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Journal of the Optical Society of America A

Journal of the Optical Society of America A


  • Vol. 20, Iss. 10 — Oct. 1, 2003
  • pp: 1859–1866

Optoacoustic diffraction tomography: analysis of algorithms

Stephen J. Norton and Tuan Vo-Dinh  »View Author Affiliations

JOSA A, Vol. 20, Issue 10, pp. 1859-1866 (2003)

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We consider the problem of using the photoacoustic effect to image the optical properties of tissue. A region of tissue is assumed to be illuminated by frequency-modulated light that creates an ultrasonic wave of the same frequency. This wave is detected on a passive array of receiving transducers distributed over a circular or a cylindrical aperture. If the frequency is swept over a broad band (or, equivalently, if we illuminate with a pulse and Fourier transform the response), then a spatial map of a parameter that depends on the optical absorption coefficient of the tissue can be recovered. Analytical inversion formulas are derived in both two and three dimensions. The effects of band-limited data on image quality are also investigated.

© 2003 Optical Society of America

OCIS Codes
(110.5120) Imaging systems : Photoacoustic imaging
(110.6960) Imaging systems : Tomography
(170.3010) Medical optics and biotechnology : Image reconstruction techniques
(170.3880) Medical optics and biotechnology : Medical and biological imaging
(170.5120) Medical optics and biotechnology : Photoacoustic imaging
(170.6960) Medical optics and biotechnology : Tomography

Original Manuscript: March 27, 2003
Revised Manuscript: June 16, 2003
Manuscript Accepted: June 16, 2003
Published: October 1, 2003

Stephen J. Norton and Tuan Vo-Dinh, "Optoacoustic diffraction tomography: analysis of algorithms," J. Opt. Soc. Am. A 20, 1859-1866 (2003)

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  14. In the 600–1000-nm near-infrared window, the intensity distribution I(r) is dominated primarily by multiple scattering within the tissue and to a lesser extent by optical absorption. A reasonable assumption is that the intensity distribution in the tissue, for the purpose of computing I(r), is dominated entirely by the multiple scattering. One would expect that a good first-order approximation should result from computing I(r) under the assumption of a homogeneous-tissue model with a constant (mean) scattering cross section. Then the spatial variations in the optical absorption coefficient α(r), which is what we wish to image, arise entirely from the first-order dependence of fν(r) on α(r), as defined in Eq. (5). Thus we neglect a small second-order contribution that may arise through a dependence on I(r). See Ref. 1 for comprehensive articles on the diffusion of light in tissue.
  15. P. M. Morse, K. U. Ingard, Theoretical Acoustics (McGraw-Hill, New York, 1968), p. 365, Eq. (7.3.15).
  16. Ref. 15, p. 365.
  17. G. N. Watson, Theory of Bessel Functions (Cambridge U. Press, Cambridge, UK, 1966), p. 429.

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