WO1999044089A1 - Confocal microscopy with multi-spectral encoding - Google Patents

Confocal microscopy with multi-spectral encoding Download PDF

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Publication number
WO1999044089A1
WO1999044089A1 PCT/US1999/004356 US9904356W WO9944089A1 WO 1999044089 A1 WO1999044089 A1 WO 1999044089A1 US 9904356 W US9904356 W US 9904356W WO 9944089 A1 WO9944089 A1 WO 9944089A1
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Prior art keywords
probe
spectrum
light
confocal
tissue
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PCT/US1999/004356
Other languages
French (fr)
Inventor
Robert H. Webb
Guillermo J. Tearney
Brett E. Bouma
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The General Hospital Corporation
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Filing date
Publication date
Application filed by The General Hospital Corporation filed Critical The General Hospital Corporation
Priority to AU28823/99A priority Critical patent/AU758078B2/en
Priority to US09/622,971 priority patent/US6341036B1/en
Priority to EP99909668A priority patent/EP1057063A4/en
Priority to JP2000533782A priority patent/JP4709969B2/en
Publication of WO1999044089A1 publication Critical patent/WO1999044089A1/en

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    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B21/00—Microscopes
    • G02B21/0004—Microscopes specially adapted for specific applications
    • G02B21/002—Scanning microscopes
    • G02B21/0024—Confocal scanning microscopes (CSOMs) or confocal "macroscopes"; Accessories which are not restricted to use with CSOMs, e.g. sample holders
    • G02B21/0052—Optical details of the image generation
    • G02B21/0064—Optical details of the image generation multi-spectral or wavelength-selective arrangements, e.g. wavelength fan-out, chromatic profiling
    • 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
    • A61B5/0062—Arrangements for scanning
    • A61B5/0068—Confocal scanning
    • 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
    • A61B5/68—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
    • G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
    • G01J3/00—Spectrometry; Spectrophotometry; Monochromators; Measuring colours
    • G01J3/28—Investigating the spectrum
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B21/00—Microscopes
    • G02B21/0004—Microscopes specially adapted for specific applications
    • G02B21/002—Scanning microscopes
    • G02B21/0024—Confocal scanning microscopes (CSOMs) or confocal "macroscopes"; Accessories which are not restricted to use with CSOMs, e.g. sample holders
    • G02B21/0028—Confocal scanning microscopes (CSOMs) or confocal "macroscopes"; Accessories which are not restricted to use with CSOMs, e.g. sample holders specially adapted for specific applications, e.g. for endoscopes, ophthalmoscopes, attachments to conventional microscopes
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B21/00—Microscopes
    • G02B21/0004—Microscopes specially adapted for specific applications
    • G02B21/002—Scanning microscopes
    • G02B21/0024—Confocal scanning microscopes (CSOMs) or confocal "macroscopes"; Accessories which are not restricted to use with CSOMs, e.g. sample holders
    • G02B21/0052—Optical details of the image generation
    • G02B21/0056—Optical details of the image generation based on optical coherence, e.g. phase-contrast arrangements, interference arrangements
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B21/00—Microscopes
    • G02B21/0004—Microscopes specially adapted for specific applications
    • G02B21/002—Scanning microscopes
    • G02B21/0024—Confocal scanning microscopes (CSOMs) or confocal "macroscopes"; Accessories which are not restricted to use with CSOMs, e.g. sample holders
    • G02B21/0052—Optical details of the image generation
    • G02B21/0076—Optical details of the image generation arrangements using fluorescence or luminescence
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
    • G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
    • G02B23/2407—Optical details
    • G02B23/2453—Optical details of the proximal end
    • 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
    • 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

Definitions

  • the present invention relates to systems (method and apparatus) for confocal microscopy for the examination or imaging of sections of a specimen of biological tissue, and particularly to such systems using multi-spectral illumination and processing of multi-spectral light.
  • Multi-spectral light was proposed for use in confocal microscopy, but only for imaging vertically-spaced regions of a body under examination. See B. Picard, U.S. Patent No. 4,965,441, issued October 25, 1990.
  • An interferometer using a grating to obtain multi- spectral light which is resolved in the interferometer to obtain a spectroscopic image is disclosed in A. Knuttal, U.S. Patent 5,565,986, issued October 15, 1996.
  • a lens having a color separation grating which obtains a multi-spectral light is disclosed in U.S. Patent No. 5,600,486, issued February 4, 1997.
  • Such multi-spectral proposals are not effective for high resolution imaging using a compact, flexible probe.
  • a confocal microscope system can be miniaturized and incorporated into a compact probe.
  • the probe may also be easily incorporated into catheters or endoscopes.
  • a confocal microscope in accordance with -2- the invention allows imaging of all accessible surfaces of the body and increases the biomedical applications of confocal microscopy by an order of magnitude.
  • a confocal microscopy system embodying the invention illuminates a region of interest in a body into which said probe may be inserted with a confocal spectrum extending along one dimension.
  • Optics in said probe or physical movement of said probe enabled by attachment thereto of a flexible light conductive member (which may be an optical fiber), enables scanning of said spectrum along one or two additional dimensions thereby providing for two or three dimensional imaging of the region.
  • the reflected confocal spectrum may be detected or decoded spectroscopically, preferably with a heterodyne detection mechanism which may be implemented interferometrically.
  • Fig. 1 is a schematic diagram of a spectrally encoded confocal probe in accordance with the invention where specific wavelengths are shown for illustrative purposes, their exact values depending on the optical parameters of the system.
  • Fig. 2 is a plot of spectrally encoded light obtained by confocal detection using direct spectral detection in accordance with this invention, where different wavelengths are detected by turning the spectrometer grating.
  • Fig. 3 is a schematic diagram showing a system embodying the invention using a spectrometer for measurement of the spectrum, I( ⁇ ), which corresponds to reflectance from different transverse locations, x, on the specimen.
  • Fig. 4 is a schematic diagram of a system embodying the invention having spectrally encoded confocal detection using interference spectroscopy.
  • Fig. 5A-D are schematic diagrams showing: (a) image formation; (b) translation of the optical fiber in the y direction; (c) rotation of the optical fiber in the forward firing mode; and
  • FIG. 6 is a schematic diagram showing cross-sectional image formation by scanning the optical fiber or the objective lens along the z axis using a system embodying the invention.
  • Fig. 7 is another schematic diagram of a system embodying the invention wherein optical zoom is achieved by moving the focus of an intermediate lens in and out of the image plan of the objective.
  • multi-spectral encoding for confocal microscopy uses a broad bandwidth source 10 as the input to the microscope.
  • the source spectrum provided via an optical fiber 9 is dispersed by a grating 12 and focused by an objective lens 14 onto the sample 16.
  • a lens 9a is preferably disposed between the optical fiber 9 and the grating 12 to collimate the light from the optical fiber, as shown in Fig. 1, however, lens 9a may be removed.
  • the spot for each wavelength is focused at a separate position, x, on the sample (Fig.l).
  • the reflectance as a function of transverse location is determined by measuring the reflected confocal spectrum from the sample 16 returned from probe 8.
  • the number of wavelengths or points that may be resolved is determined by:
  • ⁇ is the center wavelength
  • ⁇ is the bandwidth of the spectrum
  • N is the number of lines in the grating 12 illuminated by the polychromatic input beam 10
  • m is the diffraction order. If the total bandwidth of the source is ⁇ , the number of resolvable points, n is defined by:
  • the parameters used in this example may be found in common, inexpensive optical components.
  • the number of points may be increased by simply increasing the input spot diameter or the bandwidth of the source. Increasing the spot diameter increases the resultant probe diameter.
  • Increasing the bandwidth of the source could be accomplished by using a broader bandwidth superluminescent diode, a rare earth doped fiber superfluorescent source, or a solid state modelocked laser.
  • the reflectance from the sample 16 as a function of transverse location is determined by measuring the reflected confocal spectrum from the sample arm 18.
  • the spectrum may be measured efficiently by incorporating the probe 8 in the sample arm of a Michelson interferometer 20 (Fig. 3) and detecting the light transmitted through a high resolution spectrometer 21 at the output port 19 of the interferometer.
  • each wavelength measured corresponds to a separate position, x, on the sample (Fig. 3).
  • the advantage to this method over traditional real time confocal microscopy is that the fast axis scanning (- 15 kHz) may be performed external to the probe 8 by the spectrometer 21 with approximately .1 nm spectral resolution for the parameters given above, well within reach of high quality spectrometers. High sensitivity may be achieved through the use of heterodyne detection. If the reference arm 22 is modulated, such as by modulator 23 with mirror 24 (Fig. 3), the interference of light from the sample arm 18 and the reference arm 22 will also be modulated. High signal-to-noise ratios may be then achieved by lock-in detection on the reference arm modulation frequency of detector 26.
  • Another method for measuring the spectrum is interference or Fourier transform spectroscopy. This may be accomplished by inserting a linearly translating mirror 28 in the reference arm 22 and measuring the cross-correlation output 30 from the interference spectrometer due to the interference of the reflected light from the sample and reference arms 18 and 22, respectively (Fig. 4).
  • the advantages to this type of spectroscopic detection include the ability to achieve higher spectral resolutions than direct detection methods, efficient use of the returned light, inherent modulation of the reference arm 22 by the Doppler shift of the moving mirror 28, and the capability to extract both reflectance and phase data from the sample 16.
  • phase data from the sample may allow detection of refractive index as a function of transverse position, x, which is useful to reveal the molecular composition of the sample as well as provide an additional source of image contrast other than the reflectivity of the sample specimen 16.
  • interferometric detection has the potential to allow elimination of high order multiple scattering from the confocal signal by coherence gating.
  • the multi-spectral encoding of the transverse location, x allows the performance of a one-dimensional raster scan.
  • a scan of another axis must be performed, which is usually slower.
  • Methods of accomplishing this slow scanning of the y axis include moving the optical fiber 9 in the y direction (Fig. 5B), or rotating the entire probe 8 around the optical fiber axis either in a forward scanning configuration (Fig. 5C) or a side-firing configuration (Fig. 5D).
  • Cross-sectional images may be created by scanning the optical fiber 9 or the objective lens 14 along the z axis (Fig. 6).
  • a zoom mode may be created by scanning the optical fiber 9 (or another lens 32 between grating 12 and objective lens 14), in and out of the image plane of the objective lens (Fig. 7). Both linear motion along the y or z axis and rotation are easily accomplished in a compact probe by use of piezoelectric transducers.
  • signals may be received by a computer 34 from spectroscopic detector 32 by a spectrometer (such as described in connection with FIG. 3) or Fourier transform (such as described connection with -6- FIG. 4) representing an image of the a microscopic section of the sample, and the image displayed on a display coupled to the computer.
  • the invention provides a confocal microscopy system which (a) is compact, optical fiber-based, capable of enabling confocal microscopy through a flexible catheter or endoscope; (b) is fast-scanning which takes place external to the probe; (c) allows phase information to be retrieved; and (d) provides a number of resolvable points proportional to the bandwidth of the source and the beam diameter on the grating.
  • Variations and modifications in the herein described confocal microscopy system in accordance with the invention will undoubtedly suggest themselves to those skilled in the art. Accordingly, the foregoing description should be taken as illustrative and not in a limiting sense.

Abstract

A scanning confocal microscopy system, especially useful for endoscopy with a flexible probe which is connected to the end of an optical fiber (9). The probe has a grating (12) and a lens (14) which delivers a beam of multi-spectral light having spectral components which extend in one dimension across a region of an object and which is moved to scan in another dimension. The reflected confocal spectrum is measured to provide an image of the region.

Description

CONFOCAL MICROSCOPY WITH MULTI-SPECTRAL ENCODING
This application claims the priority benefit of U.S. Provisional Application No. 60/076,041, filed 26 February 1998.
Description The present invention relates to systems (method and apparatus) for confocal microscopy for the examination or imaging of sections of a specimen of biological tissue, and particularly to such systems using multi-spectral illumination and processing of multi-spectral light.
Currently, the use of fast scanning confocal microscopy is limited to accessible surfaces of the skin and the eye. The reason for this is that the only reliable methods for optical scanning must be performed in free space. In addition, the size of these optical scanners prohibit their use in small probes such as endoscopes or catheters. It is a feature of the invention to miniaturize the fast scanning mechanism and increase the number of medical applications of confocal microscopy to include all surfaces of the body, gynecologic applications, probe-based applications, and internal organ systems.
Multi-spectral light was proposed for use in confocal microscopy, but only for imaging vertically-spaced regions of a body under examination. See B. Picard, U.S. Patent No. 4,965,441, issued October 25, 1990. An interferometer using a grating to obtain multi- spectral light which is resolved in the interferometer to obtain a spectroscopic image is disclosed in A. Knuttal, U.S. Patent 5,565,986, issued October 15, 1996. A lens having a color separation grating which obtains a multi-spectral light is disclosed in U.S. Patent No. 5,600,486, issued February 4, 1997. Such multi-spectral proposals are not effective for high resolution imaging using a compact, flexible probe. A confocal microscope system according to this invention can be miniaturized and incorporated into a compact probe. In addition, by allowing light delivery through a single optical fiber, the probe may also be easily incorporated into catheters or endoscopes. Thus, a confocal microscope in accordance with -2- the invention allows imaging of all accessible surfaces of the body and increases the biomedical applications of confocal microscopy by an order of magnitude.
Briefly described, a confocal microscopy system embodying the invention illuminates a region of interest in a body into which said probe may be inserted with a confocal spectrum extending along one dimension. Optics in said probe or physical movement of said probe enabled by attachment thereto of a flexible light conductive member (which may be an optical fiber), enables scanning of said spectrum along one or two additional dimensions thereby providing for two or three dimensional imaging of the region. The reflected confocal spectrum may be detected or decoded spectroscopically, preferably with a heterodyne detection mechanism which may be implemented interferometrically. The invention will be more apparent from the following drawings wherein
Fig. 1 is a schematic diagram of a spectrally encoded confocal probe in accordance with the invention where specific wavelengths are shown for illustrative purposes, their exact values depending on the optical parameters of the system.
Fig. 2 is a plot of spectrally encoded light obtained by confocal detection using direct spectral detection in accordance with this invention, where different wavelengths are detected by turning the spectrometer grating.
Fig. 3 is a schematic diagram showing a system embodying the invention using a spectrometer for measurement of the spectrum, I(λ), which corresponds to reflectance from different transverse locations, x, on the specimen. Fig. 4 is a schematic diagram of a system embodying the invention having spectrally encoded confocal detection using interference spectroscopy.
Fig. 5A-D are schematic diagrams showing: (a) image formation; (b) translation of the optical fiber in the y direction; (c) rotation of the optical fiber in the forward firing mode; and
(d) rotation of the optical fiber in the side firing mode. Fig. 6 is a schematic diagram showing cross-sectional image formation by scanning the optical fiber or the objective lens along the z axis using a system embodying the invention. Fig. 7 is another schematic diagram of a system embodying the invention wherein optical zoom is achieved by moving the focus of an intermediate lens in and out of the image plan of the objective. Referring now to the figures, multi-spectral encoding for confocal microscopy uses a broad bandwidth source 10 as the input to the microscope. In the probe 8 of the microscope, the source spectrum provided via an optical fiber 9 is dispersed by a grating 12 and focused by an objective lens 14 onto the sample 16. A lens 9a is preferably disposed between the optical fiber 9 and the grating 12 to collimate the light from the optical fiber, as shown in Fig. 1, however, lens 9a may be removed. The spot for each wavelength is focused at a separate position, x, on the sample (Fig.l). The reflectance as a function of transverse location is determined by measuring the reflected confocal spectrum from the sample 16 returned from probe 8.
The number of wavelengths or points that may be resolved is determined by:
=mN, δλ (1)
where λ is the center wavelength, δλ is the bandwidth of the spectrum, N is the number of lines in the grating 12 illuminated by the polychromatic input beam 10, and m is the diffraction order. If the total bandwidth of the source is Δλ, the number of resolvable points, n is defined by:
Δλ -4-
For an input source with a center wavelength of 800 nm, a bandwidth of 25 nm, an input spot diameter of 5 mm, a diffraction grating of 1800 lines/mm and a diffraction order of 1, n = 281 points may be resolved by the spectrally encoded confocal system (FIG. 2). The parameters used in this example may be found in common, inexpensive optical components. The number of points may be increased by simply increasing the input spot diameter or the bandwidth of the source. Increasing the spot diameter increases the resultant probe diameter. Increasing the bandwidth of the source could be accomplished by using a broader bandwidth superluminescent diode, a rare earth doped fiber superfluorescent source, or a solid state modelocked laser.
Consider next the multi-spectral process. First, consider direct spectral measurement. The reflectance from the sample 16 as a function of transverse location is determined by measuring the reflected confocal spectrum from the sample arm 18. The spectrum may be measured efficiently by incorporating the probe 8 in the sample arm of a Michelson interferometer 20 (Fig. 3) and detecting the light transmitted through a high resolution spectrometer 21 at the output port 19 of the interferometer. Thus, each wavelength measured corresponds to a separate position, x, on the sample (Fig. 3). The advantage to this method over traditional real time confocal microscopy is that the fast axis scanning (- 15 kHz) may be performed external to the probe 8 by the spectrometer 21 with approximately .1 nm spectral resolution for the parameters given above, well within reach of high quality spectrometers. High sensitivity may be achieved through the use of heterodyne detection. If the reference arm 22 is modulated, such as by modulator 23 with mirror 24 (Fig. 3), the interference of light from the sample arm 18 and the reference arm 22 will also be modulated. High signal-to-noise ratios may be then achieved by lock-in detection on the reference arm modulation frequency of detector 26.
Another method for measuring the spectrum is interference or Fourier transform spectroscopy. This may be accomplished by inserting a linearly translating mirror 28 in the reference arm 22 and measuring the cross-correlation output 30 from the interference spectrometer due to the interference of the reflected light from the sample and reference arms 18 and 22, respectively (Fig. 4). The advantages to this type of spectroscopic detection include the ability to achieve higher spectral resolutions than direct detection methods, efficient use of the returned light, inherent modulation of the reference arm 22 by the Doppler shift of the moving mirror 28, and the capability to extract both reflectance and phase data from the sample 16. The ability to extract phase data from the sample may allow detection of refractive index as a function of transverse position, x, which is useful to reveal the molecular composition of the sample as well as provide an additional source of image contrast other than the reflectivity of the sample specimen 16. Finally, interferometric detection has the potential to allow elimination of high order multiple scattering from the confocal signal by coherence gating.
Consider finally image formation. The multi-spectral encoding of the transverse location, x, allows the performance of a one-dimensional raster scan. To obtain an image, a scan of another axis must be performed, which is usually slower. Methods of accomplishing this slow scanning of the y axis include moving the optical fiber 9 in the y direction (Fig. 5B), or rotating the entire probe 8 around the optical fiber axis either in a forward scanning configuration (Fig. 5C) or a side-firing configuration (Fig. 5D). Cross-sectional images may be created by scanning the optical fiber 9 or the objective lens 14 along the z axis (Fig. 6). Finally, a zoom mode may be created by scanning the optical fiber 9 (or another lens 32 between grating 12 and objective lens 14), in and out of the image plane of the objective lens (Fig. 7). Both linear motion along the y or z axis and rotation are easily accomplished in a compact probe by use of piezoelectric transducers. As shown in FIG. 5 A, signals may be received by a computer 34 from spectroscopic detector 32 by a spectrometer (such as described in connection with FIG. 3) or Fourier transform (such as described connection with -6- FIG. 4) representing an image of the a microscopic section of the sample, and the image displayed on a display coupled to the computer.
From the foregoing description, it will be apparent that the invention provides a confocal microscopy system which (a) is compact, optical fiber-based, capable of enabling confocal microscopy through a flexible catheter or endoscope; (b) is fast-scanning which takes place external to the probe; (c) allows phase information to be retrieved; and (d) provides a number of resolvable points proportional to the bandwidth of the source and the beam diameter on the grating. Variations and modifications in the herein described confocal microscopy system in accordance with the invention will undoubtedly suggest themselves to those skilled in the art. Accordingly, the foregoing description should be taken as illustrative and not in a limiting sense.

Claims

-7-Claims
1. A confocal microscope system which comprises a probe movable into a body region of interest, said probe having means for illuminating said region with a confocal spectrum of light extending along one dimension, means for obtaining an image of the region of the specimen by moving said spectrum along another dimension and measuring the reflected confocal spectrum of said light.
2. The system according to Claim 1 wherein said probe is mounted on the end of a flexible, light-conducting member.
3. The system according to Claim 2 wherein said member is an optical fiber.
4. The system according to Claim 3 wherein said fiber is rotatable or translatable to move said probe in said another dimension.
5. The system according to Claim 1 wherein said means for moving said spectrum comprises means for moving an image plane containing said spectrum optically or by physically moving said probe.
6. The system according to Claim 5 wherein said probe is moved physically to scan said spectrum in said another dimension and said probe has means for optically moving said image plane to scan in still another direction, thereby enabling 3-D imaging.
7. The system according to Claim 1 wherein said means for obtaining said image comprises heterodyne detection means.
8. The system according to Claim 7 wherein said heterodyne detection means includes an interferometer.
9. The system according to Claim 8 wherein said interferometer has a sample arm terminated by said probe, a reference arm terminated by a mirror, an output arm having a spectroscopic detector, an input arm having a source of polychromatic illumination, and a beam splitter for directing light from said source to said sample and reference arms and directing interfering light containing said reflected confocal spectrum into said output arm. -8-
10. The system according to Claim 9 wherein said reference arm includes means for modulating said reflected spectrum.
11. The system according to Claim 10 wherein said modulating means comprising means for reciprocally oscillating said mirror or a modulator.
12. The system according to Claim 11 wherein said modulator or reciprocal oscillation is at a certain frequency, and means for lock-in operation of said detector at said frequency.
13. The system according to Claim 9 wherein said detector is a spectrometer.
14. The system according to Claim 9 wherein said detector includes a cross- correlator or a Fourier transform spectrometer.
15. The system according to Claim 1 wherein said probe comprises a grating and an objective which provides said confocal spectrum in an image plan of said objective.
16. The system according to Claim 15 wherein said probe is sufficiently small size to be insertable into an organ internal of said body.
17. A system for confocally imaging tissue comprising: a source for producing light; means for producing a confocal spectrum of said light; means for focusing said confocal spectrum into said tissue, in which said confocal spectrum extends across said tissue at a focal plane, and receiving returned light from said tissue; and means for detecting said returned light in accordance with spectrum of said returned light to provide an image representing said tissue.
18. The system according to Claim 17 further comprising means for scanning said confocal spectrum in at least one dimension with respect to said tissue.
19. The system according to Claim 17 wherein at least said producing means and said focusing and receiving means are located is a probe capable of insertion in a body. -9- 20. The system according to Claim 17 further comprising an optical fiber which provides said light from said source to said producing means, and provides said returned light from said focusing and receiving means to said detecting means.
PCT/US1999/004356 1998-02-26 1999-02-26 Confocal microscopy with multi-spectral encoding WO1999044089A1 (en)

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AU28823/99A AU758078B2 (en) 1998-02-26 1999-02-26 Confocal microscopy with multi-spectral encoding
US09/622,971 US6341036B1 (en) 1998-02-26 1999-02-26 Confocal microscopy with multi-spectral encoding
EP99909668A EP1057063A4 (en) 1998-02-26 1999-02-26 Confocal microscopy with multi-spectral encoding
JP2000533782A JP4709969B2 (en) 1998-02-26 1999-02-26 Confocal microscopy using multispectral coding

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US7604198P 1998-02-26 1998-02-26
US60/076,041 1998-02-26

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US09/999,182 Continuation-In-Part US6831781B2 (en) 1998-02-26 2001-11-29 Confocal microscopy with multi-spectral encoding and system and apparatus for spectroscopically encoded confocal microscopy

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Cited By (83)

* Cited by examiner, † Cited by third party
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