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Optics Express

  • Vol. 16, Iss. 16 — Aug. 4, 2008
  • pp: 12350–12361
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Single-pass volumetric bidirectional blood flow imaging spectral domain optical coherence tomography using a modified Hilbert transform

Yuankai K. Tao, Anjul M. Davis, and Joseph A. Izatt  »View Author Affiliations


Optics Express, Vol. 16, Issue 16, pp. 12350-12361 (2008)
http://dx.doi.org/10.1364/OE.16.012350


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Abstract

We demonstrate in vivo volumetric bidirectional blood flow imaging in animal models using single-pass flow imaging spectral domain optical coherence tomography. This technique uses a modified Hilbert transform algorithm to separate moving and non-moving scatterers within a depth. The resulting reconstructed image maps the components of moving scatterers flowing into and out of the imaging axis onto opposite image half-planes, enabling volumetric bidirectional flow mapping without manual segmentation.

© 2008 Optical Society of America

1. Introduction

Spectral domain optical coherence tomography (SDOCT) , including both spectrometer-based and swept-source systems, has demonstrated clinical potential for in vivo high-resolution and high-speed imaging of biological structures [1

1. N. A. Nassif, B. Cense, B. H. Park, M. C. Pierce, S. H. Yun, B. E. Bouma, G. J. Tearney, T. C. Chen, and J. F. de Boer, “In vivo high-resolution video-rate spectral-domain optical coherence tomography of the human retina and optic nerve,” Optics Express 12, 10 (2004). http://www.opticsinfobase.org/abstract.cfm?URI=oe-12-3-367 [CrossRef] [PubMed]

, 2

2. M. Wojtkowski, Srinivasan V. J., Ko T. H., J. G. Fujimoto, A. Kowalczyk, and J. S. Duker, “Ultrahigh-Resolution, high-speed, Fourier domain optical coherence tomography and methods for dispersion compensation,” Optics Express 12, 2404 (2004). http://www.opticsinfobase.org/abstract.cfm?URI=oe-12-11-2404 [CrossRef] [PubMed]

]. Advances in Doppler SDOCT have demonstrated several image acquisition schemes that enabled real-time, high-resolution, volumetric display of blood flow maps [3

3. A. Mariampillai, B. A. Standish, N. R. Munce, C. Randall, G. Liu, J. Y. Jiang, A. E. Cable, I. A. Vitkin, and V. X. D. Yang, “Doppler optical cardiogram gated 2D color flow imaging at 1000 fps and 4D in vivo visualization of embryonic heart at 45 fps on a swept source OCT system,” Optics Express 15, 1627 (2007). http://www.opticsinfobase.org/abstract.cfm?id=127228 [CrossRef] [PubMed]

8

8. B. R. White, M. C. Pierce, N. A. Nassif, B. Cense, B. H. Park, G. J. Tearney, B. E. Bouma, T. C. Chen, and J. F. De Boer, “In vivo dynamic human retinal blood flow imaging using ultra-high-speed spectral domain optical Doppler tomography,” Optics Express 11, 8 (2003). http://www.opticsinfobase.org/abstract.cfm?URI=oe-11-25-3490 [CrossRef] [PubMed]

]. These techniques, while able to provide 3D flow maps and velocimetry data, are inherently oversampled, and therefore have reduced imaging speed and are more susceptible to sample motion.

Spatial frequency modulations across lateral scans have been introduced as a method for full range complex conjugate resolved imaging [12

12. R. A. Leitgeb, R. Michaely, T. Lasser, and S. C. Sekhar, “Complex ambiguity-free Fourier domain optical coherence tomography through transverse scanning,” Opt Letters 32, 3453 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=ol-32-23-3453 [CrossRef]

17

17. S. Makita, T. Fabritius, and Y. Yasuno, “Full-range, high-speed, high-resolution 1-mu m spectral-domain optical coherence tomography using BM-scan for volumetric imaging of the human posterior eye,” Optics Express 16, 8406 (2008). http://www.opticsinfobase.org/abstract.cfm?URI=oe-16-12-8406 [CrossRef] [PubMed]

]. Similar to previously described complex conjugate resolving techniques using electro-optic phase modulators [18

18. J. Zhang, J. S. Nelson, and Z. P. Chen, “Removal of a mirror image and enhancement of the signal-to-noise ratio in Fourier-domain optical coherence tomography using an electro-optic phase modulator,” Optics Letters 30, 147 (2005). http://www.opticsinfobase.org/abstract.cfm?URI=ol-30-2-147 [CrossRef] [PubMed]

, 19

19. E. Gotzinger, M. Pircher, R. A. Leitgeb, and C. K. Hitzenberger, “High speed full range complex spectral domain optical coherence tomography,” Optics Express 13, 583 (2005). http://www.opticsexpress.org/abstract.cfm?URI=OPEX-13-2-583 [CrossRef] [PubMed]

] and acousto-optic frequency shifters [20

20. S. H. Yun, G. J. Tearney, J. F. de Boer, and B. E. Bouma, “Removing the depth-degeneracy in optical frequency domain imaging with frequency shifting,” Optics Express 12, 4822 (2004). http://www.opticsexpress.org/abstract.cfm?id=81308 [CrossRef] [PubMed]

22

22. A. H. Bachmann, R. A. Leitgeb, and T. Lasser, “Heterodyne Fourier domain optical coherence tomography for full range probing with high axial resolution,” Optics Express 14, 1487 (2006). http://www.opticsinfobase.org/abstract.cfm?URI=oe-14-4-1487 [CrossRef] [PubMed]

], the spatial frequency modulation technique separates real and complex conjugate reflectivities by imposing a spatial carrier frequency laterally across a B-scan. The carrier frequency is generated by adding a phase delay to each A-scan using a moving reference arm or an off-pivot scanning beam. Similarly, a 3D optical angiography technique [23

23. R. K. Wang, S. L. Jacques, Z. Ma, S. Hurst, S. R. Hanson, and A. Gruber, “Three dimensional optical angiography,” Optics Express 15, 4083 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-7-4083 [CrossRef] [PubMed]

] has been demonstrated by using a modulated reference arm delay and by detecting scatterers not modulated at the carrier frequency as a result of flow-induced Doppler frequency-shifts. Resonant Doppler flow imaging [24

24. A. H. Bachmann, M. L. Villiger, C. Blatter, T. Lasser, and R. A. Leitgeb, “Resonant Doppler flow imaging and optical vivisection of retinal blood vessels,” Optics Express 15, 408 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-2-408 [CrossRef] [PubMed]

] also uses reference arm modulations to detect flow, but instead of using a moving reference arm mirror, resonant Doppler uses an electro-optic modulator, driven at a flow detection frequency, to phase-match the reference signal to that of the moving scatterer. These techniques rely on precise synchronization of reference arm modulation and B-scan acquisition, require expensive or cumbersome modulators, and are unable to detect bidirectional flow in a single B-scan pass. Here we demonstrate an improvement on 3D optical angiography. Single-pass volumetric bidirectional blood flow imaging (SPFI) SDOCT detects moving scatterers using a modified Hilbert transform without the use of spatial frequency modulation. Since no frequency modulations are required and SPFI processing is applied to the spatial frequency content across a single B-scan, SPFI is applicable for both spectrometer-based and swept-source OCT systems, provided they have comparable B-scan acquisition rates. Unlike previously described techniques [23

23. R. K. Wang, S. L. Jacques, Z. Ma, S. Hurst, S. R. Hanson, and A. Gruber, “Three dimensional optical angiography,” Optics Express 15, 4083 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-7-4083 [CrossRef] [PubMed]

, 24

24. A. H. Bachmann, M. L. Villiger, C. Blatter, T. Lasser, and R. A. Leitgeb, “Resonant Doppler flow imaging and optical vivisection of retinal blood vessels,” Optics Express 15, 408 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-2-408 [CrossRef] [PubMed]

], which require two separate B-scans to detect positive and negative flow, each with modulations tuned to the desired flow direction, SPFI is able to resolve bidirectional flow in a single B-scan pass across the sample.

2. Theory

The depth-encoded complex spectral interferometric signal from M discrete sample reflectors for an SDOCT system can be written as

s[k,x]=m=1MAmexp[(2nkΔzm+θh[x]+θm[x])]
(1)

Fig. 1. Flow chart of SDOCT spectral datacube processing. (a) Spectral inverse Fourier transform of B-scan yields (b,c) conventional SDOCT depth-resolved reflectivity map and lateral Fourier transform yields (d,e) sample spatial frequency information.

The recorded interferometric signal represents the real-part of a summation of signals from M discrete reflectors (Eq. (1)) in a coherence volume (i.e. spot-size x coherence-length) and thus the phase term, θm [x], can be represented as

θm[x]=2nkw02[xdLD]vmvxxdLD+w02
(2)

where vm and vx are the axial components of scatterer velocities and lateral scan speed, respectively. ∏ is the boxcar function defined by w02[xdLD]=H[xdlD+w02]H[xdLDw02] and restricts the measured phase to moving scatterers within the spot-size, w 0. d represents the A-scan location of the moving scatterer across a lateral scan of length L, sampled with a density of D A-scans. Combining Eq. (1) and Eq. (2), the sampled interferometric signal can be represented as the conventional SDOCT signal with a velocity-associated phase modulation

s[k,x]=m=1MAmexp[i2nkΔzm]exp[iθh[x]]exp[2ink∏w02[xdLD]vmvxxdLD+w02]
=m=1MAmexp[i2nkΔzm]g[x]h[x]
(3)

where g[x] and h[x] are the interferometric components associated with the optical heterogeneity and moving scatterers, respectively.

The recorded spectral datacube, I[k, x, y], in SDOCT is comprised of the real-parts of the interferometric signals (Eq. (3)) accumulated during a 2D raster scan and can be separated into a series of B-scan, I[k,x], data slices (Fig. 1(a)). The inverse Fourier transform in the spectral dimension, FTkz1[I[k,x]]=R[z,x]+R̅[z,x], represents the depth-resolved reflectivity map in conventional SDOCT (Fig. 1(b),(c)). Fourier transforming the lateral dimension (B-scan) yields the spatial frequency content

FTxu[I[k,x]]=m=1MAmcos[2nkΔzm]⊗Re[G[u]]⊗Re[H[u]].
(4)

H[u] is the spatial frequency content of the phase associated with moving scatterers integrated across a spot size

Re[H[u]]=Re[dLDw02dLD+w02exp[2inkvmvxxdLD+w02]exp[iux]dx]
=κcos[w0u2nkvmvx]1u2nkvmvx
(5)

σh[u]=x=1Lσh2[x]
(6)

and is representative of the spatial correlation between sequentially sampled A-scans with a high correlation lower limit associated with the optical heterogeneity of scatterers within a coherence volume, θh [x], and a Nyquist sampling upper limit.

Fig. 2. Flow chart of SPFI-SDOCT processing. (a) Lateral Fourier transform of B-scan yields (b) spatial frequency of sample centered around DC and spatial frequency of moving scatterers shifted by their respective Doppler frequencies. (c) Applying a frequency-shifted Heaviside step function and inverse Fourier transform of spatial frequencies recreates (d) the analytic interferometric signal (modified Hilbert transf'rm). (e) Spectral inverse Fourier transform of the analytic interferometric signal maps depth-solved reflectivities of bidirectionally moving scatterers on opposite image half-planes which can then be (f) overlaid for vessel identification.

FTxu[I[k,x]]H[ufT]=α(V+[k,u+fD,+]+V__[k,ufD,])
(7)

dv=Lλ02nDτw0cosθD
(8)

where λ 0 is the center wavelength, τ is the integration time, and θD is the Doppler angle between the scanning beam and the direction of scatterer motion. n is the index of refraction, L is the lateral scan length, D is the number of A-scans acquired across the lateral scan, and wo is the scanning beam spot size. Eq. (8) shows that velocity resolution in SPFI increases and the maximum detectable velocity decreases linearly with increased spatial oversampling.

Fig. 3. SPFI-SDOCT microscope. 2-dimensional scanning was implemented using a galvanometer scanning pair and f/8.5 microscope optics were optimized for a 9μm spot-size. The reference arm was blocked to allow for commonpath imaging.

3. Methods

SPFI-SDOCT was implemented on a high-speed SDOCT microscope (Fig. 3) with the central wavelength at 859nm and a FWHM bandwidth of 99nm. The sample arm was a custom-built f/8.5 microscope equipped with scanning galvanometers and imaging optics optimized for a 9μm spot-size. SPFI data was demonstrated using both conventional and commonpath SDOCT configurations by blocking the reference arm of a typical SDOCT interferometer to implement a self-referenced [26

26. M. A. Choma, A. K. Ellerbee, C. Yang, T. L. Creazzo, and J. A. Izatt, “Spectral-domain phase microscopy,” Opt Lett 30, 1162 (2005). http://www.opticsinfobase.org/abstract.cfm?URI=oe-11-18-2183 [CrossRef] [PubMed]

] imaging scheme to reduce phase-noise such that fT is dominated by lateral sampling. Phase-noise between sequential A-scans in a homogeneous phantom was measured to be 127mrad and 4.2mrad in conventional and commonpath configurations, respectively. Since the lower limit of the resolving power in SPFI is proportional to the phase-noise, the commonpath configuration was used for animal model imaging. Interferometric signals were captured using a 2048 pixel line-scan camera (e2v, Ltd.). Custom software (Bioptigen, Inc.) performed real-time data acquisition, processing, archiving, and display. Using a 1.3mW sample beam, the SNR measured near DC was 108dB with an axial resolution of 3.29μm in tissue and a 6dB falloff at 0.8mm. DC removal, k-space resampling, and flow imaging using the modified Hilbert transform algorithm [14

14. R. K. Wang, “In vivo full range complex Fourier domain optical coherence tomography,” Applied Physics Letters 90, 054103 (2007).

, 15

15. B. Baumann, M. Pircher, E. Gotzinger, and C. K. Hitzenberger, “Full range complex spectral domain optical coherence tomography without additional phase shifters,” Optics Express 15, 13375 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-20-13375 [CrossRef] [PubMed]

, 23

23. R. K. Wang, S. L. Jacques, Z. Ma, S. Hurst, S. R. Hanson, and A. Gruber, “Three dimensional optical angiography,” Optics Express 15, 4083 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-7-4083 [CrossRef] [PubMed]

] were computed during post-processing using Matlab (MathWorks, Inc.). Vessel and structure were visualized using Amira (Visage Imaging, Inc.).

Fig. 4. Phantom and in vivo flow models.(a) Two micro-capillaries were connected and oriented such that fluid flowed in opposite directions in a B-scan cross-section (line indicates B-scan orientation).(b) Chicken embryo preparation showing live embryo and peripheral vessels on both amnion and yolk surfaces (arrow).(c) Mouse window chamber preparation showing skin fold vasculature and tumor.

Bidirectional flow imaging was demonstrated on a flow phantom using the conventional SDOCT configuration. Two glass micro-capillary tubes (1.5mm outer diameter, 0.6mm inner diameter) were connected using silastic tubing and pumped with 1% liposyn at 0.01mL/min (Harvard Apparatus). The micro-capillaries were then positioned adjacent to each other on an angled stage such that fluid in the tubes flowed in opposite directions in a B-scan cross-section (Fig. 4(a)), simulating bidirectional flow.

Vessel imaging was demonstrated on chicken embryo and mouse tumor window chamber models (Fig. 4(b),(c)). Fertilized Hubert Ross chicken eggs were incubated at 38°C and 97% humidity in a forced-draft incubation chamber [27

27. T. M. Yelbuz, M. A. Choma, L. Thrane, M. L. Kirby, and J. A. Izatt, “Optical coherence tomography - A new high-resolution imaging technology to study cardiac development in chick embryos,” Circulation 106, 2771 (2002). [CrossRef] [PubMed]

]. At Hamburger-Hamilton (HH)-stages 23–25 [28

28. V. Hamburger and H. L. Hamilton, “A series of normal stages in the development of the chick embryo,” Journal of Morphology 88, 54 (1951). [CrossRef]

], a window was created through the outer shell and the chorionic membrane was removed. Peripheral yolk vasculature (Fig. 4(b)) was then imaged using the commonpath configuration with the top amnion surface as the reference reflector. Vessels away from the embryo were imaged to avoid pulsatile flow as a result of heart beat. Embryo temperatures were maintained using a heat-lamp during the course of imaging.

Mouse in vivo experiments were conducted under protocols approved by the Duke University Institutional Animal Care and Use Committee. Mouse tumor models were prepared by surgically implanting a titanium window chamber on the back of anthymic (nu/nu) nude mice under anesthesia (ketamine 100mg/kg and xylazine 10mg/kg intraperitoneal). 4T1 metastatic mouse mammary adenocarcinoma cells were used. During window implantation, 10μL of a cell suspension of 5×103 cells was injected into the dorsal skin flap and covered with a 12mm diameter #2 round glass coverslip over the exposed skin (Fig. 4(c)) [29

29. B. S. Sorg, M. E. Hardee, N. Agarwal, B. J. Moeller, and M. W. Dewhirst, “Spectral imaging facilitates visualization and measurements of unstable and abnormal microvascular oxygen transport in tumors,” Journal of Biomedical Optics 13 (2008). [CrossRef] [PubMed]

].

Animals were housed in an environmental chamber with free access to food and water and standard 12hr light and dark cycles. Mice tumors were imaged two weeks after implantation using the window chamber surface as a reference reflector. The mice were anesthetized during imaging using isoflurane (1.5–2.5%) in medical air. Mice were imaged using the commonpath configuration, self-referenced using the surface of the window chamber as the reference reflector.

Fig. 5. Flow phantom imaging showing (a) conventional SDOCT depth image with complex conjugate mirror image,(b) SPFI processed flow image showing bidirectional flow, and (c) overlaid flow and structure image. Negative flow (blue), positive flow (red), and non-moving structure (orange) are identified.

4. Results and Discussion

Bidirectional flow imaging was demonstrated on a liposyn-pumped flow phantom (Fig. 5). The phantom was angled such that components of flow were oriented in the axis of the imaging beam to enable SPFI detection. We assume a standard minimum B-scan size of 1000 A-scans/frame for a 3mm lateral scan at an integration time of 50μs. Faster lateral scan velocities result in galvanometer jitter, and therefore poor image quality and phase stability. Spatial oversampling for SPFI is defined based on these scan parameters in the following. A 3mm B-scan was acquired with 1800A-scans/frame with an A-scan integration period of 50μs, a factor of 1.8 increase in lateral oversampling. Conventional SDOCT processing (Fig. 5(a)) showed depth-ranged reflectivity of scatterers including structure, flow, and their complex conjugate mirror images. The directionality of flow in each tube is not readily discernable using conventional processing steps (Fig. 5(a) – red/blue arrows). After applying the modified Hilbert transform algorithm (Fig. 5(b)), all non-moving scatterer reflectivities (structure) and mirror images of flow are resolved leaving only positive and negative flow on opposite image half-planes. The phantom structural heterogeneity was bandlimited as a result of lateral oversampling, allowing the frequency-shifted Heaviside function to window out only moving scatterers (Eq. (6)). Similarly, the mirror images of moving scatterers were also eliminated by application of the modified Hilbert transform, leaving only the real-valued positive flow and complex conjugate negative flow, which are imaged to opposite sides of DC (Fig. 5(b)). Using the SPFI processed image, positive and negative flow are separated and overlaid onto the structural image for visualization (Fig. 5(c)). Given the oversampling parameters and the threshold frequency determined experimentally from the phantom data, the magnitude of the detectable positive and negative flow velocities was 0.39–1.12mm/s.

Fig. 6. 3D reconstruction of bidirectional volumetric flow magnitude in chicken embryo model. 3mm × 3mm volume is comprised of nine 1mm × 1mm volumes sampled with 1ms integration time. Vessel sizes of 40μm (purple) to 270μm (orange) were within detection limits. Amionic vessel (blue), amionic vessel branch point (green), and motion artifact (red) are indentified.
Fig. 7. (7.73MB) Movie of 3D rendering of bidirectional flow magnitude in chicken embryo model. [Media 1]

In vivo volumetric blood flow imaging was demonstrated on Hubert Ross chicken embryos and mice window chamber models. A 3mm × 3mm volume mosaic was created by acquiring nine 1mm × 1mm volumes imaged with 1800A-scans/frame and 100frames/volume, a factor of 5.4 increase in lateral oversampling. Each SPFI-SDOCT reconstructed frame was separated into two halves and combined to create bidirectional flow maps with intensities corresponding to the reflectivity of scatterers moving into or out of the A-scan axis.

Fig. 8. 3D reconstruction of bidirectional volumetric flow magnitude in mouse window chamber model. 3mm × 3mm volume is comprised of nine 1mm × 1mm volumes sampled with 2ms integration time. Vessel sizes of 20μm (purple) to 110μm (green) were within detection limits. Tumor region vasculature (blue) and motion artifact (red) are indicated.

The peripheral yolk vascular network (Fig. 6) is clearly visible in the chicken embryo model. SPFI-SDOCT imaged vessels are tubular, as expected, and appear to be confined to a 500μm layer (Fig. 7). The large and partially imaged vessel across the volume mosaic (Fig. 6 – blue arrow) is a shadow artifact arising from imaging through a large vessel in the amionic (reference reflector) layer. The well defined portion of this vessel (Fig 6 – green arrow) represents areas where the vessel branches from the yolk surface up towards the surface of the amnion. The faded regions (Fig. 6 – blue arrow) are areas where the vessel is on top of the amion surface and out of the imaging depth range. Yolk surface vessels follow the curvature of the yolk sac and are shown gradually descending away from the reference surface (Fig. 7). Detected vessel sizes ranged from 40μm (Fig 6 – purple arrow) to 270μm (Fig 6 – orange arrow). “Hazy" sections (Fig. 6 – red arrow) are indicative of sample bulk motion which resulted in non-moving structural scatterers being resolved along with flow. Chicken embryo volumes were acquired using 1ms A-scan integration time in order to detect small vessels with minimal flow velocities. The magnitude of the detectable positive and negative flow velocities for the embryo model was 65.6-168.6μm/s.

Normal and tumor vasculature (Fig. 8) were imaged in the mouse window chamber model. Tumor regions were indentified prior to imaging (Fig. 8 – blue arrow) and show highly tortuous vessels indicative of neoplastic angiogenesis. Surrounding vasculature indicate normal skin fold vessels. Detected vessel sizes ranged from 20μm (Fig 8 – purple arrow), which approaches the sampling limit of the microscope, to 110μm (Fig 8 – green arrow). The volumes were acquired using 2ms A-scan integration time in order to detect small vessels however these volumes were more sensitive to bulk motion artifacts (Fig. 8 – red arrow). The magnitude of the detectable positive and negative flow velocities for the mouse tumor model was 32.8–84.3μm/s. Small noise signals throughout the volumes indicate areas of reference reflector saturation due to small optical reflectivity heterogeneities across the reference window chamber surface.

5. Conclusions

We have demonstrated a new noninvasive in vivo volumetric bidirectional flow imaging technique. SPFI-SDOCT allows for flow imaging without acquiring multiple A-scans at a single lateral position. Using a modified Hilbert transform algorithm, reflectivities of the components of moving scatterers flowing into and out of the axis of each A-scan are mapped to opposite sides of the image plane, thus allowing for volumetric visualization of flow without the need for manual segmentation.

6. Acknowledgements

We acknowledge contributions of Melissa Skala from the Department of Biomedical Engineering, Duke University and Greg Palmer and Mark Dewhirst from the Department of Radiation Oncology, Duke University Medical Center, for their assistance in mice preparations and protocols. This research was supported by NIH grants R21 EY017393 and R21 EB006338.

References and links

1.

N. A. Nassif, B. Cense, B. H. Park, M. C. Pierce, S. H. Yun, B. E. Bouma, G. J. Tearney, T. C. Chen, and J. F. de Boer, “In vivo high-resolution video-rate spectral-domain optical coherence tomography of the human retina and optic nerve,” Optics Express 12, 10 (2004). http://www.opticsinfobase.org/abstract.cfm?URI=oe-12-3-367 [CrossRef] [PubMed]

2.

M. Wojtkowski, Srinivasan V. J., Ko T. H., J. G. Fujimoto, A. Kowalczyk, and J. S. Duker, “Ultrahigh-Resolution, high-speed, Fourier domain optical coherence tomography and methods for dispersion compensation,” Optics Express 12, 2404 (2004). http://www.opticsinfobase.org/abstract.cfm?URI=oe-12-11-2404 [CrossRef] [PubMed]

3.

A. Mariampillai, B. A. Standish, N. R. Munce, C. Randall, G. Liu, J. Y. Jiang, A. E. Cable, I. A. Vitkin, and V. X. D. Yang, “Doppler optical cardiogram gated 2D color flow imaging at 1000 fps and 4D in vivo visualization of embryonic heart at 45 fps on a swept source OCT system,” Optics Express 15, 1627 (2007). http://www.opticsinfobase.org/abstract.cfm?id=127228 [CrossRef] [PubMed]

4.

Y. Wang, B. A. Bower, J. A. Izatt, O. Tan, and D. Huang, “In vivo total retinal blood flow measurement by Fourier domain Doppler optical coherence tomography,” Journal of Biomedical Optics 12, 041215 (2007). [CrossRef] [PubMed]

5.

B. A. Bower, M. Zhao, R. J. Zawadzki, and J. A. Izatt, “Real-time spectral domain Doppler optical coherence tomography and investigation of human retinal vessel autoregulation,” Journal of Biomedical Optics 12, 041214 (2007). [CrossRef] [PubMed]

6.

L. Wang, Y. Wang, S. Guo, J. Zhang, M. Bachman, G. P. Li, and Z. Chen, “Frequency domain phase-resolved optical Doppler and Doppler variance tomography,” Optics Communications 242, 6 (2004). [CrossRef]

7.

R. A. Leitgeb, L. Schmetterer, W. Drexler, A. F. Fercher, R. J. Zawadzki, and T. Bajraszewski, “Real-time assessment of retinal blood flow with ultrafast acquisition by color Doppler Fourier domain optical coherence tomography,” Optics Express 11, 3116 (2003). http://www.opticsinfobase.org/abstract.cfm?URI=oe-11-23-3116 [CrossRef] [PubMed]

8.

B. R. White, M. C. Pierce, N. A. Nassif, B. Cense, B. H. Park, G. J. Tearney, B. E. Bouma, T. C. Chen, and J. F. De Boer, “In vivo dynamic human retinal blood flow imaging using ultra-high-speed spectral domain optical Doppler tomography,” Optics Express 11, 8 (2003). http://www.opticsinfobase.org/abstract.cfm?URI=oe-11-25-3490 [CrossRef] [PubMed]

9.

M. Szkulmowski, A. Szkulmowska, T. Bajraszewski, A. Kowalczyk, and M. Wojtkowski, “Flow velocity estimation using joint Spectral and Time Domain Optical Coherence Tomography,” Optics Express 16, 6008 (2008). http://www.opticsinfobase.org/abstract.cfm?URI=oe-16-9-6008 [CrossRef] [PubMed]

10.

L. Yannuzzi, K. Rohrer, L. Tindel, R. Sobel, M. Constanza, W. Shields, and E. Zang, “Fluorescein angiography complication survey,” Ophthalmology 93, 7 (1986). [PubMed]

11.

M. Hope-Ross, L. Yannuzzi, E. Gragoudas, D. Guyer, J. Slakter, J. Sorenson, S. Krupsky, D. Orlock, and C. A. Puliafito, “Adverse reactions due to indocyanin' green,” Ophthalmology 101, 5 (1994). [PubMed]

12.

R. A. Leitgeb, R. Michaely, T. Lasser, and S. C. Sekhar, “Complex ambiguity-free Fourier domain optical coherence tomography through transverse scanning,” Opt Letters 32, 3453 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=ol-32-23-3453 [CrossRef]

13.

Y. Yasuno, S. Makita, T. Endo, G. Aoki, M. Itoh, and T. Yatagai, “Simultaneous B-M-mode scanning method for real-time full-range Fourier domain optical coherence tomography,” Applied Optics 45, 8 (2006). [CrossRef] [PubMed]

14.

R. K. Wang, “In vivo full range complex Fourier domain optical coherence tomography,” Applied Physics Letters 90, 054103 (2007).

15.

B. Baumann, M. Pircher, E. Gotzinger, and C. K. Hitzenberger, “Full range complex spectral domain optical coherence tomography without additional phase shifters,” Optics Express 15, 13375 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-20-13375 [CrossRef] [PubMed]

16.

L. An and R. K. Wang, “Use of a scanner to modulate spatial interferograms for in vivo full-range Fourier-domain optical coherence tomography,” Opt Letters 32, 3423 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=ol-32-23-3423 [CrossRef]

17.

S. Makita, T. Fabritius, and Y. Yasuno, “Full-range, high-speed, high-resolution 1-mu m spectral-domain optical coherence tomography using BM-scan for volumetric imaging of the human posterior eye,” Optics Express 16, 8406 (2008). http://www.opticsinfobase.org/abstract.cfm?URI=oe-16-12-8406 [CrossRef] [PubMed]

18.

J. Zhang, J. S. Nelson, and Z. P. Chen, “Removal of a mirror image and enhancement of the signal-to-noise ratio in Fourier-domain optical coherence tomography using an electro-optic phase modulator,” Optics Letters 30, 147 (2005). http://www.opticsinfobase.org/abstract.cfm?URI=ol-30-2-147 [CrossRef] [PubMed]

19.

E. Gotzinger, M. Pircher, R. A. Leitgeb, and C. K. Hitzenberger, “High speed full range complex spectral domain optical coherence tomography,” Optics Express 13, 583 (2005). http://www.opticsexpress.org/abstract.cfm?URI=OPEX-13-2-583 [CrossRef] [PubMed]

20.

S. H. Yun, G. J. Tearney, J. F. de Boer, and B. E. Bouma, “Removing the depth-degeneracy in optical frequency domain imaging with frequency shifting,” Optics Express 12, 4822 (2004). http://www.opticsexpress.org/abstract.cfm?id=81308 [CrossRef] [PubMed]

21.

A. M. Davis, M. A. Choma, and J. A. Izatt, “Heterodyne swept-source optical coherence tomography for complete complex conjugate ambiguity removal,” Journal of Biomedical Optics 10 (2005). [CrossRef] [PubMed]

22.

A. H. Bachmann, R. A. Leitgeb, and T. Lasser, “Heterodyne Fourier domain optical coherence tomography for full range probing with high axial resolution,” Optics Express 14, 1487 (2006). http://www.opticsinfobase.org/abstract.cfm?URI=oe-14-4-1487 [CrossRef] [PubMed]

23.

R. K. Wang, S. L. Jacques, Z. Ma, S. Hurst, S. R. Hanson, and A. Gruber, “Three dimensional optical angiography,” Optics Express 15, 4083 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-7-4083 [CrossRef] [PubMed]

24.

A. H. Bachmann, M. L. Villiger, C. Blatter, T. Lasser, and R. A. Leitgeb, “Resonant Doppler flow imaging and optical vivisection of retinal blood vessels,” Optics Express 15, 408 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-2-408 [CrossRef] [PubMed]

25.

M. A. Choma, M. V. Sarunic, C. H. Yang, and J. A. Izatt, “Sensitivity advantage of swept source and Fourier domain optical coherence tomography,” Optics Express 11, 2183 (2003). http://www.opticsinfobase.org/abstract.cfm?URI=oe-11-18-2183 [CrossRef] [PubMed]

26.

M. A. Choma, A. K. Ellerbee, C. Yang, T. L. Creazzo, and J. A. Izatt, “Spectral-domain phase microscopy,” Opt Lett 30, 1162 (2005). http://www.opticsinfobase.org/abstract.cfm?URI=oe-11-18-2183 [CrossRef] [PubMed]

27.

T. M. Yelbuz, M. A. Choma, L. Thrane, M. L. Kirby, and J. A. Izatt, “Optical coherence tomography - A new high-resolution imaging technology to study cardiac development in chick embryos,” Circulation 106, 2771 (2002). [CrossRef] [PubMed]

28.

V. Hamburger and H. L. Hamilton, “A series of normal stages in the development of the chick embryo,” Journal of Morphology 88, 54 (1951). [CrossRef]

29.

B. S. Sorg, M. E. Hardee, N. Agarwal, B. J. Moeller, and M. W. Dewhirst, “Spectral imaging facilitates visualization and measurements of unstable and abnormal microvascular oxygen transport in tumors,” Journal of Biomedical Optics 13 (2008). [CrossRef] [PubMed]

OCIS Codes
(170.3340) Medical optics and biotechnology : Laser Doppler velocimetry
(170.3880) Medical optics and biotechnology : Medical and biological imaging
(170.4500) Medical optics and biotechnology : Optical coherence tomography

ToC Category:
Medical Optics and Biotechnology

History
Original Manuscript: May 16, 2008
Revised Manuscript: July 15, 2008
Manuscript Accepted: July 17, 2008
Published: August 1, 2008

Virtual Issues
Vol. 3, Iss. 9 Virtual Journal for Biomedical Optics

Citation
Yuankai K. Tao, Anjul M. Davis, and Joseph A. Izatt, "Single-pass volumetric bidirectional blood flow imaging spectral domain optical coherence tomography using a modified Hilbert transform," Opt. Express 16, 12350-12361 (2008)
http://www.opticsinfobase.org/oe/abstract.cfm?URI=oe-16-16-12350


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References

  1. N. A. Nassif, B. Cense, B. H. Park, M. C. Pierce, S. H. Yun, B. E. Bouma, G. J. Tearney, T. C. Chen, and J. F. de Boer, "In vivo high-resolution video-rate spectral-domain optical coherence tomography of the human retina and optic nerve," Optics Express 12, 10 (2004). http://www.opticsinfobase.org/abstract.cfm?URI=oe-12-3-367 [CrossRef] [PubMed]
  2. M. Wojtkowski, V. J. Srinivasan, T. H. Ko, J. G. Fujimoto, A. Kowalczyk, and J. S. Duker, "Ultrahigh-Resolution, high-speed, Fourier domain optical coherence tomography and methods for dispersion compensation," Optics Express 12, 2404 (2004). http://www.opticsinfobase.org/abstract.cfm?URI=oe-12-11-2404. [CrossRef] [PubMed]
  3. A. Mariampillai, B. A. Standish, N. R. Munce, C. Randall, G. Liu, J. Y. Jiang, A. E. Cable, I. A. Vitkin, and V. X. D. Yang, "Doppler optical cardiogram gated 2D color flow imaging at 1000 fps and 4D in vivo visualization of embryonic heart at 45 fps on a swept source OCT system," Optics Express 15, 1627 (2007). http://www.opticsinfobase.org/abstract.cfm?id=127228 [CrossRef] [PubMed]
  4. Y. Wang, B. A. Bower, J. A. Izatt, O. Tan, and D. Huang, "In vivo total retinal blood flow measurement by Fourier domain Doppler optical coherence tomography," J. Biomedical Opt. 12, 041215 (2007). [CrossRef] [PubMed]
  5. B. A. Bower, M. Zhao, R. J. Zawadzki, and J. A. Izatt, "Real-time spectral domain Doppler optical coherence tomography and investigation of human retinal vessel autoregulation," J. Biomedical Opt. 12, 041214 (2007). [CrossRef] [PubMed]
  6. L. Wang, Y. Wang, S. Guo, J. Zhang, M. Bachman, G. P. Li, and Z. Chen, "Frequency domain phase-resolved optical Doppler and Doppler variance tomography," Opt. Commun. 242, 6 (2004). [CrossRef]
  7. R. A. Leitgeb, L. Schmetterer, W. Drexler, A. F. Fercher, R. J. Zawadzki, and T. Bajraszewski, "Real-time assessment of retinal blood flow with ultrafast acquisition by color Doppler Fourier domain optical coherence tomography," Opt. Express 11, 3116 (2003). http://www.opticsinfobase.org/abstract.cfm?URI=oe-11-23-3116 [CrossRef] [PubMed]
  8. B. R. White, M. C. Pierce, N. A. Nassif, B. Cense, B. H. Park, G. J. Tearney, B. E. Bouma, T. C. Chen, and J. F. De Boer, "In vivo dynamic human retinal blood flow imaging using ultra-high-speed spectral domain optical Doppler tomography," Opt. Express 11, 8 (2003). http://www.opticsinfobase.org/abstract.cfm?URI=oe-11-25-3490 [CrossRef] [PubMed]
  9. M. Szkulmowski, A. Szkulmowska, T. Bajraszewski, A. Kowalczyk, and M. Wojtkowski, "Flow velocity estimation using joint Spectral and Time Domain Optical Coherence Tomography," Opt. Express 16, 6008 (2008). http://www.opticsinfobase.org/abstract.cfm?URI=oe-16-9-6008 [CrossRef] [PubMed]
  10. L. Yannuzzi, K. Rohrer, L. Tindel, R. Sobel, M. Constanza, W. Shields, and E. Zang, "Fluorescein angiography complication survey," Ophthalmology 93, 7 (1986). [PubMed]
  11. M. Hope-Ross, L. Yannuzzi, E. Gragoudas, D. Guyer, J. Slakter, J. Sorenson, S. Krupsky, D. Orlock, and C. A. Puliafito, "Adverse reactions due to indocyanine green," Ophthalmology 101, 5 (1994). [PubMed]
  12. R. A. Leitgeb, R. Michaely, T. Lasser, and S. C. Sekhar, "Complex ambiguity-free Fourier domain optical coherence tomography through transverse scanning," Opt Lett. 32, 3453 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=ol-32-23-3453 [CrossRef]
  13. Y. Yasuno, S. Makita, T. Endo, G. Aoki, M. Itoh, and T. Yatagai, "Simultaneous B-M-mode scanning method for real-time full-range Fourier domain optical coherence tomography," Appl. Opt. 45, 8 (2006). [CrossRef] [PubMed]
  14. R. K. Wang, "In vivo full range complex Fourier domain optical coherence tomography," Appl. Phys. Lett. 90, 054103 (2007).
  15. B. Baumann, M. Pircher, E. Gotzinger, and C. K. Hitzenberger, "Full range complex spectral domain optical coherence tomography without additional phase shifters," Opt. Express 15, 13375 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-20-13375 [CrossRef] [PubMed]
  16. L. An, and R. K. Wang, "Use of a scanner to modulate spatial interferograms for in vivo full-range Fourier-domain optical coherence tomography," Opt Lett. 32, 3423 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=ol-32-23-3423 [CrossRef]
  17. S. Makita, T. Fabritius, and Y. Yasuno, "Full-range, high-speed, high-resolution 1-mu m spectral-domain optical coherence tomography using BM-scan for volumetric imaging of the human posterior eye," Opt. Express 16, 8406 (2008). http://www.opticsinfobase.org/abstract.cfm?URI=oe-16-12-8406 [CrossRef] [PubMed]
  18. J. Zhang, J. S. Nelson, and Z. P. Chen, "Removal of a mirror image and enhancement of the signal-to-noise ratio in Fourier-domain optical coherence tomography using an electro-optic phase modulator," Opt. Lett. 30, 147 (2005). http://www.opticsinfobase.org/abstract.cfm?URI=ol-30-2-147 [CrossRef] [PubMed]
  19. E. Gotzinger, M. Pircher, R. A. Leitgeb, and C. K. Hitzenberger, "High speed full range complex spectral domain optical coherence tomography," Opt. Express 13, 583 (2005). http://www.opticsexpress.org/abstract.cfm?URI=OPEX-13-2-583 [CrossRef] [PubMed]
  20. S. H. Yun, G. J. Tearney, J. F. de Boer, and B. E. Bouma, "Removing the depth-degeneracy in optical frequency domain imaging with frequency shifting," Opt. Express 12, 4822 (2004). http://www.opticsexpress.org/abstract.cfm?id=81308 [CrossRef] [PubMed]
  21. A. M. Davis, M. A. Choma, and J. A. Izatt, "Heterodyne swept-source optical coherence tomography for complete complex conjugate ambiguity removal," J. Biomedical Opt. 10, (2005). [CrossRef] [PubMed]
  22. A. H. Bachmann, R. A. Leitgeb, and T. Lasser, "Heterodyne Fourier domain optical coherence tomography for full range probing with high axial resolution," Opt. Express 14, 1487 (2006). nfobase.org/abstract.cfm?URI=oe-14-4-1487">http://www.opticsinfobase.org/abstract.cfm?URI=oe-14-4-1487 [CrossRef] [PubMed]
  23. R. K. Wang, S. L. Jacques, Z. Ma, S. Hurst, S. R. Hanson, and A. Gruber, "Three dimensional optical angiography," Opt. Express 15, 4083 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-7-4083 [CrossRef] [PubMed]
  24. A. H. Bachmann, M. L. Villiger, C. Blatter, T. Lasser, and R. A. Leitgeb, "Resonant Doppler flow imaging and optical vivisection of retinal blood vessels," Opt. Express 15, 408 (2007). http://www.opticsinfobase.org/abstract.cfm?URI=oe-15-2-408 [CrossRef] [PubMed]
  25. M. A. Choma, M. V. Sarunic, C. H. Yang, and J. A. Izatt, "Sensitivity advantage of swept source and Fourier domain optical coherence tomography," Opt. Express 11, 2183 (2003). http://www.opticsinfobase.org/abstract.cfm?URI=oe-11-18-2183 [CrossRef] [PubMed]
  26. M. A. Choma, A. K. Ellerbee, C. Yang, T. L. Creazzo, and J. A. Izatt, "Spectral-domain phase microscopy," Opt Lett 30, 1162 (2005). http://www.opticsinfobase.org/abstract.cfm?URI=oe-11-18-2183 [CrossRef] [PubMed]
  27. T. M. Yelbuz, M. A. Choma, L. Thrane, M. L. Kirby, and J. A. Izatt, "Optical coherence tomography - A new high-resolution imaging technology to study cardiac development in chick embryos," Circulation 106, 2771 (2002). [CrossRef] [PubMed]
  28. V. Hamburger, and H. L. Hamilton, "A series of normal stages in the development of the chick embryo," J. Morphology 88, 54 (1951). [CrossRef]
  29. B. S. Sorg, M. E. Hardee, N. Agarwal, B. J. Moeller, and M. W. Dewhirst, "Spectral imaging facilitates visualization and measurements of unstable and abnormal microvascular oxygen transport in tumors," J. Biomedical Opt. 13, (2008). [CrossRef] [PubMed]

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