WO2014089504A1 - Système et procédé de tomographie par cohérence optique d'imagerie parallèle - Google Patents

Système et procédé de tomographie par cohérence optique d'imagerie parallèle Download PDF

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Publication number
WO2014089504A1
WO2014089504A1 PCT/US2013/073704 US2013073704W WO2014089504A1 WO 2014089504 A1 WO2014089504 A1 WO 2014089504A1 US 2013073704 W US2013073704 W US 2013073704W WO 2014089504 A1 WO2014089504 A1 WO 2014089504A1
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WIPO (PCT)
Prior art keywords
light
sample
sampling
beams
light source
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PCT/US2013/073704
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English (en)
Inventor
Chao Zhou
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Lehigh University
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Application filed by Lehigh University filed Critical Lehigh University
Priority to CN201380063585.5A priority Critical patent/CN104870930A/zh
Publication of WO2014089504A1 publication Critical patent/WO2014089504A1/fr
Priority to HK15111660.9A priority patent/HK1210827A1/xx

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Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02001—Interferometers characterised by controlling or generating intrinsic radiation properties
    • G01B9/02012—Interferometers characterised by controlling or generating intrinsic radiation properties using temporal intensity variation
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02015—Interferometers characterised by the beam path configuration
    • G01B9/02027—Two or more interferometric channels or interferometers
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/0209—Low-coherence interferometers
    • G01B9/02091—Tomographic interferometers, e.g. based on optical coherence
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4795—Scattering, i.e. diffuse reflection spatially resolved investigating of object in scattering medium

Definitions

  • the present disclosure relates to tomography, and more particularly to optica coherence tomography providing multi-point illumination and parallel imaging of a specimen or sample.
  • OCT optical coherence tomography
  • OCT captures and digitiz.es visual images of tangible objects such as biological, tissue.
  • the penetratio depth of OCT is usually 1 -2 mm in biological tissues.
  • OCT has been used for a wide range of clinical and biomedical applications particularly
  • Imaging speeds for OCT characterized as number of A- scans (axial scans) per second, is limited by the line rate of line-scan cameras for spectral-domain OCT (SD-OCT) or by the laser sweep rate for swept-soutce OCT (SS-OCT).
  • Frame rate for cross-sectional 2D-OCT and volume rate for 3D-OCT are also determined by the speed of the beam scanning mechanism.
  • Parallel acquisition of OCT images using multiple imaging beams is a new approach intended to achieve significant speed improvement in A-scasi rate, frame rate, as well as in volume rate.
  • FF-OCT Full-field OCT
  • Linnik interferometer and a 2D digital camera to acquire OCT images.
  • FF-OCT takes advantages of parallel imaging by illuminating the entire sample region and detecting interference signals from each sample location using a 2D camera.
  • imaging sensiti ity is usually poor for FF-OCT due to incoherent scattered light and pixel crosstalk.
  • the sensitivity of an OCT system is inversely proportional to incoherent scattered light level. Incoherent scattered light limits the maximum usable power before the camera saturates and, hence, limits the detection sensitivity.
  • Line-scan OCT has been developed to utilize a line-field illumination, rather than full-field illumination, in order to reduce incoherent scattered light and pixel crosstalk.
  • LS-OCT enables the sensitivity to be increased by over an order of magnitude compared to FF-OCT.
  • OCT optical coherence tomography
  • a parallel imaging optica! coherence tomography system includes: a light source producing light; a scan unit receiving incident light from the light source, the scan unit movable in a scanning motion and including a plurality of apertures configured to divide the incident light into a plurality of light beams: and an
  • the interferometer includes: a beam splitter receiving the plurality of light beams from the scan unit and dividing each of the plurality of light beams into a reference beam and a sampling beam; a reference arm including a reference mirror receiving a plurality of reference beams from the beam spli tter and returning reflected reference light signals to the beam splitter; and a sampling arm receiving a plurality of sampling beams from the beam splitter and scanning the plurality of sampling beams onto a sample.
  • the beam splitter further receives and combines the reflected reference light signals from the reference arm and reflected sampling light signals returned from the sample to generate an interference signal comprising an inte ferogranr based on the reflected reference and sampling Sight signals.
  • the interferometer further includes a detector arm inciuding a detector configured to obtain the interference signal from the beam splitter and generate an output signal convertible into a digitized image of the sample.
  • the sca -unit is a spinning disk having a rotational scanning motion.
  • the apertures may be pinholes or other shaped openings.
  • a parallel imaging optical, coherence tomography system includes: a light source producing light; a scan unit recei ving incident light from the light source and movable in a scanning pattern, the scan unit including: a collector disk comprising a niicrolens array; and an aperture disk comprising an aperture array and mounted on a common rotational axis with the collector disk, the scan unit being
  • the system further includes an interferometer including; a beam splitter receiving the plurality of light beams from the spinning disk and dividing each of the plurality of light beams into a reference beam and a sampling beam; a reference arm including a reference .mirror recei ving a plurality of reference beams from the beam splitter and returning reflected reference light signals to the beam splitter: and a sampling arm receiving a plurality of sampling beams from the beam splitter and scanning the plurality of sampling beams onto a sample.
  • an interferometer including; a beam splitter receiving the plurality of light beams from the spinning disk and dividing each of the plurality of light beams into a reference beam and a sampling beam; a reference arm including a reference .mirror recei ving a plurality of reference beams from the beam splitter and returning reflected reference light signals to the beam splitter: and a sampling arm receiving a plurality of sampling beams from the beam splitter and scanning the plurality of sampling beams onto a sample.
  • the beam splitter further receives and combines the reflected reference light signals from the reference arm and reflected sampling light signals returned from the sample to. generate an interference signal comprising an mierferogram based on the reflected reference and sampling light signals.
  • the interferometer further includes a detector arm including a detector configured to obtain the interference signal from the beam splitter and generate an output signal convertible into a digitized image of the sample.
  • a light source producing light, a scan unit, and an interferometer comprising a reference arm defining a first optical path and a sample arm defining a second optical path; illuminating the scan unit with light from, the light source; moving the scan unit in a scanning motion; transmitting the light through a plurality of apertures its the scan unit to form a plurality of light beams moving in the scanning motion; splitting the plurality of light beams into a plurality of reference beams and a plurality of sampling beams; transmitting the plurality of reference beams to the reference arm, the reference arm including a reflecting mirror producing a reflected reference light signals; transmitting the plurality of sampling light beams to the sample arm; scanning the plurality of sampling beams onto a surface of a sample; combining the reflected reference light signals from the reference arm and reflected sampling light signals returned from the sample to generate an interference signal comprising an interferograra based on the reflected reference and sampling light signals; detecting the interference signal in a detector arm of the interferometer with
  • FIG . 1 is a schematic diagram of a parallel imaging optical coherence tomography (OCT) system including a spinning disk and interferometer;
  • FIG. 2 is a schematic diagram of a parallel imaging optical coherence tomography (OCT) system including a dual spinning disk assembly with microienses and interferometer;
  • FIG. 3 is a schematic diagram of the OCT system of FIG. 1 coupled with an optical fiber imaging probe
  • FIG. 4 is a schematic diagram of the OCT system of FIG . 2 coupled wi th an optical fiber imaging probe;
  • FIG. 5 is a side cross-sectional view of a single microlens and aperture from the dual spinning disk assembly of FIG. 2 showing light collection and transmittance paths, j 0018] All drawings are schematic and not to scale .
  • a parallel imaging OCT system and related method which utilize interferometry and a movable mask comprised of patterned apertures such as pinholes to produce multi-point illumination of the sample simultaneously with multiple imaging beams.
  • Each imaging beam is spatially separated by the pinholes thus significantly reducing incoherent scattered light and pixel crosstalk, thereby improving imaging sensitivity for OCT.
  • the mask can be rotated forming a spinning scanning disk ("spinning disk") or otherwise translated to ensure the entire imaging area is covered by the imaging or sampling beams.
  • the spinning disk receives incident light from a light source and divides the light to produce a plurality of imaging or sampling beams which are simultaneously scanned on a sample to capture image signals.
  • the point illumination created through each pinhole produces a plurality of corresponding scan lines or traces on the sample to be imaged.
  • a spinning-disk OCT according to the present disclosure achieves high imaging speed with parallel imaging while obtaining high imaging sensitivity by reducing incoherent scattered light and pixel crosstalk.
  • spinning-disk OCT can be used to obtain 3D structural and functional (e.g. Doppler OCT, polarization sensitive OCT) images of the sample based on intrinsic contrast rather than fluorescence labeling.
  • 3D structural and functional e.g. Doppler OCT, polarization sensitive OCT
  • acquisition, of OCT signals may be parallelized with respect to imaging depth, resulting in fast 3D imaging speed.
  • a key difference between the present interferometer-based, spinning disk OCT system 100 and the confoeal microscope is that the present system utilizes light
  • FIG, 1 is a schematic diagram of a parallel imaging spinning disk OCT system 1.00 according to the present disclosure.
  • OCT system 100 includes a spinning disk 121 and interferometer 105, as further described below.
  • a low coherence broadband light source 1 10 may provide light L for the OCT system 100 and operation of interferometer 105.
  • a light source 100 can be for example a halogen lamp, a Xenon arc lamp, a super- luminescent diode (SLD), a super continuum light source, a broadband laser, a wavelength tunable laser or other source (operated in sweeping mode), femtosecond lasers, or other suitable broadband sources.
  • the light output from a broadband light source 1 1.0 comprises multiple wavelengths or colors covering a broad range of wavelengths or frequencies.
  • Source light L output from the light source 1 10 is transmitted along a Sight source path to and illuminates a scan unit 1.20.
  • a lens or collimator (not shown) may be provided to help illuminate the light from light source 1 10 onto the scan unit.
  • CoHimated light is preferred in an exemplary non-limiting embodiment.
  • Scan unit 120 includes a movable light transmitting substrate havin a scanning motion and a plurality of apertures operable to receive and transmit source light L. Solid, portions (e.g. optically opaque) of the substrate between the apertures block part of the incident light from light source 1 10. The light transmitting substrate may be moved by a
  • any suitable scanning motion to scan the light onto sample 130 e.g. Hnear/translation&l in. one or more -directions, rotational, or combinations thereof) depending on the intended scan pattern to be produced.
  • the light transmitting substrate of scan unit 120 may be a rotating aperture disk; such as spinning disk 121 having a rotational scanning motion and axis of rotation R offset from and general ly parallel to the light source path which defines a first optical axis P.
  • Incident light L from the light source 1 10 illuminates a portion of the spinning disk 121 , as illustrated in FIG. 1.
  • Spinning disk 121 is fixedly connected to a motor-dri ven spindle 203 (defining the axis of rotation R) coupled to an electric- drive motor 204 which rotates the disk.
  • the rotational speed of the spinning disk 121 may be varied in some embodiment by appropriately configured motor control circuitry. This allows the scanning rate of the sample to be adjusted.
  • Spinning disk 121 which may be a Nipkow disk in some embodiments, includes a plurality of light transmittance apertures which are operable to receive, divide, and transmit incident source light L axialiy through the disk, thereby producing a plurality of light beams B from light source 1 0 which may be then scanned on a sample 13.0 to collect imaging data.
  • the apertures may be configured as pinholes 1.22 in some non- limiting examples which extend completely through the spinning disk 121 between a substantially flat rear surface 124 ⁇ e.g. incident light side of disk) and an opposing substantially flat front surface 125 (e.g. light transmittance side of disk).
  • the beam of source Sight L is preferably wide enough to simultaneously illuminate a pluralit of pinholes 122 for producing the multiple light beams B, as graphically depicted in FIG, I,
  • the pinholes 122 can be organized in different patterns, including without limitation a fixed angle spiral pattern, a tetragonal, pattern, and an equal-pitch spiral pattern (e.g. Archimedian spiral or other).
  • Each pinhole 12:2 acts as an independent illumination source which may each be focused onto the sample 130 through suitable optical lenses (tube lens, relay lens, objectives, etc.) in the sample arm of the
  • interferometer 105 as further described herein.
  • mitltiple sampie locations are illuminated simultaneously on the sample 130 as the sampling beams are scanned across the surface of the sample.
  • the diameter of the pinholes 122 and spacing between pinholes may be varied to adjust the light transmission rate and other parameters.
  • the pinhole ! 22 pattern on the spinning disk 121 can be designed and arranged to repeat more than one time for every revolution of the spinning disk 121.
  • TSiis arrangement advantageously increases the scan rate.
  • a plurality of pinhole arrays 123 each comprising a cluster of multiple pinholes 122 may be provided which extend radially outwards from the center of the spinning disk 121 in a suitable pattern such as linear or curved spiral arms.
  • each pinhole 122 has one or more corresponding pinholes located at the same radial distance from the center of the disk, but located i one o more of the other multi le pinhole arrays.
  • the apertures of the spinning disk may include multiple sets of slits instead of spirally arranged or other patterned pinholes 122.
  • the slits may be arranged in linear arrays on the disk which are oriented in parallel, perpendicular, or in other patterns including spirals. Slits generally produce brighter illumination, and hence higher signal throughput, whereas pinholes generally produce greater resolution and sensitivity. Either slits or pinholes may be used depending on the specific application and desired performance parameters of the OCT system 100. Spinning disks are commercially available from companies such as Yokogawa Electric Corporation and others.
  • the light transmitting substrate of scan unit 1 0 may accordingly have shapes other than disk or circular including for example polygonal or rectilinear configurations.
  • mechanisras/raotors may be provided depending on the shape and intended motion of the light transmitting substrate which, is well within the ambit of those skilled in the art: to select. Accordingly, the invention is expressly not limited by the type of translating motion provided for the light transmitting substrate of scan unit 120, shape of the substrate, or the shape of the apertures disposed therein.
  • the spinning disk 121 therefore represents one possible, but non-limiting example of a movable scan unit 120.
  • interferometer 105 includes an. optical beam splitter 150 which may be placed in light source path to receive incident light transmitted from the spinning disk 121 comprising the plurality of light beams.
  • the beam splitter 150 may be located between the spinning disk 121 and an objective lens 140 m the sampie ami 104 along a first opiicai path in one embodiment
  • a tube lens 70 may be located between the spinning disk 12.1 and beam splitter 150 to help focus the incident light onto the beam splitter.
  • any suitable type of beam splitter 1.50 may be used including a conventional transparent beam splitter cube comprised of two triangular glass prisms bonded together along mating 45 degree sides.
  • the beam splitter 150 ma ⁇ be a half-silvered mirror, pellicle beam splitter, or other commercially available type of beam splitter used m the art operable to transmit a portion of the incident light and reflec t a portion of the incident light.
  • Beam splitter 150 splits or divides the incident light into reference light in a reference ami 102 and sampling light in a sample arm 104 of the interferometer 105.
  • the interferometer may he configured as a Michelson interferometer, whose arrangement and operatio are well known in the art.
  • the reference arm 1.02 defines a reference light path which may be aligned along a second optical axis, which in one non-limiting embodiment may be transversely oriented with respect to the light source path (first optical axis) defined between beam splitter 150 and. light source 1 10.
  • Reference arm 102 includes a reference mirror 160 that is conjugated to the sample location.
  • An objective lens 162 may be provided to focus the reference light from beam splitter 150 onto the reference mirror 160.
  • the sample arm 104 defines a samplin light path which may be transversely oriented with respect to the reference light path.
  • the sampling light comprises a plurality of sampling beams produced by the spinning disk 121 and transmitted through beam splitter 50.
  • the sampling beams may be focused onto the sample through an objective lens 1 0, which may be a convex lens.
  • a 5X objective lens e.g. Mitutoyo, 5X NIR or other
  • the spacing between the sample locations corresponding to the sampling beams on the sample are determined by the spacing of pinholes in spinning disk 121 and the
  • the spacing can be optimized based on the intended applications to minimize light scattering between sampie locations and maximize imaging parallelization.
  • reflected light from the reference arm 102 and reflected light returned through the sample arm 104 produced by surface and internal structures within sample 130 from scanning the sample with the plurality of sampling beams are combined at the beam splitter 150 producing an interference signal comprising an raterferogram (i.e. interference pattern or fringe pattern).
  • the "detection light" containing the interference signal .from the beam splitter 150 is then transmitted through the detection arm 106 of the interferometer 105 to a light-sensitive digital image sensor or detector 1 0.
  • Detector 190 is operable to convert the incident optical electromagnetic light energy (i.e.
  • An objective lens 180 may be provided in the detection arm 106 to help focus the detection light containing the interference signal properly onto the detector 1 0.
  • the detector 190 may be an image sensor comprised of a 2D (two-dimensional) photodetector array (or “detector array” for short).
  • the 2D detector 190 can be charge-coupled device (CCD) camera, a complementary metal-oxide semiconductor (CMOS) camera, an InGaAs camera, or other suitable 2D detector operable to capture and detect the interference pattern in the CCD camera, a complementary metal-oxide semiconductor (CMOS) camera, an InGaAs camera, or other suitable 2D detector operable to capture and detect the interference pattern in the CCD camera, a complementary metal-oxide semiconductor (CMOS) camera, an InGaAs camera, or other suitable 2D detector operable to capture and detect the interference pattern in the CCD detector 190 .
  • CCD charge-coupled device
  • CMOS complementary metal-oxide semiconductor
  • InGaAs camera or other suitable 2D detector operable to capture and detect the interference pattern in the
  • each of the multiple sampling beams focused on the sample 130 form sample locations that change and move across the surface of the sample as the disk spins.
  • the associated interference signals produced from the different sample locations are collected by the corresponding digital camera pixels of detector 1 0.
  • the scanned sampling beams produce scanning t ines or traces across the sample surface corresponding to rotation of the spinning disk 12 ! while the sample 130 remains stationary in one embodiment.
  • Detector 190 generates electronic/electrical output signals (comprising the interference signals and hence image data for digitally reconstructing an image of sample 130) for further processing by an appropriately configured processor-based data, and signal processing system, such as without limitation a computer 192.
  • Computer 1 2 includes a processor whose operation is configured and directed by program instructions (e.g. software or control logic) including signal processing mathematical algorithms or software for extracting and generating two or three-dimensional (2D or 3D) digitized images obtained from the interference signals produced by scanning sample 130, The processor performs signal processing of the interference signals received from detector 190 in a manner well known in the art.
  • the aeqiiired output signals from detector 1 0 may be streamed continuously to the processor of computer 1 2 or other suitable processor-based device or PLC (programmable logic controller) that may be used.
  • the digital image data generated by computer 1 2 may be rendered on a visual display device such as display 194 and/or stored in the memory for further processing, export, storage, etc.
  • computer as used herein is to be broadly construed and representative of any appropriately configured data and signal processing device having a central processing unit (CPU), microprocessor, micro-controller, or computational data processing device or circuitry configured for executing computer program instructions (e.g. code or software) and processing the acquired output signals from detector 190 to generate a digitized image of sample 130.
  • CPU central processing unit
  • microprocessor micro-controller
  • computational data processing device or circuitry configured for executing computer program instructions (e.g. code or software) and processing the acquired output signals from detector 190 to generate a digitized image of sample 130.
  • This may include, for example without limitation, desktop computers, personal computers, laptops, notebooks, tablets, pad devices, and other processor-based devices having suitable processing power and speed.
  • Computer 192 may include all the usual appurtenances associated with such a device or data processing system, including without limitation the properly programmed processor, a memory device(s), a power supply, a video card, visual display device or screen (e.g. graphical user interface ⁇ , firmware, software, user input devices (e.g., a. keyboard, mouse, touch screen, etc.), wired and/or wireless output devices, wired and/or wireless communication devices ⁇ e.g. Ethernet, Wi-Fi, Bluetooth, etc) for transmitting captured sampling images. Accordingly, the invention is not limited by any particular type of processor-based device.
  • the memory may be any suitable non-transitory computer readable medium such as, without limitation, any suitable volatile or non-volatile memory including random access memory (RAM) and various types thereof, read-only memory (ROM) and various types thereof, USB flash memory, and magnetic or optical data storage devices (e.g. internal/external hard disks, floppy discs, magnetic tape CD-ROM, DVD-ROM, optical disk, ZIPTM drive, Blu-ray disk, and others), which may be written to and/or read by a processor operably connected to the medium.
  • RAM random access memory
  • ROM read-only memory
  • USB flash memory e.g. internal/external hard disks, floppy discs, magnetic tape CD-ROM, DVD-ROM, optical disk, ZIPTM drive, Blu-ray disk, and others
  • still digitized images and/or moving video digitized images of the sample 130 captured and recorded by the present OCT system 100 and the detector 1 0 may be rendered on any suitable visual display 1 4 by computer 1 2 for observation by a system user.
  • the user may be a health care provider, technician, or other health care professional.
  • the digitized sample images displayed on the visual display 194 are representati ve of the actual sample or specimen (e.g. human or other animal, tissue in some embodiments) being analyzed by the OC T system 100 and useful as a diagnostic medical tool.
  • Any suitable type of visual display 1 4 may be used, including for example without limitation LED (Sight emitting diode), LCD (liquid crystal display), or other displa screens including capacitive or resistive touch type screens,
  • the time-domain OCT detection method performed by computer 192 can be used to analyze the interference signals from detector 1 0 when a non-wavelength-tunable broadband light source, such as halogen lamp, a Xenon arc lamp, a super-luminescent diode (SLD), a super continuum light source, a broadband laser, etc. is utilized as described above.
  • a non-wavelength-tunable broadband light source such as halogen lamp, a Xenon arc lamp, a super-luminescent diode (SLD), a super continuum light source, a broadband laser, etc.
  • Such light sources produce light comprised of broadband wavelengths simultaneously.
  • Compute program instructions e.g. control logic
  • the computer 192 processor including suitable mathematical algorithms can be used to implement the time-domain OCT detection method. This detection method is well known in the art without undue elaboration.
  • the reference mirror 160 on the reference arm 102 is mounted on an oscillator 164, such as a piezoelectric transducer (PZT), that can change the phase and optical delay of the reference arm.
  • PZT piezoelectric transducer
  • At least two images are recorded successively during each period of the phase modulation, the second image called * 'out ⁇ of ⁇ phase" having a phase shifted by pi compared to the first image called w in-phase.
  • w One can substantially eliminate the background and keep only the interferometrie signal by subtracting the two images.
  • Other demodulation method such as four-quadrant integrating can also be used to extract interference signal.
  • the rotation/movement of the scan unit 120 e.g.
  • a wavelength tunable light source 1 10 (e.g. Superliira Broadsweeper Model BS840-O1 , etc.) may alternatively be used in OCT system 100, Such a light source may be operated to product* light of a broad bandwidth by operating the source in a "sweeping .mode" in which a ' single color or wavelength is discretely produced at each moment and the output is rapidly tuned/cycled through a broad wavelength range.
  • a Fourier-domain OCT detection method performed by computer 1.92 processor executing computer instructions including suitable mathematical algorithms can be used.
  • This detection method is also well known in the art without undue elaboration.
  • the reference mirror 160 can. be fixed (i.e. not oscillated) so that oscillator 164 may be omitted and no phase modulaior is needed on the reference arm 102.
  • An ultrahigh speed camera e.g. Y4, Redlake/IDT
  • the signal processing is based on standard method for processing SS-OC ' T data (i.e.
  • Swept-Soiirce OCT which may include background subtraction, phase calibration, dispersion compensation and Fourier transform steps.
  • Optical frequency of the interference signal relates to imaging depths of sampling light reflections retooled from the sample. Reflections from different sampling depths produces interference patterns with different f equencies. Resolving the reflections via Fourier transformation signal processing produces a depth reflectivity profile (A-scan) at each sample location. Two-dimensional (2D) and three-dimensional (3D) images of the sample can be obtained by combining A-scans from different sample locations.
  • a linearized tunable laser or a frequency comb tunable laser may be used to provide linear k ⁇ space light output for each frame acquisition, which ca significantly simplify image processing.
  • synchronization between the tunable laser light source 1 10. the scan unit 120 (i.e. spinning disk 121), and the 2D camera detector 1 0 is generally desirable.
  • FIG . 2 illustrates another embodiment of a parallel scanning OCT system 100 ha ving a movable scan unit 120 comprising a dual spinning disk assembly 200.
  • Spinning disk assembly 200 includes a first collector disk 201 containing with a plurality of microlenses 202 and a second ipkow-type spinning disk 121 comprising a plurality of apertures such as without limitation pinholes 122, as already described herein.
  • the location of the microlenses 202 and the pinholes 122 are axially co-registered so that each microlens focuses incident light received from light source i 10 onto a corresponding paired pinhole 122 in the spinning disk 121 (see, e.g. FIG.
  • the number and pattern of microlenses 202 in the first coll ector di sk 201 may he the same as the number and pattern of pinholes in the spinning disk 121 .
  • the microlenses 202 may therefore he clustered and arranged in microlens arrays 207 which may substantially coincide in pattern and arrangement with the aperture arrays 123 of pinholes 122 in the spinning disk 121 .
  • collector disk 201 and the spinning disk 121 are axially spaced apart and fixedly connected together by motor-driven elongated spindle 203 coupled to an electric drive motor 204. Accordingly, collector disk 201 and spinning disk 121 rotate simultaneously in unison to maintain axial coaxiai alignment of each microlens 202 with its paired pinhole 122.
  • the fill factor defined as the percentage light transmission through a Nipkow-styie spinning disk 12 L when using a first collector disk 201 with microlenses 202 is significantly improved compared to using a single Nipkow disk alone.
  • each micro lens 202 collects a greater portion of incident light on scan unit 120 than a plain aperture and efficiently focuses the captured light onto its paired pinhole 122 in the spinning disk 121 ,
  • the intensity of light transmitted through the dual spinning disk assembly 200 may be varied by adjusting the diameter of the microienses without changing size of the pinholes 122 in the lower spinning disk 121.
  • Microienses 202 and combination spinning disk-microlens assemblies are commercially available from companies such as Yokogawa Electric Corporation and others, Non4i.miti.ng examples of microienses that .may be used are small transparent optical lens having a diameter less than one millimeter; however, larger diameter lenses may also be used
  • the microienses 202 used may be any suitable type, including for example without limitation single piano-convex lens, imtiti4ayered lenses, micro- Fresnel lenses, and others.
  • the microienses maybe made of any suitable transparent material, including for example, polymers, fused silica, silicon, and others used in the art.
  • the microienses 202 may be fabricated by any suitable methods used in the art.
  • microienses 202 may be formed separately from the collector disk 201 substrate and then mounted therein, or as an. integral unitary structural part of the coliector disk 201 formed of the same material. Either approach may be used.
  • incident light from light source 1 10 strikes a portion of the rear surface 205 of collector disk 201 and is transmitted through the microlens array 207 and opposing front surface 206 to spinning disk 121 as shown in FIG. 2.
  • the plurality of light beams produced by the microlens array 207 are each transmitted in turn through the pinholes 122 of the spinning disk ⁇ 21 and onto the beam splitter 150, in a similar manner already described above.
  • the reference arm 102 in the interferometer 105 of OCT system 100 may be omitted and replaced by inserting a half mirror 250 (e.g. a half- silvered or other type half mirror) reflecting a portion of the incident light) in the sample arm 104, as shown in FIG. 2. Interference will form between light reflected from the half mirror 250 and the sample 130 to generate the interference signal (e.g. interferogram) which can be detected by the 2D deiecior 190. Accordingly, embodiments of the OCT system 100 shown in FIGS. 1 and 2 may use either a reference arm 102 or a half mirror 250 to create the interference signal,
  • the beam splitter 150 and the detection arm 106 do not need to be located after the spinning disk 121.
  • Beam splitter 150 can be placed between the collector disk and the Nipkow disk, or other location of tire optical system based on applications. Relay optics may also be inserted in the optical system i some embodiments.
  • FIG. 3 shows another embodiment where the objective lens 140 in the sample arm 104 focuses light onto a probe 300, rather than onto the sample 130 directly. Probe 300 therefore transmits the sampling light to the sample.
  • the probe 300 may have a bendable and flexible structure for use in endoscopic, laparoscopic, and similar type medical devices ncorporating the OCT system 100 disclosed herein.
  • the probe 300 can include a flexible optical fiber bundle 302 which relates or transmits the incident sampling light from sample arm 1.04 to the sample ! 30 for imaging.
  • the fiber bundle 302 is comprised of multiple individual optical fibers which are structured and configured to transmit light, as is well known in the ait,
  • Fiber bundle 302 includes a proximal end 304 which is optically and physically coupled to sample arm 104 and receives sampling light from objective lens 140.
  • a distal end 306 of fiber bundle 302 is configured to transmit and scan sampling light onto sample 130 and received reflected light signals returned from the sample.
  • the optical fibers 305 which, form fiber bundle 302 may each be a flexible and transparent fiber made of glass (i.e. silica) or plastic structured to transmits light between each end 304, 306 of the fiber.
  • the fibers 305 may be Corning Inc., SMF2S fibers or other suitable optical fibers. Any suitable length and diameter of optical fibers may be used for fiber bundle 302 depending on the intended application and desired performance parameters. Accordingly, numerous variations and configurations are possible,
  • the fiber bundle 302 of probe 300 can be less than a few millimeters in diameter and flexible, so that it can be passed through an endoscope or laparoscope to allow endoscopic imaging using OCT system 100,
  • the optical length of the reference arm 102 will match to the total optical length of the sample arm 104, including the probe 300, to enable formation of interference between the sample arm and reference arm reflected light signals.
  • the distal end 306 of the probe may be in direct contact with the sample .130, or relay optics may be used between the distal end of the probe and the sample.
  • FIG, 4 shows another embodiment of the probe based system, where a half mirror 250 is used between the distal end 306 of the probe 300 and the sample 130 to provide light interference.
  • the half mirror 250 niav he mounted to the distal end 306 in anv suitable manner.
  • the reference arm 102 as shown in FIG. 3 may therefore be removed in this embodiment to make a more compact OCT system 100,
  • the beam splitter 150 and. invention is expressly not limited to an even 50/50 light division • percentage, which represents merely one of many possible designs that might be used for the beam splitter. It will be appreciated by those skilled in the art that the determination of the optical split ratio depends on how much light is intended, to be directed into each of the sample and reference arms. It is desirable to have as much power as possible on sample while keep the power on sample to be within a safe limit. In the meantime, sufficient power is needed on the reference arm to get shot-noise limited sensitivity.

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Abstract

L'invention concerne un système de tomographie par cohérence optique d'imagerie parallèle. Selon un mode de réalisation, le système comprend une source de lumière, une unité de balayage mobile et un interféromètre comportant un bras de référence et un bras à échantillon. L'unité de balayage comprend une pluralité d'ouvertures éclairées par une lumière incidente provenant de la source de lumière. L'unité de balayage produit une pluralité de faisceaux de lumière transmis à l'interféromètre. Chaque faisceau de lumière est divisé pour produire une pluralité de faisceaux de référence et d'échantillonnage. Les faisceaux d'échantillonnage sont balayés sur un échantillon et renvoient les signaux de lumière d'échantillonnage reflétée par le biais du bras à échantillon, combinés aux signaux de lumière de référence reflétée par le biais du bras de référence. Un motif d'interférence ainsi formé est détecté par un capteur d'images et traité de sorte à générer une image numérique de l'échantillon. Selon certains modes de réalisation, l'unité de balayage peut comprendre un réseau de microlentilles. L'invention concerne en outre un procédé de balayage connexe.
PCT/US2013/073704 2012-12-06 2013-12-06 Système et procédé de tomographie par cohérence optique d'imagerie parallèle WO2014089504A1 (fr)

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CN201380063585.5A CN104870930A (zh) 2012-12-06 2013-12-06 并行成像光学相干断层扫描系统及方法
HK15111660.9A HK1210827A1 (en) 2012-12-06 2015-11-26 System and method for parallel imaging optical coherence tomography

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US11243346B2 (en) 2013-06-23 2022-02-08 Eric Swanson Interferometric optical fiber measurement system with multicore optical fiber
US11256080B2 (en) 2015-05-05 2022-02-22 Eric Swanson Fixed distal optics endoscope employing multicore fiber
EP3977915A1 (fr) * 2020-10-01 2022-04-06 Optos PLC Système d'imagerie oct confocal ophthalmique
US11397075B2 (en) 2013-06-23 2022-07-26 Eric Swanson Photonic integrated receiver
US11681093B2 (en) 2020-05-04 2023-06-20 Eric Swanson Multicore fiber with distal motor
US11774743B2 (en) 2016-05-30 2023-10-03 Eric Swanson Few-mode optical fiber measurement instrument
US11802759B2 (en) 2020-05-13 2023-10-31 Eric Swanson Integrated photonic chip with coherent receiver and variable optical delay for imaging, sensing, and ranging applications

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US11243347B2 (en) 2013-06-23 2022-02-08 Eric Swanson Optical fiber system with photonic integrated circuit coupled to multicore optical fiber
US11397075B2 (en) 2013-06-23 2022-07-26 Eric Swanson Photonic integrated receiver
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US11256080B2 (en) 2015-05-05 2022-02-22 Eric Swanson Fixed distal optics endoscope employing multicore fiber
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US11774743B2 (en) 2016-05-30 2023-10-03 Eric Swanson Few-mode optical fiber measurement instrument
US11681093B2 (en) 2020-05-04 2023-06-20 Eric Swanson Multicore fiber with distal motor
US11802759B2 (en) 2020-05-13 2023-10-31 Eric Swanson Integrated photonic chip with coherent receiver and variable optical delay for imaging, sensing, and ranging applications
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