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Fourth, large venules and veins may possibly be identified (depending on the vessel orientation and volume fraction) by evaluating the phase values of the multi-TE data.
This resulted in three output images: a binary image showing the central line of vessels (Fig. 1b), an image showing vessel orientation (Fig. 1c) and an image showing vessel width (Fig. 1d).
In contrast, with CVC, the tip of the needle should stop inside the blood vessel, which requires a method to detect the direction of blood vessel orientation, and the needle must be inserted at an appropriate angle in relation to that orientation.
Eigenvectors obtained using the model give vessel orientation, however the method can be susceptible to outliers.
Velocity is represented both by arrow length tangential to the vessel orientation, and by arrow color.
The vessel orientation can be reconstructed from properly registered 3D volumes [ 17, 18].
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This would simplify the experiments and possibly provide enhanced vascular imaging for all vessel orientations simultaneously.
The volume is probed from two distinct illumination directions with variable controlled incidence plane, allowing for reconstruction of the true flow velocity at arbitrary vessel orientations.
Segment scan DOCT time series (BM-Scans) are acquired at selected locations around the ONH, with optimally adjusted illumination plane parallel to the vessel orientations.
The maximum coronary blood flow velocity computed from the Doppler phase shift calculated above and this beam-vessel orientation angle (assuming an average tissue refractive index of 1.4 and a wavelength of 840 nm) is 23.5 mm/s.
However, several confounds hamper the specificity of T2* measures (iron content, blood vessels, tissues orientation).
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CEO of Professional Science Editing for Scientists @ prosciediting.com