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A switch parameter c generates two different characteristics for the L-J force field: in the case of c= 0, the force vector flows bi-directionally converge to boundaries, while in the case of c≠0 a morphological effect is formed.
Issues with large capture ranges and concavities are solved by other advances, which include inflation forces [10], probabilistic models [11], oriented particles [12], and gradient vector flows [13].
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Vector flow in heart and umbilical cord.
Vector flow in liver and umbilical cord.
During systole, the vector flow changed direction, as was also seen in the spectrogram (Fig. 4c).
Yiu, B. Y. S. & Yu, A. C. H. Least-squares multi-angle Doppler estimators for plane wave vector flow imaging.
Van Cauwenberge, J. et al. Assessing the performance of ultrafast vector flow imaging in the neonatal heart via multiphysics modeling and in-vitro experiments.
Three frames (40, 186 and 258 ms relative to start of spectrogram) from the vector flow analysis of the data sequence of Fig. 3.
Tissue components are segmented automatically using generalized gradient vector flow active contours.
These models rely on accurate time resolved measurements of scalar and vector flow variables.
Unlike traditional gradient vector flow snake, the improved gradient vector flow snake adopts anisotropic diffusion and a four directions edge operator to solve the blurry boundary and edge shifting problem.
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