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To enable several on-chip cell handling operations in a fused-silica substrate, small shallow micropores are radially embedded in larger deeper microchannels using an adaptation of single-level isotropic wet etching. By varying the distance between features on the photolithographic mask (mask distance), we can precisely control the overlap between two etch fronts and create a zero-thickness semi-elliptical micropore (e.g.20 µm wide, 6 µm deep). Geometrical models derived from a hemispherical etch front show that micropore width and depth can be expressed as a function of mask distance and etch depth. These models are experimentally validated at different etch depths (25.03 and 29.78 µm) and for different configurations (point-to-point and point-to-edge). Good reproducibility confirms the validity of this approach to fabricate micropores with a desired size. To illustrate the wide range of cell handling operations enabled by micropores, we present three on-chip functionalities: continuous-flow particle concentration, immobilization of single cells, and picoliter droplet generation. (1) Using pressure differentials, particles are concentrated by removing the carrier fluid successively through a series of 44 shunts terminated by 31 µm wide, 5 µm deep micropores. Theoretical values for the concentration factor determined by a flow circuit model in conjunction with finite volume modeling are experimentally validated. (2) Flowing macrophages are individually trapped in 20 µm wide, 6 µm deep micropores by hydrodynamic confinement. The translocation of transcription factor NF-κB into the nucleus upon lipopolysaccharide stimulation is imaged by fluorescence microscopy. (3) Picoliter-sized droplets are generated at a 20 µm wide, 7 µm deep micropore T-junction in an oil stream for the encapsulation of individual E. colibacteria cells. [ABSTRACT FROM AUTHOR]

Towards designing a portable diagnostic device for detecting biological toxins in bodily fluids, we have developed microfluidic chip-based immunoassays that are rapid (< 20 minutes), require minimal sample volume (<10 µL) and have appreciable sensitivity and dynamic range (µM–pM). The microfluidic chip is being integrated with miniaturized electronics, optical elements, fluid-handling components, and data acquisition software to develop a portable, self-contained device. The device is intended for rapid, point-of-care (and, in future, point-of-incident) testing in case of an accidental or intentional exposure/intoxication to biotoxins. Detection of toxins and potential host-response markers is performed using microfluidic electrophoretic immunoassays integrated with sample preconcentration and mixing of analytes with fluorescently labeled antibodies. Preconcentration is enabled by photopolymerizing a thin, nanoporous membrane with a MW cut-off of ∼10 kDa in the sample loading region of the chip. Polymeric gels with larger pores are located adjacent to the size exclusion membrane to perform electrophoretic separation of antibody–analyte complex and excess antibody. Measurement of the ratio of bound and unbound immune-complex using sensitive laser-induced fluorescence detection provides quantitation of analyte in the sample. We have demonstrated electrophoretic immunoassays for the biotoxins ricin, Shiga toxin I, and Staphylococcal enterotoxin B (SEB). With off-chip mixing and no sample preconcentration, the limits of detection (LOD) were 300 pM for SEB, 500 pM for Shiga toxin I, and 20 nM for ricin. With a 10 min on-chip preconcentration, the LOD for SEB is <10 pM. The portable device being developed is readily applicable to detection of proteinaceous biomarkers of many other diseases and is intended to represent the next-generation diagnostic devices capable of rapid and quantitative measurements of multiple analytes simultaneously. [ABSTRACT FROM AUTHOR]