Microfluidic chips controlled with elastomeric microvalve arrays

Miniaturized microfluidic systems provide simple and effective solutions for low-cost point-of-care diagnostics and high-throughput biomedical assays. Robust flow control and precise fluidic volumes are two critical requirements for these applications. We have developed microfluidic chips featuring elastomeric polydimethylsiloxane (PDMS) microvalve arrays that: 1) need no extra energy source to close the fluidic path, hence the loaded device is highly portable; and 2) allow for microfabricating deep (up to 1 mm) channels with vertical sidewalls and resulting in very precise features.The PDMS microvalves-based devices consist of three layers: a fluidic layer containing fluidic paths and microchambers of various sizes, a control layer containing the microchannels necessary to actuate the fluidic path with microvalves, and a middle thin PDMS membrane that is bound to the control layer. Fluidic layer and control layers are made by replica molding of PDMS from SU-8 photoresist masters, and the thin PDMS membrane is made by spinning PDMS at specified heights. The control layer is bonded to the thin PDMS membrane after oxygen activation of both, and then assembled with the fluidic layer. The microvalves are closed at rest and can be opened by applying negative pressure (e.g., house vacuum). Microvalve closure and opening are automated via solenoid valves controlled by computer software.Here, we demonstrate two microvalve-based microfluidic chips for two different applications. The first chip allows for storing and mixing precise sub-nanoliter volumes of aqueous solutions at various mixing ratios. The second chip allows for computer-controlled perfusion of microfluidic cell cultures.The devices are easy to fabricate and simple to control. Due to the biocompatibility of PDMS, these microchips could have broad applications in miniaturized diagnostic assays as well as basic cell biology studies.     

Sequential Push-Pull Pumping Mechanism for Washing and Evacuation of an Immunoassay Reaction Chamber on a Microfluidic CD Platform

A centrifugal compact disc (CD) microfluidic platform with reservoirs, micro-channels, and valves can be employed for implementing a complete immunoassay. Detection or biosensor chambers are either coated for immuno-interaction or a biosensor chip is inserted in them. On microfluidic CDs featuring such multi-step chemical/biological processes, the biosensor chamber must be repeatedly filled with fluids such as enzymes solutions, buffers, and washing solutions. After each filling step, the biosensor chamber needs to be evacuated by a passive siphoning process to prepare it for the next step in the assay. However, rotational speed dependency and limited space on a CD are two big obstacles to performing such repetitive filling and siphoning steps. In this work, a unique thermo-pneumatic (TP) Push-Pull pumping method is employed to provide a superior alternative biosensor chamber filling and evacuation technique. The proposed technique is demonstrated on two CD designs. The first design features a simple two-step microfluidic process to demonstrate the evacuation technique, while the second design shows the filling and evacuation technique with an example sequence for an actual immunoassay. In addition, the performance of the filling and evacuation technique as a washing step is also evaluated quantitatively and compared to the conventional manual bench top washing method. The two designs and the performance evaluation demonstrate that the technique is simple to implement, reliable, easy to control, and allows for repeated push-pulls and thus filling and emptying of the biosensor chamber. Furthermore, by addressing the issue of rotational speed dependency and limited space concerns in implementing repetitive filling and evacuation steps, this newly introduced technique increases the flexibility of the microfluidic CD platform to perform multi-step biological and chemical processes.     

Darwinian evolution on a chip

Computer control of Darwinian evolution has been demonstrated by propagating a population of RNA enzymes in a microfluidic device. The RNA population was challenged to catalyze the ligation of an oligonucleotide substrate under conditions of progressively lower substrate concentrations. A microchip-based serial dilution circuit automated an exponential growth phase followed by a 10-fold dilution, which was repeated for 500 log-growth iterations. Evolution was observed in real time as the population adapted and achieved progressively faster growth rates over time. The final evolved enzyme contained a set of 11 mutations that conferred a 90-fold improvement in substrate utilization, coinciding with the applied selective pressure. This system reduces evolution to a microfluidic algorithm, allowing the experimenter to observe and manipulate adaptation.     

Nanoliter scale microbioreactor array for quantitative cell biology

A nanoliter scale microbioreactor array was designed for multiplexed quantitative cell biology. An addressable 8 x 8 array of three nanoliter chambers was demonstrated for observing the serum response of HeLa human cancer cells in 64 parallel cultures. The individual culture unit was designed with a "C" shaped ring that effectively decoupled the central cell growth regions from the outer fluid transport channels. The chamber layout mimics physiological tissue conditions by implementing an outer channel for convective "blood" flow that feeds cells through diffusion into the low shear "interstitial" space. The 2 microm opening at the base of the "C" ring established a differential fluidic resistance up to 3 orders of magnitude greater than the fluid transport channel within a single mold microfluidic device. Three-dimensional (3D) finite element simulation were used to predict fluid transport properties based on chamber dimensions and verified experimentally. The microbioreactor array provided a continuous flow culture environment with a Peclet number (0.02) and shear stress (0.01 Pa) that approximated in vivo tissue conditions without limiting mass transport (10 s nutrient turnover). This microfluidic design overcomes the major problems encountered in multiplexing nanoliter culture environments by enabling uniform cell loading, eliminating shear, and pressure stresses on cultured cells, providing stable control of fluidic addressing, and permitting continuous on-chip optical monitoring.     

Applying microfluidics to electrophysiology

Microfluidics can be integrated with standard electrophysiology techniques to allow new experimental modalities. Specifically, the motivation for the microfluidic brain slice device is discussed including how the device docks to standard perfusion chambers and the technique of passive pumping which is used to deliver boluses of neuromodulators to the brain slice. By simplifying the device design, we are able to achieve a practical solution to the current unmet electrophysiology need of applying multiple neuromodulators across multiple regions of the brain slice. This is achieved by substituting the standard coverglass substrate of the perfusion chamber with a thin microfluidic device bonded to the coverglass substrate. This was then attached to the perfusion chamber and small holes connect the open-well of the perfusion chamber to the microfluidic channels buried within the microfluidic substrate. These microfluidic channels are interfaced with ports drilled into the edge of the perfusion chamber to access and deliver stimulants. This project represents how the field of microfluidics is transitioning away from proof-of concept device demonstrations and into practical solutions for unmet experimental and clinical needs.     

A microfluidic device with groove patterns for studying cellular behavior

We describe a microfluidic device with microgrooved patterns for studying cellular behavior. This microfluidic platform consists of a top fluidic channel and a bottom microgrooved substrate. To fabricate the microgrooved channels, a top poly(dimethylsiloxane) (PDMS) mold containing the impression of the microfluidic channels was aligned and bonded to a microgrooved substrate. Using this device, mouse fibroblast cells were immobilized and patterned within microgrooved substrates (25, 50, 75, and 100 microm wide). To study apoptosis in a microfluidic device, media containing hydrogen peroxide, Annexin V, and propidium iodide was perfused into the fluidic channel for 2 hours. We found that cells exposed to the oxidative stress became apoptotic. These apoptotic cells were confirmed by Annexin V that bound to phosphatidylserine at the outer leaflet of the plasma membrane during the apoptosis process. Using this microfluidic device with microgrooved patterns, the apoptosis process was observed in real-time and analyzed by using an inverted microscope containing an incubation chamber (37 degrees C, 5% CO(2)). Therefore, this microfluidic device incorporated with microgrooved substrates could be useful for studying the cellular behavior and performing high-throughput drug screening.     

Micropumps, microvalves, and micromixers within PCR microfluidic chips: Advances and trends

This review surveys the advances of microvalves, micropumps, and micromixers within PCR microfluidic chips over the past ten years. First, the types of microvalves in PCR chips are discussed, including active and passive microvalves. The active microvalves are subdivided into mechanical (thermopneumatic and shape memory alloy), non-mechanical (hydrogel, sol-gel, paraffin, and ice), and external (modular built-in, pneumatic, and non-pneumatic) microvalves. The passive microvalves also include mechanical (in-line polymerized gel and passive plug) and non-mechanical (hydrophobic) microvalves. The review then discusses mechanical (piezoelectric, pneumatic, and thermopneumatic) and non-mechanical (electrokinetic, magnetohydrodynamic, electrochemical, acoustic-wave, surface tension and capillary, and ferrofluidic magnetic) micropumps in PCR chips. Next, different micromixers within PCR chips are presented, including passive (Y/T-type flow, recirculation flow, and drop) and active (electrokinetically-driven, acoustically-driven, magnetohydrodynamical-driven, microvalves/pumps) micromixers. Finally, general discussions on microvalves, micropumps, and micromixers for PCR chips are given. The microvalve/micropump/micromixers allow high levels of PCR chip integration and analytical throughput.     

A Microfluidic Chip for the Versatile Chemical Analysis of Single Cells

We present a microfluidic device that enables the quantitative determination of intracellular biomolecules in multiple single cells in parallel. For this purpose, the cells are passively trapped in the middle of a microchamber. Upon activation of the control layer, the cell is isolated from the surrounding volume in a small chamber. The surrounding volume can then be exchanged without affecting the isolated cell. However, upon short opening and closing of the chamber, the solution in the chamber can be replaced within a few hundred milliseconds. Due to the reversibility of the chambers, the cells can be exposed to different solutions sequentially in a highly controllable fashion, e.g. for incubation, washing, and finally, cell lysis. The tightly sealed microchambers enable the retention of the lysate, minimize and control the dilution after cell lysis. Since lysis and analysis occur at the same location, high sensitivity is retained because no further dilution or loss of the analytes occurs during transport. The microchamber design therefore enables the reliable and reproducible analysis of very small copy numbers of intracellular molecules (attomoles, zeptomoles) released from individual cells. Furthermore, many microchambers can be arranged in an array format, allowing the analysis of many cells at once, given that suitable optical instruments are used for monitoring. We have already used the platform for proof-of-concept studies to analyze intracellular proteins, enzymes, cofactors and second messengers in either relative or absolute quantifiable manner.     

Study of the Chemotactic Response of Multicellular Spheroids in a Microfluidic Device

We report the first application of a microfluidic device to observe chemotactic migration in multicellular spheroids. A microfluidic device was designed comprising a central microchamber and two lateral channels through which reagents can be introduced. Multicellular spheroids were embedded in collagen and introduced to the microchamber. A gradient of fetal bovine serum (FBS) was established across the central chamber by addition of growth media containing serum into one of the lateral channels. We observe that spheroids of oral squamous carcinoma cells OSC–19 invade collectively in the direction of the gradient of FBS. This invasion is more directional and aggressive than that observed for individual cells in the same experimental setup. In contrast to spheroids of OSC–19, U87-MG multicellular spheroids migrate as individual cells. A study of the exposure of spheroids to the chemoattractant shows that the rate of diffusion into the spheroid is slow and thus, the chemoattractant wave engulfs the spheroid before diffusing through it.     

Microfluidic PDMS (polydimethylsiloxane) bioreactor for large-scale culture of hepatocytes

Microfluidics could provide suitable environments for cell culture because of the larger surface-to-volume ratio and fluidic behavior similar to the environments in vivo. Such microfluidic environments are now used to investigate cell-to-cell interactions and behaviors in vitro, emulating situations observed in vivo, for example, microscale blood vessels modeled by microfluidic channels. These emulated situations cannot be realized by conventional technologies. In our previous works, microfluidic channels composed of two PDMS (poly(dimethylsiloxane)) layers were successfully used for Hep G2 cell culture. To achieve physiologically meaningful functions in vitro, a culture with a larger number of cells and higher density must be performed. This will require bioreactors with larger surface areas for cell attachment and sufficient amounts of oxygen and nutrition supply. For those purposes, we fabricated a bioreactor by stacking 10 PDMS layers together, i.e., four cell culture chambers, and a chamber dedicated to the oxygen supply inserted in the middle of the 10-stacked layers. The oxygen supply chamber is separated from the microfluidic channels for the culture medium perfusion by thin 300-microm PDMS walls. The high gas permeability of PDMS allows oxygen supply to the microfluidic channels through the thin walls. On the basis of the measurement of glucose consumption and albumin production, it is shown that cellular activity exhibits a gradual increase and saturation throughout the culture. We clearly observed that in the case of the microfluidic bioreactor for large-scale cultures, the oxygen chamber is indispensable to achieve longer and healthy cultures. In the present bioreactor, the cell density was found to be about 3-4 x 10(7) cells/cm(3), which is in the same order of magnitude as the conventional macroscale bioreactors. Consequently, by stacking single culture chambers and oxygen chambers in between, we could have a scalable method to realize the microfluidic bioreactor for large-scale cultures.     

A Fully Automated Microfluidic Femtosecond Laser Axotomy Platform for Nerve Regeneration Studies in C. elegans

Femtosecond laser nanosurgery has been widely accepted as an axonal injury model, enabling nerve regeneration studies in the small model organism, Caenorhabditis elegans. To overcome the time limitations of manual worm handling techniques, automation and new immobilization technologies must be adopted to improve throughput in these studies. While new microfluidic immobilization techniques have been developed that promise to reduce the time required for axotomies, there is a need for automated procedures to minimize the required amount of human intervention and accelerate the axotomy processes crucial for high-throughput. Here, we report a fully automated microfluidic platform for performing laser axotomies of fluorescently tagged neurons in living Caenorhabditis elegans. The presented automation process reduces the time required to perform axotomies within individual worms to ∼17 s/worm, at least one order of magnitude faster than manual approaches. The full automation is achieved with a unique chip design and an operation sequence that is fully computer controlled and synchronized with efficient and accurate image processing algorithms. The microfluidic device includes a T-shaped architecture and three-dimensional microfluidic interconnects to serially transport, position, and immobilize worms. The image processing algorithms can identify and precisely position axons targeted for ablation. There were no statistically significant differences observed in reconnection probabilities between axotomies carried out with the automated system and those performed manually with anesthetics. The overall success rate of automated axotomies was 67.4±3.2% of the cases (236/350) at an average processing rate of 17.0±2.4 s. This fully automated platform establishes a promising methodology for prospective genome-wide screening of nerve regeneration in C. elegans in a truly high-throughput manner.     

Micro-bioreactors for fed-batch fermentations with integrated online monitoring and microfluidic devices

In this study an array of micro-bioreactors based on the format of 48-well microtiter plates (MTP) is presented. The process parameters pH-value and biomass are monitored online by a combination of different sensors, the biolector measurement technology and conductance measurements. A microfluidic device dispenses two fluids individually into each well for controlling the pH-value of fermentations. The micro-bioreactor consists of four wells and two reservoirs. In each well a polyimide foil with platinum electrodes for conductance measurements is integrated. The microfluidic device is fabricated using softlithographic techniques and utilizes pneumatically actuated microvalves. The device is able to dispense volumes below 5nl. Finally, fermentations of Escherichia coli are carried out in the micro-bioreactor system. During the fermentation, the pH-value is measured optically and the biomass development is monitored by the scattered light signal. Meanwhile, the pH-value is controlled by dispensing sodium hydroxide and phosphoric acid. This micro-bioreactor demonstrates the possibility of online monitored and pH-controlled fermentations in micro-scale. The pH-value in the uncontrolled culture varies within the range of 6.46-8.83 whereas the pH-value in the controlled cultures can be kept within 6.85-7.07. This results in an increase in biomass in the pH-controlled culture compared to the nearly completely inhibited pH-uncontrolled culture.     

Isolation, molecular and functional properties of the C-terminal domain of colicin A

Partial proteolytic digestion of colicin A with bromelain allowed the isolation of a 20-kd fragment. This fragment has been purified to homogeneity and its molecular properties have been studied. The sequence of the 54 N-terminal amino acid residues has been determined by automated Edman degradation. This sequence is identical to that of the predicted amino acid sequence of the 20-kd C-terminal part of the colicin A polypeptide deduced from the nucleotide sequence of the caa gene. This polypeptide can produce channels in phospholipid planar bilayers of the same size as those formed by colicin A. However, the voltage-dependence for opening and closing was drastically altered in the peptide fragment channels. The latter, in contrast to colicin A channels, remained open over a wide range of voltage. Large negative potentials were required to close the peptide fragment channels although opening took place in the same voltage range as for colicin A ionic pores.     

Contoured elastic-membrane microvalves for microfluidic network integration

A contoured elastic-membrane microvalve is presented that enables integrated microfluidic processing at the network level. This method takes advantage of two ideas to improve performance: flexible elastic membranes (which enable high-performance shutoff and reduced footprint), and three-dimensionally contoured valve geometries (which reduce dead volume, improve fluidic priming, and reduce susceptibility to cavitation at high fluid velocities). We describe the use of laser-induced etching for microfluidic manifold fabrication, discuss the nonlinear load-deflection behavior of elastic membranes that can occur below 30 psi, and present flow-rate data for microvalves under inlet pressures of 0-20 psi with zero applied membrane pressure. Valve-closure data for inlet pressures of 0-30 psi are presented for fully assembled microvalve structures. The microvalve structures under test were capable of turning off flows of > 20 microL/s. These flow rates were shown to be limited by inlet and outlet flow resistances and not by the valve structure itself, so that higher maximum flow rate capabilities should be readily achieved.     

Bordered pit structure and vessel wall surface properties. Implications for embolism repair

The idea that embolized xylem vessels can be refilled while adjacent vessels remain under tension is difficult to accept if the cavitated vessels remain hydraulically connected to vessels under tension. A mechanism by which embolized conduits could be hydraulically isolated from adjacent conduits requires the existence of a non-zero contact angle and a flared opening into the bordered pit chamber such that a convex air-water interface forms at the entrance into the pit chamber. We measured the contact angle and pit chamber geometry for six species. The contact angle measured in the vessel lumen ranged between 42 degrees to 55 degrees, whereas the opening into the pit chamber ranged between 144 degrees and 157 degrees. If the surface properties within the pit chamber are similar to those in the lumen, a convex meniscus will form at the flared opening into the pit chamber. The maximum pressure difference between water in the lumen and gas in the pit chamber that could be stabilized by this interface was calculated to be within the range of 0.07 to 0.30 MPa.     

The effect of dilution levels in premixes on micro-ingredient dispersion in animal feeds

A drug, a salt, and a coloured iron-particle tracer were used in experiments to determine the effect of micro-ingredient dilution on the dispersion of micro-ingredients in animal feeds.The drug and tracer materials were introduced into the final feed-batch mixing process at six dilution levels. As a control, the test materials were added into the final batch, undiluted, as supplied by the manufacturers. Premixes were prepared by diluting the drug, iron-particle tracer, vitamins, and trace minerals at one part micro-ingredient to one part diluent (1:1) and, similarly, at dilution ratios of 1:5, 1:10, 1:25 and 1:50. Each dilution was added to a separate batch of a 32% medicated supplement for feedlot cattle. Ten samples of the final feed were drawn from each batch of supplement and assayed for the test materials. A salt was included in the macro-ingredient portion of the formula and assayed to test the efficiency of the final mixer and to study the effect of the dilution level of micro-ingredients on the total mixing process.Results of these experiments do not indicate a significant difference in micro-ingredient or tracer dispersion at any of the six dilution levels. Additionally, no differences were observed in the dispersion of salt in the final blends, regardless of the dilution level.     

Selective bioparticle retention and characterization in a chip‐integrated confocal ultrasonic cavity

We demonstrate selective retention and positioning of cells or other bioparticles by ultrasonic manipulation in a microfluidic expansion chamber during microfluidic perfusion. The chamber is designed as a confocal ultrasonic resonator for maximum confinement of the ultrasonic force field at the chamber center, where the cells are trapped. We investigate the resonant modes in the expansion chamber and its connecting inlet channel by theoretical modeling and experimental verification during no‐flow conditions. Furthermore, by triple‐frequency ultrasonic actuation during continuous microfluidic sample feeding, a set of several manipulation functions performed in series is demonstrated: sample bypass—injection—aggregation and retention—positioning. Finally, we demonstrate transillumination microscopy imaging of ultrasonically trapped COS‐7 cell aggregates. Biotechnol. Bioeng. 2009;103: 323–328. © 2009 Wiley Periodicals, Inc.     

A realistic evaluation of the action of ozone on whole human blood

We have clarified the role of the ozone concentration in relation to the resistance of human erythrocytes in whole human blood or in blood diluted either in saline or in distilled water.

Spectrophotometric data related to haemoglobin were evaluated by exposing samples of fresh human blood directly to ozone doses (ratio 1:1 volume), within the therapeutic range (0.21–1.68 mM) and to one toxic dose (3.36 mM). Furthermore, the same determinations have been carried out after previous dilution of the same blood with either pure water or physiological saline (1 ml blood + 29 ml diluent) followed by ozonation with the above reported ozone doses. Addition of either saline or water implies a dilution of plasma antioxidants and also total haemolysis after water dilution. Particularly the latter case represents a most unphysiological situation because the osmotic shock causes the solubilization of the erythrocytic content. While it is possible to demonstrate that after haemolysis there is an ozone-concentration dependent transformation of some oxyhaemoglobin to methaemoglobin, no such process occurs after ozonation of whole blood.

The results of this study fully confirm our previous data that judicious ozone doses neither damage erythrocytes, nor induce oxidation of intracellular haemoglobin. We hope that our conclusions will definitively clarify the absence of toxicity of ozonetherapy.     

The Microfluidic Probe: Operation and Use for Localized Surface Processing

Microfluidic devices allow assays to be performed using minute amounts of sample and have recently been used to control the microenvironment of cells. Microfluidics is commonly associated with closed microchannels which limit their use to samples that can be introduced, and cultured in the case of cells, within a confined volume. On the other hand, micropipetting system have been used to locally perfuse cells and surfaces, notably using push-pull setups where one pipette acts as source and the other one as sink, but the confinement of the flow is difficult in three dimensions. Furthermore, pipettes are fragile and difficult to position and hence are used in static configuration only.The microfluidic probe (MFP) circumvents the constraints imposed by the construction of closed microfluidic channels and instead of enclosing the sample into the microfluidic system, the microfluidic flow can be directly delivered onto the sample, and scanned across the sample, using the MFP. . The injection and aspiration openings are located within a few tens of micrometers of one another so that a microjet injected into the gap is confined by the hydrodynamic forces of the surrounding liquid and entirely aspirated back into the other opening. The microjet can be flushed across the substrate surface and provides a precise tool for localized deposition/delivery of reagents which can be used over large areas by scanning the probe across the surface. In this video we present the microfluidic probe¹ (MFP). We explain in detail how to assemble the MFP, mount it atop an inverted microscope, and align it relative to the substrate surface, and finally show how to use it to process a substrate surface immersed in a buffer.Open in a separate windowClick here to view.^{(47M, flv)}     

Microfluidic formation of single cell array for parallel analysis of Ca release-activated Ca (CRAC) channel activation and inhibition

High-throughput single cell analysis is required for understanding and predicting the complex stochastic responses of individual cells in changing environments. We have designed a microfluidic device consisting of parallel, independent channels with cell-docking structures for the formation of an array of individual cells. The microfluidic cell array was used to quantify single cell responses and the distribution of response patterns of calcium channels among a population of individual cells. In this device, 15 cell-docking units in each channel were fabricated with each unit containing 5 sandbag structures, such that an array of individual cells was formed in 8 independent channels. Single cell responses to different treatments in different channels were monitored in parallel to study the effects of the specific activator and inhibitor of the Ca²⁺ release-activated Ca²⁺ (CRAC) channels. Multichannel detection was performed to obtain the response patterns of the population of cells within this single cell array. The results demonstrate that it is possible to acquire single cell features in multichannels simultaneously with passive structural control, which provides an opportunity for high-throughput single cell response analysis in a microfluidic chip.