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Phase-resolved optical frequency domain imaging

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Abstract

Phase-resolved Doppler optical coherence tomography has been used to image blood flow dynamics in various tissues using both time-domain and spectral-domain optical coherence tomography techniques. In this manuscript, we present phase-resolved Doppler imaging with a high-speed optical frequency domain imaging system. We demonstrate that by correcting for spurious timing-induced phase errors, excellent flow sensitivity can be achieved, limited only by the imaging signal-to-noise ratio. Conventional and Doppler images showing flow in an Intralipid phantom and in human skin are presented. Additionally, we demonstrate the ability of phase-resolved OFDI to measure high flow rates without the deleterious effects of fringe washout.

©2005 Optical Society of America

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Figures (7)

Fig. 1.
Fig. 1. Basic configuration of the OFDI system.
Fig. 2.
Fig. 2. (a) The implementation of a calibration mirror used to generate a calibration signal which allows measurement of the timing-induced phase variations for each A-line pair. (b) A representative A-line showing the signal from the sample (tissue) and the calibration signal.
Fig. 3.
Fig. 3. A typical measured phase (a), phase difference (b), and corrected phase difference (c) for a sample signal at depth Z=0.54.
Fig. 4.
Fig. 4. The measured (circle) and predicted (solid curve) phase noise as a function of the sample signal SNR (Xs) at depths (a) Zs=0.07 and (b) Zs=0.84. The individual contribution to the overall noise resulting from only the sample signal noise (dash-dot curve) and calibration signal noise (dashed curve) are also shown. In both cases, the calibration signal was located at a depth Zc=0.96 with Xc ~31 dB.
Fig. 5.
Fig. 5. Images of Intralipid flow through an 800 µm tube immersed in stationary Intralipid. (a) Structural image. (b) Flow image. The transverse distance is 3 mm and the imaging depth is 2.6 mm in air. Each image comprises 2000 A-lines.
Fig. 6.
Fig. 6. M-mode image showing depth-resolved Intralipid flow as a function of time for high-rate, pulsatile flow. The beam was positioned at the center of the tube (see arrow in Fig. 5). In (a), the measured phase difference is shown without unwrapping phase discontinuities. In (b), a phase unwrapping algorithm is used to reconstruct the flow. Note the difference in scale between the images. In (c) the flow profile at time T (indicated on the time axis) is plotted. The maximum flow in (c) induced a phase difference of -8.5π corresponding to a flow rate of 191 mm/s.
Fig. 7.
Fig. 7. Images of human finger near the nailbed. Fig. 7(a) shows the structural image and 7(b) shows the flow image. Two blood vessels (circled) are clearly visible in the flow image. The transverse dimension is 3 mm and the depth is 2.6 mm. Each image contains 2000 A-lines.

Equations (5)

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σ Δ ϕ 2 = ( 1 X ) .
S ( t ) R cos ( 2 k o z + 2 α z [ t + ε ] )
Δ ϕ = 2 α z Δ ε 2 α z T cl π Z .
Δ ϕ ̂ i , j = Δ ϕ i , j ( i m ) Δ ϕ m , j .
σ Δ ϕ ̂ 2 = ( 1 X s ) + ( Z s Z c ) 2 ( 1 X c )
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