Abstract
The aim of our research was to develop a numerical model of microflows occurring in the culture chambers (CC) of a microfluidic device of our construction for high-throughput drug screening. The incompressible fluid flow model is based on the lattice-Boltzmann equation, with an external body force term approximated by the He-Shan-Doolen scheme and the Bhatnagar-Gross-Krook approximation of the collision operator. The model accuracy was validated by the algebraic solution of the Navier–Stokes equation (NSE) for a fully developed duct flow, as well as experimentally. The mean velocity prediction error for the middle-length cross-section of CC was 1.0%, comparing to the NSE algebraic solution. The mean error of volumetric flow rate prediction was 6.1%, comparing to the experimental results. The analysis of flow hydrodynamics showed that the discrepancies from the plug-flow-like velocity profile are observed close to the inlets only, and do not influence cell cultures in the working area of CC. Within its workspace area, the biochip provides stable and homogeneous fully developed laminar flow conditions, which make the procedures of gradient generation, cell seeding, and cell-staining repeatable and uniform across CC, and weakly dependent on perturbations.
Highlights
Flows in microsystems, to a large degree, are influenced by boundaries, much more than macro-flows
The phenomena are the basis of inertial microfluidic platforms
The channels’ inlets and outlets can play a significant role in forming the flow structure, especially in short and wide channels such as cell culture chambers (CC), but there is a lack of analysis in the literature of such effects
Summary
To a large degree, are influenced by boundaries, much more than macro-flows. It is because of a large surface-to-volume ratio, and due to high-velocity gradients that can be achieved through microchannels, even in the Stokes flow regime (Re 1) at low mean fluid velocities (u < 1 · 10−3 m/s) [1]. In the laminar flow regime, geometry-induced flow patterns are commonly observed and employed, e.g., secondary flow in curved channels (Dean flow) for fluid mixing [4] and particle separation [5], or lateral flow, serpentine flow, pinched flow, multi-orifice flow, etc., for cell sorting [6]. The channels’ inlets and outlets can play a significant role in forming the flow structure, especially in short and wide channels such as cell culture chambers (CC), but there is a lack of analysis in the literature of such effects
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