Phase-resolved optical coherence tomography and optical doppler tomography for imaging fluid flow in tissue with fast scanning speed and high velocity sensitivity

• US 6,549,801 B1
• Filed: 05/19/2000
• Issued: 04/15/2003
• Est. Priority Date: 06/11/1998
• Status: Expired due to Term

• Current Assignee: Regents of the University of California (University of California)
• Original Assignee: Regents of the University of California (University of California)
• Inventors: Chen, Zhongping, Zhao, Yonghua, Nelson, J. Stuart, DeBoer, Johannes F.
• Primary Examiner(s): Lateef, Marvin M.
• Assistant Examiner(s): Lin, Jeoyuh
• Application Number:
  US09/574,560
• Time in Patent Office: 1,061 Days
• Field of Search: 600/476, 600/310, 600/368, 600/407, 600/425, 600/473, 250/363.02, 250/368, 250/356, 250/385, 250/483
• US Class Current: 600/425
• CPC Class Codes: A61B 5/0066 Optical coherence imaging
• CPC Class Codes: A61B 5/0073 by tomography, i.e. reconstruction of 3D images from 2D projections A61B5/0066 takes precedence
• CPC Class Codes: A61B 5/0261 using optical means, e.g. infrared light
• CPC Class Codes: G01B 2290/35 Mechanical variable delay line
• CPC Class Codes: G01B 2290/70 Using polarization in the interferometer
• CPC Class Codes: G01B 9/0201 using temporal phase variation
• CPC Class Codes: G01B 9/02045 using the Doppler effect
• CPC Class Codes: G01B 9/02082 Caused by speckles
• CPC Class Codes: G01B 9/02091 Tomographic interferometers, e.g. based on optical coherence
• CPC Class Codes: G01N 21/4795 spatially resolved investigating of object in scattering medium in vivo A61B

Abstract

The invention is a fast-scanning ODT system that uses phase information derived from a Hilbert transformation to increase the sensitivity of flow velocity measurements while maintaining high spatial resolution. The significant increases in scanning speed and velocity sensitivity realized by the invention make it possible to image in vivo blood flow in human skin. The method of the invention overcomes the inherent limitations of the prior art ODT by using a phase change between sequential line scans for velocity image reconstruction. The ODT signal phase or phase shifts at each pixel can be determined from the complex function, {tilde over (Γ)}_ODT(t), which is determined through analytic continuation of the measured interference fringes function, Γ_ODT(t), by use of a Hilbert transformation, by electronic phase demodulation, by optical means, or a fast Fourier transformation. The phase change in each pixel between axial-line scans is then used to calculate the Doppler frequency shift. Sequential measurements of a single line scan, measurements of sequential line scans or measurements of line scans in sequential frames may be used. Because the time between line scans is much longer than the pixel time window, very small Doppler shifts can be detected with this technique. In addition, spatial resolution and velocity sensitivity are decoupled. Furthermore, because two axial-line scans are compared at the same location, speckle modulations in the fringe signal cancel each other and, therefore, will not affect the phase-difference calculation.

Claims

1. A method for phase-resolved optical tomography capable of simultaneously imaging fluid flow and morphology in a sample with fast scanning speed and high velocity sensitivity comprising:

providing a source of at least partially coherent radiation through an interferometer, said at least partially coherent radiation characterized by a phase;

phase modulating said radiation in said interferometer at a modulation frequency;

scanning said sample with said source of at least partially coherent radiation through said interferometer in a sequence of pixel line scans, said sample having a fluid flow therein;

changing said phase of said at least partially coherent radiation in response to said fluid flow at each pixel of each pixel line scan;

detecting interference fringes of said radiation backscattered from said sample into said interferometer;

processing said detected interference fringes to determine ODT phase signals of said detected backscattered interference fringes at each pixel of said pixel line scans to determine said corresponding phase at each pixel in a data window;

comparing said phase between corresponding pixels in two line scans to generate a difference between said phase at said two corresponding pixels in two line scans whereby speckle is substantially reduced; and

generating a tomographic image of the fluid flow in said sample from said phase difference at each pixel.

2. The method of claim 1 wherein comparing said phase between corresponding pixels in two line scans comprises comparing said phase between corresponding pixels in two sequential line scans.

3. The method of claim 1 wherein comparing said phase between corresponding pixels in two line scans comprises comparing said phase between corresponding pixels in two sequential scans of a single line.

4. The method of claim 1 wherein said sequence of pixel line scans are scanned in groups of line scans organized into sequential frames, and wherein comparing said phase between corresponding pixels in two line scans comprises comparing said phase between corresponding pixels in two scans of a single line in two sequential frames.

5. The method of claim 1 where processing said detected interference fringes to determine ODT phase signals of said detected backscattered interference fringes comprises determining said ODT phase signals in a computer from a complex function, {tilde over (Γ

)}_ODT(t), which is determined through analytic continuation of said detected interference fringes function, Γ

_ODT(t), by use of said Hilbert transformations, namely;

${\widetilde{\mathrm{\Gamma <br><br>}}}_{\mathrm{ODT}}<br><br>\left(t\right)={\mathrm{\Gamma <br><br>}}_{\mathrm{ODT}}<br><br>\left(t\right)+\frac{\mathrm{<br><br>}}{\mathrm{\pi <br><br>}}<br><br>P<br><br>{\int <br><br>}_{-\mathrm{\infty <br><br>}}^{\mathrm{\infty <br><br>}}<br><br>\frac{{\mathrm{\Gamma <br><br>}}_{\mathrm{ODT}}<br><br>\left(\mathrm{\tau <br><br>}\right)}{\mathrm{\tau <br><br>}-t}<br><br>\text{\hspace{1em}<br><br>}<br><br><br><br>\mathrm{\tau <br><br>}=A<br><br>\left(t\right)<br><br>\exp <br><br>\left[\mathrm{<br><br>\varphi <br><br>}<br><br>\left(t\right)\right]$

where P denotes the Cauchy principle value and A(t) and ψ

(t) are the amplitude and the phase of {tilde over (Γ

)}_ODT(t) respectively.

6. The method of claim 5 where processing said detected interference fringes to determine ODT phase signals of said detected backscattered interference fringes through the use of a Hilbert transformation comprises determining said phase shift, Δ

ψ

, in said computer at each pixel between sequential line scans by the Doppler frequency shift at each pixel between, ω

=Δ

ω

/T where T is the time interval between successive line scans.

7. The method of claim 1 where processing said detected interference fringes to determine ODT phase signals of said detected backscattered interference fringes comprises determining said ODT phase signals in a computer or digital signal processor by:

applying a first fast Fourier transformation in said computer to said detected interference fringes to produce a transformed signal;

passing said transformed signal through a digital filter in said computer to reduce noise to produce a filtered signal;

multiplying said filtered signal by the Heaviside function, H(ω

) in said computer to produce a multiplied signal; and

applying a second fast Fourier transformation in said computer to said multiplied signal to producer {tilde over (Γ

)}_ODT(t) ; and

extracting in said computer said ODT phase signals from {tilde over (Γ

)}_ODT(t).

8. The method of claim 1 wherein said interferometer has a reference arm, a sample arm and a detection arm and further comprising prior to detecting interference fringes of said radiation backscattered from said sample into said interferometer:

providing circularly polarized reflected radiation from said reference arm;

providing linearly polarized reflected radiation from said sample arm;

combining said circularly polarized reflected radiation from said reference arm and said linearly polarized reflected radiation from said sample arm in a coupler; and

splitting radiation from said coupler into two polarized beams in said detection arm with a polarizing beam splitter with an axis of polarization set at 45°

to said linearly polarized reflected radiation from said sample arm,

wherein detecting interference fringes comprises detecting said two polarized beams in two corresponding detectors to generate two corresponding signals comprising in turn the real and imaginary parts of {tilde over (Γ

)}_ODT(t) so that said phase is directly measured.

9. The method of claim 1 where generating said tomographic image of the fluid flow in said sample comprises generating a structural image of said sample.

10. The method of claim 1 where generating said tomographic image of the fluid flow in said sample comprises generating a velocity image of fluid in said sample.

11. The method of claim 1 further comprising determining a phase shift Δ

f=Δ

ψ

/T from an average Doppler frequency shift, <

Δ

f>

, between sequential line scans using the equation;

$〈<br><br>\mathrm{\Delta <br><br>}<br><br>\text{\hspace{1em}<br><br>}<br><br>f〉<br><br><br><br>\text{\hspace{1em}<br><br>}=\frac{1}{2<br><br>\mathrm{\pi <br><br>}<br><br>\text{\hspace{1em}<br><br>}<br><br>T}<br><br>{\tan }^{-1}<br><br>\left(\frac{\mathrm{Im}<br><br>\left(\underset{j=1}{\overset{n}{\sum <br><br>}}<br><br>\text{\hspace{1em}<br><br>}<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_j·<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_{j+1}^{*}\right)}{\mathrm{Re}<br><br>\left(\underset{j=1}{\overset{n}{\sum <br><br>}}<br><br>\text{\hspace{1em}<br><br>}<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_j·<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_{j+1}^{*}\right)}\right)$

where T is the time interval between sequential scans, and n is the number of sequential scans averaged.

12. The method of claim 11 where determining a phase shift from an average Doppler frequency shift between sequential line scans comprises averaging at least three sequential line scans to increase the signal-to-noise ratio in images.

13. The method of claim 1 further comprising determining a standard deviation of a Doppler power spectrum and generating said tomographic image of the fluid flow in said sample from said standard deviation of said Doppler power spectrum.

14. The method of claim 13 where determining said standard deviation of a Doppler power spectrum comprises determining said standard deviation from the equation:

${\mathrm{\sigma <br><br>}}^2=\frac{{\int <br><br>}_{-\mathrm{\infty <br><br>}}^{\mathrm{\infty <br><br>}}<br><br>{\left(\mathrm{\omega <br><br>}-\stackrel{\_}{\mathrm{\omega <br><br>}}\right)}^2<br><br>P<br><br>\left(\mathrm{\omega <br><br>}\right)<br><br>\text{\hspace{1em}<br><br>}<br><br><br><br>\mathrm{\omega <br><br>}}{{\int <br><br>}_{-\mathrm{\infty <br><br>}}^{\mathrm{\infty <br><br>}}<br><br>P<br><br>\left(\mathrm{\omega <br><br>}\right)<br><br>\text{\hspace{1em}<br><br>}<br><br><br><br>\mathrm{\omega <br><br>}}=\frac{1}{T^2}<br><br>\left(1-\frac{<br><br>\underset{j=1}{\overset{n}{\sum <br><br>}}<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_j·<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_{j+1}^{*}<br><br>}{\underset{j=1}{\overset{n}{\sum <br><br>}}<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_j·<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_j^{*}}\right)$

where T is the time interval between sequential scans, P(ω

) is said Doppler power spectrum, and {overscore (ω

)} is the centroid value of a Doppler frequency shift.

15. The method of claim 1 where generating said corresponding phase at each pixel in a data window comprises extracting said phase shift by electronic demodulation of said detected interference fringes.

16. The method of claim 1 where said scanning is characterized by a scanning rate, and adding π

to said phase difference because tan(φ

)=tan(φ

+π

), when a Doppler frequency difference related to said phase difference is greater than half of said scanning rate so that said Doppler frequency difference can exceed said scanning rate.

17. A method for phase-resolved optical tomography comprising:

providing a source of at least partially coherent radiation through an interferometer, said at least partially coherent radiation characterized by a phase;

phase modulating said radiation in said interferometer at a modulation frequency;

scanning said sample with said source of at least partially coherent radiation through said interferometer in a sequence of pixel line scans, said sample having a fluid flow therein;

changing said phase of said at least partially coherent radiation in response to said fluid flow at each pixel of each pixel line scan;

detecting interference fringes of said radiation backscattered from said sample into said interferometer;

processing said detected interference fringes to determine ODT phase signals of said detected backscattered interference fringes at each pixel of said pixel line scans to generate a corresponding rate of change of said phase at each pixel in a data window through the use of a Hilbert transformation at each pixel, and

generating a tomographic image of the fluid flow in said sample from said rate of change of said phase at each pixel.

18. A method for phase-resolved optical tomography comprising:

providing a source of at least partially coherent radiation through an interferometer with a reference arm, a sample arm and a detection arm, said at least partially coherent radiation characterized by a phase;

phase modulating said radiation in said interferometer at a modulation frequency;

scanning said sample with said source of at least partially coherent radiation through said interferometer in a sequence of pixel line scans, said sample having a fluid flow therein so that said phase of said at least partially coherent radiation is changed in response to said fluid flow at each pixel of each pixel line scan;

providing circularly polarized reflected radiation from said reference arm;

providing linearly polarized reflected radiation from said sample arm;

combining said circularly polarized reflected radiation from said reference arm and said linearly polarized reflected radiation from said sample arm in a coupler; and

splitting radiation from said coupler into two polarized beams in said detection arm with a polarizing beam splitter with an axis of polarization set at 45°

to said linearly polarized reflected radiation from said sample arm,

detecting interference fringes of said radiation backscattered from said sample into said interferometer in said two polarized beams in two corresponding detectors to generate two corresponding signals comprising in turn the real and imaginary parts of {tilde over (Γ

)}_ODT(t) so that said phase is directly measured; and

generating a tomographic image of the fluid flow in said sample from said phase at each pixel.

19. An apparatus for phase-resolved optical tomography capable of simultaneously imaging fluid flow and morphology in sample with fast scanning speed and high velocity sensitivity comprising:

an interferometer;

a source of at least partially coherent radiation through coupled to said interferometer, said at least partially coherent radiation characterized by a phase;

phase modulator coupled to said source to modulate said radiation in said interferometer at a modulation frequency;

a scanner for scanning said sample with said source of at least partially coherent radiation through said interferometer in a sequence of pixel line scans, said sample having a fluid flow therein so that said phase of said at least partially coherent radiation is changed in response to said fluid flow at each pixel of each pixel line scan;

a detector to detect interference fringes of said radiation backscattered from said sample into said interferometer;

a processor to determine said corresponding phase at each pixel of said pixel line scans from said ODT phase signals of said detected backscattered interference fringes and to compare said phase between corresponding pixels in two line scans to generate a difference between said phase at said two corresponding pixels in two line scans whereby speckle is substantially reduced; and

a display to generate a tomographic image of the fluid flow in said sample from said difference at each pixel.

20. The apparatus of claim 19 wherein said processor compares said phase between corresponding pixels in two sequential line scans.

21. The apparatus of claim 19 wherein said processor compares said phase between corresponding pixels in two sequential scans of a single line.

22. The apparatus of claim 19 wherein said sequence of pixel line scans are scanned in groups of line scans organized into sequential frames, and wherein said processor compares said phase between corresponding pixels in two scans of a single line in two sequential frames.

23. The apparatus of claim 19 where processor determines said ODT phase signals from a complex function, {tilde over (Γ

)}_ODT(t), which. is determined through analytic continuation of said detected interference fringes function, Γ

_ODT(t), by use of said Hilbert transformations, namely;

${\widetilde{\mathrm{\Gamma <br><br>}}}_{\mathrm{ODT}}<br><br>\left(t\right)={\mathrm{\Gamma <br><br>}}_{\mathrm{ODT}}<br><br>\left(t\right)+\frac{\mathrm{<br><br>}}{\mathrm{\pi <br><br>}}<br><br>P<br><br>{\int <br><br>}_{-\mathrm{\infty <br><br>}}^{\mathrm{\infty <br><br>}}<br><br>\frac{{\mathrm{\Gamma <br><br>}}_{\mathrm{ODT}}<br><br>\left(\mathrm{\tau <br><br>}\right)}{\mathrm{\tau <br><br>}-t}<br><br>\text{\hspace{1em}<br><br>}<br><br><br><br>\mathrm{\tau <br><br>}=A<br><br>\left(t\right)<br><br>\exp <br><br>\left[\mathrm{<br><br>}<br><br>\text{\hspace{1em}<br><br>}<br><br>\mathrm{\varphi <br><br>}<br><br>\left(t\right)\right]$

where P denotes the Cauchy principle value and A(t) and ψ

(t) are the amplitude and the phase of {tilde over (Γ

)}_ODT(t) respectively.

24. The apparatus of claim 19 where said display for generating said tomographic image of the fluid flow in said sample comprises generates a velocity image of said sample.

25. The apparatus of claim 19 where said processor determines a phase shift Δ

f=Δ

ψ

/T from an average Doppler frequency shift, <

Δ

f>

, between sequential line scans using the equation;

$〈<br><br>\mathrm{\Delta <br><br>}<br><br>\text{\hspace{1em}<br><br>}<br><br>f〉<br><br><br><br>\text{\hspace{1em}<br><br>}=\frac{1}{2<br><br>\mathrm{\pi <br><br>}<br><br>\text{\hspace{1em}<br><br>}<br><br>T}<br><br>{\tan }^{-1}<br><br>\left(\frac{\mathrm{Im}<br><br>\left(\underset{j=1}{\overset{n}{\sum <br><br>}}<br><br>\text{\hspace{1em}<br><br>}<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_j·<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_{j+1}^{*}\right)}{\mathrm{Re}<br><br>\left(\underset{j=1}{\overset{n}{\sum <br><br>}}<br><br>\text{\hspace{1em}<br><br>}<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_j·<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_{j+1}^{*}\right)}\right)$

where T is the time interval between sequential scans, and n is the number of sequential scans averaged.

26. The apparatus of claim 25 where said processor determines a phase shift from an average Doppler frequency shift between sequential line scans comprises averaging at least three sequential line scans to increase the signal-to-noise ratio in images.

27. The apparatus of claim 19 where said processor determines a standard deviation of a Doppler power spectrum and said display generates said tomographic image of the fluid flow in said sample from said standard deviation of said Doppler power spectrum.

28. The apparatus of claim 27 where said processor determines said standard deviation of a Doppler power spectrum comprises determining said standard deviation from the equation:

${\mathrm{\sigma <br><br>}}^2=\frac{{\int <br><br>}_{-\mathrm{\infty <br><br>}}^{\mathrm{\infty <br><br>}}<br><br>{\left(\mathrm{\omega <br><br>}-\stackrel{\_}{\mathrm{\omega <br><br>}}\right)}^2<br><br>P<br><br>\left(\mathrm{\omega <br><br>}\right)<br><br>\text{\hspace{1em}<br><br>}<br><br><br><br>\mathrm{\omega <br><br>}}{{\int <br><br>}_{-\mathrm{\infty <br><br>}}^{\mathrm{\infty <br><br>}}<br><br>P<br><br>\left(\mathrm{\omega <br><br>}\right)<br><br>\text{\hspace{1em}<br><br>}<br><br><br><br>\mathrm{\omega <br><br>}}=\frac{1}{T^2}<br><br>\left(1-\frac{<br><br>\underset{j=1}{\overset{n}{\sum <br><br>}}<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_j·<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_{j+1}^{*}<br><br>}{\underset{j=1}{\overset{n}{\sum <br><br>}}<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_j·<br><br>{\widetilde{\mathrm{\Gamma <br><br>}}}_j^{*}}\right)$

where T is the time interval between sequential scans, P(ω

) is said Doppler power spectrum, and {overscore (ω

)} is the centroid value of a Doppler frequency shift.

29. The apparatus of claim 19 where said processor determines said corresponding phase at each pixel in a data window by extracting said phase by electronic demodulation of said detected interference fringes.

30. The apparatus of claim 19 where said scanner is characterized by a scanning rate, and wherein said processor adds π

to said phase difference when a Doppler frequency difference related to said phase difference is greater than half of said scanning rate, because tan(φ

)=tan(φ

+π

), so that said Doppler frequency difference can exceed said scanning rate.

31. The apparatus of claim 19 where said processor determines said ODT phase signals of said detected backscattered interference fringes through the use of a Hilbert transformation by determining said phase shift, Δ

ψ

, in said computer at each pixel between sequential line scans by the Doppler frequency shift at each pixel between, ω

=Δ

ψ

/T where T is the time interval between successive line scans.

32. The apparatus of claim 19 where said display for generating said tomographic image of the fluid flow in said sample comprises generates a structural image of said sample.

33. An apparatus for phase-resolved optical tomography of a sample comprising:

an interferometer

a source of at least partially coherent radiation coupled to said interferometer, said at least partially coherent radiation characterized by a phase;

a modulator for phase modulating said radiation in said interferometer at a modulation frequency;

a scanner for scanning said sample with said source of at least partially coherent radiation through said interferometer in a sequence of pixel line scans, said sample having a fluid flow therein in which said phase of said at least partially coherent radiation is changed in response to said fluid flow at each pixel of each pixel line scan;

a detector for detecting interference fringes of said radiation backscattered from said sample into said interferometer;

a processor for processing said detected interference fringes to determine ODT phase signals of said detected backscattered interference fringes at each pixel of said pixel line scans to generate a corresponding rate of change of said phase at each pixel in a data window through the use of a Hilbert transformation at each pixel, and

a display for generating a tomographic image of the fluid flow in said sample from said rate of change of said phase at each pixel.

34. An apparatus for phase-resolved optical tomography in a sample comprising:

an interferometer with a reference arm, a sample arm and a detection arm;

a source of at least partially coherent radiation coupled to said interferometer, said at least partially coherent radiation characterized by a phase;

a modulator for phase modulating said radiation in said interferometer at a modulation frequency;

a scanner for scanning said sample with said source of at least partially coherent radiation through said interferometer in a sequence of pixel line scans, said sample having a fluid flow therein so that said phase of said at least partially coherent radiation is changed in response to said fluid flow at each pixel of each pixel line scan;

a circular polarizer for circularly polarizing reflected radiation from said reference arm;

a linear polarizer for linearly polarized reflected radiation from said sample arm;

a coupler for combining said circularly polarized reflected radiation from said reference arm and said linearly polarized reflected radiation from said sample arm; and

a beam splitter for splitting radiation from said coupler into two polarized beams in said detection arm with a polarizing beam splitter with an axis of polarization set at 45°

to said linearly polarized reflected radiation from said sample arm,

two corresponding detectors for detecting interference fringes of said radiation backscattered from said sample into said interferometer in said two polarized beams to generate two corresponding signals comprising in turn the real and imaginary parts of {tilde over (Γ

)}_ODT(t) so that said phase is directly measured; and

a display for generating a tomographic image of the fluid flow in said sample from said phase at each pixel.

35. A method for optical tomography comprising:

providing a source of at least partially coherent radiation through an interferometer, said at least partially coherent radiation characterized by a phase;

providing a rapid-scanning optical delay line and an electro-optic modulator coupled to said rapid-scanning optical delay line;

phase modulating said radiation in said interferometer by means of said rapid-scanning optical delay line and electro-optic modulator in combination at a modulation frequency with a stable phase modulation;

scanning said sample with said source of at least partially coherent radiation through said interferometer;

detecting interference fringes of said radiation backscattered from said sample into said interferometer.

36. The method of claim 35 further comprising operating said rapid-scanning optical delay line at a zero carrier frequency.

37. The method of claim 35 where phase modulating said radiation in said interferometer comprises phase modulating said radiation in a reference arm of said interferometer.

38. The method of claim 35 where said optical tomography is phase-resolved optical tomography capable of simultaneously imaging fluid flow and morphology in a sample with fast scanning speed and high velocity sensitivity, where phase modulating said radiation in said interferometer phase modulates said radiation with a stable phase modulation which is repeatable between multiple scans of said sequence of pixel line scans, where scanning said sample scans said sample in a sequence of pixel line scans, said sample having a fluid flow therein;

and further comprising;

changing said phase of said at least partially coherent radiation in response to said fluid flow at each pixel of each pixel line scan;

processing said detected interference fringes to determine ODT phase signals of said detected backscattered interference fringes at each pixel of said pixel line scans to determine said corresponding phase at each pixel in a data window;

comparing said phase between corresponding pixels in two line scans to generate a difference between said phase at said two corresponding pixels in two line scans whereby speckle is substantially reduced; and

generating a tomographic image of the fluid flow in said sample from said phase difference at each pixel.

39. An apparatus for optical tomography comprising:

an interferometer;

a source of at least partially coherent radiation coupled to said interferometer, said at least partially coherent radiation characterized by a phase;

a rapid-scanning optical delay line;

an electro-optic modulator coupled to said rapid-scanning optical delay line to modulate said radiation in said interferometer at a modulation frequency with a stable phase modulation;

a scanner for scanning said sample with said source of at least partially coherent radiation through said interferometer; and

a detector to detect interference fringes of said radiation backscattered from said sample into said interferometer.

40. The apparatus of claim 39 where said rapid-scanning optical delay line operates at a zero carrier frequency.

41. The apparatus of claim 39 where said interferometer has a reference arm and where said rapid-scanning optical delay line and electro-optic modulator are disposed in said reference arm of said interferometer.

42. The apparatus of claim 39 where said optical tomography is phase-resolved optical tomography capable of simultaneously imaging fluid flow and morphology in sample with fast scanning speed and high velocity sensitivity, where said rapid-scanning optical delay line and electro-optic modulator phase modulator in combination modulate said radiation in said interferometer at a modulation frequency in which said radiation is phase modulated with a stable phase modulation which is repeatable between multiple scans of a sequence of pixel line scans, where said scanner scans said sequence of pixel line scans, said sample having a fluid flow therein so that said phase of said at least partially coherent radiation is changed in response to said fluid flow at each pixel of each pixel line scan, and further comprising:

a processor to determine said corresponding phase at each pixel of said pixel line scans from said ODT phase signals of said detected backscattered interference fringes and to compare said phase between corresponding pixels in two line scans to generate a difference between said phase at said two corresponding pixels in two line scans whereby speckle is substantially reduced; and

a display to generate a tomographic image of the fluid flow in said sample from said difference at each pixel.