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To solve this problem, the average flow profile is introduced to account for the actual three-dimensional flow non-uniformity in the rectangular duct.
It is further found that the effective Mach number, corresponding to a slightly modified average flow profile, can be used to achieve a considerable collapse of the impedance spectra educed at different Mach numbers.
Similarly, the flow amplitude in composite images is usually lower than in single images because it represents the average flow profile across several cardiac cycles.
Flow amplitude in a radial profile (or any averaged profile) represents the average flow profile across the vessel and may be lower than the instantaneous peak flow represented in individual phase pixels.
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These time-averaged flow profiles were then averaged across all embryos for one experimental condition.
The average flow velocity of the last profile can be estimated by f_{t} = frac{r(t) - r(t)}{Delta t}, (22 where (Delta t) is the motion period of the last profile and the surfacing time is assumed to be contained in the period.
For horizontal flow, profiles are obtained for average flow velocities of 2.0, 3.0, and 3.5 m/s.
Reduction of the electroosmotic mobility is most pronounced in the 27 nm channel with κ 1 = 30 nm for 0.1 mM NaCl, where double layer overlap results in a parabolic flow profile with a reduced average mobility compared to the flat-flow profile in microchannels with a higher average mobility.
The prediction of the shear stress distribution and flow profile characteristics were within an average error of about ±10%.
According to a previous study, the maximum velocity of the baffle flow profile at 4.1 years on average after the completion of a total cavo-pulmonary connection (TCPC) ranged from 35 to 45 cm/s [1].
The peak flow may therefore be rather similar in the 2,000 μm and the 1,000 μm vessels, but due to the shape of the flow profile this corresponds to a lower average flow velocity in the 1,000 μm vessel.
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