WO2003060423A2 - Apparatus for low coherence ranging - Google Patents

Apparatus for low coherence ranging Download PDF

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Publication number
WO2003060423A2
WO2003060423A2 PCT/US2003/000699 US0300699W WO03060423A2 WO 2003060423 A2 WO2003060423 A2 WO 2003060423A2 US 0300699 W US0300699 W US 0300699W WO 03060423 A2 WO03060423 A2 WO 03060423A2
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WO
WIPO (PCT)
Prior art keywords
optical element
sample
light
detector
optical
Prior art date
Legal status (The legal status 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 status listed.)
Ceased
Application number
PCT/US2003/000699
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English (en)
French (fr)
Other versions
WO2003060423A8 (en
WO2003060423A3 (en
Inventor
Guillermo J. Tearney
Brett Eugene Bouma
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
General Hospital Corp
Original Assignee
General Hospital Corp
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
Priority to JP2003560471A priority Critical patent/JP2005530128A/ja
Priority to US10/501,268 priority patent/US7310150B2/en
Priority to EP03705716A priority patent/EP1468245B1/en
Priority to AT03705716T priority patent/ATE503982T1/de
Priority to DE60336534T priority patent/DE60336534D1/de
Priority to AU2003207507A priority patent/AU2003207507A1/en
Application filed by General Hospital Corp filed Critical General Hospital Corp
Priority to CA2473465A priority patent/CA2473465C/en
Publication of WO2003060423A2 publication Critical patent/WO2003060423A2/en
Publication of WO2003060423A3 publication Critical patent/WO2003060423A3/en
Anticipated expiration legal-status Critical
Publication of WO2003060423A8 publication Critical patent/WO2003060423A8/en
Priority to AU2009202383A priority patent/AU2009202383B2/en
Ceased legal-status Critical Current

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Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02034—Interferometers characterised by particularly shaped beams or wavefronts
    • G01B9/02035—Shaping the focal point, e.g. elongated focus
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02015—Interferometers characterised by the beam path configuration
    • G01B9/02027—Two or more interferometric channels or interferometers
    • G01B9/02028—Two or more reference or object arms in one interferometer
    • 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
    • G01B9/02034—Interferometers characterised by particularly shaped beams or wavefronts
    • G01B9/02035—Shaping the focal point, e.g. elongated focus
    • G01B9/02036—Shaping the focal point, e.g. elongated focus by using chromatic effects, e.g. a wavelength dependent focal point
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/0209—Low-coherence interferometers
    • G01B9/02091—Tomographic interferometers, e.g. based on optical coherence
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4795—Scattering, i.e. diffuse reflection spatially resolved investigating of object in scattering medium

Definitions

  • the present invention relates to apparatus for imaging tissue samples using optical coherence tomography and incorporating an optical element to improve transverse resolution and depth of focus.
  • OCT optical coherence tomography
  • optical coherence tomography configurations that can perform high transverse resolution imaging over a large depth of field. It would be desirable to have a simple device for performing high transverse resolution, large depth of field optical coherence tomography. In addition, by allowing light delivery through a single optical fiber, this device would be also be easily incorporated into catheters or endoscopes. These properties would make this device an enabling technology for performing optical coherence tomography in applications requiring sub-cellular resolution imaging at remote sites within biological systems.
  • Fig. 1 is a schematic view describing focusing using a refractive axicon.
  • a collimated beam, incident from the left, is focused to an axial line with a narrow width and large depth.
  • Fig. 2 is a schematic view of an OCT system with axicon optic in sample arm.
  • Fig. 3 is a schematic view of the relationship between axial location and annulus of illumination.
  • Fig. 4A is a schematic view of the image formation.
  • Fig. 4B is a schematic view of the translation of the entire optical assembly in the y- direction.
  • Fig. 4C is a schematic view of the rotation of the entire optical assembly.
  • Fig. 4D is a schematic view of the angular deflection of the axial line focus in the x-y plane.
  • Fig. 5 is a schematic view of a system used to perform high transverse resolution ranging with a high depth of field.
  • Fig. 6 is a schematic view of an offset fiber array.
  • Fig. 7 is a schematic of a fiber array, microlens array and diffraction grating.
  • Fig. 8 is a schematic view of an embodiment of an apodized pupil plane filter.
  • Fig. 9 is a schematic view of the use of an apodizer in front of an imaging lens.
  • Axicon shall mean any optic element (or combination thereof) capable of generating an axial line focus. Refractive, diffractive, and reflective axicons have been demonstrated. See, J.H. McLeod, J. Opt. Soc. Am 44, 592 (1954); J.H. McLeod, J. Opt. Soc. Am 50, 166 (1960); and J.R. Rayces, J. Opt. Soc. Am. 48, 576 (1958).
  • ⁇ sqrt(2) or 2
  • the depth of focus for a uniform beam (3 dB full-width-half-maximum intensity response for a planar reflector moved through the longitudinal plane) may be defined as
  • Longitudinal shall mean substantially parallel to the optical axis.
  • Longitudinal resolution shall mean the minimum distance, ⁇ z, in the longitudinal direction that two points may be separated while still being differentiated by an optical detection means.
  • spot size shall mean the transverse diameter of a focused spot.
  • the spot size is defined as transverse width of the spot where the intensity at the focus has decreased by a factor of 1/e 2 .
  • the spot size, d is defined as
  • the spot radius is defined as the transverse position of the first zero of the Airy disk
  • n is the refractive index of the immersion medium.
  • Transverse shall mean substantially perpendicular to the optical axis.
  • Transverse resolution shall mean the minimum distance, ⁇ r, in the transverse direction that two points may be separated while still being differentiated by an optical detection means.
  • An axial line focus with a narrow transverse beam diameter and over a large length (or depth of focus), is generated. Used in conjunction with OCT, the diameter of the line focus determines the transverse resolution and the length determines the depth of field.
  • the detection of light backreflected from sites along the axial focus is performed using a Michelson interferometer. When the light source has a finite spectral width, this configuration can be used to determine the axial location of the backreflection site. The axial resolution is determined by the coherence length of the light source.
  • An axicon (reflective, transmissive, or diffractive optical element (“DOE")) is an acceptable model known to those skilled in the art for this and will be the method that is used in the present invention to demonstrate use of OCT with an axial line focus to achieve high resolution imaging over large depths of field. It is to be understood that this method is illustrative and not intended to be the exclusive model.
  • Other known models include, but are not limited to, multi-focal lenses, such as the Rayleigh-Wood lens (Optical Processing and Computing, H.H Arsenault, T. Szoplik, and B. Macukow eds., Academic Press Inc., San Diego, CA, 1989), the use of chromatic aberration to produce an array of wavelength dependent foci along the longitudinal axis, and the like.
  • Equation (1) The intensity distribution of light transmitted through a refractive axicon lens (see R. Arimoto, C. Saloma, T. Tanaka, and S. Kawata, Appl. Opt. 31, 6653 (1992)) is given by Equation (1):
  • Equation (3) Equation (3)
  • Equation (1) is modified, but in all cases it is the diameter of the axial focus that determines the transverse resolution of the imaging system.
  • a theme of the present invention is that the poor transverse resolution typical of current OCT systems can be improved by changing from a standard focusing geometry in which the focal volume (power distribution) is limited in both the transverse and the axial dimensions to one in which the focal volume is limited only in the transverse direction.
  • ⁇ is the spectral width (full- width half maximum (“FWHM”))of the light source.
  • Fig. 4A illustrates the entire OCT/axicon system of one embodiment of the present invention. All components, other than the axicon probe, are standard to OCT.
  • OCT to determine the backreflection as a function of distance along the axial line focus provides a one dimensional raster scan. This is typically accomplished by scanning the length of the interferometer reference arm.
  • An axicon has the property each axial location of the focus corresponds to a unique annulus at the input aperture of the axicon (see Fig. 3). This relationship could allow the reference arm length scanning to be replaced by scanning an annulus of illumination at the axicon aperture.
  • a scan of another axis must be performed.
  • This second scanning dimension is usually performed at a slower rate.
  • Methods of accomplishing this slow scanning of the secondary axis include moving the sample arm optics, including the optical fiber, collimating lens and axicon, in the y direction (see Fig. 4B), rotating the entire probe around the optical fiber axis (see Fig. 4C) or angularly deflecting the line focus in the x-y plane (see Fig. 4D). See, (G.J. Tearney, S.A. Boppart, B.E. Bouma, M.E. Brezinski, N.J. Weissman, J.F. Southern, and J.G.
  • Fig. 5 is a schematic of an alternative apparatus used to perform high transverse resolution ranging with a high depth of field.
  • the system comprises a light source, beam redirecting element, detector, and an optical element.
  • the optical element provides line focus and an array of focused spots on the sample.
  • Fig. 6 shows an offset fiber array are directed by the mirror through the objective and used to displace focused (imaged) spots in the longitudinal and transverse dimensions on the sample.
  • the spots are scanned (scan direction being indicated by the horizontal line and arrows) to create a multidimensional image.
  • Fig. 7 is a schematic of a fiber array, microlens array and diffraction grating (array of mirrors) used to displace focused (imaged) spots in the longitudinal and transverse dimensions on the sample.
  • Light from the light source (not shown) passes through the fibers in the array, and through the microlens array to the diffraction grating.
  • Light directed by the grating passes through the objective lens and focused on the sample.
  • the spots are scanned (scan direction being indicated by the horizontal line and arrows) to create a multidimensional image.
  • An alternative means for providing a high transverse resolution over a large depth of focus is the use of a filter in the back plane of the imaging lens.
  • This technique commonly termed apodization, allows the production of either a line focus as in the axicon or a multitude of focused spots positioned along the longitudinal dimension.
  • the use of annular apodization to shape a beam focus has been previously described in the literature (M. Martinez-Corral, P. Andres, J. Ojeda-Castaneda, G. Saavedra, Opt. Comm. 119, 491 (1995)).
  • use of apodization to create high transverse resolution over a large focal distance, where the longitudinal data is further resolved by OCT has not been previously described.
  • Fig. 8 shows an embodiment of an apodized pupil plane filter.
  • Fig. 9 shows a schematic of the use of an apodizer in front of an imaging lens the output of which is focused in the axial line.
  • the present invention also provides a method of obtaining a high resolution and high depth of focus image of a sample, comprising:
  • An advantage of the present invention is that the OCT imaging apparatus is capable of enabling sub-cellular resolution imaging along transverse and longitudinal dimensions of the sample in a compact, optical fiber-based package.
  • Other advantages include the potential compact size and low cost of axial line focus optical elements such as the apodizer-lens combination or axicon.

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  • Physics & Mathematics (AREA)
  • General Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Optics & Photonics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Analytical Chemistry (AREA)
  • Biochemistry (AREA)
  • Immunology (AREA)
  • Pathology (AREA)
  • Investigating Or Analysing Materials By Optical Means (AREA)
  • Length Measuring Devices By Optical Means (AREA)
  • Measurement Of Optical Distance (AREA)
  • Endoscopes (AREA)
  • Microscoopes, Condenser (AREA)
  • Instruments For Viewing The Inside Of Hollow Bodies (AREA)
PCT/US2003/000699 2002-01-11 2003-01-10 Apparatus for low coherence ranging Ceased WO2003060423A2 (en)

Priority Applications (8)

Application Number Priority Date Filing Date Title
CA2473465A CA2473465C (en) 2002-01-11 2003-01-10 Apparatus for low coherence ranging
US10/501,268 US7310150B2 (en) 2002-01-11 2003-01-10 Apparatus and method for low coherence ranging
EP03705716A EP1468245B1 (en) 2002-01-11 2003-01-10 Apparatus for OCT imaging with axial line focus for improved resolution and depth of field
AT03705716T ATE503982T1 (de) 2002-01-11 2003-01-10 Vorrichtung zur oct bildaufnahme mit axialem linienfokus für verbesserte auflösung und tiefenschärfe
DE60336534T DE60336534D1 (de) 2002-01-11 2003-01-10 Vorrichtung zur OCT Bildaufnahme mit axialem Linienfokus für verbesserte Auflösung und Tiefenschärfe
JP2003560471A JP2005530128A (ja) 2002-01-11 2003-01-10 解像度と深さ領域を改善するための軸方向線焦点を用いたｏｃｔ撮像用装置
AU2003207507A AU2003207507A1 (en) 2002-01-11 2003-01-10 Apparatus for oct imaging with axial line focus for improved resolution and depth of field
AU2009202383A AU2009202383B2 (en) 2002-01-11 2009-06-15 Apparatus for low coherence ranging

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US34752802P 2002-01-11 2002-01-11
US60/347,528 2002-01-11

Publications (3)

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WO2003060423A2 true WO2003060423A2 (en) 2003-07-24
WO2003060423A3 WO2003060423A3 (en) 2003-12-11
WO2003060423A8 WO2003060423A8 (en) 2005-05-19

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PCT/US2003/000699 Ceased WO2003060423A2 (en) 2002-01-11 2003-01-10 Apparatus for low coherence ranging

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US (1) US7310150B2 (https=)
EP (4) EP2327954A1 (https=)
JP (1) JP2005530128A (https=)
CN (2) CN101598685B (https=)
AT (1) ATE503982T1 (https=)
AU (2) AU2003207507A1 (https=)
CA (1) CA2473465C (https=)
DE (1) DE60336534D1 (https=)
WO (1) WO2003060423A2 (https=)

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