WO1998038907A1 - Instrument d'analyse a balayage optique de tissu vivant - Google Patents

Instrument d'analyse a balayage optique de tissu vivant Download PDF

Info

Publication number
WO1998038907A1
WO1998038907A1 PCT/US1998/004364 US9804364W WO9838907A1 WO 1998038907 A1 WO1998038907 A1 WO 1998038907A1 US 9804364 W US9804364 W US 9804364W WO 9838907 A1 WO9838907 A1 WO 9838907A1
Authority
WO
WIPO (PCT)
Prior art keywords
fiber
lens
optical
housing
imaging
Prior art date
Application number
PCT/US1998/004364
Other languages
English (en)
Other versions
WO1998038907B1 (fr
Inventor
Stephen A. Boppart
Gary J. Tearney
Brett E. Bouma
Mark E. Brezinski
James G. Fujimoto
Eric A. Swanson
Original Assignee
Massachusetts Institute Of Technology
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Massachusetts Institute Of Technology filed Critical Massachusetts Institute Of Technology
Priority to EP98915128A priority Critical patent/EP0971626A1/fr
Priority to JP53882698A priority patent/JP2001515382A/ja
Publication of WO1998038907A1 publication Critical patent/WO1998038907A1/fr
Publication of WO1998038907B1 publication Critical patent/WO1998038907B1/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00163—Optical arrangements
    • A61B1/00188—Optical arrangements with focusing or zooming features
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00064—Constructional details of the endoscope body
    • A61B1/00071—Insertion part of the endoscope body
    • A61B1/0008—Insertion part of the endoscope body characterised by distal tip features
    • A61B1/00096—Optical elements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00163—Optical arrangements
    • A61B1/00172—Optical arrangements with means for scanning
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00163—Optical arrangements
    • A61B1/00174—Optical arrangements characterised by the viewing angles
    • A61B1/00183—Optical arrangements characterised by the viewing angles for variable viewing angles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/07—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements using light-conductive means, e.g. optical fibres
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/41—Detecting, measuring or recording for evaluating the immune or lymphatic systems
    • A61B5/414—Evaluating particular organs or parts of the immune or lymphatic systems
    • A61B5/415—Evaluating particular organs or parts of the immune or lymphatic systems the glands, e.g. tonsils, adenoids or thymus
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/41—Detecting, measuring or recording for evaluating the immune or lymphatic systems
    • A61B5/414—Evaluating particular organs or parts of the immune or lymphatic systems
    • A61B5/417—Evaluating particular organs or parts of the immune or lymphatic systems the bone marrow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/41—Detecting, measuring or recording for evaluating the immune or lymphatic systems
    • A61B5/414—Evaluating particular organs or parts of the immune or lymphatic systems
    • A61B5/418—Evaluating particular organs or parts of the immune or lymphatic systems lymph vessels, ducts or nodes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6852—Catheters
    • 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
    • G01B9/0201—Interferometers characterised by controlling or generating intrinsic radiation properties using temporal phase 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
    • G01B9/02022—Interferometers characterised by the beam path configuration contacting one object by grazing incidence
    • 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
    • G01B9/02049—Interferometers characterised by particular mechanical design details
    • G01B9/0205—Interferometers characterised by particular mechanical design details of probe head
    • 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
    • G01B9/02055—Reduction or prevention of errors; Testing; Calibration
    • G01B9/02062—Active error reduction, i.e. varying with time
    • G01B9/02063—Active error reduction, i.e. varying with time by particular alignment of focus position, e.g. dynamic focussing in optical coherence tomography
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/002—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor having rod-lens arrangements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/04—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor combined with photographic or television appliances
    • A61B1/043—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor combined with photographic or television appliances for fluorescence imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0071—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by measuring fluorescence emission
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B2290/00—Aspects of interferometers not specifically covered by any group under G01B9/02
    • G01B2290/65—Spatial scanning object beam
    • G—PHYSICS
    • G11—INFORMATION STORAGE
    • G11B—INFORMATION STORAGE BASED ON RELATIVE MOVEMENT BETWEEN RECORD CARRIER AND TRANSDUCER
    • G11B7/00—Recording or reproducing by optical means, e.g. recording using a thermal beam of optical radiation by modifying optical properties or the physical structure, reproducing using an optical beam at lower power by sensing optical properties; Record carriers therefor
    • G11B2007/0003—Recording, reproducing or erasing systems characterised by the structure or type of the carrier
    • G11B2007/0009—Recording, reproducing or erasing systems characterised by the structure or type of the carrier for carriers having data stored in three dimensions, e.g. volume storage
    • G11B2007/0013—Recording, reproducing or erasing systems characterised by the structure or type of the carrier for carriers having data stored in three dimensions, e.g. volume storage for carriers having multiple discrete layers

Definitions

  • This invention relates generally to the field of optical imaging and more specifically to the field of optical image guided procedures.
  • adeno carcinoma or in locating voids in multi-layer polymer packages.
  • improved visualization enables new image guided procedures such as guiding an atherectomy catheter to
  • optical imaging offers certain advantages over other approaches because it is non-ionizing, non-contact, and can achieve high resolution.
  • optical imaging techniques including optical coherence tomography (OCT) and
  • OCT optical coherence tomography
  • OCT achieves depth resolution via a combination of the focal properties of the imaging optics used and the coherence properties of the optical' source used.
  • OCT and other interferometric imaging modalities has three fundamental advantages over standard direct detection optical imaging techniques: 1) the ability to achieve nearly shot-
  • 5,321,501 describe several OCT imaging embodiments and their application in ophthalmology.
  • the present forward directing imaging system includes forward directed optical coherence tomography (OCT) in a probe including a scanning mechanism .
  • OCT optical coherence tomography
  • the system uses non-retroreflected OCT and includes a light source, a sample illuminator, a reference arm, a beam splitter, a sample light collector, a detector to
  • a beam combiner positioned to direct light from a sample light collector and a reference arm to a detector where output from the detector is
  • the scanning mechanism includes a motor and a cam
  • the motor causes rotation of the cam moving the lens and optical fiber to orthogonally to the longitudinal axis of the probe housing to scan a sample.
  • a piezoelectric transducer or by a wire around a pivot, pnenumatic devices, or by an
  • the scanning mechanism includes
  • the forward scaning OCT imaging system may be applied in a hand-held probe, or surgical tools such as probes, scalpels, scissors, forceps and biopsy instruments.
  • surgical tools such as probes, scalpels, scissors, forceps and biopsy instruments.
  • Embodiments of these devices include the application of surgical laser fibers.
  • the optical probe is an endoscope used to examine natural
  • the invention contemplates a surgical grinding endoscope which uses a cutting element in the forward or side direction combined with
  • the OCT imaging system is used with a laparoscope to perform diagnostics and surgical procedures within body cavities.
  • laparoscope embodiment also contemplates the use of forward scanning lasers.
  • the imaging system is applied to a surgical microsope for procedures requiring an en face as well as a cross sectional view into the tissue.
  • the imaging system is also applied to a high numerical aperture microscope in yet another
  • Another important embodiment of the invention is for therapeutics such as atherectomy,
  • this invention are implantable to allow for continuous or periodic extraction of information from the tissue site where implanted.
  • FIG. 1 is a block diagram of an embodiment of an OCT imaging system.
  • FIG. 2 is a block diagram of an embodiment of a Non-Retroreflected OCT configuration.
  • FIG. 3 is a block diagram of the modular system configuration.
  • FIG. 4a-i are crossectional views of embodiments of a catheter with forward scanning capabilities.
  • FIG. 5 a and 5b are longitudinal sectional views of embodiments of devices which permit forward
  • FIG. 6 a-f are longitudinal sectional views of embodiments of a catheter that utilizes a fixed lens and movable fiber for forward scanning.
  • FIG. 7 a-f are longitudinal sectional views of embodiments of a catheter that utilizes a fixed fiber and movable lens for forward scanning.
  • FIG. 8a-d are crossectional views of general methods for deflecting imaging beam in a forward direction.
  • FIG. 9a-c are longitudinal sectional views of embodiments of imaging beam characteristics.
  • FIG. 10 is a longitudinal sectional view of an embodiment of a forward-scanning hand-held probe.
  • FIG. 11 is a longitudinal sectional view of an embodiment of a forward-scanning hand-held probe
  • FIG. 12 is a longitudinal sectional view of an embodiment of the integration of a hand-held probe
  • FIG. 13 is a longitudinal sectional view of an embodiment of a forward-scanning hand-held
  • FIG. 14 is a longitudinal sectional view of an embodiment of a forward-scanning laparoscope with
  • FIG. 15 is a longitudinal sectional view of an embodiment of a forward-scanning laser surgical
  • FIG. 16a-c is a longitudinal sectional view of an embodiment of a surgical/dissecting microscope with multiple scan methods.
  • FIG. 17a-b is a longitudinal sectional view of an embodiment of a high numerical 'aperture OCT microscope.
  • FIG. 18a-b is a longitudinal sectional view of an embodiment of a flexible forward-directed optical guidewire/scanning endoscope.
  • FIG. 19 is a longitudinal sectional view and a cross-sectional view of an embodiment of the integration of forward-imaging devices with endoscope accessory ports.
  • FIG. 20 is a longitudinal sectional view of an embodiment of a close-pack fiber bundle with cross- talk reduction.
  • FIG. 21a-c is a longitudinal sectional view of an embodiment of an imaging surgical grinding catheter.
  • FIG. 22 is a longitudinal sectional view of an embodiment of the distal end of a device with an integrated microchip for image acquisition.
  • FIG. 23a-b is a longitudinal sectional top and side view of an embodiment of optical phased array
  • FIG. 24 is a frontal view of anatomical sites for implantable probes.
  • FIG. 25a-d are longitudinal sectional views of embodiments of surgical tools and probes.
  • FIG. 26a-c is a longitudinal sectional view of an embodiment of laparoscopic and endoscopic
  • FIG. 27 is a longitudinal sectional view of an embodiment of a surgical biopsy punch tool.
  • FIG. 28a-c is a longitudinal and cross-sectional view of embodiments of devices for cervical imaging.
  • the imaging engine can be of a variety of embodiments including optical coherence tomography or other interferometric imaging systems, fluorescence and other spectroscopic imaging systems, Raman imaging, diffuse wave optical imaging, two photon imaging systems or combinations thereof.
  • the imaging engine includes the associated imaging system sub-systems
  • light from an optical source 10 is directed to a given position on a
  • the interferometric imaging technique is often of an embodiment where the optical beam directed onto the specimen
  • the delivery system can be from a
  • the detected light is processed in a receiver processor 38 to extract
  • optical properties as a function of depth or other spatial metrics (e.g. location of incident beam on the sample). For instance, a reflectivity profile, or plot of the
  • the probe module may include methods for performing scanning of the radiation pattern. Thus, by performing repeated
  • image information can be obtained.
  • images can be acquired in parallel.
  • Three basic types of OCT imaging engines are known in the art and include: reference-arm scanning, frequency tunable optical source, and optical spectral analysis imaging. In each of these
  • the interferometer 19 and associated optics are used to couple light from the optical source onto the sample and optical reference.
  • the interferometer 19 also couples light after being altered by the sample and optical reference (either delayed, transmitted, reflected, or scattered)
  • the interferometer may contain free-space optics and/or optical fibers. In one embodiment the fibers are single-mode fibers.
  • the interferometer may be of a variety of embodiments including Michelson or Mach-Zehnder configurations. Within the interferometer frequency or phase
  • modulation elements enable en face imaging or enhanced signal processing; dispersion balancing
  • Transverse (including lateral, axial, or radial) scans are acquired using the actuator to scan
  • probe unit For OCT imaging engines, depth (or longitudinal) scans are acquired using one of the three methods mentioned above and described below. The computer controls the interaction
  • the OCT optical coherence tomography
  • images represent information on the microstructural optical properties of a sample. These include index-of-refraction discontinuities, scattering, absorption, birefringence, dispersion, and spectra-
  • the properties can be spatially resolved using a variety of scanning techniques. Such techniques include performing sequential depth scans interlaced with transverse scans or vise versa or the images can be acquired in parallel. Because rapid images can be obtained, the extensions beyond 1, 2, or 3-D imaging are possible with this invention. In particular, by visualizing images over time, functional imaging is possible. For example, the visualization of a beating embryo heart in response to various stimulants can be achieved.
  • a mode-locked, superluminescent or other suitably broad-bandwidth optical source is used and coupled to the interferometer.
  • reflectivity profiles of the sample can be
  • the receiver processing unit 38 can consist of a single
  • a frequency tunable optical source is coupled to the interferometer.
  • the receiver processing unit 38 includes photo-detectors which receive signals
  • the source is again a broad bandwidth source coupled to an interferometer. Reflections from the sample/specimen and
  • reference reflection(s) will optically interfere at the receiver, which is an optical spectrum analyzer.
  • the optical spectrum will consist of fringe profiles, the contrast of which is proportional
  • processing algorithms such as Fourier analysis the reflectivity or other interferometric profile of the optical properties of the sample can be obtained.
  • processing algorithms such as Fourier analysis the reflectivity or other interferometric profile of the optical properties of the sample can be obtained.
  • spectral analysis including single or multiple gratings or prisms combined with
  • the source is a Raman pumped master-oscillator power amplifier (MOP A) source.
  • MOP A Raman amplifiers are commonly used in Wavelength Division Multiplexing (WDM) optical
  • pulsed pump laser one can create a broadband optical power amplifier at the Stokes shift away from the pump laser (- 13 THz). If this amplifier is seeded with a lower power semiconductor,
  • Raman pumps are spaced by approximately the
  • Raman gain bandwidth then the bandwidth of the amplifier will be broadened, approximately, by a factor of two. Additional pumps can be used to further broadened the amplifier bandwidth and the gain spectra associated with the individual pumps can be tailored to shape the gain spectra by tailoring their respective pump powers.
  • the master oscillator can be tailored to be very broadband by using in-fiber Bragg or long
  • the pump laser can be derived from a cladding pumped Yb or Nd fiber or other rare earth doped fibers pumped from broad area or other semiconductor lasers as is known in the art. These lasers lase at -1.1 ⁇ m and they can be used to pump Er:Yb fiber to create a Raman pump laser at a wavelength
  • optical source 10 used
  • This aiming laser can be directly visualized by a human operator using a hand-held probe or surgical microscope or other
  • a special imaging camera capable of detecting radiation unseen by the human eye, can be used to visualize the optical source radiation.
  • the visible aiming laser or the imaging from the special camera can be used to feed the
  • the optical source 10 is coupled to a 2:2 fiber optic splitter 14 containing paths to a reference mirror 18 (corner cube) and to a probe unit 22 that illuminates
  • the beam waist of the illumination port 26 of the probe unit 22 is offset from the beam
  • the receiver processor 38 whose output is analyzed by a computer 42.
  • embodiments often a large surface reflection, at, for example, an air/skin interface, can mask all
  • This non-retroreflection embodiment may be
  • optical imaging engines can be used with the scanning and probe modules described in this invention. These include: transillumination techniques, diffuse-wave
  • Diffuse-wave imaging is a fairly new optical imaging technology that uses
  • Diffuse-wave imaging has
  • An interferometer is not required for diffuse-wave imaging.
  • the source is often a
  • the receiver is a direct detection receiver that measures
  • Images of the specimens' optical properties can be obtained by plotting the phase or magnitude of the detected optical intensity as a function of scan location. As with the OCT imaging engine, the images are displayed and used for diagnosis or in guiding therapeutic procedures.
  • Laser induced fluorescence imaging is another attractive imaging engine technology
  • Fluorescence imaging is based on using short wavelength visible light to excite native fluorescence (or fluorescence from selectively bound exogenous chromophores) in tissues. Differences in the biochemical constituents of the tissue will produce differences in fluorescence
  • the optically accessible tissue surface or as an image of the tissue surface Differences in fluorescence are then interpreted with an algorithm in order to differentiate the pathology of the tissue.
  • the desired endpoint is to assess the presence of dysplasia or cancer.
  • An interferometer is not required for this engine technology nor are single-mode optical fibers.
  • optical spectrum analysis of one or more regions tuned to the fluorescence wavelength As the incident excitation radiation and collected fluorescence radiation is scanned, optical images of the
  • probe-module scanning designs can be use as
  • fluorescence imaging engine could be used simultaneously over the same single-mode probe
  • the OCT source and the short wavelength excitation laser could be combined using a fiber optic wavelength division multiplexer (WDM) coupler and the collected OCT light
  • the probe module could contain two
  • one single-mode fiber for OCT imaging and one single or multi-mode fiber for fluorescence imaging could be used to direct the respective radiation patterns.
  • Common or separate scanning elements could be used to direct the respective radiation patterns.
  • Scanning is performed using a
  • image data and all associated imaging sub-systems including optics, electronics, motors,
  • controllers and computers to control the incident light, detect the image signal, process the
  • the Beam Delivery/Scanning Module 12 which includes the general forward-scanning (or other types of
  • scanning e.g. radial, lateral, or axial
  • Various methods are used to scan or translate the optical beam in order for the system to collect data and form an image.
  • These general forward-scanning methods include any number of beam delivery or
  • probe modules including, but not limited to hand-held probes, laparoscopes, surgical microscopes, high numerical aperture or standard microscopes, forward-scanning flexible catheters, fiber
  • the forward-scanning method may:
  • catheter function as a phased array; or function as an attachment which inherently adds to the functionality of the research or clinical instrument or tool as in the hand-held probe attached to
  • An OCT Scanning Engine Module 11 includes a light source, axial (depth or range)
  • the three engines described above permit axial ranging to be performed within the optical system and components.
  • the reference-arm scanning, source frequency scanning, and spectral analysis OCT all permit axial ranging, but perform this by distinctly different methods.
  • Each of the three methods may be used in conjunction with any of the beam scanning methods.
  • optical scanning engines including other interferometric imaging
  • fluorescence and other spectroscopic imaging systems fluorescence and other spectroscopic imaging systems, Raman imaging, diffuse wave optical imaging, two photon imaging systems or combinations thereof.
  • the OCT Scanning Engine Module 11 and the Beam Delivery/Scanning Module 12 are controlled by a Control Computer Module 13 typically including a central computer which is responsible for synchronization, generating drive waveforms, generating necessary trigger pulses,
  • control computer may also function as part of the last module, the Nisualization Module, although this may be a
  • the Nisualization Module 15 receives the image data from the Control Computer Module
  • Nisualization may be performed with an OCT image monitor and/or a standard video monitor
  • a screen containing all the system parameters and settings to control the operation of the system 2) a screen containing all the system parameters and settings to control the operation of the system.
  • the video image is the en face surface view
  • the OCT image is a cross-sectional profile, en face, or
  • the video technology can permit integration with heads-up display allowing the user to view these
  • Heads-up display concepts can be integrated within the eyepieces of the microscopes allowing the user to visualize the OCT image and the cross-sectional, sub-surface morphology of the specimen without having to remove his/her eyes from the microscope and
  • Video technology may also permit such images to be overlaid thereby
  • the visible aiming laser described previously 1 can also be displayed in the Visualization Module 15. This visible aiming beam can be displayed on the screen containing the video image to allow registration of the OCT and video images by the user.
  • the Therapeutic Engine Module 17 is associated with medical, scientific, and industrial
  • This module 17 uses the information output from the Visualization Module 15 to guide therapeutic procedures. This guidance can be through a human feedback aided by the Visualization Module 15 or autonomous via computer or
  • Module 17 itself.
  • Example applications where this imaging guide therapy would be beneficial include guidance of mechanical or laser-based atherectomy catheters, placing stents, inflating balloons using percutaneous angioplasty catheters, operating microsurgical tools during laparoscopy procedures, etc.
  • Forward-directed optical scanning can be performed via a number of methods. These methods are then incorporated into various instruments. In the most general description, the optical device will involveone or more optical fibers to deliver the light to the sample, focusing
  • optics to focus the beam to the desired spot with a predetermined spot size and confocal parameter, and a means of translation to enable the acquisition of adjacent axial scans for the
  • Scanning methods can be generally, categorized as one of five general principles: 1) methods which move the fiber/lens as a single
  • the forward- scanning optics and mechanicals are contained within, but not limited to, a cylindrical enclosure 50 that is small in diameter (-1-10 mm) such as a catheter, endoscope
  • This enclosure 50 may be rigid or flexible and readily integrated into the instruments discussed in later sections.
  • the distal end of the enclosure 50 consists of anoptional transparent window 54 that permits the optical beam to be transmitted with little attenuation while protecting the optics and mechanics from fluids and contaminants. Such an enclosure allows easy
  • the optical imaging plane Distal to the tip of the enclosure lies the optical imaging plane.
  • this image plane may be the plane where the optical beam is focused to a minimum spot size. This plane should fall within the region of interest for
  • Figure 4a describes an apparatus for mechanical translation of the fiber/lens unit.
  • single-mode fiber 58 is fixed to a GRIN lens 62 or a small diameter lens such as a ball lens at a given separation. This separation specifies the working distance to the focal plane, the spot size,
  • the lens can be fabricated directly into the fiber forming a single focusing unit.
  • the fiber/lens unit lies within a track (not shown) which permits
  • a spring-apparatus (not shown) returns the fiber/lens unit back to its original location when not displaced by the elliptical knob 70 .
  • the motor unit 61 may also be located at the proximal end of the device with
  • Figure 4b translates the fiber/lens unit with a piezoelectric cantilever 74.
  • a piezoelectric cantilever 74 Such a cantilever
  • the cantilever 78 does not have to be made of piezoelectric material. Rather, piezoelectric stacks may be used in conjunction with a metal or flexible material cantilever .
  • the cantilever 78 would be flat to prevent twisting and thin in the axis of flexure to
  • Displacements can be increased by progressively locating the piezoelectric stack closer to the cantilever site of attachment.
  • the cantilevers piezoelectric or otherwise
  • they may be oriented
  • one or more movable wires or guides 90 are used to mechanically displace in a push/pull manner the fiber/lens unit in an arc about a pivot point 94.
  • the movable wire 90 is housed within the cylindrical enclosure along with the single-mode optical fiber 58.
  • the translation of the fiber/lens unit 63 is dependent on the point of attachment of the wire 90
  • Figure 4d utilizes pneumatic principles to displace the fiber/lens unit 63 within the enclosure.
  • two or more air/fluid-filled bags 96, 96' are used in a complementary fashion to
  • a rigid tube 100 can house the fiber 58 and lens
  • a translation track 104 is located near the distal end of
  • This track is offset at an angle with respect to the axis of the cylindrical enclosure 50.
  • fiber/lens unit 63 to be translated at an angle, as well as in the transverse direction. Such a scan
  • Figure 4f illustrates how electrostatic/magnetic principles can be applied to laterally translating the fiber/lens unit.
  • the lens 63 is coated with a metalized material which can be
  • electrostatically charged plates 108 can be used to translate the fiber/lens unit 63.
  • the metalized lens 63 will be attracted to this region and hence, be displaced in the lateral direction.
  • the metalized fiber/lens 63 unit is attached to a flexural pivot (not shown). Very high lateral velocities can be achieved by rapidly alternating the charges on the
  • a secondary imaging fiber bundle 120 an optical imaging processing mechanism at distal end 124
  • the sensing mechanism shown in Figure 5b is a position sensing rolling mechanism 125 analogous to the computer
  • the device is physically placed on the specimen or sample to be imaged and translated
  • a flat or angle- cleaved optical fiber 58 is located on the translation mechanism.
  • the fiber 58 is then translated on one side (in the image plane) of the lens 62.
  • the focal region will not lie in a single image plane, but will sweep out an arc.
  • the focal spot size will change.
  • a lens system can be manufactured which reduces the aberrations which
  • Figure 8a utilizes a rotating cable 128 within the cylindrical enclosure 50.
  • the optical fiber 58 is contained within and is protected by the cable
  • an offset GRIN lens 62 (or other type of lens) is metered with respect to
  • the optical fiber 58 Because the lens axis is offset with respect to the optical fiber 58, the emitted
  • the beam is not focused on axis with the fiber. Instead, the focus occurs at an angle which is
  • Drive unit 60 may be implemented in a number of ways including mechanical linkage from a motor to a rotating
  • This forward-directed scanning method has the advantage that the device can be incorporated into flexible instruments or catheters.
  • the lens can be mounted on-axis
  • a second method, illustrated in Figure 8b, describes a technique for arbitrary scan patterns
  • This method also utilizes an internal cable 128 and an additional internal
  • the sheath 132 which rotate in counter-directions with respect to one another.
  • the outer cylindrical enclosure 50 remains fixed.
  • the most inner element is a metal cable 128 which houses and protects an optical fiber 58 within its core.
  • the distal end of this includes a circular prism 136 (trapezoidal in cross section).
  • External to this cable/fiber/prism 128, 58, 136 is a counter-rotating
  • arbitrary scan patterns can be produced.
  • the emitted beam is focused by a lens 152 prior to exiting the cylindrical enclosure 50.
  • an alternate embodiment (not shown) is to have one drive
  • variable cone angle can be rigidly mounted to the fiber prior to
  • Figure 8c illustrates the use of a beam-deflector element 148 placed between a pair of lenses 153, 153'.
  • the proximal lens 153 directs the light from the fiber 58 through the beam-
  • the deflector element 148 After passing through the beam-deflector 148, a second lens 153' is used to focus the light into the image plane.
  • the beam-deflecting element can consist of, but is not limited to, liquid-crystal, electro-optic, or acousto-optic modulators. Note that alternative
  • embodiments can use different lens arrangements depending on the aperture size and type of beam-deflector used.
  • the design illustrated in Figure 6d utilizes a two-dimensional miniaturized deflector 146 such as an electrostatic deflector that can be microfabricated on semiconductor or other substrates
  • the imaging beam exiting the fiber is reflected by a prism/mirror 150 on to
  • This design has the potential for arbitrary scan patterns generated at high speeds.
  • Other types of deflectors such as electromagnetic, piezoelectric, etc., can be use as well in this configuration.
  • beam deflection can be accomplished by translating or displacing a mirror in front
  • Side-directed radial scanning can be performed by using a fold mirror and rotating the
  • the inner cylindrical unit may be rotated about the central axis while the outer cylindrical unit is held stationary. This permits linear scanning at arbitrary angles in order for the user to choose which angle is most suitable for a particular application.
  • the acquired linear scans would form a spoke-like pattern about a center point.
  • three-dimensional data sets can be acquired.
  • the first is called FOCUS POSITIONING (Fig 9 A) which is the axial displacement/adjustment of the beam focus without changing any of the beam
  • FIG. 9b VARYING (FIG. 9b) which implies changes in spot size, depth of focus, and working distance, and finally, FOCUS TRACKING (FIG. 9c) which refers more specifically to the OCT imaging
  • the beam spot size could be increased or decreased (hence the transverse resolution
  • One method involves translating the entire apparatus in the z (depth) direction either toward or away from the specimen. This repositions the focus
  • Translation can be performed manually with a micrometer adjustment or via a
  • the two lenses 156, 156' can be varied without affecting the beam characteristics.
  • telescopic arrangement is important for several implementations including endoscopes where it is
  • Both focus positioning and focus varying are likely to be used in combination.
  • large regions of a specimen or sample may be scanned at lower resolutions and with a
  • Focus varying can be implemented to reduce the spot size (increase resolution) and hence, reduce the depth-of-field. At this point, focus positioning would be
  • Focus varying is illustrated in FIG. 9b.
  • lens 156 is translated and changes spot size, depth field, and working distances.
  • zoom lens configurations Several alternative embodiments are possible such as zoom lens configurations.
  • a high numerical aperture objective or lens and a small beam spot diameter are required to achieve sufficient lateral resolution.
  • This small spot diameter has a correspondingly small depth-of-field or depth-of-focus as is known in the art.
  • focus tracking must also be
  • Figure 9C illustrates an example of focus tracking.
  • ⁇ L is the displacement of the focusing
  • ⁇ F is the displacement of the focusing spot within the specimen 164
  • ⁇ R is the
  • ⁇ R can be a complicated non-linear equation depending on the index of refraction profile
  • the index profile of the sample is approximately uniform and given by n sam pi e , and small angle approximations to the focused light
  • the liquid volume will adjust to maintain a constant focal
  • mirror 160 can remain stationary.
  • Another approach for focus tracking that can easily accommodate more complex sample index profiles is to perform transverse priority scanning and adjust the reference mirror location to
  • the adjustment can be manual in response to a human operator visualizing the real-time OCT image or it can be automated by maximizing the detected
  • imaging thick specimens e.g. histological
  • one algorithm is to block the
  • the reference optical signal uses the OCT system in a direct detection confocal microscope.
  • a highly reflecting substrate e.g. a mirror
  • the specimen is then scanned manually or in an automated way to profile the back scattered signal power in search for the weaker reflection off of the more distant mirror.
  • the OCT system is
  • the focusing lens is then placed at the back surface (mirror) reflection and the OCT reference reflection optical path length is again
  • the lens location is stepped and the reference arm is swept and this
  • a hand-held probe has applications in, but is not confined to, the medical field, materials
  • a forward-directed imaging probe offers the advantage that no portion of the
  • the instrument has to come in contact with the tissue prior to obtaining imaging data. This is in contrast to devices that image in the radial or transverse direction.
  • the catheter or device
  • the hand-held probe can be used to access any external region of the human body, or any external orifice, without have the
  • the fiber path lengths between the sample and reference arms must be matched or otherwise compensated for dispersion
  • the OCT imaging engine, to which is connected the hand-held probe can be of any reasonable
  • a hand-held probe can be used to image any external region of the human body while the patient stands, sits, or lies in a bed.
  • the use of micro-optics the
  • distal portion of the device can be made very small and able to be inserted short distances into
  • FIG. 10 One implementation of a forward-scanning hand-held probe is shown in Figure 10. This design utilizes a piezoelectric cantilever 74 to displace the fiber/lens unit 63 in an arc, however,
  • the design is not limited to the use of cantilevers and may incorporate any of the general methods described herein.
  • the overall dimensions of this device are no larger than a standard ink pen,
  • the cylindrical enclosure 50 is made of a protective and insulating plastic that shields the cantilever 74, fiber 58, and lens 62 from
  • the piezoelectric bimorph material is centered within the cylindrical enclosure 50 probe
  • the proximal end 79 of the cantilever 74 is fixed to a micrometer 168 to vary the location of the imaging beam focus with respect to the
  • the tube also protects the small lens 62 and single-mode fiber 58.
  • the lens 62 used in this design is a GRIN (GRadient INdex) lens which allows effective focusing of the light emitted from the fiber while maintaining a small outer diameter.
  • the small cylindrical GRIN lens 62 easily fits within the cylindrical tube 172. To reduce the degree of -optical back-
  • the fiber can be
  • angle-cleaved and the GRIN can be angle-polished.
  • the fiber is attached to the GRIN lens using ultraviolet cured optical cement at a pre-determined distance. This distance determines the
  • focusing properties of the emitted light such as working distance, spot size, and confocal parameter.
  • Alternate lens embodiments include using fiber up-tapers with an integrated polished
  • lens or other lenses that are known in the art.
  • the distal end of the cylindrical enclosure has a clear plastic cap 176 that is removable after contact with biological tissue.
  • This cap serves four major purposes: 1) to allow the probe to be placed in contact with the tissue specimen or material sample thereby fixing the image plane
  • the probe can move with the tissue or sample, 3) the clear plastic permits the user to visualize where
  • the replaceable cap maintains cleanliness and avoids transmission of bacteria or viruses between
  • arm 172 increases the displacement to 2 mm. Larger displacements can be achieved by increasing the applied voltage (while remaining below the damage threshold of the material) and increasing the length of the extension arm.
  • FIG. 11 A second hand-held probe design is illustrated in Figure 11. This design utilizes similar cantilever-displacement principles, but offers an interchangeable lens 180 to vary the magnification of the device. Instead of affixing a GRIN lens to the fiber, the fiber 58 alone is
  • fiber 184 is collimated by lens 152 and directed toward a second, more distal lens 180 where it is focused at a forward imaging plane, within the sample to be imaged.
  • the pair of lenses 152, 180 are collimated by lens 152 and directed toward a second, more distal lens 180 where it is focused at a forward imaging plane, within the sample to be imaged.
  • the pair of lenses 152, 180 are collimated by lens 152 and directed toward a second, more distal lens 180 where it is focused at a forward imaging plane, within the sample to be imaged.
  • magnification is determined by the ratio of the focal lengths
  • magnification Other imaging systems may also be used.
  • the distal cap 176 and lens 180 are interchangeable by replacing unit 190 or 176 thereby permitting various imaging systems
  • the interchangeable cap 176 and lens 180 are disposable and serves to protect the remainder of the probe from liquids and contaminants. This
  • micrometer 168 represented in Figure 11 is
  • directed imaging probe 164 is comparable in size to a surgical scalpel 186, the two can be
  • Two-dimensional imaging can be integrated or multiple image planes can be imaged simultaneously by interweaving the scan
  • Images obtained with the imaging probe will permit the surgeon to view the substructure and avoid sensitive structures such as nerves or vessels or assist in determining locations of tumors and identifying tumor margins prior to resection.
  • OCT may be configured to perform laser Doppler velocimetry of the tissue prior to incision. Images can be generated
  • the scalpel 186 and probe 164 could angle the beam more closely to the tip of the scalpel 186. Also the scalpel blade could be rotated 90° with respect to the axis of imaging, and the
  • probe could be located below the scalpel so that the cutting axis is imaged prior to incision.
  • one or more optical fibers can be positioned within the scalpel blade itself (for example in
  • a blade made of optically translucent material or in a more conventional metal blade with appropriate imaging ports (not shown) with the tip of the fiber located at the tip or along the edge of the scalpel blade.
  • imaging can be performed whereas with lower numbers of fibers, isolated depth information can be acquired.
  • Single axial scans can be
  • the lenses If the fibers are in near contact with the specimen or sample, the lenses to focus the
  • Such fibers may be located within a blunt- tipped probe (see Figure 25a) which is commonly used during surgical procedures to move tissue
  • the blunt probe is typically held in the opposite hand as the scalpel and frequently used to point to and identify tissue.
  • an entire micro-scanning device can be incorporated onto the end of the scalpel which scans the beam in an angular pattern along the incision plane.
  • an entire micro-scanning device can be incorporated onto the end of the scalpel which scans the beam in an angular pattern along the incision plane.
  • high power continuous wave lasers or high energy pulsed lasers can be integrated with the OCT imaging system to replace the surgeons scalpel.
  • High power or high energy laser light can effectively disrupt biological tissues.
  • High power or high energy laser light can effectively disrupt
  • Figure 13 illustrates the concept of
  • Each fiber 58, 59 could be translated with a piezoelectric
  • each of the fibers 58, 59 could be attached to the same piezoelectric cantilever 74, 74' or the surgical laser fiber 59 could
  • Both the OCT imaging beam and the high power/energy laser radiation may be propagated down the same optical fiber permitting precise registration between OCT image and location of laser surgical procedures. This design will enable a single, integrated hand-held device
  • This configuration also permits the acquisition of images prior to, during, and immediately following the delivery of the laser
  • the high power laser could be delivered using the same single mode fiber used for OCT, then wavelength selective beam splitters/couplers (not shown) or fast optical switches (not shown) could be used to
  • a small pair of orthogonal galvanometers (not shown) can also be incorporated at the proximal end of the hand-held probe
  • the internal scanning mechanism can be configured to
  • the design of the forward- scanning hand-held probe represents a general method of transverse displacement that is modular in design. Using the probe to transversely displace a
  • a laparoscope is an optical device that is used typically in medical applications to visualize tissue surfaces with magnification at a remote internal site.
  • the concept of laparoscopic surgery has contributed to minimally invasive surgery; the idea that surgical procedures can be
  • the laparoscope 192 consists of a rigid cylindrical enclosure 50 1-2 cm in diameter and 10-50 cm in length.
  • the proximal end 200 contains optics
  • a CCD camera 194 can be mounted at the proximal end 200 with the en face image of the tissue
  • white-light fiber-optic bundles (198) that run parallel to the imaging optics which provide illumination of the tissue surface.
  • Typical surgical procedures using laparoscopes involve inflating the human abdominal cavity with a gas to provide space to visualize internal organs and
  • Sub-surface imaging can significantly complement the en face imaging that is currently performed
  • the en face imaging significantly complements the sub-surface OCT imaging by allowing the user to simultaneously visualize the
  • Figure 14 illustrates the optical design of a forward-
  • proximal end 200 At the proximal end 200 are optics which permit the simultaneous en face viewing and OCT imaging utilizing the same optics along the length of the laparoscope.
  • transverse scanning mechanism (not shown) is employed based on either those described in Figures 4-8, galvanometer scanners, or the modular concept of the forward scanning probe.
  • proximally located scanning elements can be extended to two dimensions and permit arbitrary scan patterns at the distal end 204 of the laparoscope. This arbitrary pattern can be
  • the CCD imaging camera 194 can display the scan location, pattern, and
  • a transversely scanned beam is focused by a lens 152 and fully reflected by a beam splitter 14 which transmits visible wavelengths, but reflects near
  • the OCT imaging beam is focused at the image plane of the laparoscope relay optics 202.
  • the relay optics 202 consists of either a series of GRIN or relay lenses or a
  • translations of the OCT beam focus in the image plane are relayed as translations in the object plane where the tissue sample is located.
  • an alternative to transverse scanning is to locate a angular scanning device(s) in a pupil plan at the distal end of the laparoscope.
  • Rod lenses are
  • An integral pitch length rod lens will relay a non-inverted image from one face to the other. In this case, a beam which is focused into the proximal end of
  • the rod lens will be focused at the distal end as if the rod was of zero length.
  • the image at the opposite rod face will be
  • these non-integral pitch length rod lenses are used
  • lenses can be small standard lenses, ball lens, or additional GRIN lenses which can be attached directly to the rod lens.
  • the magnification of the lens/rod lens of the laparoscope sets the resolution and depth-of-
  • Focus positioning can be performed by
  • an eyepiece Referring again to FIG. 14 for simultaneous visualization of the scan location, an eyepiece
  • lens 151 is used to image the image plane, through the beam splitter 14, on to either the human eye or a CCD 194 camera.
  • White-light illumination is delivered through multi-mode fibers 198
  • imaging beam e.g. 1300 nm
  • visible wavelengths « 650 nm
  • relay optics 202 results in non-coincident image/object planes. This, however, can be compensated for by adjusting the location of the eyepiece 151 and focusing lens 152 located at
  • the object planes for the two wavelengths are made to coincide.
  • the proximal end there will be two image planes,
  • each wavelength can effectively be relayed down the laparoscope 192 to a single coplanar
  • a chromatic optical element(s) can be used in the common path to maintain a common image plane.
  • one modification includes the addition of a second beamsplitter 14' to allow the high-energy/power light to enter the relay optics 202 and be
  • focal lengths of the eyepiece 151 and image beam focusing lens 152 are lengthened.
  • yet another embodiment has the surgical laser integrated into the OCT imaging port.
  • the surgical laser can be integrated via a WDM coupler (or other means) to deliver the surgical light to the
  • This integrated laparoscope design will combine the ability to visualize intra-abdominal contents or other internal body structures via minimally invasive surgical procedures with sub ⁇
  • Forward-directed scanning can be integrated with existing surgical or dissecting microscopes to permit imaging of an arbitrarily oriented sub-surface tomographic plane to be
  • NA numerical aperture
  • microscope is not only limited to medical applications, but is useful when acquiring
  • infrared imaging beam can be captured and stored on either video tape or digitized and stored on
  • Figure 16a The concept of the forward-scanning surgical microscope 210 is illustrated in Figure 16. Three scan methods are shown. In Figure 16a, the optical fiber 57 from the sample arm of the
  • OCT imaging engine is inserted into a collimator 67.
  • the collimated beam is directed through a
  • scanners enable the forward-directed imaging beam to be scanned in arbitrary patterns on the specimen or sample. This arbitrary pattern also enables the acquisition of multiple cross-sectional
  • a beamsplitter 14 mounted at 45° redirects the near infrared imaging beam and the visible aiming beam downward
  • the beam splitter 14 is coated to reflect the imaging and aiming beam wavelengths while allowing other visible wavelengths to transmit.
  • the focusing lens 152 will focus the imaging and aiming beams at two different locations. Since the visible aiming beam is only used to trace the location of the imaging beam, its focal position is relatively insignificant.
  • FIG. 16b A second method for forward-scanning is shown in Figure 16b. This concept reiterates the modularity of the forward-scanning instruments. The methods previously can be used to perform forward-directing scanning beneath a surgical/dissecting microscope.
  • the cylindrical enclosure 50 or probe 164 can be attached to the scope 210 to place the forward imaging plane
  • the probe 164 can be positioned at an angle with respect to the imaging axis of the microscope 210.
  • the probe 164 can be placed within 10-20° of the microscope axis if the dimensions
  • a fold mirror (not shown), similar to the beamsplitter in Figure 16a can be used to allow a freely held probe to be positioned horizontally
  • Linear scans at arbitrary angles can be obtained by rotating the forward-directed imaging probe 164 about its axis. If the scanning
  • stage 217 and/or and imaging probe 164 can be rotated about a fixed point on the specimen to
  • two-dimensional scanning can be performed by incorporating multi-axis cantilevers or other two-dimensional displacement mechanisms.
  • the confocal parameter of this device is large, focus varying and focus positioning can be incorporated to improve the flexibility of the device and its ease-of-use when integrated with the microscope 210.
  • a visible aiming laser could be included in the probe unit 164 to easily facilitate
  • the microscope can be designed with a small monitor 167 to allow the OCT image to be seen directly through the eyepiece 218 so a surgeon/operator may remove the probe 164 and freely move it
  • the hand-held probe 164 may contain a therapeutic device such as discussed with respect to figures 12 and 13.
  • FIG. 16c the same axis of the microscope 210 is shown in Figure 16c.
  • This design utilizes the piezoelectric cantilever 74 described in earlier sections.
  • the cantilever 74 is attached to a translation stage 214
  • a fiber/GRIN lens unit 63 is attached at the end of the cantilever 74 so the
  • optical imaging beam is directed downward toward specimen.
  • This unit can be positioned
  • a second stage (not shown)can be used to
  • the translation stage 214 can be used to acquire multiple arcs and construct a 3-D data set. Positioning this design beneath a
  • stereo-microscope does limit the view of the sample or specimen to be imaged.
  • the stereo-microscope does limit the view of the sample or specimen to be imaged.
  • the profile of the cantilever 74 and GRIN lens 63 can be made very thin and if placed far enough away from the focus of the microscope imaging optics, then the cantilever 74 will not be distracting to the user.
  • cross- sectional image obtained with the OCT or other type of imaging engine can be overlaid or otherwise combined so that a human user can simultaneously view both images through the eye
  • NA numerical aperture
  • microscopes are higher than in the surgical/dissecting microscopes, typically between 50-400X.
  • the numerical apertures for these objectives is higher ranging from 0.1 to 0.5 and higher.
  • high NA microscope is to allow the precise positioning of the imaging beam on the specimen or
  • Focus tracking permits the coherence envelope of the OCT source to be continuously aligned with the focal region of the microscope objective and hence, collect image information only within 'the confocal
  • the focus depth in the specimen is not simply related to any
  • custom generated waveforms will be generated to focus track inside a specimen.
  • a high speed dynamic feedback system can be used to compensate as imaging is performed.
  • Figure 17 illustrates the integration of forward-directed imaging with a high NA
  • microscope 222 Commercial microscopes have been designed to provide several access ports
  • Typical ports include the camera port
  • the port 226' designed for direct
  • galvanometer scanning mechanism 206 to scan the imaging beam through the direct illumination
  • FIG. 17b a galvanometer-based scanning mechanism 206' in an objective mount
  • the sample to be imaged is placed on the stage 214 of the microscope 222.
  • the stage 214 is raised or lowered to position the focus of the imaging beam within the sample as well as to focus the image for visualization through the eyepieces 218.
  • a monitor could also be added analogous to 167 in FIG. 16.
  • the optical fiber 57 from the sample arm of the OCT imaging engine is attached to a connectorized fiber collimator 238 which collimates the imaging beam before being
  • the orthogonal galvanometers 206 allow arbitrary scan patterns at the object plane of the microscope 222 as well as for acquiring
  • the collimated beam passes through the
  • the collimated imaging beam is focused by an infinity-corrected
  • microscope objective 234 which is anti-reflection coated for the wavelength of the imaging beam.
  • the advantage of this implementation is the inconspicuous location of the forward-scanning
  • the second implementation shown in Figure 17 utilizes micro-galvanometer scanners
  • a beam splitter 14' designed to reflect the imaging and the aiming beams. If the
  • a negative lens 158 can be placed within the optical path of the microscope to correct for the
  • the advantage of this implementation is the ease of access for a wide variety of microscopes and the rapid installation prior to use. In both implementations, because the imaging wavelength is out of the visible spectrum, specially coated optics and objective lenses are required. These, however,
  • scanning is performed with depth priority. That is, the beam is positioned at one location via a two-dimensional scanning mechanism while the OCT engine varies the effective path length between the sample and reference arms of the interferometer in order to collect data in depth (z direction). The scanning mechanism then repositions the beam and another axial depth
  • Imaging can also be performed with transverse priority by keeping the axial position fixed during a single transverse scan and then stepping in depth as subsequent transverse
  • Rapid transverse scanning can readily be performed with galvanometers and mirrors.
  • the OCT imaging embodiment can be extended to include non- retroreflected imaging embodiments as described with respect to Figure 2.
  • the illumination could be scanned from above the sample and the detection light could be scanned as
  • the illumination pattern could be stationary and only the detection
  • a flexible endoscope (a type of laparoscope) can be use to image in non-vascular tissue and a flexible catheter or guidewire can be used for intravascular imaging.
  • the concept of forward-scanning can be extended to devices such as these designed to access remote sites that
  • catheter, or guidewire sheath are two imaging techniques which are used to provide both an en
  • sheath is designed for en face imaging and is performed through a sealed transparent tip 254 located at the distal end 254 of the device.
  • a fiber bundle and lens combination 258 is used both
  • this fiber bundle 258 is used to visualize where OCT imaging is being performed by observing where the visible scanning beam is located.
  • the second imaging technique contained within the sheath is designed for OCT or other
  • second sheath 262 Contained within an inner, second sheath 262 is a
  • a metal pin 270 is located at the distal end of the cable and is displaced from the center of the cable axis. This metal pin 270 inserts into a groove 274 at the base of a pivoting GRIN, ball, or small lens housing 280.
  • the GRIN lens 62 is located at the distal end of the housing 280, over the site where the housing pivots. In one embodiment a
  • single-mode fiber 58 runs parallel to the sheath 262 and cable 266 and inserts into the GRIN lens housing 280 where it is fixed to the GRIN lens 62 at a given distance.
  • the fiber 58 may run inside the speedometer cable with appropriate sheathing to protect it (not shown). The fiber/lens separation and the lens characteristics determine the beam focusing properties of the
  • endoscope, catheter, or guidewire can be varied as in focus varying techniques.
  • the endoscope, catheter, or guidewire can be varied as in focus varying techniques.
  • GRIN lens housing 280 is free to pivot about an axis located at the GRIN lens 62. As the cable 266 is rotated at the proximal end 256 of the endoscope 250, catheter, or guidewire, the rotation is translated to the distal end to drive the GRIN lens housing 280. The displaced, rotating pin 270
  • GRIN lens housing 280 to pivot back and forth.
  • the appropriately shaped elliptical grove will achieve a linear sweep of the
  • forward- scanning light Alternative groove designs may be circular and implement sinusoidal forward scanning of the emitted light from the endoscope.
  • the linear (transverse) scanning of the forward-directed light is preferred since the dwell time (and hence signal-to-noise) on each
  • transverse pixel is constant.
  • One method to achieve this is to have the cable 266 rotated at the proximal end 256 at a constant angular velocity.
  • the off-axis metal pin 270 from the perspective of the GRIN lens housing 280, is translated in one plane in a sinusoidal manner. To convert this
  • Multidimensional data sets can be acquired by rotating the entire endoscope 250, catheter, or guidewire within the lumen or cavity and collecting multiple pie-shaped cross-sections about a single central axis.
  • Forward-directed optical image data can be acquired without transverse displacement by
  • optical fiber 58 is located within the core of a metal guidewire or guidewire 284 made of other material.
  • the distal end of the fiber 58 has some means of focusing the light into the specimen either by a molded, integrated, fiber lens or an attached micro-GRIN lens (not shown).
  • Guidewires are used in nearly every catheter-based procedure to define the path of the catheter through the lumen. Often, the procedure is performed without visualizing via ultrasound
  • the single axial ranging data can provide information regarding the tissue type and structural morphology distal to the end of the guidewire and reduce the likelihood of forcing the guidewire through sensitive areas. Note that in addition to this design housing only one single-mode fiber, multiple
  • fibers bundled packed in a line or in two dimensions could be utilized to provide some imaging in
  • Each fiber could be connected to a separate imaging engine or scanned sequentially (using an optical switch or angular scanning optics) at the distal end.
  • outer diameters range from 1-3 mm for the flexible forward-scanning endoscope, catheter,
  • Forward-directed imaging using a flexible fiber bundle 288 is another embodiment of this invention and is shown in Figure 20.
  • the flexible bundle 288 is composed of a large number of
  • proximal 292 and distal 294 ends of the bundle are maintained which implies that a scan pattern at the proximal end 292 is accurately represented at the distal end 294 of the bundle.
  • a previous attempt to perform forward-directed imaging through a fiber bundle using low-coherence interferometry resulted in moderate to significant inter-fiber mode coupling which increased the
  • each individual fiber can be coated during the fiber manufacturing process.
  • forward-directed scanning can be performed in arbitrary
  • aperture lens 296 is used to focus the OCT imaging beam on to the proximal face 292 and to individually and sequentially address in time each fiber 58.
  • the propagating light is focused at the object plane, distal to the end of the bundle, by an integrated fiber lens (not shown). Fiber lenses integrated into each fiber eliminate the need for additional, larger focusing lenses at the distal end and eliminate the aberrations induced with this type of optical setup.
  • proximal end 292 accomplished at the proximal end 292 by placing either the microscope objective of the proximal end 292 of the bundle on a translation stage (not shown) that has sufficient resolution and precision to address each individual fiber 58 or by using a combination of angle scanning devices and lenses. Alternatively, a direct parallel detection of the image can be utilized.
  • the flexible-endoscope can be integrated to guide or autonomously control laser and other surgical devices.
  • a single or multi-mode optical fiber could be integrated into the center of the imaging bundle.
  • forward-directed imaging methods can be integrated with forward and radial-directed rotating blade/grinding
  • Figure 21ai shows the distal end 304 of a radial-directed rotating blade catheter 300 with additional imaging optics.
  • the catheter 300 used for this procedure is flexible and of small diameter ( ⁇ 3 mm).
  • the distal end 304 has a region of the outer sheath 308 removed to expose
  • axis of the catheter is a rotating shaft 316 which is used to rotate the blade 312 at the distal end 304.
  • the curved, rotating blades 312 also provide a mirror-like surface off of which the OCT imaging beam is reflected.
  • the area of the blade 312 where the imaging beam is incident can be physically isolated from the grinding region in applications where the
  • One or a pair of single-mode optical fibers 58 run along the length of the catheter
  • Each is attached to a focusing element 320 which focuses the beam at the object plane located outside of the catheter sheath 308 in the region to be removed by the rotating blades
  • the blades are machined at a precise
  • the imaging plane may not necessarily be
  • helical blades used simply for performing lateral imaging.
  • an imaging port 324 could be located within the rotating shaft 316.
  • the optical fiber 58 could run along or within the axis of the rotating shaft 316 and a
  • small beam director 328 e.g. GRIN lens attached to a small prism
  • the essential design feature is that the rotation used to drive the cutting blade is
  • the optical imaging port could be designed so as to allow automated or manual adjustment of the location of the beam director element along the axis
  • FIG. 21b A forward-directed rotating blade with forward-directed imaging is shown in Figure 21b.
  • the concepts are similar to those described above except here the distal face 304 of the catheter
  • Imaging is performed through the rotating blades 312 with the imaging plane located distal to the end 304 of the catheter 300. If the pitch of the rotating blades 312 is small, the duty cycle for imaging will be large. There will only be brief periods when imaging cannot be
  • the second method in Figure 21b. ii uses a single focusing element 320 and relies on the curvature or pitch of the blades 312 to reflect the imaging
  • this type of deflecting technique can be used solely for diagnostics.
  • an imaging port 324 could be located within the distal portion of the rotation shaft 316. As described in reference to Figure 8 and other
  • a small spinning beam director 328 can be used to sweep out a conical section in
  • Figure 2 lei shows another embodiment of a forward grinding catheter/endoscope 300.
  • an optically clear block 332 with an integral grinding surface is rotated.
  • OCT or other laser imaging system is used to image through the grinding element 332 and into
  • the grinder 332 is open to interface with the tissue. Alternate designs can convert the circular motion of the rotating shaft 316 to a gearing mechanism that rotates the clear grinding block 332
  • an optical beam director element could be
  • an internal or external optical imaging port can be extended to include a transverse grinder as well.
  • One of the central concepts of this aspect of the invention is the use of the mechanical motion of rotational or reciprocal cutting tools to also drive the optical imaging port which can be coupled physically with the cutting tool so that motion of the cutting tool is used to simultaneously perform scanning thereby maintaining registration of the cutting tool surface and
  • the catheter sheath or cylindrical enclosure consists of a distal
  • the connections between the integrated microchip 344 and the remaining instrumentation consists of only a few electrical wires 174 for control, input, and output of data. Located on the microchip 344 are the necessary micro-fabricated components for the light
  • Input to the microchip 344 include power, control for source output,
  • Output from the chip includes any feedback signals for control and the data
  • imaging can be implemented on a microchip, future reductions in micro-fabricated components will only lead to additional implementation in existing optical instruments or as autonomous imaging robots.
  • Phased arrays have the advantage that they contain no moving parts and thus can be scanned quickly. They rely on the precise relative optical phase of the emitted light from each array element which either constructively or destructively
  • This OEIC 352 contains one or a series of beam dividers (not shown) which
  • the OEIC 352 may be made of silica on silicon (Si ⁇ 2/Si), LiNbO3, InGaAsP, or other elements commonly used for creating optical waveguides and/or phase shifting elements.
  • Each of the N channels contains an electro-optic or thermo-optic phase
  • This phase shifter 356 may be on the same optical substrate as the beam divider
  • phase shifters 356 varying linear phase shift is implemented in between elements, the beam will be scanned off-axis as shown.
  • phased array Another embodiment (not shown) for the phased array is to utilize multiple (e.g. 100)
  • beam conditioning optics may be necessary to optimize
  • the performance of the array and to reduce the focal region of the array.
  • the focal region of the array For operation, the
  • proximal end of the device must include piezoelectric or mechanical fiber stretchers which vary
  • each fiber and/or rotate each fiber (and hence change the phase of the light) by several hundred microns, or enough to sufficiently vary the phase by 360°.
  • the imaging engine must perform all of these operations in parallel. We note that this approach to control the phase in individual fibers despite catheter bending and fiber stretching must be done precisely.
  • One embodiment of this invention is the concept of implantable or embeddable probes (or other devices) in living biological tissues or other structures/specimens such as a structural
  • the implanted fibers may consist of a single fiber or fiber bundles and they
  • transmitters may work in retro-reflection mode, transillumination mode, or any relative location of transmitters
  • the number of transmission fibers may be different from the number of receiver fibers.
  • the receiver processing unit can have a mechanical
  • multiple receivers may be used or the fibers may be wavelength or time division multiplexed.
  • Multiple fibers can have any orientation with respect to one another around the tissue of interest so as to optimize the detection of salient features necessary for diagnosis of disease state, structural
  • the interface between the OCT system and implanted probes may
  • the body for instance a small distance below the surface of the skin such that transcutaneous illumination is possible
  • outside the body for instance a small fiber optic
  • the implanted device can be used to monitor the effect of radiation
  • oriented around and/or within the tissue of interest can be used to detect structural and/or metabolic changes indicative of response or toxicity of the agent of interest.
  • the implanted device may be used to assess neural activity. Fiber(s) may be placed in
  • Neural activity may be monitored by either changes in nerve size, spectral properties
  • Solute In one embodiment, chemical concentrations (such as solute, gas, or metabolite concentrations) may be measured in organ parenchyma (such as the myocardium), lumen
  • support structures such as fascia
  • free space such as air
  • the implanted device may be used to assess regional or whole body vascular function.
  • Probes for example, may be placed in both external cerebral and lower extremity
  • the implantable device may be implanted within and/or in the general vicinity of the bone marrow for the purpose of monitoring the production of both normal and abnormal blood cells.
  • the implanted device may be placed in the organ of interest for the
  • phenotypic changes such as cell size, cell number, muscle strain/contraction, nuclear concentration, or cell surface maker concentration.
  • the device will be placed within or in the
  • Forward directed imaging can be performed with the source fiber or fibers proximal to the
  • tissue of interest and the receiving fiber/detector distal to the tissue of interest.
  • This is a special case of the concepts previously described with respect to Figure 2.
  • the procedure would be of particular use for assessing or surgically manipulating vessels, nerves, and lymph nodes.
  • the illumination beam and/or receiver aperture can be scanned with any of the previously described methods.
  • the receiving element can consist of a single fiber or detector (aperture scanned or not)
  • Forward, axial, or cross-sectional directed imaging can be performed during transurethral prostatectomy procedures such as: transurethral resection of the prostate (TURP), suprapubic
  • one or more fibers can be placed within, adjacent, or on the struts of
  • Fibers will extend to sites from the distal to proximal end of the blade.
  • a flush port may be included on the guide
  • Open Field Surgical Tools Forward directed backscattering or transillumination imaging can be used with instruments used in the surgical field including scissors, forceps, hemostats, and snares. Uses will include
  • the probes could be used for one-dimensional ranging and thus do not require scanning or could be of any of the scanning embodiments described previously.
  • Figure 25 shows some examples.
  • Figure 25a shows a simple hand held surgical probe 340
  • a fiber 57 runs down the center of the surgical probe 340 and contains the imaging and scanning optics 346 as a simple lens such as GRIN lens 62 (or no lens) at the distal end 344.
  • Figure 25b shows an
  • optical imaging and scanning module 346 is mounted near the hinge 352 and aligned so as to illuminate the region
  • Figure 25d shows an example where the optical imaging and scanning module 346 is used to illuminate the region near the end of a snare
  • the integration with the OCT or other optical imaging engine can include single or multiple
  • Forward-directed backscattering or transillumination imaging also can be used with
  • instruments used in laparoscopy/endoscopy including scissors, forceps, snares, or dissecting
  • the imaging and scanning optics be located within the long smooth body of the tool as
  • the devices can have a simple single
  • fiber 57 for performing longitudinal ranging and 1-D imaging can contain a fiber bundle (not
  • the integration with the OCT system can include single or multiple fibers.
  • punch biopsy tools typically consist of small (1-5 mm diameter) cylindrical blades 372 at the distal
  • fibers and beam focusing optics can be located within the cylindrical blade or, in the case of
  • excisional grippers pinchers (not shown), can be located at the pivot-point of the instrument
  • Tissue extraction or disruption (performed with rotating spurs, blades, or similar devices,
  • compression, heat, Shockwave, RF, toxin, or laser illumination can be guided with forward,
  • Single fibers or fiber bundles may be used to perform ranging or imaging as required. Tissue extraction or disruption may be performed in an antegrade or retrograde direction.
  • extraction or disruption can be performed in a cross-sectional direction or parallel to the
  • Tissue extraction or disruption may be guided with feedback from the OCT system, thereby changing, for example, regional blade speed or pressure or in the event
  • the devices can be individually controlled by separate OCT imaging engines.
  • Figure 25 a in side and end view provides an
  • imaging is accomplished using a fiber bundle 288 that is arranged in a series of one
  • each fiber can be coupled (not shown) to a small lens, an integral fiber up-taper, or a single lens group.
  • a small lens an integral fiber up-taper, or a single lens group.
  • fibers 57 can be scanned sequentially using a free space beam steering mirror and lenses, coupled
  • FIG. 28b Shown in Figure 28b is a radial/circular scanning embodiment similar to that previously described with respect to Figure 18c.
  • the output of fiber 57 is collinated using lens 152 and reflected off mirror 154 and adjustable fold mirror 158.
  • the radial distance or angle of fold mirror 158 can be

Abstract

L'invention concerne un système d'imagerie comprenant une tomographie à cohérence optique (OCT) dirigée vers l'avant, et une OCT par balayage vers l'avant non rétroréfléchissant. On peut également utiliser des techniques de télémétrie et d'image interférométriques et une image fluorescente, à effet Raman, à deux photons, et à ondes diffuses. Les mécanismes de balayage vers l'avant comprennent une came fixée à un moteur, des dispositifs pneumatiques, un dispositif pivotant, des transducteurs piézoélectriques, et des lames électrostatiques permettant un balayage essentiellement transversal; des prismes contrarotatifs et des lentilles décalées permettent un balayage arbitraire. Le système d'image de l'invention s'applique à des sondes manuelles y compris des sondes intégrées à des sondes chirurgicales, des scalpels, des ciseaux, des pinces et des instruments de biopsie. Les sondes manuelles comprennent des lasers à balayage vers l'avant. Le système d'image s'applique également à des laparoscopes et des endoscopes destinés à des interventions diagnostiques et thérapeutiques dans des orifices du corps, des canaux, des tubes, des conduits, des vaisseaux, et des cavités du corps.
PCT/US1998/004364 1997-03-06 1998-03-06 Instrument d'analyse a balayage optique de tissu vivant WO1998038907A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
EP98915128A EP0971626A1 (fr) 1997-03-06 1998-03-06 Instrument d'analyse a balayage optique de tissu vivant
JP53882698A JP2001515382A (ja) 1997-03-06 1998-03-06 生体組織の光学走査用機器

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US3804797P 1997-03-06 1997-03-06
US60/038,047 1997-03-06
US5416397P 1997-07-29 1997-07-29
US60/054,163 1997-07-29

Publications (2)

Publication Number Publication Date
WO1998038907A1 true WO1998038907A1 (fr) 1998-09-11
WO1998038907B1 WO1998038907B1 (fr) 1998-11-05

Family

ID=26714802

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1998/004364 WO1998038907A1 (fr) 1997-03-06 1998-03-06 Instrument d'analyse a balayage optique de tissu vivant

Country Status (3)

Country Link
EP (1) EP0971626A1 (fr)
JP (1) JP2001515382A (fr)
WO (1) WO1998038907A1 (fr)

Cited By (185)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2000011511A1 (fr) * 1998-08-19 2000-03-02 Boston Scientific Limited Procede et systeme de balayage optique et de formation d'image
WO2000032102A1 (fr) * 1998-12-02 2000-06-08 The Board Of Regents, University Of Texas System Methode et dispositif pour la caracterisation structurelle et biochimique concomitante de tissus
WO2000042912A1 (fr) * 1999-01-25 2000-07-27 Massachusetts Institute Of Technology Spectroscopie de tissus par diffusion de la lumiere polarisee
EP1065468A1 (fr) * 1999-06-26 2001-01-03 Carl Zeiss TCO linéaire pour l'utilisation comme capteur optique dans la métrologie et la technique médicale
WO2000042906A3 (fr) * 1999-01-22 2001-01-11 Massachusetts Inst Technology Sondes a aiguille a fibre optique pour l'imagerie topographique de coherence optique
US6191862B1 (en) 1999-01-20 2001-02-20 Lightlab Imaging, Llc Methods and apparatus for high speed longitudinal scanning in imaging systems
EP1125095A1 (fr) * 1998-09-11 2001-08-22 Joseph A. Izatt Interferometres pour reflectometrie de domaine de coherence optique et tomographie a coherence optique utilisant des elements optiques non reciproques
WO2001039665A3 (fr) * 1999-12-03 2001-12-13 Lightouch Medical Inc Procede et appareil d'evaluation non invasive de l'etat de la peau et de diagnostic des anomalies de la peau
WO2001041685A3 (fr) * 1999-12-10 2002-01-03 Iscience Corp Traitement de maladies oculaires
JP2002095663A (ja) * 2000-09-26 2002-04-02 Fuji Photo Film Co Ltd センチネルリンパ節光断層画像取得方法および装置
US6381490B1 (en) 1999-08-18 2002-04-30 Scimed Life Systems, Inc. Optical scanning and imaging system and method
EP1201182A2 (fr) 2000-10-31 2002-05-02 Fuji Photo Film Co., Ltd. Appareil d'imagerie
JP2002243641A (ja) * 2001-02-09 2002-08-28 Inst Of Physical & Chemical Res 生体機能測定装置
US6456769B1 (en) 1999-09-02 2002-09-24 Asahi Kogaku Kogyo Kabushiki Kaisha Fiber bundle and endoscope apparatus
US6466713B2 (en) 2000-08-18 2002-10-15 The Regents Of The University Of California Optical fiber head for providing lateral viewing
EP1283413A1 (fr) * 2001-08-08 2003-02-12 Lucent Technologies Inc. Endoscopie par absorption à plusieurs photons
WO2003050590A1 (fr) * 2001-12-10 2003-06-19 University Of Pittsburgh Systeme d'imagerie endoscopique
WO2003063696A1 (fr) * 2002-01-30 2003-08-07 Qinetiq Limited Appareil et procede permettant de differencier des types de tissu
US6643071B2 (en) 2001-12-21 2003-11-04 Lucent Technologies Inc. Graded-index lens microscopes
WO2004010856A1 (fr) * 2002-07-25 2004-02-05 Lightlab Imaging, Llc. Sondes optiques miniatures a balayage avec correction de distorsion optique et commande de rotation
WO2004023992A1 (fr) * 2002-09-11 2004-03-25 University Of Maryland, Baltimore Sonde de tomographie par coherence optique
JP2004325461A (ja) * 2004-06-07 2004-11-18 Institute Of Physical & Chemical Research 非ヒト由来の生体試料の特定部位検出方法、非ヒト由来の生体試料の生理学的測定方法、生体試料の特定部位検出装置、光ファイバ保持装置
WO2005001445A2 (fr) * 2001-12-18 2005-01-06 Massachusetts Institute Of Technology Systemes et procedes de mesures de phases
US6847454B2 (en) 2001-07-16 2005-01-25 Scimed Life Systems, Inc. Systems and methods for processing signals from an interferometer by an ultrasound console
US6847456B2 (en) 2000-04-28 2005-01-25 Massachusetts Institute Of Technology Methods and systems using field-based light scattering spectroscopy
WO2005009236A1 (fr) 2003-07-31 2005-02-03 Koninklijke Philips Electronics N.V. Procede et appareil permettant de determiner une propriete d'un fluide en ecoulement traversant une structure tubulaire biologique a ouverture numerique variable
DE10351319A1 (de) * 2003-10-31 2005-06-16 Medizinisches Laserzentrum Lübeck GmbH Interferometer zur optischen Kohärenztomographie
WO2005072602A1 (fr) * 2004-01-27 2005-08-11 Infraredx, Inc. Sonde presentant un reseau de fibres optiques a combustion cyclonique
EP1618836A1 (fr) * 2004-07-21 2006-01-25 Rowiak GmbH Laryngoscope avec tomographie à cohérence optique
US7006231B2 (en) 2001-10-18 2006-02-28 Scimed Life Systems, Inc. Diffraction grating based interferometric systems and methods
WO2006078839A2 (fr) * 2005-01-20 2006-07-27 Duke University Procedes, systemes et produits programmes informatiques pour caracteriser des structures sur la base de donnees de phase interferometriques
EP1685366A1 (fr) * 2003-10-27 2006-08-02 The General Hospital Corporation Procede et appareil d'imagerie optique par interferometrie dans le domaine frequentiel
US7091500B2 (en) 2003-06-20 2006-08-15 Lucent Technologies Inc. Multi-photon endoscopic imaging system
US7177491B2 (en) 2001-01-12 2007-02-13 Board Of Regents The University Of Texas System Fiber-based optical low coherence tomography
EP1768564A2 (fr) * 2004-06-28 2007-04-04 University of Washington Scanneur a fibre optique utilise pour l'imagerie optique multimodale
WO2007084849A1 (fr) * 2006-01-18 2007-07-26 The General Hospital Corporation Système et procédé pour produire des données au moyen d'une ou plusieurs techniques de microscopie endoscopique
WO2007100937A2 (fr) * 2006-01-19 2007-09-07 The Regents Of The University Of Michigan Système et procédé pour tomographie photo-acoustique spectroscopique
DE102006046925A1 (de) * 2006-09-28 2008-04-03 Jenlab Gmbh Verfahren und Anordnung zur Laser-Endoskopie für die Mikrobearbeitung
WO2010014059A1 (fr) * 2008-07-30 2010-02-04 Medtronic, Inc. Système médical implantable comprenant de multiples modules de détection
EP2156804A1 (fr) 2008-08-18 2010-02-24 FUJIFILM Corporation Appareil de traitement laser
WO2010060622A2 (fr) * 2008-11-26 2010-06-03 Carl Zeiss Surgical Gmbh Système d'imagerie
EP2240068A1 (fr) * 2008-01-04 2010-10-20 Koninklijke Philips Electronics N.V. Sonde optique
EP2328111A1 (fr) * 2002-05-09 2011-06-01 Sony Corporation Procédé pour identifier un modèle biologique, détecteur de modèle biologique, procédé et dispositif pour établir un certificat biologique
EP2333522A1 (fr) * 2001-04-30 2011-06-15 The General Hospital Corporation Procédé et appareil permettant d'améliorer la clarté et la sensibilité de l'image en tomographie à cohérence optique au moyen d'une interaction permettant de contrôler les propriétés focales et la synchronisation de cohérence
WO2012012565A3 (fr) * 2010-07-20 2012-05-10 The Johns Hopkins University Capteur de force interférométrique pour des instruments chirurgicaux
EP2520221A1 (fr) * 2011-05-03 2012-11-07 W & H Dentalwerk Bürmoos GmbH Pièce manuelle pour un appareil de diagnostic médical et appareil de diagnostic médical
USRE43875E1 (en) 2004-09-29 2012-12-25 The General Hospital Corporation System and method for optical coherence imaging
WO2013072796A1 (fr) * 2011-11-14 2013-05-23 Koninklijke Philips Electronics N.V. Sonde de microscopie optique permettant une microscopie à balayage d'un objet associé
CN103222846A (zh) * 2007-01-19 2013-07-31 桑尼布鲁克健康科学中心 用于成像探头的扫描机构
JP2014504520A (ja) * 2011-01-21 2014-02-24 アルコン リサーチ， リミテッド 逆回転する眼科スキャナ駆動機構
US8690762B2 (en) 2008-06-18 2014-04-08 Raytheon Company Transparent endoscope head defining a focal length
US8838213B2 (en) 2006-10-19 2014-09-16 The General Hospital Corporation Apparatus and method for obtaining and providing imaging information associated with at least one portion of a sample, and effecting such portion(s)
US8840566B2 (en) 2007-04-02 2014-09-23 University Of Washington Catheter with imaging capability acts as guidewire for cannula tools
US8854627B2 (en) 2001-07-16 2014-10-07 Boston Scientific Scimed, Inc. Electronically scanned optical coherence tomography with frequency modulated signals
WO2014165820A1 (fr) * 2013-04-05 2014-10-09 University Of Massachusetts Dispositif et procédé pour imagerie d'une structure de collagène in vivo
US8861910B2 (en) 2008-06-20 2014-10-14 The General Hospital Corporation Fused fiber optic coupler arrangement and method for use thereof
US8896838B2 (en) 2010-03-05 2014-11-25 The General Hospital Corporation Systems, methods and computer-accessible medium which provide microscopic images of at least one anatomical structure at a particular resolution
DE10249674B4 (de) * 2002-10-24 2014-12-24 Carl Zeiss Meditec Ag Operationsinstrument zum Schneiden, Abtragen oder Absaugen von Material in einem Operationsgebiet
US8922781B2 (en) 2004-11-29 2014-12-30 The General Hospital Corporation Arrangements, devices, endoscopes, catheters and methods for performing optical imaging by simultaneously illuminating and detecting multiple points on a sample
US8928889B2 (en) 2005-09-29 2015-01-06 The General Hospital Corporation Arrangements and methods for providing multimodality microscopic imaging of one or more biological structures
US8937724B2 (en) 2008-12-10 2015-01-20 The General Hospital Corporation Systems and methods for extending imaging depth range of optical coherence tomography through optical sub-sampling
US8965487B2 (en) 2004-08-24 2015-02-24 The General Hospital Corporation Process, system and software arrangement for measuring a mechanical strain and elastic properties of a sample
DE10041878B4 (de) * 1999-08-25 2015-02-26 Hoya Corp. Endoskopsystem
US8983580B2 (en) 2008-01-18 2015-03-17 The Board Of Trustees Of The University Of Illinois Low-coherence interferometry and optical coherence tomography for image-guided surgical treatment of solid tumors
CN104519804A (zh) * 2012-07-02 2015-04-15 皇家飞利浦有限公司 微创医疗器械
US9060704B2 (en) 2008-11-04 2015-06-23 Sarcos Lc Method and device for wavelength shifted imaging
US9069130B2 (en) 2010-05-03 2015-06-30 The General Hospital Corporation Apparatus, method and system for generating optical radiation from biological gain media
US9087368B2 (en) 2006-01-19 2015-07-21 The General Hospital Corporation Methods and systems for optical imaging or epithelial luminal organs by beam scanning thereof
US9144664B2 (en) 2009-10-01 2015-09-29 Sarcos Lc Method and apparatus for manipulating movement of a micro-catheter
US9161684B2 (en) 2005-02-28 2015-10-20 University Of Washington Monitoring disposition of tethered capsule endoscope in esophagus
US9161694B2 (en) 2005-01-24 2015-10-20 The Board Of Trustees Of The Leland Stanford Junior University Optical analysis system and approach therefor
US9176319B2 (en) 2007-03-23 2015-11-03 The General Hospital Corporation Methods, arrangements and apparatus for utilizing a wavelength-swept laser using angular scanning and dispersion procedures
US9178330B2 (en) 2009-02-04 2015-11-03 The General Hospital Corporation Apparatus and method for utilization of a high-speed optical wavelength tuning source
US9186066B2 (en) 2006-02-01 2015-11-17 The General Hospital Corporation Apparatus for applying a plurality of electro-magnetic radiations to a sample
US9226660B2 (en) 2004-08-06 2016-01-05 The General Hospital Corporation Process, system and software arrangement for determining at least one location in a sample using an optical coherence tomography
US9226687B2 (en) 2003-12-12 2016-01-05 University Of Washington Catheterscope 3D guidance and interface system
US9226665B2 (en) 2003-01-24 2016-01-05 The General Hospital Corporation Speckle reduction in optical coherence tomography by path length encoded angular compounding
US9254102B2 (en) 2004-08-24 2016-02-09 The General Hospital Corporation Method and apparatus for imaging of vessel segments
US9254089B2 (en) 2008-07-14 2016-02-09 The General Hospital Corporation Apparatus and methods for facilitating at least partial overlap of dispersed ration on at least one sample
US9286673B2 (en) 2012-10-05 2016-03-15 Volcano Corporation Systems for correcting distortions in a medical image and methods of use thereof
US9282931B2 (en) 2000-10-30 2016-03-15 The General Hospital Corporation Methods for tissue analysis
US9292918B2 (en) 2012-10-05 2016-03-22 Volcano Corporation Methods and systems for transforming luminal images
US9295391B1 (en) 2000-11-10 2016-03-29 The General Hospital Corporation Spectrally encoded miniature endoscopic imaging probe
US9301687B2 (en) 2013-03-13 2016-04-05 Volcano Corporation System and method for OCT depth calibration
US9307926B2 (en) 2012-10-05 2016-04-12 Volcano Corporation Automatic stent detection
EP1835861B1 (fr) 2005-01-10 2016-04-13 Optimedica Corporation Appareil de trepanation par laser induit par plasma en forme de capsule de lentille
US9324141B2 (en) 2012-10-05 2016-04-26 Volcano Corporation Removal of A-scan streaking artifact
US9330092B2 (en) 2011-07-19 2016-05-03 The General Hospital Corporation Systems, methods, apparatus and computer-accessible-medium for providing polarization-mode dispersion compensation in optical coherence tomography
US9326682B2 (en) 2005-04-28 2016-05-03 The General Hospital Corporation Systems, processes and software arrangements for evaluating information associated with an anatomical structure by an optical coherence ranging technique
US9332942B2 (en) 2008-01-28 2016-05-10 The General Hospital Corporation Systems, processes and computer-accessible medium for providing hybrid flourescence and optical coherence tomography imaging
US9341783B2 (en) 2011-10-18 2016-05-17 The General Hospital Corporation Apparatus and methods for producing and/or providing recirculating optical delay(s)
US9351642B2 (en) 2009-03-12 2016-05-31 The General Hospital Corporation Non-contact optical system, computer-accessible medium and method for measurement at least one mechanical property of tissue using coherent speckle technique(s)
US9360630B2 (en) 2011-08-31 2016-06-07 Volcano Corporation Optical-electrical rotary joint and methods of use
US9367965B2 (en) 2012-10-05 2016-06-14 Volcano Corporation Systems and methods for generating images of tissue
US9364143B2 (en) 2006-05-10 2016-06-14 The General Hospital Corporation Process, arrangements and systems for providing frequency domain imaging of a sample
US9375147B2 (en) 2007-01-19 2016-06-28 Sunnybrook Health Sciences Centre Scanning mechanisms for imaging probe
US9375158B2 (en) 2007-07-31 2016-06-28 The General Hospital Corporation Systems and methods for providing beam scan patterns for high speed doppler optical frequency domain imaging
US9383263B2 (en) 2012-12-21 2016-07-05 Volcano Corporation Systems and methods for narrowing a wavelength emission of light
US9415550B2 (en) 2012-08-22 2016-08-16 The General Hospital Corporation System, method, and computer-accessible medium for fabrication miniature endoscope using soft lithography
US9441948B2 (en) 2005-08-09 2016-09-13 The General Hospital Corporation Apparatus, methods and storage medium for performing polarization-based quadrature demodulation in optical coherence tomography
US9478940B2 (en) 2012-10-05 2016-10-25 Volcano Corporation Systems and methods for amplifying light
US9486143B2 (en) 2012-12-21 2016-11-08 Volcano Corporation Intravascular forward imaging device
US9510758B2 (en) 2010-10-27 2016-12-06 The General Hospital Corporation Apparatus, systems and methods for measuring blood pressure within at least one vessel
US9516997B2 (en) 2006-01-19 2016-12-13 The General Hospital Corporation Spectrally-encoded endoscopy techniques, apparatus and methods
US9528817B2 (en) 2001-12-18 2016-12-27 Massachusetts Institute Of Technology Systems and methods for phase measurements
US9557154B2 (en) 2010-05-25 2017-01-31 The General Hospital Corporation Systems, devices, methods, apparatus and computer-accessible media for providing optical imaging of structures and compositions
US9561078B2 (en) 2006-03-03 2017-02-07 University Of Washington Multi-cladding optical fiber scanner
US9596993B2 (en) 2007-07-12 2017-03-21 Volcano Corporation Automatic calibration systems and methods of use
US9612105B2 (en) 2012-12-21 2017-04-04 Volcano Corporation Polarization sensitive optical coherence tomography system
US9622706B2 (en) 2007-07-12 2017-04-18 Volcano Corporation Catheter for in vivo imaging
US9629528B2 (en) 2012-03-30 2017-04-25 The General Hospital Corporation Imaging system, method and distal attachment for multidirectional field of view endoscopy
WO2017066872A1 (fr) * 2015-10-22 2017-04-27 Medtronic Cryocath Lp Technique d'analyse de tissu post-ablation
WO2017078226A1 (fr) * 2015-11-03 2017-05-11 고려대학교 산학협력단 Exciseur de tissu et système d'excision de tissu
USRE46412E1 (en) 2006-02-24 2017-05-23 The General Hospital Corporation Methods and systems for performing angle-resolved Fourier-domain optical coherence tomography
US9664615B2 (en) 2004-07-02 2017-05-30 The General Hospital Corporation Imaging system and related techniques
US9661996B2 (en) 2009-10-01 2017-05-30 Sarcos Lc Needle delivered imaging device
US9668652B2 (en) 2013-07-26 2017-06-06 The General Hospital Corporation System, apparatus and method for utilizing optical dispersion for fourier-domain optical coherence tomography
US9709379B2 (en) 2012-12-20 2017-07-18 Volcano Corporation Optical coherence tomography system that is reconfigurable between different imaging modes
US9733460B2 (en) 2014-01-08 2017-08-15 The General Hospital Corporation Method and apparatus for microscopic imaging
US9730613B2 (en) 2012-12-20 2017-08-15 Volcano Corporation Locating intravascular images
EP3082564A4 (fr) * 2013-12-18 2017-08-30 Novartis AG Sonde de balayage vers l'avant bidimensionnel
US9770172B2 (en) 2013-03-07 2017-09-26 Volcano Corporation Multimodal segmentation in intravascular images
US9777053B2 (en) 2006-02-08 2017-10-03 The General Hospital Corporation Methods, arrangements and systems for obtaining information associated with an anatomical sample using optical microscopy
US9784681B2 (en) 2013-05-13 2017-10-10 The General Hospital Corporation System and method for efficient detection of the phase and amplitude of a periodic modulation associated with self-interfering fluorescence
US9795301B2 (en) 2010-05-25 2017-10-24 The General Hospital Corporation Apparatus, systems, methods and computer-accessible medium for spectral analysis of optical coherence tomography images
US9814390B2 (en) 2013-03-15 2017-11-14 Synaptive Medical (Barbados) Inc. Insert imaging device for surgical procedures
US20170343791A1 (en) * 2016-05-30 2017-11-30 Eric Swanson Few-mode fiber endoscope
US9858668B2 (en) 2012-10-05 2018-01-02 Volcano Corporation Guidewire artifact removal in images
US9867530B2 (en) 2006-08-14 2018-01-16 Volcano Corporation Telescopic side port catheter device with imaging system and method for accessing side branch occlusions
EP3323340A1 (fr) * 2016-11-16 2018-05-23 Karl Storz SE & Co. KG Sonde endoscopique, système et procédé de tomographie par cohérence optique et d'endoscopie confocale
US10058284B2 (en) 2012-12-21 2018-08-28 Volcano Corporation Simultaneous imaging, monitoring, and therapy
US10070827B2 (en) 2012-10-05 2018-09-11 Volcano Corporation Automatic image playback
US10080499B2 (en) 2008-07-30 2018-09-25 Medtronic, Inc. Implantable medical system including multiple sensing modules
US10117576B2 (en) 2013-07-19 2018-11-06 The General Hospital Corporation System, method and computer accessible medium for determining eye motion by imaging retina and providing feedback for acquisition of signals from the retina
US10166003B2 (en) 2012-12-21 2019-01-01 Volcano Corporation Ultrasound imaging with variable line density
US10191220B2 (en) 2012-12-21 2019-01-29 Volcano Corporation Power-efficient optical circuit
DE102005059271B4 (de) 2005-12-12 2019-02-21 Siemens Healthcare Gmbh Kathetervorrichtung
US10219780B2 (en) 2007-07-12 2019-03-05 Volcano Corporation OCT-IVUS catheter for concurrent luminal imaging
US10219887B2 (en) 2013-03-14 2019-03-05 Volcano Corporation Filters with echogenic characteristics
US10228556B2 (en) 2014-04-04 2019-03-12 The General Hospital Corporation Apparatus and method for controlling propagation and/or transmission of electromagnetic radiation in flexible waveguide(s)
US10226597B2 (en) 2013-03-07 2019-03-12 Volcano Corporation Guidewire with centering mechanism
US10241028B2 (en) 2011-08-25 2019-03-26 The General Hospital Corporation Methods, systems, arrangements and computer-accessible medium for providing micro-optical coherence tomography procedures
US10238367B2 (en) 2012-12-13 2019-03-26 Volcano Corporation Devices, systems, and methods for targeted cannulation
US10286107B2 (en) 2011-03-07 2019-05-14 The Regents Of The University Of Colorado, A Body Corporate Shape memory polymer intraocular lenses
US10285568B2 (en) 2010-06-03 2019-05-14 The General Hospital Corporation Apparatus and method for devices for imaging structures in or at one or more luminal organs
US10292771B2 (en) 2013-03-15 2019-05-21 Synaptive Medical (Barbados) Inc. Surgical imaging systems
US10292677B2 (en) 2013-03-14 2019-05-21 Volcano Corporation Endoluminal filter having enhanced echogenic properties
EP3443922A3 (fr) * 2009-09-14 2019-06-12 Memorial Sloan-Kettering Cancer Center Appareil, système et procédé de fourniture d'orientation et de mise au point laser pour incision, excision et ablation de tissus en chirurgie mini-invasive
US10332228B2 (en) 2012-12-21 2019-06-25 Volcano Corporation System and method for graphical processing of medical data
US10413317B2 (en) 2012-12-21 2019-09-17 Volcano Corporation System and method for catheter steering and operation
US10420530B2 (en) 2012-12-21 2019-09-24 Volcano Corporation System and method for multipath processing of image signals
US10426590B2 (en) 2013-03-14 2019-10-01 Volcano Corporation Filters with echogenic characteristics
US10426548B2 (en) 2006-02-01 2019-10-01 The General Hosppital Corporation Methods and systems for providing electromagnetic radiation to at least one portion of a sample using conformal laser therapy procedures
USRE47675E1 (en) 2003-06-06 2019-10-29 The General Hospital Corporation Process and apparatus for a wavelength tuning source
US10478072B2 (en) 2013-03-15 2019-11-19 The General Hospital Corporation Methods and system for characterizing an object
US10534129B2 (en) 2007-03-30 2020-01-14 The General Hospital Corporation System and method providing intracoronary laser speckle imaging for the detection of vulnerable plaque
US10568586B2 (en) 2012-10-05 2020-02-25 Volcano Corporation Systems for indicating parameters in an imaging data set and methods of use
WO2020047660A1 (fr) * 2018-09-04 2020-03-12 Provincial Health Services Authority Microspectroscopie raman guidée par image
US10595820B2 (en) 2012-12-20 2020-03-24 Philips Image Guided Therapy Corporation Smooth transition catheters
EP3086704B1 (fr) * 2013-12-23 2020-04-22 Alcon Inc. Sonde optique de balayage vers l'avant
US10638939B2 (en) 2013-03-12 2020-05-05 Philips Image Guided Therapy Corporation Systems and methods for diagnosing coronary microvascular disease
US10724082B2 (en) 2012-10-22 2020-07-28 Bio-Rad Laboratories, Inc. Methods for analyzing DNA
US10736494B2 (en) 2014-01-31 2020-08-11 The General Hospital Corporation System and method for facilitating manual and/or automatic volumetric imaging with real-time tension or force feedback using a tethered imaging device
US10758207B2 (en) 2013-03-13 2020-09-01 Philips Image Guided Therapy Corporation Systems and methods for producing an image from a rotational intravascular ultrasound device
DE102019207873A1 (de) * 2019-05-29 2020-12-03 Leica Microsystems Cms Gmbh Optischer Aufbau für ein Mikroskop und Mikroskop
US10893806B2 (en) 2013-01-29 2021-01-19 The General Hospital Corporation Apparatus, systems and methods for providing information regarding the aortic valve
US10912462B2 (en) 2014-07-25 2021-02-09 The General Hospital Corporation Apparatus, devices and methods for in vivo imaging and diagnosis
US10942022B2 (en) 2012-12-20 2021-03-09 Philips Image Guided Therapy Corporation Manual calibration of imaging system
US10939826B2 (en) 2012-12-20 2021-03-09 Philips Image Guided Therapy Corporation Aspirating and removing biological material
US10993694B2 (en) 2012-12-21 2021-05-04 Philips Image Guided Therapy Corporation Rotational ultrasound imaging catheter with extended catheter body telescope
US11026591B2 (en) 2013-03-13 2021-06-08 Philips Image Guided Therapy Corporation Intravascular pressure sensor calibration
US11040140B2 (en) 2010-12-31 2021-06-22 Philips Image Guided Therapy Corporation Deep vein thrombosis therapeutic methods
CN113197555A (zh) * 2021-06-04 2021-08-03 哈尔滨医科大学 多方向oct图像采集导管
US11123047B2 (en) 2008-01-28 2021-09-21 The General Hospital Corporation Hybrid systems and methods for multi-modal acquisition of intravascular imaging data and counteracting the effects of signal absorption in blood
CN113455992A (zh) * 2021-06-04 2021-10-01 哈尔滨医科大学 一种成像导管及成像装置
US11141063B2 (en) 2010-12-23 2021-10-12 Philips Image Guided Therapy Corporation Integrated system architectures and methods of use
US11154313B2 (en) 2013-03-12 2021-10-26 The Volcano Corporation Vibrating guidewire torquer and methods of use
US11179028B2 (en) 2013-02-01 2021-11-23 The General Hospital Corporation Objective lens arrangement for confocal endomicroscopy
US11272845B2 (en) 2012-10-05 2022-03-15 Philips Image Guided Therapy Corporation System and method for instant and automatic border detection
WO2022130022A1 (fr) * 2020-12-14 2022-06-23 Rockley Photonics Limited Dispositif minimalement invasif pourvu d'un spectrophotomètre
US11406498B2 (en) 2012-12-20 2022-08-09 Philips Image Guided Therapy Corporation Implant delivery system and implants
US11452433B2 (en) 2013-07-19 2022-09-27 The General Hospital Corporation Imaging apparatus and method which utilizes multidirectional field of view endoscopy
US11490826B2 (en) 2009-07-14 2022-11-08 The General Hospital Corporation Apparatus, systems and methods for measuring flow and pressure within a vessel
US11490797B2 (en) 2012-05-21 2022-11-08 The General Hospital Corporation Apparatus, device and method for capsule microscopy
US11517199B2 (en) 2014-08-08 2022-12-06 Medlumics S.L. Crossing coronary occlusions

Families Citing this family (33)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6831781B2 (en) * 1998-02-26 2004-12-14 The General Hospital Corporation Confocal microscopy with multi-spectral encoding and system and apparatus for spectroscopically encoded confocal microscopy
US6263133B1 (en) * 1999-03-29 2001-07-17 Scimed Life Systems, Inc. Optical focusing, collimating and coupling systems for use with single mode optical fiber
FR2834348B1 (fr) * 2001-12-28 2004-02-27 Mauna Kea Technologies Tete optique de focalisation miniaturisee, notamment pour endoscope
US7160248B2 (en) * 2002-06-06 2007-01-09 Optiscope Technologies Ltd. Optical device for viewing of cavernous and/or inaccessible spaces
JP4133013B2 (ja) * 2002-06-18 2008-08-13 Ｈｏｙａ株式会社 Ｏｃｔ観察用プローブ
JP2004321696A (ja) * 2003-04-28 2004-11-18 Olympus Corp 光イメージング装置
FR2864631B1 (fr) * 2003-12-31 2006-04-14 Mauna Kea Technologies Procede et systeme de super-resolution d'images confocales acquises a travers un guide d'image, et dispositif utilise pour la mise en oeuvre d'un tel procede
FR2865538B1 (fr) * 2004-01-22 2007-10-19 Centre Nat Rech Scient Dispositif et procede pour mesurer le contraste des franges dans un interferometre de michelson, et systeme d'examen de l'oeil incluant un tel dispositif
US7261687B2 (en) * 2004-03-23 2007-08-28 California Institute Of Technology Forward scanning imaging optical fiber probe
JP5623692B2 (ja) * 2004-11-02 2014-11-12 ザ ジェネラル ホスピタル コーポレイション 試料の画像形成のための光ファイバ回転装置、光学システム及び方法
JP5695001B2 (ja) * 2004-11-02 2015-04-01 ザ ジェネラル ホスピタル コーポレイション 試料の画像形成のための光ファイバ回転装置、光学システム及び方法
JP4640813B2 (ja) * 2005-09-30 2011-03-02 富士フイルム株式会社 光プローブおよび光断層画像化装置
US8537366B2 (en) 2005-10-11 2013-09-17 Duke University Systems and methods for endoscopic angle-resolved low coherence interferometry
EP2110776B1 (fr) * 2005-12-23 2012-10-31 Ingenia Holdings Limited Authentification optique
US8537363B2 (en) 2006-11-21 2013-09-17 Brown University Picosecond ultrasonic system incorporating an optical cavity
WO2008078254A1 (fr) * 2006-12-22 2008-07-03 Koninklijke Philips Electronics N.V. Système d'imagerie utilisant deux modalités d'imagerie
WO2009070161A1 (fr) * 2007-11-27 2009-06-04 University Of Washington Ajout d'une capacité d'imagerie à des extrémités distales d'outils médicaux, de cathéters, et de conduits
US9131845B2 (en) * 2008-01-04 2015-09-15 Koninklijke Philips N.V. Optical probe
WO2010014792A2 (fr) 2008-07-30 2010-02-04 Sterling Lc Procédé et dispositif permettant une variation par incréments de la longueur d’ondes pour analyser un tissu
EP2389093A4 (fr) 2009-01-20 2013-07-31 Gen Hospital Corp Appareil, système et procédé de biopsie endoscopique
US20130128264A1 (en) * 2010-03-19 2013-05-23 Duke University Single-mode optical fiber-based angle-resolved low coherence interferometric (lci)(a/lci) and non-interferometric systems and methods
TWI554243B (zh) * 2011-01-21 2016-10-21 愛爾康研究有限公司 用於光學同調斷層掃描、照明或光凝治療的組合式外科內探針
JP2014104138A (ja) * 2012-11-27 2014-06-09 Olympus Corp 内視鏡及び内視鏡システム
EP2948758B1 (fr) 2013-01-28 2024-03-13 The General Hospital Corporation Appareil pour fournir une spectroscopie diffuse co-enregistrée avec imagerie de domaine de fréquence optique
US9844318B2 (en) 2013-03-26 2017-12-19 Novartis Ag Devices, systems, and methods for calibrating an OCT imaging system in a laser surgical system
US9668645B2 (en) * 2014-05-09 2017-06-06 Novartis Ag Imaging probes and associated devices, systems, and methods utilizing electrostatic actuators
US9295384B2 (en) * 2014-05-16 2016-03-29 Novartis Ag Imaging probes and associated devices, systems, and methods utilizing lever arm actuators
US10666928B2 (en) * 2015-02-06 2020-05-26 The University Of Akron Optical imaging system and methods thereof
JP6784667B2 (ja) * 2015-04-23 2020-11-11 オリンパス株式会社 外科処置装置
WO2017047739A1 (fr) * 2015-09-17 2017-03-23 並木精密宝石株式会社 Sonde d'imagerie optique
JP2018079225A (ja) * 2016-11-18 2018-05-24 株式会社日立製作所 タイムドメイン式ｏｃｔカテーテルシステム及びタイムドメイン式ｏｃｔカテーテルシステムの制御方法
JP2018169246A (ja) * 2017-03-29 2018-11-01 エヌ・ティ・ティ・アドバンステクノロジ株式会社 光偏向器の出射光制御装置
WO2020217448A1 (fr) * 2019-04-26 2020-10-29 株式会社島津製作所 Dispositif d'imagerie d'image d'interférence

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3627420A1 (de) * 1985-08-13 1987-02-26 Toshiba Kawasaki Kk Optisches system zur strahlenlenkung
US4913142A (en) * 1985-03-22 1990-04-03 Massachusetts Institute Of Technology Catheter for laser angiosurgery
US5217456A (en) * 1992-02-24 1993-06-08 Pdt Cardiovascular, Inc. Device and method for intra-vascular optical radial imaging
US5305759A (en) * 1990-09-26 1994-04-26 Olympus Optical Co., Ltd. Examined body interior information observing apparatus by using photo-pulses controlling gains for depths
US5321501A (en) 1991-04-29 1994-06-14 Massachusetts Institute Of Technology Method and apparatus for optical imaging with means for controlling the longitudinal range of the sample
US5393467A (en) 1992-06-04 1995-02-28 Sumitomo Rubber Industries, Ltd. Electrically conductive rubber material used for electrophotographic copying apparatus

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4913142A (en) * 1985-03-22 1990-04-03 Massachusetts Institute Of Technology Catheter for laser angiosurgery
DE3627420A1 (de) * 1985-08-13 1987-02-26 Toshiba Kawasaki Kk Optisches system zur strahlenlenkung
US5305759A (en) * 1990-09-26 1994-04-26 Olympus Optical Co., Ltd. Examined body interior information observing apparatus by using photo-pulses controlling gains for depths
US5321501A (en) 1991-04-29 1994-06-14 Massachusetts Institute Of Technology Method and apparatus for optical imaging with means for controlling the longitudinal range of the sample
US5459570A (en) 1991-04-29 1995-10-17 Massachusetts Institute Of Technology Method and apparatus for performing optical measurements
US5217456A (en) * 1992-02-24 1993-06-08 Pdt Cardiovascular, Inc. Device and method for intra-vascular optical radial imaging
US5393467A (en) 1992-06-04 1995-02-28 Sumitomo Rubber Industries, Ltd. Electrically conductive rubber material used for electrophotographic copying apparatus

Cited By (281)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6564087B1 (en) 1991-04-29 2003-05-13 Massachusetts Institute Of Technology Fiber optic needle probes for optical coherence tomography imaging
US7415303B2 (en) 1998-08-19 2008-08-19 Boston Scientific Scimed, Inc. Optical scanning and imaging system and method
US6895270B2 (en) 1998-08-19 2005-05-17 Scimed Life Systems, Inc. Optical scanning and imaging method
WO2000011511A1 (fr) * 1998-08-19 2000-03-02 Boston Scientific Limited Procede et systeme de balayage optique et de formation d'image
EP1125095A4 (fr) * 1998-09-11 2006-07-12 Joseph A Izatt Interferometres pour reflectometrie de domaine de coherence optique et tomographie a coherence optique utilisant des elements optiques non reciproques
EP1125095A1 (fr) * 1998-09-11 2001-08-22 Joseph A. Izatt Interferometres pour reflectometrie de domaine de coherence optique et tomographie a coherence optique utilisant des elements optiques non reciproques
WO2000032102A1 (fr) * 1998-12-02 2000-06-08 The Board Of Regents, University Of Texas System Methode et dispositif pour la caracterisation structurelle et biochimique concomitante de tissus
US6681133B2 (en) 1998-12-03 2004-01-20 Lightouch Medical, Inc. Methods and apparatus for obtaining enhanced spectroscopic information from living tissue
US6352502B1 (en) 1998-12-03 2002-03-05 Lightouch Medical, Inc. Methods for obtaining enhanced spectroscopic information from living tissue, noninvasive assessment of skin condition and detection of skin abnormalities
US6191862B1 (en) 1999-01-20 2001-02-20 Lightlab Imaging, Llc Methods and apparatus for high speed longitudinal scanning in imaging systems
WO2000042906A3 (fr) * 1999-01-22 2001-01-11 Massachusetts Inst Technology Sondes a aiguille a fibre optique pour l'imagerie topographique de coherence optique
US6404497B1 (en) 1999-01-25 2002-06-11 Massachusetts Institute Of Technology Polarized light scattering spectroscopy of tissue
WO2000042912A1 (fr) * 1999-01-25 2000-07-27 Massachusetts Institute Of Technology Spectroscopie de tissus par diffusion de la lumiere polarisee
US6624890B2 (en) 1999-01-25 2003-09-23 Massachusetts Institute Of Technology Polarized light scattering spectroscopy of tissue
US6396587B1 (en) 1999-06-26 2002-05-28 Carl-Zeiss-Stiftung Method for recording depth profiles in a specimen and apparatus therefor
EP1065468A1 (fr) * 1999-06-26 2001-01-03 Carl Zeiss TCO linéaire pour l'utilisation comme capteur optique dans la métrologie et la technique médicale
US6381490B1 (en) 1999-08-18 2002-04-30 Scimed Life Systems, Inc. Optical scanning and imaging system and method
DE10041878B4 (de) * 1999-08-25 2015-02-26 Hoya Corp. Endoskopsystem
US6600861B2 (en) 1999-09-02 2003-07-29 Pentax Corporation Fiber bundle and endoscope apparatus
US6456769B1 (en) 1999-09-02 2002-09-24 Asahi Kogaku Kogyo Kabushiki Kaisha Fiber bundle and endoscope apparatus
WO2001039665A3 (fr) * 1999-12-03 2001-12-13 Lightouch Medical Inc Procede et appareil d'evaluation non invasive de l'etat de la peau et de diagnostic des anomalies de la peau
KR100771150B1 (ko) * 1999-12-10 2007-10-29 아이싸이언스 인터벤셔날 코포레이션 안 질환의 치료방법
KR100771149B1 (ko) * 1999-12-10 2007-10-30 아이싸이언스 인터벤셔날 코포레이션 안 질환의 치료방법
WO2001041685A3 (fr) * 1999-12-10 2002-01-03 Iscience Corp Traitement de maladies oculaires
KR100855740B1 (ko) * 1999-12-10 2008-09-03 아이싸이언스 인터벤셔날 코포레이션 안 질환의 치료방법
JP2003530144A (ja) * 1999-12-10 2003-10-14 アイサイエンス コーポレイション 眼の病気の治療
AU784936B2 (en) * 1999-12-10 2006-08-03 Iscience Corporation Treatment of ocular disease
US6847456B2 (en) 2000-04-28 2005-01-25 Massachusetts Institute Of Technology Methods and systems using field-based light scattering spectroscopy
US6466713B2 (en) 2000-08-18 2002-10-15 The Regents Of The University Of California Optical fiber head for providing lateral viewing
JP2002095663A (ja) * 2000-09-26 2002-04-02 Fuji Photo Film Co Ltd センチネルリンパ節光断層画像取得方法および装置
US9282931B2 (en) 2000-10-30 2016-03-15 The General Hospital Corporation Methods for tissue analysis
US6999608B2 (en) 2000-10-31 2006-02-14 Fuji Photo Film Co., Ltd. Imaging apparatus
EP1201182A2 (fr) 2000-10-31 2002-05-02 Fuji Photo Film Co., Ltd. Appareil d'imagerie
EP1201182A3 (fr) * 2000-10-31 2003-07-02 Fuji Photo Film Co., Ltd. Appareil d'imagerie
US9295391B1 (en) 2000-11-10 2016-03-29 The General Hospital Corporation Spectrally encoded miniature endoscopic imaging probe
US7177491B2 (en) 2001-01-12 2007-02-13 Board Of Regents The University Of Texas System Fiber-based optical low coherence tomography
JP2002243641A (ja) * 2001-02-09 2002-08-28 Inst Of Physical & Chemical Res 生体機能測定装置
US9897538B2 (en) 2001-04-30 2018-02-20 The General Hospital Corporation Method and apparatus for improving image clarity and sensitivity in optical coherence tomography using dynamic feedback to control focal properties and coherence gating
EP1402244B1 (fr) * 2001-04-30 2020-03-11 The General Hospital Corporation Procede et appareil permettant d'ameliorer la clarte et la sensibilite de l'image en tomographie a coherence optique au moyen d'une interaction permettant de controler les proprietes focales et la synchronisation de coherence
EP2333523B1 (fr) * 2001-04-30 2020-04-08 The General Hospital Corporation Procédé et appareil permettant d'améliorer la clarté et la sensibilité de l'image en tomographie à cohérence optique au moyen d'une interaction permettant de contrôler les propriétés focales et la synchronisation de cohérence
EP2333522A1 (fr) * 2001-04-30 2011-06-15 The General Hospital Corporation Procédé et appareil permettant d'améliorer la clarté et la sensibilité de l'image en tomographie à cohérence optique au moyen d'une interaction permettant de contrôler les propriétés focales et la synchronisation de cohérence
EP2333521B1 (fr) * 2001-04-30 2019-12-04 The General Hospital Corporation Procédé et appareil permettant d'améliorer la clarté et la sensibilité de l'image en tomographie à cohérence optique au moyen d'une interaction permettant de contrôler les propriétés focales et la synchronisation de cohérence
US8854627B2 (en) 2001-07-16 2014-10-07 Boston Scientific Scimed, Inc. Electronically scanned optical coherence tomography with frequency modulated signals
US6847454B2 (en) 2001-07-16 2005-01-25 Scimed Life Systems, Inc. Systems and methods for processing signals from an interferometer by an ultrasound console
US7336988B2 (en) 2001-08-08 2008-02-26 Lucent Technologies Inc. Multi-photon endoscopy
EP1283413A1 (fr) * 2001-08-08 2003-02-12 Lucent Technologies Inc. Endoscopie par absorption à plusieurs photons
JP2003116775A (ja) * 2001-08-08 2003-04-22 Lucent Technol Inc 多光子内視鏡検査法
US7006231B2 (en) 2001-10-18 2006-02-28 Scimed Life Systems, Inc. Diffraction grating based interferometric systems and methods
US7426037B2 (en) 2001-10-18 2008-09-16 Boston Scientific Scimed, Inc. Diffraction grating based interferometric systems and methods
US7130054B2 (en) 2001-10-18 2006-10-31 Scimed Life Systems, Inc. Diffraction grating based interferometric systems and methods
US7728983B2 (en) 2001-10-18 2010-06-01 Boston Scientific Scimed, Inc. Diffraction grating based interferometric systems and methods
WO2003050590A1 (fr) * 2001-12-10 2003-06-19 University Of Pittsburgh Systeme d'imagerie endoscopique
US9528817B2 (en) 2001-12-18 2016-12-27 Massachusetts Institute Of Technology Systems and methods for phase measurements
WO2005001445A3 (fr) * 2001-12-18 2005-12-15 Massachusetts Inst Technology Systemes et procedes de mesures de phases
WO2005001445A2 (fr) * 2001-12-18 2005-01-06 Massachusetts Institute Of Technology Systemes et procedes de mesures de phases
US6643071B2 (en) 2001-12-21 2003-11-04 Lucent Technologies Inc. Graded-index lens microscopes
WO2003063696A1 (fr) * 2002-01-30 2003-08-07 Qinetiq Limited Appareil et procede permettant de differencier des types de tissu
US8144942B2 (en) 2002-05-09 2012-03-27 Sony Corporation Compact biometric authentication device and associated methodology of imaging and detecting living-tissue patterns
US10371629B2 (en) 2002-05-09 2019-08-06 Sony Corporation Compact biometric authentication device and associated methodology of imaging and detecting living-tissue patterns
US8811680B2 (en) 2002-05-09 2014-08-19 Sony Corporation Compact biometric authentication device and associated methodology of imaging and detecting living-tissue patterns
US9234842B2 (en) 2002-05-09 2016-01-12 Sony Corporation Compact biometric authentication device and associated methodology of imaging and detecting living-tissue patterns
EP2328111A1 (fr) * 2002-05-09 2011-06-01 Sony Corporation Procédé pour identifier un modèle biologique, détecteur de modèle biologique, procédé et dispositif pour établir un certificat biologique
US6891984B2 (en) 2002-07-25 2005-05-10 Lightlab Imaging, Llc Scanning miniature optical probes with optical distortion correction and rotational control
WO2004010856A1 (fr) * 2002-07-25 2004-02-05 Lightlab Imaging, Llc. Sondes optiques miniatures a balayage avec correction de distorsion optique et commande de rotation
WO2004023992A1 (fr) * 2002-09-11 2004-03-25 University Of Maryland, Baltimore Sonde de tomographie par coherence optique
DE10249674B4 (de) * 2002-10-24 2014-12-24 Carl Zeiss Meditec Ag Operationsinstrument zum Schneiden, Abtragen oder Absaugen von Material in einem Operationsgebiet
US9226665B2 (en) 2003-01-24 2016-01-05 The General Hospital Corporation Speckle reduction in optical coherence tomography by path length encoded angular compounding
USRE47675E1 (en) 2003-06-06 2019-10-29 The General Hospital Corporation Process and apparatus for a wavelength tuning source
US7091500B2 (en) 2003-06-20 2006-08-15 Lucent Technologies Inc. Multi-photon endoscopic imaging system
WO2005009236A1 (fr) 2003-07-31 2005-02-03 Koninklijke Philips Electronics N.V. Procede et appareil permettant de determiner une propriete d'un fluide en ecoulement traversant une structure tubulaire biologique a ouverture numerique variable
EP1685366A1 (fr) * 2003-10-27 2006-08-02 The General Hospital Corporation Procede et appareil d'imagerie optique par interferometrie dans le domaine frequentiel
US9812846B2 (en) 2003-10-27 2017-11-07 The General Hospital Corporation Method and apparatus for performing optical imaging using frequency-domain interferometry
EP1685366B1 (fr) * 2003-10-27 2011-06-15 The General Hospital Corporation Procede et appareil d'imagerie optique par interferometrie dans le domaine frequentiel
US9377290B2 (en) 2003-10-27 2016-06-28 The General Hospital Corporation Method and apparatus for performing optical imaging using frequency-domain interferometry
DE10351319B4 (de) * 2003-10-31 2005-10-20 Med Laserzentrum Luebeck Gmbh Interferometer für die optische Kohärenztomographie
DE10351319A1 (de) * 2003-10-31 2005-06-16 Medizinisches Laserzentrum Lübeck GmbH Interferometer zur optischen Kohärenztomographie
US9226687B2 (en) 2003-12-12 2016-01-05 University Of Washington Catheterscope 3D guidance and interface system
US9554729B2 (en) 2003-12-12 2017-01-31 University Of Washington Catheterscope 3D guidance and interface system
WO2005072602A1 (fr) * 2004-01-27 2005-08-11 Infraredx, Inc. Sonde presentant un reseau de fibres optiques a combustion cyclonique
JP2004325461A (ja) * 2004-06-07 2004-11-18 Institute Of Physical & Chemical Research 非ヒト由来の生体試料の特定部位検出方法、非ヒト由来の生体試料の生理学的測定方法、生体試料の特定部位検出装置、光ファイバ保持装置
EP1768564A2 (fr) * 2004-06-28 2007-04-04 University of Washington Scanneur a fibre optique utilise pour l'imagerie optique multimodale
EP1768564A4 (fr) * 2004-06-28 2009-11-11 Univ Washington Scanneur a fibre optique utilise pour l'imagerie optique multimodale
US9664615B2 (en) 2004-07-02 2017-05-30 The General Hospital Corporation Imaging system and related techniques
EP1618836A1 (fr) * 2004-07-21 2006-01-25 Rowiak GmbH Laryngoscope avec tomographie à cohérence optique
US9226660B2 (en) 2004-08-06 2016-01-05 The General Hospital Corporation Process, system and software arrangement for determining at least one location in a sample using an optical coherence tomography
US9254102B2 (en) 2004-08-24 2016-02-09 The General Hospital Corporation Method and apparatus for imaging of vessel segments
US9763623B2 (en) 2004-08-24 2017-09-19 The General Hospital Corporation Method and apparatus for imaging of vessel segments
US8965487B2 (en) 2004-08-24 2015-02-24 The General Hospital Corporation Process, system and software arrangement for measuring a mechanical strain and elastic properties of a sample
USRE45512E1 (en) 2004-09-29 2015-05-12 The General Hospital Corporation System and method for optical coherence imaging
USRE43875E1 (en) 2004-09-29 2012-12-25 The General Hospital Corporation System and method for optical coherence imaging
US8922781B2 (en) 2004-11-29 2014-12-30 The General Hospital Corporation Arrangements, devices, endoscopes, catheters and methods for performing optical imaging by simultaneously illuminating and detecting multiple points on a sample
EP1835861B1 (fr) 2005-01-10 2016-04-13 Optimedica Corporation Appareil de trepanation par laser induit par plasma en forme de capsule de lentille
EP2636383B1 (fr) 2005-01-10 2021-02-24 AMO Development, LLC Appareil pour trépanation à plasma à motifs de capsule lentille
US11364147B2 (en) 2005-01-10 2022-06-21 Amo Development, Llc Apparatus for patterned plasma-mediated laser ophthalmic surgery
US10130510B2 (en) 2005-01-10 2018-11-20 Optimedica Corporation Apparatus for patterned plasma-mediated laser ophthalmic surgery
EP2548528B1 (fr) 2005-01-10 2020-09-30 AMO Development, LLC Appareil pour trépanation à plasma à motifs de capsule lentille et phaco-segmentation tridimensionnelle
US10874553B2 (en) 2005-01-10 2020-12-29 Amo Development, Llc Apparatus for patterned plasma-mediated laser ophthalmic surgery
WO2006078839A2 (fr) * 2005-01-20 2006-07-27 Duke University Procedes, systemes et produits programmes informatiques pour caracteriser des structures sur la base de donnees de phase interferometriques
WO2006078839A3 (fr) * 2005-01-20 2006-11-16 Univ Duke Procedes, systemes et produits programmes informatiques pour caracteriser des structures sur la base de donnees de phase interferometriques
US9839361B2 (en) 2005-01-24 2017-12-12 The Board Of Trustees Of The Leland Stanford Junior University Optical analysis system and approach therefor
US9161694B2 (en) 2005-01-24 2015-10-20 The Board Of Trustees Of The Leland Stanford Junior University Optical analysis system and approach therefor
US9161684B2 (en) 2005-02-28 2015-10-20 University Of Washington Monitoring disposition of tethered capsule endoscope in esophagus
US9872613B2 (en) 2005-02-28 2018-01-23 University Of Washington Monitoring disposition of tethered capsule endoscope in esophagus
US9326682B2 (en) 2005-04-28 2016-05-03 The General Hospital Corporation Systems, processes and software arrangements for evaluating information associated with an anatomical structure by an optical coherence ranging technique
US9441948B2 (en) 2005-08-09 2016-09-13 The General Hospital Corporation Apparatus, methods and storage medium for performing polarization-based quadrature demodulation in optical coherence tomography
US9513276B2 (en) 2005-09-29 2016-12-06 The General Hospital Corporation Method and apparatus for optical imaging via spectral encoding
US8928889B2 (en) 2005-09-29 2015-01-06 The General Hospital Corporation Arrangements and methods for providing multimodality microscopic imaging of one or more biological structures
US9304121B2 (en) 2005-09-29 2016-04-05 The General Hospital Corporation Method and apparatus for optical imaging via spectral encoding
DE102005059271B4 (de) 2005-12-12 2019-02-21 Siemens Healthcare Gmbh Kathetervorrichtung
WO2007084849A1 (fr) * 2006-01-18 2007-07-26 The General Hospital Corporation Système et procédé pour produire des données au moyen d'une ou plusieurs techniques de microscopie endoscopique
US10987000B2 (en) 2006-01-19 2021-04-27 The General Hospital Corporation Methods and systems for optical imaging or epithelial luminal organs by beam scanning thereof
WO2007100937A2 (fr) * 2006-01-19 2007-09-07 The Regents Of The University Of Michigan Système et procédé pour tomographie photo-acoustique spectroscopique
US9516997B2 (en) 2006-01-19 2016-12-13 The General Hospital Corporation Spectrally-encoded endoscopy techniques, apparatus and methods
US9791317B2 (en) 2006-01-19 2017-10-17 The General Hospital Corporation Spectrally-encoded endoscopy techniques and methods
US9646377B2 (en) 2006-01-19 2017-05-09 The General Hospital Corporation Methods and systems for optical imaging or epithelial luminal organs by beam scanning thereof
WO2007100937A3 (fr) * 2006-01-19 2008-07-03 Univ Michigan Système et procédé pour tomographie photo-acoustique spectroscopique
US9087368B2 (en) 2006-01-19 2015-07-21 The General Hospital Corporation Methods and systems for optical imaging or epithelial luminal organs by beam scanning thereof
US9186067B2 (en) 2006-02-01 2015-11-17 The General Hospital Corporation Apparatus for applying a plurality of electro-magnetic radiations to a sample
US9186066B2 (en) 2006-02-01 2015-11-17 The General Hospital Corporation Apparatus for applying a plurality of electro-magnetic radiations to a sample
US10426548B2 (en) 2006-02-01 2019-10-01 The General Hosppital Corporation Methods and systems for providing electromagnetic radiation to at least one portion of a sample using conformal laser therapy procedures
US9777053B2 (en) 2006-02-08 2017-10-03 The General Hospital Corporation Methods, arrangements and systems for obtaining information associated with an anatomical sample using optical microscopy
USRE46412E1 (en) 2006-02-24 2017-05-23 The General Hospital Corporation Methods and systems for performing angle-resolved Fourier-domain optical coherence tomography
US9561078B2 (en) 2006-03-03 2017-02-07 University Of Washington Multi-cladding optical fiber scanner
US10413175B2 (en) 2006-05-10 2019-09-17 The General Hospital Corporation Process, arrangements and systems for providing frequency domain imaging of a sample
US9364143B2 (en) 2006-05-10 2016-06-14 The General Hospital Corporation Process, arrangements and systems for providing frequency domain imaging of a sample
US9867530B2 (en) 2006-08-14 2018-01-16 Volcano Corporation Telescopic side port catheter device with imaging system and method for accessing side branch occlusions
DE102006046925A1 (de) * 2006-09-28 2008-04-03 Jenlab Gmbh Verfahren und Anordnung zur Laser-Endoskopie für die Mikrobearbeitung
US8496579B2 (en) 2006-09-28 2013-07-30 Jenlab Gmbh Method and arrangement for high-resolution microscope imaging or cutting in laser endoscopy
US8838213B2 (en) 2006-10-19 2014-09-16 The General Hospital Corporation Apparatus and method for obtaining and providing imaging information associated with at least one portion of a sample, and effecting such portion(s)
CN103222846A (zh) * 2007-01-19 2013-07-31 桑尼布鲁克健康科学中心 用于成像探头的扫描机构
US9375147B2 (en) 2007-01-19 2016-06-28 Sunnybrook Health Sciences Centre Scanning mechanisms for imaging probe
US9176319B2 (en) 2007-03-23 2015-11-03 The General Hospital Corporation Methods, arrangements and apparatus for utilizing a wavelength-swept laser using angular scanning and dispersion procedures
US10534129B2 (en) 2007-03-30 2020-01-14 The General Hospital Corporation System and method providing intracoronary laser speckle imaging for the detection of vulnerable plaque
US8840566B2 (en) 2007-04-02 2014-09-23 University Of Washington Catheter with imaging capability acts as guidewire for cannula tools
US9622706B2 (en) 2007-07-12 2017-04-18 Volcano Corporation Catheter for in vivo imaging
US10219780B2 (en) 2007-07-12 2019-03-05 Volcano Corporation OCT-IVUS catheter for concurrent luminal imaging
US11350906B2 (en) 2007-07-12 2022-06-07 Philips Image Guided Therapy Corporation OCT-IVUS catheter for concurrent luminal imaging
US9596993B2 (en) 2007-07-12 2017-03-21 Volcano Corporation Automatic calibration systems and methods of use
US9375158B2 (en) 2007-07-31 2016-06-28 The General Hospital Corporation Systems and methods for providing beam scan patterns for high speed doppler optical frequency domain imaging
EP2240068A1 (fr) * 2008-01-04 2010-10-20 Koninklijke Philips Electronics N.V. Sonde optique
US11779219B2 (en) 2008-01-18 2023-10-10 The Board Of Trustees Of The University Of Illinois Low-coherence interferometry and optical coherence tomography for image-guided surgical treatment of solid tumors
US8983580B2 (en) 2008-01-18 2015-03-17 The Board Of Trustees Of The University Of Illinois Low-coherence interferometry and optical coherence tomography for image-guided surgical treatment of solid tumors
US11123047B2 (en) 2008-01-28 2021-09-21 The General Hospital Corporation Hybrid systems and methods for multi-modal acquisition of intravascular imaging data and counteracting the effects of signal absorption in blood
US9332942B2 (en) 2008-01-28 2016-05-10 The General Hospital Corporation Systems, processes and computer-accessible medium for providing hybrid flourescence and optical coherence tomography imaging
US9521946B2 (en) 2008-06-18 2016-12-20 Sarcos Lc Transparent endoscope head defining a focal length
US8690762B2 (en) 2008-06-18 2014-04-08 Raytheon Company Transparent endoscope head defining a focal length
US8861910B2 (en) 2008-06-20 2014-10-14 The General Hospital Corporation Fused fiber optic coupler arrangement and method for use thereof
US9254089B2 (en) 2008-07-14 2016-02-09 The General Hospital Corporation Apparatus and methods for facilitating at least partial overlap of dispersed ration on at least one sample
US10835110B2 (en) 2008-07-14 2020-11-17 The General Hospital Corporation Apparatus and method for facilitating at least partial overlap of dispersed ration on at least one sample
US10080499B2 (en) 2008-07-30 2018-09-25 Medtronic, Inc. Implantable medical system including multiple sensing modules
WO2010014059A1 (fr) * 2008-07-30 2010-02-04 Medtronic, Inc. Système médical implantable comprenant de multiples modules de détection
EP2156804A1 (fr) 2008-08-18 2010-02-24 FUJIFILM Corporation Appareil de traitement laser
US9060704B2 (en) 2008-11-04 2015-06-23 Sarcos Lc Method and device for wavelength shifted imaging
US9717418B2 (en) 2008-11-04 2017-08-01 Sarcos Lc Method and device for wavelength shifted imaging
WO2010060622A2 (fr) * 2008-11-26 2010-06-03 Carl Zeiss Surgical Gmbh Système d'imagerie
US9618326B2 (en) 2008-11-26 2017-04-11 Carl Zeiss Meditec Ag Imaging system
US9377293B2 (en) 2008-11-26 2016-06-28 Carl Zeiss Meditec Ag Imaging system
US8922882B2 (en) 2008-11-26 2014-12-30 Carl Zeiss Meditec Ag Imaging system
US9962076B2 (en) 2008-11-26 2018-05-08 Carl Zeiss Meditec Ag Imaging system
US10098538B2 (en) 2008-11-26 2018-10-16 Carl Zeiss Meditec Ag Imaging system
WO2010060622A3 (fr) * 2008-11-26 2010-07-29 Carl Zeiss Surgical Gmbh Système d'imagerie
US8937724B2 (en) 2008-12-10 2015-01-20 The General Hospital Corporation Systems and methods for extending imaging depth range of optical coherence tomography through optical sub-sampling
US9178330B2 (en) 2009-02-04 2015-11-03 The General Hospital Corporation Apparatus and method for utilization of a high-speed optical wavelength tuning source
US9351642B2 (en) 2009-03-12 2016-05-31 The General Hospital Corporation Non-contact optical system, computer-accessible medium and method for measurement at least one mechanical property of tissue using coherent speckle technique(s)
US11490826B2 (en) 2009-07-14 2022-11-08 The General Hospital Corporation Apparatus, systems and methods for measuring flow and pressure within a vessel
US10433910B2 (en) 2009-09-14 2019-10-08 Memorial Sloan Kettering Cancer Center Apparatus, system and method for providing laser steering and focusing for incision, excision and ablation of tissue in minimally-invasive surgery
EP3443922A3 (fr) * 2009-09-14 2019-06-12 Memorial Sloan-Kettering Cancer Center Appareil, système et procédé de fourniture d'orientation et de mise au point laser pour incision, excision et ablation de tissus en chirurgie mini-invasive
US9661996B2 (en) 2009-10-01 2017-05-30 Sarcos Lc Needle delivered imaging device
US9144664B2 (en) 2009-10-01 2015-09-29 Sarcos Lc Method and apparatus for manipulating movement of a micro-catheter
US9408539B2 (en) 2010-03-05 2016-08-09 The General Hospital Corporation Systems, methods and computer-accessible medium which provide microscopic images of at least one anatomical structure at a particular resolution
US10463254B2 (en) 2010-03-05 2019-11-05 The General Hospital Corporation Light tunnel and lens which provide extended focal depth of at least one anatomical structure at a particular resolution
US8896838B2 (en) 2010-03-05 2014-11-25 The General Hospital Corporation Systems, methods and computer-accessible medium which provide microscopic images of at least one anatomical structure at a particular resolution
US9642531B2 (en) 2010-03-05 2017-05-09 The General Hospital Corporation Systems, methods and computer-accessible medium which provide microscopic images of at least one anatomical structure at a particular resolution
US9081148B2 (en) 2010-03-05 2015-07-14 The General Hospital Corporation Systems, methods and computer-accessible medium which provide microscopic images of at least one anatomical structure at a particular resolution
US9069130B2 (en) 2010-05-03 2015-06-30 The General Hospital Corporation Apparatus, method and system for generating optical radiation from biological gain media
US9951269B2 (en) 2010-05-03 2018-04-24 The General Hospital Corporation Apparatus, method and system for generating optical radiation from biological gain media
US10939825B2 (en) 2010-05-25 2021-03-09 The General Hospital Corporation Systems, devices, methods, apparatus and computer-accessible media for providing optical imaging of structures and compositions
US9557154B2 (en) 2010-05-25 2017-01-31 The General Hospital Corporation Systems, devices, methods, apparatus and computer-accessible media for providing optical imaging of structures and compositions
US9795301B2 (en) 2010-05-25 2017-10-24 The General Hospital Corporation Apparatus, systems, methods and computer-accessible medium for spectral analysis of optical coherence tomography images
US10285568B2 (en) 2010-06-03 2019-05-14 The General Hospital Corporation Apparatus and method for devices for imaging structures in or at one or more luminal organs
US9241693B2 (en) 2010-07-20 2016-01-26 The Johns Hopkins University Interferometric force sensor for surgical instruments
CN103153248A (zh) * 2010-07-20 2013-06-12 约翰霍普金斯大学 用于外科手术仪器的干涉型力传感器
US10039530B2 (en) 2010-07-20 2018-08-07 The Johns Hopkins University Interferometric force sensor for surgical instruments
WO2012012565A3 (fr) * 2010-07-20 2012-05-10 The Johns Hopkins University Capteur de force interférométrique pour des instruments chirurgicaux
US9510758B2 (en) 2010-10-27 2016-12-06 The General Hospital Corporation Apparatus, systems and methods for measuring blood pressure within at least one vessel
US11141063B2 (en) 2010-12-23 2021-10-12 Philips Image Guided Therapy Corporation Integrated system architectures and methods of use
US11040140B2 (en) 2010-12-31 2021-06-22 Philips Image Guided Therapy Corporation Deep vein thrombosis therapeutic methods
JP2014504520A (ja) * 2011-01-21 2014-02-24 アルコン リサーチ， リミテッド 逆回転する眼科スキャナ駆動機構
US10286106B2 (en) 2011-03-07 2019-05-14 The Regents Of The University Of Colorado Intraocular lenses
US10286107B2 (en) 2011-03-07 2019-05-14 The Regents Of The University Of Colorado, A Body Corporate Shape memory polymer intraocular lenses
EP2520221A1 (fr) * 2011-05-03 2012-11-07 W & H Dentalwerk Bürmoos GmbH Pièce manuelle pour un appareil de diagnostic médical et appareil de diagnostic médical
US9330092B2 (en) 2011-07-19 2016-05-03 The General Hospital Corporation Systems, methods, apparatus and computer-accessible-medium for providing polarization-mode dispersion compensation in optical coherence tomography
US10241028B2 (en) 2011-08-25 2019-03-26 The General Hospital Corporation Methods, systems, arrangements and computer-accessible medium for providing micro-optical coherence tomography procedures
US9360630B2 (en) 2011-08-31 2016-06-07 Volcano Corporation Optical-electrical rotary joint and methods of use
US9341783B2 (en) 2011-10-18 2016-05-17 The General Hospital Corporation Apparatus and methods for producing and/or providing recirculating optical delay(s)
US11051698B2 (en) 2011-11-14 2021-07-06 Koninklijke Philips N.V. Optical microscopy probe for scanning microscopy of an associated object
WO2013072796A1 (fr) * 2011-11-14 2013-05-23 Koninklijke Philips Electronics N.V. Sonde de microscopie optique permettant une microscopie à balayage d'un objet associé
US9629528B2 (en) 2012-03-30 2017-04-25 The General Hospital Corporation Imaging system, method and distal attachment for multidirectional field of view endoscopy
US11490797B2 (en) 2012-05-21 2022-11-08 The General Hospital Corporation Apparatus, device and method for capsule microscopy
CN104519804A (zh) * 2012-07-02 2015-04-15 皇家飞利浦有限公司 微创医疗器械
US9415550B2 (en) 2012-08-22 2016-08-16 The General Hospital Corporation System, method, and computer-accessible medium for fabrication miniature endoscope using soft lithography
US10070827B2 (en) 2012-10-05 2018-09-11 Volcano Corporation Automatic image playback
US10568586B2 (en) 2012-10-05 2020-02-25 Volcano Corporation Systems for indicating parameters in an imaging data set and methods of use
US9324141B2 (en) 2012-10-05 2016-04-26 Volcano Corporation Removal of A-scan streaking artifact
US11864870B2 (en) 2012-10-05 2024-01-09 Philips Image Guided Therapy Corporation System and method for instant and automatic border detection
US11272845B2 (en) 2012-10-05 2022-03-15 Philips Image Guided Therapy Corporation System and method for instant and automatic border detection
US9286673B2 (en) 2012-10-05 2016-03-15 Volcano Corporation Systems for correcting distortions in a medical image and methods of use thereof
US11890117B2 (en) 2012-10-05 2024-02-06 Philips Image Guided Therapy Corporation Systems for indicating parameters in an imaging data set and methods of use
US9307926B2 (en) 2012-10-05 2016-04-12 Volcano Corporation Automatic stent detection
US9858668B2 (en) 2012-10-05 2018-01-02 Volcano Corporation Guidewire artifact removal in images
US9292918B2 (en) 2012-10-05 2016-03-22 Volcano Corporation Methods and systems for transforming luminal images
US9478940B2 (en) 2012-10-05 2016-10-25 Volcano Corporation Systems and methods for amplifying light
US9367965B2 (en) 2012-10-05 2016-06-14 Volcano Corporation Systems and methods for generating images of tissue
US11510632B2 (en) 2012-10-05 2022-11-29 Philips Image Guided Therapy Corporation Systems for indicating parameters in an imaging data set and methods of use
US10724082B2 (en) 2012-10-22 2020-07-28 Bio-Rad Laboratories, Inc. Methods for analyzing DNA
US10238367B2 (en) 2012-12-13 2019-03-26 Volcano Corporation Devices, systems, and methods for targeted cannulation
US11406498B2 (en) 2012-12-20 2022-08-09 Philips Image Guided Therapy Corporation Implant delivery system and implants
US10595820B2 (en) 2012-12-20 2020-03-24 Philips Image Guided Therapy Corporation Smooth transition catheters
US9709379B2 (en) 2012-12-20 2017-07-18 Volcano Corporation Optical coherence tomography system that is reconfigurable between different imaging modes
US11892289B2 (en) 2012-12-20 2024-02-06 Philips Image Guided Therapy Corporation Manual calibration of imaging system
US11141131B2 (en) 2012-12-20 2021-10-12 Philips Image Guided Therapy Corporation Smooth transition catheters
US10942022B2 (en) 2012-12-20 2021-03-09 Philips Image Guided Therapy Corporation Manual calibration of imaging system
US10939826B2 (en) 2012-12-20 2021-03-09 Philips Image Guided Therapy Corporation Aspirating and removing biological material
US9730613B2 (en) 2012-12-20 2017-08-15 Volcano Corporation Locating intravascular images
US10993694B2 (en) 2012-12-21 2021-05-04 Philips Image Guided Therapy Corporation Rotational ultrasound imaging catheter with extended catheter body telescope
US10191220B2 (en) 2012-12-21 2019-01-29 Volcano Corporation Power-efficient optical circuit
US9486143B2 (en) 2012-12-21 2016-11-08 Volcano Corporation Intravascular forward imaging device
US10166003B2 (en) 2012-12-21 2019-01-01 Volcano Corporation Ultrasound imaging with variable line density
US10058284B2 (en) 2012-12-21 2018-08-28 Volcano Corporation Simultaneous imaging, monitoring, and therapy
US10420530B2 (en) 2012-12-21 2019-09-24 Volcano Corporation System and method for multipath processing of image signals
US10413317B2 (en) 2012-12-21 2019-09-17 Volcano Corporation System and method for catheter steering and operation
US11786213B2 (en) 2012-12-21 2023-10-17 Philips Image Guided Therapy Corporation System and method for multipath processing of image signals
US9383263B2 (en) 2012-12-21 2016-07-05 Volcano Corporation Systems and methods for narrowing a wavelength emission of light
US10332228B2 (en) 2012-12-21 2019-06-25 Volcano Corporation System and method for graphical processing of medical data
US11253225B2 (en) 2012-12-21 2022-02-22 Philips Image Guided Therapy Corporation System and method for multipath processing of image signals
US9612105B2 (en) 2012-12-21 2017-04-04 Volcano Corporation Polarization sensitive optical coherence tomography system
US10893806B2 (en) 2013-01-29 2021-01-19 The General Hospital Corporation Apparatus, systems and methods for providing information regarding the aortic valve
US11179028B2 (en) 2013-02-01 2021-11-23 The General Hospital Corporation Objective lens arrangement for confocal endomicroscopy
US10226597B2 (en) 2013-03-07 2019-03-12 Volcano Corporation Guidewire with centering mechanism
US9770172B2 (en) 2013-03-07 2017-09-26 Volcano Corporation Multimodal segmentation in intravascular images
US11154313B2 (en) 2013-03-12 2021-10-26 The Volcano Corporation Vibrating guidewire torquer and methods of use
US10638939B2 (en) 2013-03-12 2020-05-05 Philips Image Guided Therapy Corporation Systems and methods for diagnosing coronary microvascular disease
US9301687B2 (en) 2013-03-13 2016-04-05 Volcano Corporation System and method for OCT depth calibration
US11026591B2 (en) 2013-03-13 2021-06-08 Philips Image Guided Therapy Corporation Intravascular pressure sensor calibration
US10758207B2 (en) 2013-03-13 2020-09-01 Philips Image Guided Therapy Corporation Systems and methods for producing an image from a rotational intravascular ultrasound device
US10426590B2 (en) 2013-03-14 2019-10-01 Volcano Corporation Filters with echogenic characteristics
US10292677B2 (en) 2013-03-14 2019-05-21 Volcano Corporation Endoluminal filter having enhanced echogenic properties
US10219887B2 (en) 2013-03-14 2019-03-05 Volcano Corporation Filters with echogenic characteristics
US9814390B2 (en) 2013-03-15 2017-11-14 Synaptive Medical (Barbados) Inc. Insert imaging device for surgical procedures
US10292771B2 (en) 2013-03-15 2019-05-21 Synaptive Medical (Barbados) Inc. Surgical imaging systems
US10478072B2 (en) 2013-03-15 2019-11-19 The General Hospital Corporation Methods and system for characterizing an object
US10945656B2 (en) 2013-04-05 2021-03-16 The University Of Massachusetts Device and method for imaging collagen structure in vivo
WO2014165820A1 (fr) * 2013-04-05 2014-10-09 University Of Massachusetts Dispositif et procédé pour imagerie d'une structure de collagène in vivo
US9784681B2 (en) 2013-05-13 2017-10-10 The General Hospital Corporation System and method for efficient detection of the phase and amplitude of a periodic modulation associated with self-interfering fluorescence
US10117576B2 (en) 2013-07-19 2018-11-06 The General Hospital Corporation System, method and computer accessible medium for determining eye motion by imaging retina and providing feedback for acquisition of signals from the retina
US11452433B2 (en) 2013-07-19 2022-09-27 The General Hospital Corporation Imaging apparatus and method which utilizes multidirectional field of view endoscopy
US9668652B2 (en) 2013-07-26 2017-06-06 The General Hospital Corporation System, apparatus and method for utilizing optical dispersion for fourier-domain optical coherence tomography
US10058250B2 (en) 2013-07-26 2018-08-28 The General Hospital Corporation System, apparatus and method for utilizing optical dispersion for fourier-domain optical coherence tomography
EP3082564A4 (fr) * 2013-12-18 2017-08-30 Novartis AG Sonde de balayage vers l'avant bidimensionnel
EP3086704B1 (fr) * 2013-12-23 2020-04-22 Alcon Inc. Sonde optique de balayage vers l'avant
US9733460B2 (en) 2014-01-08 2017-08-15 The General Hospital Corporation Method and apparatus for microscopic imaging
US10736494B2 (en) 2014-01-31 2020-08-11 The General Hospital Corporation System and method for facilitating manual and/or automatic volumetric imaging with real-time tension or force feedback using a tethered imaging device
US10228556B2 (en) 2014-04-04 2019-03-12 The General Hospital Corporation Apparatus and method for controlling propagation and/or transmission of electromagnetic radiation in flexible waveguide(s)
US10912462B2 (en) 2014-07-25 2021-02-09 The General Hospital Corporation Apparatus, devices and methods for in vivo imaging and diagnosis
US11517199B2 (en) 2014-08-08 2022-12-06 Medlumics S.L. Crossing coronary occlusions
WO2017066872A1 (fr) * 2015-10-22 2017-04-27 Medtronic Cryocath Lp Technique d'analyse de tissu post-ablation
US11806064B2 (en) 2015-10-22 2023-11-07 Medtronic Cryocath Lp Post ablation tissue analysis technique
US10799280B2 (en) 2015-10-22 2020-10-13 Medtronic Cryocath Lp Post ablation tissue analysis technique
KR101835043B1 (ko) 2015-11-03 2018-03-08 (주) 인텍플러스 조직절제기 및 조직절제시스템
WO2017078226A1 (fr) * 2015-11-03 2017-05-11 고려대학교 산학협력단 Exciseur de tissu et système d'excision de tissu
US20170343791A1 (en) * 2016-05-30 2017-11-30 Eric Swanson Few-mode fiber endoscope
US11774743B2 (en) 2016-05-30 2023-10-03 Eric Swanson Few-mode optical fiber measurement instrument
US10969571B2 (en) * 2016-05-30 2021-04-06 Eric Swanson Few-mode fiber endoscope
EP3323340A1 (fr) * 2016-11-16 2018-05-23 Karl Storz SE & Co. KG Sonde endoscopique, système et procédé de tomographie par cohérence optique et d'endoscopie confocale
US11555742B2 (en) 2018-09-04 2023-01-17 Provincial Health Services Authority Image guided micro-Raman spectroscopy
WO2020047660A1 (fr) * 2018-09-04 2020-03-12 Provincial Health Services Authority Microspectroscopie raman guidée par image
DE102019207873A1 (de) * 2019-05-29 2020-12-03 Leica Microsystems Cms Gmbh Optischer Aufbau für ein Mikroskop und Mikroskop
DE102019207873B4 (de) 2019-05-29 2021-10-14 Leica Microsystems Cms Gmbh Optischer Aufbau für ein Mikroskop und Mikroskop
WO2022130022A1 (fr) * 2020-12-14 2022-06-23 Rockley Photonics Limited Dispositif minimalement invasif pourvu d'un spectrophotomètre
CN113197555A (zh) * 2021-06-04 2021-08-03 哈尔滨医科大学 多方向oct图像采集导管
CN113455992A (zh) * 2021-06-04 2021-10-01 哈尔滨医科大学 一种成像导管及成像装置

Also Published As

Publication number Publication date
JP2001515382A (ja) 2001-09-18
EP0971626A1 (fr) 2000-01-19

Similar Documents

Publication Publication Date Title
US6485413B1 (en) Methods and apparatus for forward-directed optical scanning instruments
WO1998038907A1 (fr) Instrument d'analyse a balayage optique de tissu vivant
US6564087B1 (en) Fiber optic needle probes for optical coherence tomography imaging
US7616986B2 (en) Optical fiber scanner for performing multimodal optical imaging
EP2789291B1 (fr) Sonde d'imagerie endoscopique miniature codée spectralement
US9014788B2 (en) Apparatus and method for real-time imaging and monitoring of an electrosurgical procedure
US6831781B2 (en) Confocal microscopy with multi-spectral encoding and system and apparatus for spectroscopically encoded confocal microscopy
US6370422B1 (en) Fiber-optic confocal imaging apparatus and methods of use
EP0883793B1 (fr) Procede et appareil permettant d'effectuer des mesures optiques a l'aide d'un endoscope, un catheter ou un fil de guidage d'imagerie a fibre optique
US8666209B2 (en) Delivering light via optical waveguide and multi-view optical probe head
US20110282192A1 (en) Multimodal depth-resolving endoscope
US20130317294A1 (en) Scanning endoscopic imaging probes and related methods
WO1998038907B1 (fr) Instrument d'analyse a balayage optique de tissu vivant
WO2001097902A9 (fr) Imagerie medicale, diagnostic et therapie reposant sur l'utilisation d'un systeme de balayage a une seule fibre optique
US11681093B2 (en) Multicore fiber with distal motor
US10070784B2 (en) OCT vitrectomy probe
Boppart Surgical diagnostics, guidance, and intervention using optical coherence tomography
Pitris et al. A Novel GRISM-Based Probe for Spectrally Encoded Confocal Microscopy

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): JP

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): AT BE CH DE DK ES FI FR GB GR IE IT LU MC NL PT SE

DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
121 Ep: the epo has been informed by wipo that ep was designated in this application
ENP Entry into the national phase

Ref country code: JP

Ref document number: 1998 538826

Kind code of ref document: A

Format of ref document f/p: F

WWE Wipo information: entry into national phase

Ref document number: 1998915128

Country of ref document: EP

WWP Wipo information: published in national office

Ref document number: 1998915128

Country of ref document: EP