-1)L; a cascade of optical switches to increase the tuning range (also referred to as the dynamic range) of optical path length differences and increasing the optical path length differences can increase the resolution of the spectrometer [see 0043].
Regarding claim 5, Swanson et al don’t disclose wherein the variable delay has N delay path elements and N+1 binary switches, one binary switch before each delay path element, to selectively switch between a direct path or the delay path element, one binary switch at the output to selectively switch from the direct path or a final delay path element to an output of the variable delay.
Nonetheless, Hu et al disclose wherein the variable delay has N delay path elements and N+1 binary switches, one binary switch before each delay path element, to selectively switch between a direct path or the delay path element, one binary switch at the output to selectively switch from the direct path or a final delay path element to an output of the variable delay [see claims 2-7, 0087-0094, abstract, 0008, 0023, 0029, 0037] by disclosing a cascade of optical switches to increase the tuning range (also referred to as the dynamic range) of optical path length differences and increasing the optical path length differences can increase the resolution of the spectrometer [see 0043].
Therefore, it is obvious to one skilled in the art at the time the invention was filed and would have been motivated to combine Swanson et al and Hu et al by using variable delay has N delay path elements and N+1 binary switches, one binary switch before each delay path element, to selectively switch between a direct path or the delay path element, one binary switch at the output to selectively switch from the direct path or a final delay path element to an output of the variable delay; a cascade of optical switches to increase the tuning range (also referred to as the dynamic range) of optical path length differences and increasing the optical path length differences can increase the resolution of the spectrometer [see 0043].
Regarding claim 7, Swanson et al disclose wherein the variable delay acts as on the reference signal [see 0014, 0044, 0065, 0074-0075, 0093, figs 6, 8, 15].
Regarding claim 8, Swanson et al disclose wherein one of the paths of different lengths includes a tunable labyrinth with integrated phase shifter [see 0081, 0115-0116, 0120, 0127].
Regarding claim 9, Swanson et al disclose wherein the at least one source comprises a broadband light source and the detector for analyzing and detecting the interference signal comprises a spectrometer [see 0042] by disclosing interferometric electro-optical detection, for example, ranging, medical imaging, non-destructive evaluation and testing, laser radar, spectroscopy [see 0042].
Regarding claim 12, Swanson et al disclose wherein the at least one source comprises a beam-splitter, and wherein the beam-splitter beam-splits the first signal [see 0119, 0131].
Regarding claim 13, Swanson et al disclose wherein the second path is a 2 x 2 coupler, and wherein the 2 x 2 coupler is one of a directional coupler [see 0123], a multimode interferometer [see 0120] or a Mach-Zender interferometer [see 0125].
Regarding claim 14, Swanson et al disclose wherein the photonic integrated circuit comprises:
a first path for guiding the first signal to a set of imaging optics to the subject and for guiding reflected light from the subject back through the set of imaging optics to the second path for coupling the reflected first signal to the reference signal to provide an interference signal [see claims 1, 12] by disclosing a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal [se claim 1];
a second path for guiding the reference signal to a reflector and back to the second path for coupling the reflected first signal to the reference signal to provide an interference signal [see claims 1, 12] by disclosing a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal [se claim 1].
Regarding claim 15, Swanson et al disclose wherein the first and second paths comprise polarization-maintaining fibers for maintaining polarization of the first signal and the reference signal respectively [see 0070, 0077] by disclosing both polarization (states) signals in the fiber maintain the same polarization in the PIC [see 0070].
Regarding claim 16, Swanson et al disclose an output image processor for remote viewing of the analyzed interference signal processor and the an on-chip control unit for remote control of the variable delay [see 0065].
Regarding claim 17, Swanson et al disclose method suitable for performing an optical coherence tomography scan, the method comprising:
providing a first signal provided by a light source [see claims 1, 12] by disclosing a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal [se claim 1];
providing a reference signal [see claims 1, 12];
reflecting the first signal from a subject and coupling the reflected first signal to the reference signal to provide an interference signal [see claims 1, 12] by disclosing a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal [se claim 1];
adjusting a delay of one of the reference signal and the first signal by a variable delay to match an optical path length of the reference signal to an optical path length of the reflected first signal [see 0075, 0096, 0109, 0116],
wherein the step of adjusting comprises selecting between paths of different lengths [see 0093, 0127, 0131] by disclosing various phase shifters are for adjusting optical path lengths [see 0131];
analyzing the interference signal [see claim 12, 0006, 0044 and figs 2, 18-22] by disclosing a detection system that detects the interference signal from which a ranging or longitudinal reflectance imaging of a sample positioned in the sample arm may be generated [see claim 12].
Swanson et al don’t disclose a series of binary switches and path elements of different selectable lengths and wherein the path elements are of length L, 2L, etc. up to 2NL, where N is an integer.
Therefore, it is obvious to one skilled in the art at the time the invention was filed and would have been motivated to combine Swanson et al and Hu et al by using variable delay has N delay path elements and N+1 binary switches, one binary switch before each delay path element, to selectively switch between a direct path or the delay path element, one binary switch at the output to selectively switch from the direct path or a final delay path element to an output of the variable delay; a cascade of optical switches to increase the tuning range (also referred to as the dynamic range) of optical path length differences and increasing the optical path length differences can increase the resolution of the spectrometer [see 0043].
Claim 6 is rejected under 35 U.S.C. 103 as being unpatentable over Swanson et al (Pub. No.:  US 2014/0376000) in view of Gerstel et al (Pub. No.:  US 2007/0237524).
Regarding claim 6, Swanson et al don’t disclose wherein the switches are two-way multiplexing or demultiplexing switches.
Nonetheless, Gerstel et al disclose wherein the switches are two-way multiplexing or demultiplexing switches [see 0039].
Therefore, it is obvious to one skilled in the art at the time the invention was filed and would have been motivated to combine Swanson et al and Gerstel et al by using two-way multiplexing or demultiplexing switches; switched multiplexer 64 and demultiplexer 63 can be used for higher value services, such as channels requiring optical protection [see 0039].
Claim 10 is rejected under 35 U.S.C. 103 as being unpatentable over Swanson et al (Pub. No.:  US 2014/0376000) in view of Garcia et al (Pub. No.:  US 2017/0366880)
Regarding claim 10, Swanson et al disclose wherein the spectrometer is implemented as one of an arrayed waveguide grating, AWG, a ring bus, a ring fan-out, a binary asymmetric Mach-Zehnder interferometer or an AMZI fan out [see 0123, 0125].
Swanson et al don’t explicitly mention Mach-Zehnder interferometer is asymmetric.
Nonetheless, Garcia et al disclose an asymmetric Mach-Zehnder interferometer configured to selectively switch the multi-wavelength light signal between an output channel and a loopback path [see claim 19, 0026].
Therefore, it is obvious to one skilled in the art at the time the invention was filed and would have been motivated to combine Swanson et al and Isogai et al by using an asymmetric Mach-Zehnder interferometer; Mach–Zehnder interferometers exhibit salient merits of high sensitivity, a high degree of integration, simplicity, and compact in-line measurement, with wealthy physical mechanisms for applications ranging from waveguide, routing, filtering.
Claim 11 is rejected under 35 U.S.C. 103 as being unpatentable over Swanson et al (Pub. No.:  US 2014/0376000) as applied to claim 1 above and further in view of Isogai et al (Pub. No.:  US 2017/0238798)
Regarding claim 11, Swanson et al disclose wherein the at least one source a swept laser source [see 0135].
Swanson et al don’t disclose a point photodetector.
Nonetheless, Isogai et al disclose the OCT includes a point detector as a detector [see 0024].
Therefore, it is obvious to one skilled in the art at the time the invention was filed and would have been motivated to combine Swanson et al and Isogai et al by using a point detector; because it is important that detected points be independent of noise, blurring contrast and geometric shapes.
Claims 18-19 are rejected under 35 U.S.C. 103 as being unpatentable over Swanson et al (Pub. No.:  US 2014/0376000) in view of Wang et al (Pub. No.:  US 2020/0116489).
Regarding claim 18, Swanson et al disclose method suitable for performing an optical coherence tomography (OCT) scan,
the method comprising providing a first signal provided by a light source;
providing a reference signal [see claim 12, fig 2] by disclosing a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal [see claim 12];
reflecting the first signal from a subject and coupling the reflected first signal to the reference signal to provide an interference signal [see claim 12, fig 2] by disclosing a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal [see claim 12];
adjusting a delay of one of the reference signal and the first signal by a variable delay to match (using adjustable path length device that sets measurement range of interest and include other devices (e.g., polarization rotators, attenuators, lenses, mirrors, etc. see 0051-0052) an optical path length of the reference signal to an optical path length of the reflected first signal [see 0014, 0044, 0051, 0062, 0065, 0074-0075, 0093, figs 6, 8, 15] by disclosing adjustable path length device that sets measurement range of interest and include other devices (e.g., polarization rotators, attenuators, lenses, mirrors, etc.) and  an optional polarization controller that may be automatically or manually adjusted [see 0051-0053];
wherein the step of adjusting comprises selecting between paths of different lengths [see 0051-0053] by disclosing adjustable path length device that sets measurement range of interest and include other devices (e.g., polarization rotators, attenuators, lenses, mirrors, etc.) and an optional polarization controller that may be automatically or manually adjusted [see 0051-0052];
automatically selecting between the paths of different lengths [see 0051-0053] by disclosing adjustable path length device that sets measurement range of interest and include other devices (e.g., polarization rotators, attenuators, lenses, mirrors, etc.) and an optional polarization controller that may be automatically or manually adjusted [see 0051-0053];
analyzing the interference signal [see claim 12, 0006, 0044 and figs 2, 18-22] by disclosing a detection system that detects the interference signal from which a ranging or longitudinal reflectance imaging of a sample positioned in the sample arm may be generated [see claim 12].
Swanson et al don’t disclose an interference peak is identified in the interference signal and performing image recognition on the interference signal to identify the interference peak.
Nonetheless, Wang et al disclose automatically selecting between the paths of different lengths until an interference peak is identified in the interference signal [see fig 5, 0054-0055] by disclosing Since the source has a very short coherence length, an interference peak appears at a location where a cross-polarization coupling happens when the moving mirror scans along equivalently the optical path of the fixed arm [see 0054] and performing image recognition on the interference signal to identify the interference peak [see 0062], the peak has been identified by image projection [see 0062].
Therefore, it is obvious to one skilled in the art at the time the invention was filed and would have been motivated to combine Swanson et al and Wang et al by performing image recognition on the interference signal to identify the interference peak; because each peak may be helpful to suppress the 2π phase jump and other influence of noise.
Conclusion


NEXT OFFICE ACTION: Notice of Pre-AIA  or AIA  Status
The present application, filed on or after March 16, 2013, is being examined under the first inventor to file provisions of the AIA .
The following is an examiner’s statement of reasons for allowance: No prior arts of record alone or in combination discloses the following:
“adjusting a delay of one of the reference signal and the first signal by a variable delay to match an optical path length of the reference signal to an optical path length of the reflected first signal, wherein the step of adjusting comprises selecting between paths of different lengths, wherein the variable delay comprises a series of binary switches and a series of different selectable path lengths, wherein the series of path elements comprise lengths of L, 2L, etc. up to 2NL, where N is a positive integer”
Any comments considered necessary by applicant must be submitted no later than the payment of the issue fee and, to avoid processing delays, should preferably accompany the issue fee.  Such submissions should be clearly labeled “Comments on Statement of Reasons for Allowance.”

CITED REFERENCE SUMMARIES: Ref US20170238798A1: Claims:
An optical coherence tomography device comprising: an OCT optical system configured to irradiate a tissue of a subject's eye with measurement light from a light source, the OCT optical system including a detector configured to detect interference between reference light and the measurement light reflected from the tissue and a processor configured to: a generation process of acquiring A-scan data based on a signal output from the detector in a cycle of 300 kilohertz or more and generating three-dimensional OCT data based on the acquired A-scan data; and an analysis process on each piece of the three-dimensional OCT data generated through the generation process, so as to output a real-time analysis result of the three-dimensional OCT data which is generated.
an OCT optical system configured to irradiate a tissue of a subject's eye with measurement light from a light source, the OCT optical system including a detector configured to detect interference between reference light and the measurement light reflected from the tissue and
a processor configured to:
a generation process of acquiring A-scan data based on a signal output from the detector in a cycle of 300 kilohertz or more and generating three-dimensional OCT data based on the acquired A-scan data; and
an analysis process on each piece of the three-dimensional OCT data generated through the generation process, so as to output a real-time analysis result of the three-dimensional OCT data which is generated.
The optical coherence tomography device according to claim 1 , wherein the processor displays a graphics in which the three-dimensional OCT data generated through the generation process is visualized on a monitor in real time, and outputs to the monitor the analysis result corresponding to the graphics displayed on the monitor to display the analysis result on the monitor.
wherein the processor
displays a graphics in which the three-dimensional OCT data generated through the generation process is visualized on a monitor in real time, and
outputs to the monitor the analysis result corresponding to the graphics displayed on the monitor to display the analysis result on the monitor.
The optical coherence tomography device according to claim 1 , wherein the processor generates pieces of time-series three-dimensional OCT data through the generation process, and obtains the analysis result by processing at least two pieces of three-dimensional OCT data among the pieces of time-series three-dimensional OCT data in the analysis process.
The optical coherence tomography device according to claim 3 , wherein the processor generates three-dimensional motion contrast data regarding the subject's eye through the analysis process, and displays a moving image formed of a three-dimensional motion contrast image which is a graphics obtained by visualizing the three-dimensional motion contrast data, on the monitor as the analysis result.
The optical coherence tomography device according to claim 3 , wherein the processor generates three-dimensional motion contrast data through the analysis process, and obtains information regarding pulsation of a blood flow in the subject's eye as the analysis result based on the three-dimensional motion contrast data.
The optical coherence tomography device according to claim 5 , wherein the processor acquires the information regarding pulsation as the analysis result of the analysis process based on a blood flow direction based on the three-dimensional motion contrast data, and at least the two pieces of three-dimensional OCT data.
The optical coherence tomography device according to claim 6 , wherein at least the two pieces of three-dimensional OCT data include first three-dimensional OCT data, second three-dimensional OCT data having a time interval with the first three-dimensional OCT data as a first time interval, and third three-dimensional OCT data having a time interval with the first three-dimensional OCT data as a second time interval, and the processor simultaneously obtains pieces of the information regarding pulsation at a plurality of locations in which diameters of blood vessels are different from each other based on a Doppler phase shift between the first three-dimensional OCT data and the second three-dimensional OCT data and a Doppler phase shift between the first three-dimensional OCT data and the third three-dimensional OCT data by performing the analysis process.
at least the two pieces of three-dimensional OCT data include first three-dimensional OCT data, second three-dimensional OCT data having a time interval with the first three-dimensional OCT data as a first time interval, and third three-dimensional OCT data having a time interval with the first three-dimensional OCT data as a second time interval, and
the processor simultaneously obtains pieces of the information regarding pulsation at a plurality of locations in which diameters of blood vessels are different from each other based on a Doppler phase shift between the first three-dimensional OCT data and the second three-dimensional OCT data and a Doppler phase shift between the first three-dimensional OCT data and the third three-dimensional OCT data by performing the analysis process.
The optical coherence tomography device according to claim 1 , wherein the processor analyzes a coagulation spot formed on the subject's eye by photocoagulation laser light based on the three-dimensional OCT data generated through the generation process by performing the analysis process, and outputs at least one of information regarding a size of the coagulation spot and information regarding a position of the coagulation spot in the subject's eye as the analysis result.
The optical coherence tomography device according to claim 1 , wherein the processor generates the three-dimensional OCT data including the fundus of the subject's eye in a data acquisition range through the generation process, analyzes a separation location of layers forming the fundus based on the three-dimensional OCT data generated in the analysis process, and outputs separation location information which is information indicating at least one of the presence or absence of a separation location of layers and a position of the separation location as the analysis result.
The optical coherence tomography device according to claim 2 , wherein the processor forms a three-dimensional blood vessel image of the subject's eye through the analysis process, and displays the formed three-dimensional blood vessel image on the monitor in an overlapping manner with a three-dimensional image of the subject's eye obtained by visualizing the three-dimensional OCT data.
The optical coherence tomography device according to claim 1 , wherein the processor generates the three-dimensional OCT data including the subject's eye and an instrument used for diagnosis, treatment, or surgery of the subject's eye in a data acquisition range through the generation process, analyzes a gap between a tissue of the subject's eye and the instrument in a depth direction, based on the three-dimensional OCT data generated through the analysis process, and outputs information regarding the gap as the analysis result.
The optical coherence tomography device according to claim 1 , wherein the processor analyzes a thickness of a tissue of the subject's eye by performing the analysis process on the three-dimensional OCT data generated through the generation process, and outputs information regarding the thickness as the analysis result.
The optical coherence tomography device according to claim 1 , further comprising: an input interface configured to receive an instruction from an examiner, wherein the processor displays a graphics obtained by visualizing the three-dimensional OCT data generated through the generation process, on the monitor in real time, receives a region in which the analysis process is performed on the graphics based on a signal from the input interface, and displays a result of an analysis process on the region on the monitor.
an input interface configured to receive an instruction from an examiner,
wherein the processor displays a graphics obtained by visualizing the three-dimensional OCT data generated through the generation process, on the monitor in real time, receives a region in which the analysis process is performed on the graphics based on a signal from the input interface, and displays a result of an analysis process on the region on the monitor.
The optical coherence tomography device according to claim 1 , wherein the processor obtains an analysis result of a three-dimensional region included in an acquisition range of three-dimensional OCT data through the analysis process.
An optical coherence tomography device comprising: an OCT optical system configured to irradiate a tissue of the subject's eye with measurement light from a light source, the OCT optical system including a detector configured to detect interference between reference light and the measurement light reflected from the tissue; and a processor configured to: a generation process of acquiring A-scan data based on a signal output from the detector in a cycle of 300 kilohertz or more and generating three-dimensional OCT data based on the acquired A-scan data; and a display control process of generating a two-dimensional image indicating a section in an acquisition range of the three-dimensional OCT data as a graphics in which the three-dimensional OCT data is visualized based on each piece of the three-dimensional OCT data generated through the generation process, and updating and displaying the generated two-dimensional image on a monitor.
an OCT optical system configured to irradiate a tissue of the subject's eye with measurement light from a light source, the OCT optical system including a detector configured to detect interference between reference light and the measurement light reflected from the tissue; and
a display control process of generating a two-dimensional image indicating a section in an acquisition range of the three-dimensional OCT data as a graphics in which the three-dimensional OCT data is visualized based on each piece of the three-dimensional OCT data generated through the generation process, and updating and displaying the generated two-dimensional image on a monitor.
The optical coherence tomography device according to claim 15 , further comprising: an input interface configured to receive an instruction from an examiner, wherein the processor performs a selection process of selecting a position of the section related to the two-dimensional image in the acquisition range of the three-dimensional OCT data based on a signal from the input interface, and displays a two-dimensional image of a selected section on the monitor.
wherein the processor performs a selection process of selecting a position of the section related to the two-dimensional image in the acquisition range of the three-dimensional OCT data based on a signal from the input interface, and displays a two-dimensional image of a selected section on the monitor.
The optical coherence tomography device according to claim 16 , wherein the processor: generates a front image as the two-dimensional image based on some data of the three-dimensional OCT data in a depth direction in the display control process; and further selects the section related to the front image in an acquisition range of the three-dimensional OCT data in the depth direction based on a signal from the input interface through the selection process.
wherein the processor:
generates a front image as the two-dimensional image based on some data of the three-dimensional OCT data in a depth direction in the display control process; and
further selects the section related to the front image in an acquisition range of the three-dimensional OCT data in the depth direction based on a signal from the input interface through the selection process.
The optical coherence tomography device according to claim 17 , wherein the processor: selects any one of a plurality of layers forming the fundus as a position in the depth direction in the selection process; and further generates the front image indicating a front view of a layer selected in the selection process, through the display control process, so as to display the front image on the monitor.
selects any one of a plurality of layers forming the fundus as a position in the depth direction in the selection process; and
further generates the front image indicating a front view of a layer selected in the selection process, through the display control process, so as to display the front image on the monitor.
The optical coherence tomography device according to claim 17 , wherein the processor selects any coordinate of the three-dimensional OCT data in the depth direction as a position in the depth direction through the selection process, and displays the front image indicating a horizontal plane at the selected coordinate in the depth direction on the monitor through the display control process.
An optical coherence tomography device comprising: an OCT optical system configured to irradiate a tissue of the subject's eye with measurement light from a light source, the OCT optical system including a detector configured to detect interference between reference light and the measurement light reflected from the tissue; a scanning unit that includes an optical scanner for main scanning that includes one or a plurality of galvanomirrors which scan the subject's eye with the measurement light in a predetermined main scanning direction by performing reciprocation driving formed of forward moving and backward moving, and an optical scanner for sub-scanning that is different from the optical scanner for main scanning in terms of a scanning direction, and scans the subject's eye with the measurement light in a two-dimensional manner based on operations of the optical scanner for main scanning and the optical scanner for sub-scanning; and a processor configured to: acquire A-scan data based on a signal output from the detector in a cycle of 300 kilohertz or more; and perform scanning with measurement light continuously twice or more in the main scanning direction by repeatedly reciprocating the galvanomirror at a constant swing angle, and controls at least the galvanomirror so that a time difference between start timings of respective scanning operations is set to a value which is equal to or less than 5 milliseconds.
an OCT optical system configured to irradiate a tissue of the subject's eye with measurement light from a light source, the OCT optical system including a detector configured to detect interference between reference light and the measurement light reflected from the tissue;
a scanning unit that includes an optical scanner for main scanning that includes one or a plurality of galvanomirrors which scan the subject's eye with the measurement light in a predetermined main scanning direction by performing reciprocation driving formed of forward moving and backward moving, and an optical scanner for sub-scanning that is different from the optical scanner for main scanning in terms of a scanning direction, and scans the subject's eye with the measurement light in a two-dimensional manner based on operations of the optical scanner for main scanning and the optical scanner for sub-scanning; and
acquire A-scan data based on a signal output from the detector in a cycle of 300 kilohertz or more; and
perform scanning with measurement light continuously twice or more in the main scanning direction by repeatedly reciprocating the galvanomirror at a constant swing angle, and controls at least the galvanomirror so that a time difference between start timings of respective scanning operations is set to a value which is equal to or less than 5 milliseconds.
Ref US20200116489A1: [content unavailable]
Ref US20140376000A1: Claims:
An optical system for optical coherence tomography comprising: an interferometer that divides a tunable optical signal between a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal, said interferometer including a dual-polarization, dual-balanced, in-phase and quadrature (I/Q) detection outputs and integrated photodetectors; and a tunable optical source that generates the tunable optical signal; wherein the interferometer, and the tunable optical source are integrated onto a photonic integrated circuit (PIC) and said interference signal is used to determine information about a longitudinal reflectivity profile of optical properties of a sample positioned in the sample path.
an interferometer that divides a tunable optical signal between a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal, said interferometer including a dual-polarization, dual-balanced, in-phase and quadrature (I/Q) detection outputs and integrated photodetectors; and
a tunable optical source that generates the tunable optical signal;
wherein the interferometer, and the tunable optical source are integrated onto a photonic integrated circuit (PIC) and said interference signal is used to determine information about a longitudinal reflectivity profile of optical properties of a sample positioned in the sample path.
The optical system of claim 1 further comprising a k-clock module for generating a k-clock signal for triggering the detector system wherein said k-clock module is integrated onto the single PIC.
The optical system of claim 1 wherein said tunable optical source system includes one or more optical frequency modulators.
The optical system of claim 1 wherein said tunable optical source includes one or more tunable optical filters.
The optical system of claim 1 further comprising one or more surface grating couplers integrated onto the PIC for coupling light between the PIC and one or more optical fibers.
The optical system of claim 1 further comprising one or more facet couplers integrated onto the PIC for coupling light between the PIC and one or more optical fibers.
The optical system of claim 1 further comprising a non-silicon optical gain element in optical communication with the PIC, wherein the PIC is a silicon photonic PIC.
The optical system of claim 1 wherein the PIC includes more than one optical port and each one of said ports is coupled to an optical fiber, and each one of said optical fibers included in a single block affixed to the PIC.
The optical system of claim 1 further comprising a carrier substrate onto which is mounted the PIC and one or more additional electrical chips.
The optical system of claim 1 further comprising an optical gain element including multiple optical waveguides providing gain peak at different locations integrated onto the PIC.
The optical system of claim 1 further comprising a modulator integrated onto the PIC, said modulator positioned in the optical path of the tunable optical signal.
An electro-optical system comprising: one or more couplers for optically coupling light comprising a tunable optical signal into one or more of the photonic integrated circuits, an interferometer that divides the tunable optical signal between a reference path and a sample path and combines optical signals returning from the reference path and the sample path to generate an interference signal; and a detection system that detects the interference signal from which a ranging or longitudinal reflectance imaging of a sample positioned in the sample arm may be generated; wherein the interferometer, couplers and detection system are all integrated onto one or more closely coupled photonic integrated circuits (PICs) commonly packaged or positioned on a common substrate.
one or more couplers for optically coupling light comprising a tunable optical signal
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