Glenn M. Walker

Microenvironment design considerations for cellular scale studies

In vivo cellular microenvironments are not well-mimicked in present in vitro cell culture systems. Microtechnology, and microfluidics in particular, provides the tools to create in vivo-like cellular microenvironments in vitro. Features of in vitro cellular microenvironments are discussed and compared to macroscale cell culture environments; the concept of an effective culture volume (ECV) is introduced to facilitate the comparison. Current research using microtechnology to investigate in vitro cellular microenvironments is presented and areas where more research is needed in characterizing the in vitro microenvironment are outlined.

A passive pumping method for microfluidic devices

The surface energy present in a small drop of liquid is used to pump the liquid through a microchannel. The flow rate is determined by the volume of the drop present on the pumping port of the microchannel. A flow rate of 1.25 microL s(-1) is demonstrated using 0.5 microL drops of water. Two other fluid manipulations are demonstrated using the passive pumping method: pumping liquid to a higher gravitational potential energy and creating a plug within a microchannel.

Microfluidic aqueous two phase system for leukocyte concentration from whole blood

Leukocytes from a whole blood sample were concentrated using a microfluidic aqueous two phase system (μATPS). Whole blood was simultaneously exposed to polyethylene glycol (PEG) and dextran (Dex) phase streams and cells were partitioned based on their differential affinity for the streams. The laminar flow characteristic of microfluidic devices was used to create zero, one, and two stable interfaces between the polymer streams. Three different patterns of three polymer streams each were evaluated for their effectiveness in concentrating leukocytes: immiscible PEG-PEG-Dex, immiscible Dex-PEG-Dex, and miscible PEG-PBS-Dex. The most effective configuration was the Dex-PEG-Dex stream pattern which on average increased the ratio of leukocytes to erythrocytes by a factor of 9.13 over unconcentrated blood.

A linear dilution microfluidic device for cytotoxicity assays

A two-layer polymer microfluidic device is presented which creates nine linear dilutions from two input fluid streams mixed in varying volumetric proportions. The linearity of the nine dilutions is conserved when the flow rate is held constant at 1.0 microl min(-1) (R(2) = 0.9995) and when it is varied from 0.5-16 microl min(-1) (R(2) = 0.9998). An analytical expression is presented for designing microfluidic devices with arbitrary numbers of linear dilutions. To demonstrate the efficacy of this device, primary human epidermal keratinocytes (HEK) were stained with nine dilutions of calcein, resulting in a linear spread of fluorescent intensities (R(2) = 0.94). The operating principles of the device can be scaled up to incorporate any number of linear dilutions. This scalability, coupled with an intrinsic ability to create linear dilutions under a variety of operating conditions, makes the device applicable to high throughput screening applications such as combinatorial chemistry or cytotoxicity assays.

An evaporation-based microfluidic sample concentration method

We present a method for sample concentration within microfluidic devices using evaporation-induced flow. Evaporation-induced flow is easy to incorporate into microfluidic designs and can be used to concentrate a wide variety of molecules. The practicality of this method was demonstrated with 0.2 microm fluorescent spheres and FITC-labeled BSA. Thirty two percent of the 0.6 microL fluorescent sphere suspension was concentrated into a well within a microfluidic device. In the same amount of time, 93% of the 0.6 microL FITC-labeled BSA solution was concentrated.

Insect Cell Culture in Microfluidic Channels

Microfluidic channels were constructed out of polydimethylsiloxane (PDMS) and used as culture vessels for ovary cells from the fall armyworm, Spodoptera frugiperda, (Sf9). PDMS allows cells to be visually inspected and provides excellent permeability to oxygen and carbon dioxide. Cells were grown in static culture conditions and observed every 24 hours for seven days. The growth rate in microchannels of varying volume (2.8 μl to 0.6 μl) was significantly slower in two sets of experiments (P<0.05 and P<0.001) than in a 25 ml tissue culture flask.

The IL sequence in the LLKIL motif in CXCR2 is required for full ligand induced activation of ERK, AKT and chemotaxis in HL60 cells

The chemotaxis of differentiated HL60 cells stably expressing CXCR2 was examined in a microfluidic gradient device where the steepness of the CXCL8 chemokine gradient was varied from 2 pg/ml/μm (0-1 ng/ml over a width of 500 μm) to 50 pg/ml/μm (0-25 ng/ml over 500 μm). The differentiated HL60 cells stably expressing CXCR2 exhibited little chemotaxis in response to a 0-1 ng/ml gradient, but displayed an increasing chemotactic response as the gradient steepness increased from 0 to 5, 0 to 10, and 0 to 25 ng/ml, demonstrating that steepness of gradient is a major determinant of the relative ability of cells to persistently migrate up a chemotactic gradient. When HL60 cells expressed CXCR2 mutated in the C terminus LLKIL motif (IL to AA), ligand-induced internalization of receptors was reduced 50%, whereas cell migration along the gradient of CXCL8 was completely lost. Although both mutant and wild-type receptors could mediate Akt and Erk activation in response to CXCL8, the level of activation of these two kinases was much lower in the cell line expressing the mutant receptors. These data imply that the IL amino acid residues in the LLKIL motif are very important for activation of the signal transduction cascade, which is necessary for cells to sense the chemokine gradient and respond with chemotaxis. Moreover, because mutation of the IL residues in the LLKIL motif resulted in only 50% reduction in receptor internalization, and a 50% reduction in Akt and Erk phosphorylation, but a complete loss of chemotactic response, the data imply that IL amino acid residues in the LLKIL motif are key either for amplification or oscillation of crucial signaling events or for establishment of a threshold for signals required for chemotaxis.

Microneedles Integrated with Pancreatic Cells and Synthetic Glucose-Signal Amplifiers for Smart Insulin Delivery

An innovative microneedle (MN)-based cell therapy is developed for glucose-responsive regulation of the insulin secretion from exogenous pancreatic β-cells without implantation. One MN patch can quickly reduce the blood-sugar levels (BGLs) of chemically induced type-1 diabetic mice and stabilize BGLs at a reduced level for over 10 h.

Point-of-care diagnostics for niche applications.

Point-of-care or point-of-use diagnostics are analytical devices that provide clinically relevant information without the need for a core clinical laboratory. In this review we define point-of-care diagnostics as portable versions of assays performed in a traditional clinical chemistry laboratory. This review discusses five areas relevant to human and animal health where increased attention could produce significant impact: veterinary medicine, space travel, sports medicine, emergency medicine, and operating room efficiency. For each of these areas, clinical need, available commercial products, and ongoing research into new devices are highlighted.

Microfluidic cytometer for the characterization of cell lysis

Blood cytometry and intercellular analysis typically requires lysis as a preparatory step, which can alter the results of downstream analyses. We fabricated a microfluidic cytometer to characterize erythrocyte lysis kinetics. Forward light scatter from erythrocytes was used for enumeration at specific locations on a microfluidic chip. Diffusive transport coupled with laminar flow was used to control the concentration and exposure time of the lysis reagent Zap-OGLOBIN II to erythrocytes. Standard clinical practice is to expose erythrocytes to lysis reagent for 10 min. Under optimum conditions, we achieved complete erythrocyte lysis of a blood sample in 0.7 s. A maximum lysis reaction rate of 1.55 s(-1) was extrapolated from the data. Lysis began after 0.2 s and could be initiated with a lysis reagent concentration of 1.0% (68.5 mM). An equation that related lysis reagent concentration, [A], to erythrocyte lysis, [B], was determined to be [B] = -0.77[A](0.29)t.