This paper is based on work supported by the National Health Research Institutes (NHRI) in Taiwan under the Innovative Research Grant (IRG) (EX105-10523EI), the Taiwan Ministry of Science and Technology (MOST 103-2221-E-001-001-MY2, 104-2221-E-001-015-MY3, 105-2221-E-001-002-MY2), the Academia Sinica Thematic Project (AS-105-TP-A06), and the Research Program in Nanoscience and Nanotechnology. The authors would like to thank Ms. Rachel A. Lucas for proofreading the manuscript.

1. Fabrication of the Microfluidic Device
NOTE: The entire microfluidic device is fabricated using the soft lithography replica molding process13.
<ol>
	<li>Fabrication of molds for the PDMS layers in the microfluidic device
	<ol>
		<li>Design the microfluidic channel patterns using commercially available illustration or drawing software. Submit the file to a company for high-resolution transparency photomask printing14.</li>
		<li>Clean silicon wafers with acetone (&#8805;99.5%), isopropyl alcohol (IPA; &#8805;99.9%), and buffered oxide etch (BOE; 6:1 NH4F.HF). Rinse with deionized (DI) water and dehydrate the wafer with a nitrogen gun.</li>
		<li>Spin coat approximate 20 g of negative tone photoresist, SU-8 2050, onto the wafers at 500 rpm for 15 sec and then 2,000 rpm for 30 sec. 
		&#8203;NOTE: The spin coating condition should yield SU-8 2050 photoresist layers with a thickness of approximately 75 &#181;m on the wafers after optical lithography.</li>
		<li>Soft bake the wafers on a 65 &#176;C hotplate for 3 min and then at 95 &#176;C for 9 min. After the soft bake, expose the wafers using a mask aligner with the designed transparency masks under UV light; the total exposure energy should be about 300 mJ/cm2. Post-exposure bake (PEB) the wafers at 65 &#176;C for 2 min and then at 95 &#176;C for 7 min.</li>
		<li>After the PEB, immerse the wafers in SU-8 developer with strong agitation or in an ultrasonic bath (37 kHz and 180 W effective ultrasonic power) for 7 min. Rinse the wafer with acetone and IPA to remove the residual SU-8.</li>
		<li>Place the wafer and 100 &#181;l of silane (1H,1H,2H,2H-perfluorooctyltrichlorosilane) into a 6 cm diameter Petri dish in a desiccator connected with a diaphragm vacuum pump for wafer surface silanization in order to prevent undesired bonding. Turn on the pump for 15 min, turn it off, and seal the desiccator with a vacuum for 30 min.</li>
		<li>Take the silanized wafers out of the desiccator and tape them to 15 cm diameter Petri dishes for the following soft lithography process:</li>
	</ol>
	</li>
	<li>Fabrication and assembly of PDMS layers
	<ol>
		<li>Preparation of the PDMS pre-polymer
		<ol>
			<li>Mix PDMS monomer (base) and the curing agent at a 10:1 ratio (v/v). Degas the mixture in the desiccator setup for 60 min.</li>
		</ol>
		</li>
		<li>Fabrication of the PC-embedded top layer
		<ol>
			<li>Transfer 2 g of the PDMS pre-polymer onto the mold with the top-layer fluidic channel patterns to make a thin layer of PDMS. Place the mold in the desiccator setup to degas the PDMS for 60 min.</li>
			<li>Place the mold overnight in a 60 &#176;C oven for PDMS curing. Make sure that the mold is on a horizontal plane.</li>
			<li>Cool down the mold to room temperature. Pour an additional 13 g of PDMS pre-polymer onto the mold and degas the PDMS in the desiccator setup for 60 min.</li>
			<li>Slowly embed a 1 mm thick PC film into the fresh PDMS layer as a gas diffusion barrier; expel any bubbles if needed.</li>
			<li>Put the mold overnight in the 60 &#176;C oven, and make sure that it is on a horizontal plane.</li>
			<li>Cool down the cured PDMS to room temperature. Cut the device with a scalpel to an area of approximately 5.5 x 5 cm2, which can cover all channel patterns, and peel off the PDMS slab from the mold.</li>
			<li>Punch holes for inlets and outlets using a 2 mm-diameter biopsy punch. Store the fabricated top PDMS-PC layer away from ambient dust for later assembly.</li>
		</ol>
		</li>
		<li>Fabrication of the bottom PDMS layer
		<ol>
			<li>Pour 11 g of the PDMS pre-polymer onto the mold for the bottom layer. Place the mold in the desiccator to degas the PDMS for 60 min. Keep the mold overnight in a 60 &#176;C oven to cure the PDMS. Make sure that it is lying on a horizontal plane.</li>
			<li>Cool down the PDMS to room temperature. Cut the device to an area of approximately 5.5 x 5 cm2, which can cover all channel patterns, and peel it off of the mold. Store the fabricated bottom PDMS layer away from ambient dust for later assembly.</li>
		</ol>
		</li>
		<li>Fabrication of the PDMS membrane
		<ol>
			<li>Spin coat approximate 4 g of PDMS pre-polymer onto a silanized blank wafer at 100 rpm for 90 sec and then 3,000 rpm for 4 sec. Bake the spin-coated wafer in a 60 &#176;C oven overnight.</li>
		</ol>
		</li>
		<li>Assembly of the device
		<ol>
			<li>Place the fabricated PDMS-PC top layer and the wafer with the spin-coated PDMS membrane in an O2 plasma surface treatment machine with the bonding surfaces facing up. Treat the PDMS surfaces with 90 W of O2 plasma for 40 sec.</li>
			<li>Bond the top layer onto the PDMS membrane right after the O2 plasma surface treatment. Place a weight (about 600 g) on top of the bonded layers and put them in a 60 &#176;C oven overnight to promote bonding.</li>
			<li>Cool down the bonded layers to room temperature and cut the membrane bonded to the top layer with a scalpel to an area of approximately 5.5 x 5 cm2, which can cover all channel patterns. Peel off the bonded structure from the silicon wafer and punch holes at the inlets and outlet of the chemical gradient channel using a 2 mm-diameter biopsy punch.</li>
			<li>Place the membrane-bonded top layer and the fabricated PDMS bottom layer in the O2 plasma surface treatment machine, with the bonding surfaces facing up, to activate the PDMS surfaces using the plasma at 90 W for 40 sec.</li>
			<li>Attach the top and bottom layers together for bonding immediately after the surface treatment. Place a weight (about 600 g) on top of the entire bonded device and put it in a 60 &#176;C oven overnight.</li>
			<li>Take the entire fabricated device out of the oven and cool it down to room temperature.</li>
		</ol>
		</li>
	</ol>
	</li>
</ol>
2. Microfluidic Cell Migration Assay
NOTE: In this paper, we use a commonly used cell line, adenocarcinomic human alveolar basal epithelial cell (A549), and a chemokine, stromal cell derived factor (SDF-1&#945;), as examples. For researchers working on other cells and chemokines, please adjust the experimental processes accordingly.
<ol>
	<li>Day 0: Cell preparation
	<ol>
		<li>Culture the stock of A549 cells in complete growth medium containing DMEM F12 L-glutamine substitute, 10% (v/v) fetal bovine serum (FBS), and 1% (v/v) antimicrob-antimycotic solution. Sub-culture by dissociation with 0.25% trypsin-EDTA.</li>
		<li>Prepare cell suspensions for the experiments by centrifuging dissociated cells at 140 x g for 3 min at room temperature. For the microfluidic device experiments, count the cells using a hemocytometer and seed at least 1 x 106 cells in a T75 flask with 10 ml of complete growth medium. 
		&#8203;NOTE: All cell culture processes are performed in an incubator with a 37 &#176;C and 5% CO2 atmosphere.</li>
	</ol>
	</li>
	<li>Day 1: Device preparation
	<ol>
		<li>Place the device into the O2 plasma machine and treat it with O2 plasma at 90 W for 40 sec to render the microfluidic channel surfaces hydrophilic.</li>
		<li>Immediately after the surface treatment, install two 14 G blunt needles by directly inserting the needles into the 2 mm diameter holes punched into the PDMS layer at the chemical gradient channel inlets. Make sure that the needles do not block the microfluidic channels. Draw 0.8 ml of ddH2O using a 1 ml syringe with a blunt 14 G needle. Inject the ddH2O into the chemical gradient channel from the outlet until the water flows out from both needles at the inlets.</li>
		<li>Prepare 1 ml of 50 &#181;g/ml fibronectin solution by diluting fibronectin stock with Dulbecco&#39;s Phosphate-Buffered Saline (DPBS).</li>
		<li>Infuse the fibronectin solution from the outlet of the chemical gradient channel using a 1 ml syringe with a blunt 14 G needle until the solution flows out from both needles at the inlets.</li>
		<li>Incubate the entire device overnight in a conventional cell culture incubator.</li>
	</ol>
	</li>
	<li>Day 2: Cell seeding and microscopy imaging
	<ol>
		<li>Cell seeding
		<ol>
			<li>Aspirate the medium from the cells that were cultured since day 0 and wash the cells with 5 ml of DPBS 2 times. Aspirate the DPBS, add 2 ml of trypsin-EDTA, and incubate the cells in the incubator for 5 min to detach the cells from the flask surface.</li>
			<li>Wait until the cells are detached and suspended in the solution and add 8 ml of serum-free medium (DMEM F12 + 1% (v/v) antimicrob-antimycotic solution) to the flask. Transfer all of the liquid into a 15 ml conical tube and centrifuge it at 140 x g for 5 min under room temperature.</li>
			<li>Aspirate the supernatant after centrifuging and add an appropriate amount of the serum-free medium to make the final cell density 1 x 106 cells/ml. Take out the microfluidic device prepared on Day 1. Count the cells using a hemocytometer or another automatic cell counting instrument.</li>
			<li>Inject serum-free medium from the outlet of the chemical gradient channel using a 1 ml syringe with a blunt 14 G needle until the medium flows out from both needles at the inlets. Inject 200 &#181;l of the cell suspension from the outlet of the chemical gradient channel.</li>
			<li>Observe the cell culture chamber in the device under a microscope to confirm that the cells have been introduced to the microfluidic channel. Place the device into a humid container (e.g., a plastic box with ddH2O inside) and keep it in a cell culture incubator for 5 hr to promote the adhesion of the cells onto the device surface.</li>
		</ol>
		</li>
		<li>Preparation of reagents for chemical gradient generation
		<ol>
			<li>Prepare the chemical (SDF-1&#945;) at the desired concentration (100 ng/ml) in serum-free medium. Draw the serum-free medium with and without the chemical into two separate 3 ml syringes connected to high-purity tubing. Set up the syringes on a syringe pump with a flow rate of 1 &#181;l/min for later use.</li>
		</ol>
		</li>
		<li>Preparation of the reagents for oxygen gradient generation
		<ol>
			<li>Make 15 ml of 1 M NaOH solution and 15 ml of 200 mg/ml pyrogallol solution. Draw the NaOH and pyrogallol solutions into two separate 15 ml syringes connected to high-purity PTFE tubing and high-purity tubing, respectively. Set up the syringes on a syringe pump with flow rate of 5 &#181;l/min for later use.</li>
		</ol>
		</li>
		<li>Microfluidic device setup
		<ol>
			<li>After the 5 hr incubation, take the entire device out and place it on a 15 cm diameter Petri dish. Fix the device in the Petri dish using adhesive putty. Transfer the Petri dish to a live cell imaging microscope in an incubator.</li>
			<li>Connect the tubing from the syringes for the chemical gradient generation to the inlets of the chemical gradient channel. Connect the outlet to tubing leading to a waste reservoir. Turn on the syringe pump with the syringes for chemical gradient generation.</li>
			<li>Connect the high-purity tubing from the syringes containing NaOH and pyrogallol to the inlets of the oxygen gradient channel. Connect tubing to the outlet to collect the waste. Turn on the syringe pump with the syringes for oxygen gradient generation.</li>
			<li>Add about 15 ml of ddH2O to the Petri dish to keep the device moisturized. Set up the live cell imaging microscope for time-lapsed image capture, and take an image every 15 min.</li>
		</ol>
		</li>
	</ol>
	</li>
	<li>Day 3: Data collection and analysis
	<ol>
		<li>Transfer the captured image files to a computer. Analyze the images using an open source image analysis software, ImageJ, with an open source plugin for Manual Tracking (https://imagej.nih.gov/ij/plugins/track/track.html) and a free Chemotaxis Tool software (http://ibidi.com/xtproducts/en/Software-and-Image-Analysis/Manual-Image-Analysis/Chemotaxis-and-Migration-Tool)15,16.</li>
	</ol>
	</li>
</ol>
3. Characterization of the Gradients
NOTE: The chemical and oxygen gradients can be characterized before or after the cell experiments.
<ol>
	<li>Numerical simulation of the chemical gradient
	<ol>
		<li>Estimate the laminar flow nature of microfluidics using computational fluidic dynamics (CFD) simulation.</li>
	</ol>
	</li>
	<li>Experimental characterization of the oxygen gradient
	<ol>
		<li>Prepare an oxygen-sensitive fluorescent dye, tris(2,2&#8242;-bipyridyl) ruthenium(III) chloride hexahydrate, solution in water at a concentration of 5 mg/ml.</li>
		<li>Draw the oxygen-sensitive dye solution into two separate 3 ml syringes connected to high-purity tubing. Set up the syringes on a syringe pump with flow rate of 1 &#181;l/min (identical to the flow rates used for the chemical gradient generation).</li>
		<li>Connect the tubing from the syringes to the inlets of the chemical gradient channel. Connect the outlet to tubing leading to a waste reservoir. Turn on the syringe pump with the syringes for chemical gradient generation.</li>
		<li>Measure the fluorescence intensity using an inverted fluorescence microscope with the excitation light passing through a 470 &#177; 20 nm optical filter. Collect the emission light through a 515 nm long-pass emission filter using a cool CCD camera.</li>
		<li>Connect the high-purity tubing from the syringes containing NaOH and pyrogallol to the inlets of the oxygen gradient channel. Connect tubing to the outlet to collect the waste. Turn on the syringe pump with the syringes for oxygen gradient generation.</li>
		<li>Collect the fluorescence images of the oxygen-sensitive dye flowing in the cell culture chamber.</li>
		<li>Stop the flow for oxygen gradient generation and disconnect all the tubing to the oxygen generation channel. Connect high-purity tubing from the gas cylinders to the outlet of the oxygen gradient channel.</li>
		<li>Collect the fluorescence images of the oxygen-sensitive dye flowing in the cell culture chamber when flowing air, pure nitrogen, and pure oxygen into the tubing connected to the oxygen gradient channel.</li>
		<li>Estimate the oxygen gradients by analyzing the fluorescence images using the Stern-Volmer equation according to References 10 and 11.</li>
	</ol>
	</li>
</ol>

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The authors declare that they have no competing financial interests.

The most critical steps to fabricate the PDMS microfluidic device with an embedded PC thin film are: (1) expelling all the bubbles when inserting the PC film into the PDMS pre-polymer while fabricating the PDMS-PC top layer and (2) making sure all the PDMS curing processes are performed on a well-leveled horizontal plane. For cell migration experiments, the most critical steps are: (1) eliminating the bubbles within the microfluidic device, tubing, and syringe pumps during the experiments; (2) ensuring that the microfluidic device is placed on a well-leveled horizontal plane during live cell imaging for the cell migration observation; and (3) keeping the device moisturized by adding ddH2O to the Petri dish during the experiments and making sure that the water is not dried out.
In order to successfully fabricate the PDMS-PC hybrid microfluidic device without delamination, it is critical to remove all bubbles during the PC film insertion. The PC film can be slowly inserted from an angle (about 15 to 30 degrees away from the PDMS pre-polymer surface) to prevent bubbles generation during the insertion of the PC film into the PDMS pre-polymer. If necessary, the entire PDMS pre-polymer with the embedded PC film can be placed in the desiccator connected to the vacuum pump for 10 min to expel the trapped bubbles. If the PC film floats up after the vacuum process, a pipette tip can be used to press the PC film down onto the cured PDMS layer. Repeat the vacuum and press processes if necessary.
For the cell experiments, a lack of air bubbles is critical for the microfluidic cell culture. Make sure that no air bubbles are introduced into the entire microfluidic setup (including syringe pumps, tubing, and the microfluidic device) when making connections. If air bubbles are created within the microfluidic setup due to the decrease of gas solubility under the elevated temperature of the experiments inside the incubator, all the experimental components (including the syringes and tubing) and reagents (including the growth medium, pyrogallol, and NaOH) can be placed into the incubator beforehand (at least 20 min prior to usage) to minimize the temperature variation. Syringe pumps often generate heat from the operation of the motors within the pumps. It is usually acceptable to operate syringe pumps inside incubators; however, do check the incubator temperature during the experiments. If the temperature elevates during the experiments, additional cooling procedures need to be carried out. Several feasible cooling methods can be employed, such as placing a box of ice into the incubator, reducing the number of syringe pumps placed inside the incubator, or using an incubator with a force cooling system.
The PDMS-PC microfluidic cell culture device developed in this paper is capable of reliably generating perpendicular chemical and oxygen gradients for cell migration studies. The limitation of the developed device is that the generated oxygen gradient profiles depend on the balance between oxygen flux, driven by chemical reaction scavenging, and oxygen diffusion from the ambient atmosphere, through the device, and into the medium. As a result, the oxygen gradient profiles cannot be arbitrarily controlled inside the device. Compared to existing microfluidic cell culture platforms, the device developed in this paper is the first one capable of performing cell culture studies under combinations of chemical and oxygen gradients. The entire device can be fabricated using the conventional soft lithography replica molding process, without tedious alignment and expensive instrumentation. The gradients can be numerically simulated and experimentally characterized to provide more physiological microenvironment-like conditions for in vitro cell studies. By using a spatially confined chemical reaction method with a PC film as a gas diffusion barrier, the oxygen gradient can be generated without using pressurized gas cylinders and sophisticated gas flow control units. In addition, the setup requires only small amounts of chemicals (less than 10 ml per day) to maintain the oxygen gradients. Since the oxygen tension control is confined locally around the microfluidic channel, and does not disturb the ambient oxygen concentration, the entire setup can be placed inside a conventional cell culture incubator without additional temperature, humidity, and CO2 control instrumentation. As a result, the developed device has great potential to be practically used in biological labs.
Due to technical limitations, cellular behaviors under oxygen tensions have seldom been studied in the existing literature. With the help of the device developed in this paper, cell culture under oxygen gradients can be performed in a facile manner that greatly promotes cell studies under oxygen gradients. Furthermore, a similar operation principle can be applied to generate other physiologically relevant gaseous gradients, such as carbon dioxide and nitric oxide, for in vitro cell culture studies17. These capabilities demonstrate that the PDMS-PC microfluidic device shows great potential for various cell culture applications, including drug testing and cell proliferation and migration assays, to advance in vitro cell culture studies.

The spatial distribution of soluble factors and oxygen tension can regulate a number of important cellular functions in vivo1,2,3,4. In order to better investigate their effect on cells, an in vitro cell culture platform capable of stably generating chemical and oxygen gradients is highly desired. Various soluble factors play key roles in biological activities and affect cellular behavior. Recently, due to the advancement of microfluidic techniques, a number of microfluidic devices capable of stably generating chemical gradients have been developed to study cell migration5. Furthermore, several studies have also revealed the necessity of oxygen tension for in vitro cell cultures6,7,8. However, the control of oxygen tension for cell culture mainly relies on direct chemical addition for oxygen scavenging or cell incubators with pressurized gas cylinders. Direct chemical addition alters the cell culture medium and affects the cellular responses. Oxygen control incubators require special incubator design, precise gas flow control, and a large volume of nitrogen gas in order to achieve hypoxia conditions. Moreover, it is infeasible to control the spatial distribution of oxygen using this setup, which retards the cellular behavior study under various oxygen tensions and gradients. To overcome these limitations, a number of microfluidic devices have been developed to generate oxygen gradients for cell culture applications9. However, most of them are operated using pressurized gases, which may cause evaporation and bubble generation problems. Therefore, they often require sophisticated instrumentation and may not be reliable for long-term cell culture studies.
To overcome the challenges and to further study the interactions between chemical and oxygen gradients for cell migration, we developed a microfluidic cell culture device made of polydimethylsiloxane (PDMS) with an embedded polycarbonate (PC) thin film10. The device is composed of two microfluidic channel layers separated by a PDMS membrane. The top layer is a PDMS-PC layer for oxygen gradient generation; the bottom layer is made of PDMS for chemical gradient generation and cell culture. The device can simultaneously generate perpendicular chemical and oxygen gradients without using gas cylinders and sophisticated flow control systems. In the device, PDMS provides great optical transparency, gas permeability, and biological compatibility for cell culture and imaging. The embedded PC film serves as a gas diffusion barrier for efficient oxygen tension control. In the microfluidic channel, we used a series of serpentine-shaped channels to generate chemical gradients. The design has been broadly exploited to generate chemical gradients in microfluidic devices for various applications due to its reliability and easy experimental setup. Furthermore, the chemical gradient profiles can be designed by varying the channel geometries beforehand with numerical simulation. For oxygen gradient generation, we took advantage of the spatially confined chemical reaction method that was previously developed in our lab10,11,12. The oxygen can be scavenged from the designated areas without nitrogen purging. For practical usage in biological labs, the entire experimental setup is compatible with conventional cell culture incubators. By integrating these methods, we can simultaneously generate stable chemical and oxygen gradients without bulk gas cylinders and sophisticated instrumentation in order to study cell migration.

<table><tbody><tr><td>1 ml Syringe</td><td>Becton-Dickinson, Franklin Lakes, NJ</td><td>302104</td><td></td></tr><tr><td>1.5 ml Microcentrifuge Tube</td><td>Smartgene</td><td>6011-000</td><td></td></tr><tr><td>10 ml Syringe</td><td>Becton-Dickinson, Franklin Lakes, NJ</td><td>302151</td><td></td></tr><tr><td>15 ml Centrifuge Tube</td><td>ThermoFisher Scientific,Waltham, MA</td><td>Falcon 352096</td><td></td></tr><tr><td>150 mm Petri dish</td><td>Dogger Science</td><td>DP-43151</td><td></td></tr><tr><td>1H,1H,2H,2H-Perfluorooctyltrichlorosilane</td><td>Alfa Aesar, Ward Hill, MA</td><td>78560-45-9</td><td></td></tr><tr><td>3 ml Syringe</td><td>Becton-Dickinson, Franklin Lakes, NJ</td><td>302118</td><td></td></tr><tr><td>4&#039;&#039; Silicon Dummy Wafer</td><td>Wollemi Technical, Taoyuan, Taiwan</td><td></td><td></td></tr><tr><td>Acetone</td><td>ECHO Chemical, Miaoli, Taiwan</td><td>AH3102-000000-72EC</td><td></td></tr><tr><td>AG Double Expose Mask Aligner</td><td>M&amp;amp;R Nano Technology, Taoyuan, Taiwan</td><td>AG500-4D-D-V-S-H</td><td></td></tr><tr><td>Antibiotic-Antimyotic solution</td><td>ThermoFisher Scientific,Waltham, MA</td><td>GIBCO 15240-062</td><td></td></tr><tr><td>Biopsy punch</td><td>Miltex, Plainsboro, NJ</td><td>33-31</td><td></td></tr><tr><td>Blunt needle</td><td>JensenGlobal, Santa Barbara, CA</td><td>Gauge 14</td><td></td></tr><tr><td>Bright-Line Hemocytometer</td><td>Sigma-Aldrich, St. Louis, MO</td><td>Z359629</td><td>for cell counting</td></tr><tr><td>Buffered Oxide Etch</td><td>ECHO Chemical, Miaoli, Taiwan</td><td>PH3101-000000-72EC</td><td></td></tr><tr><td>Cell Culture Incubator</td><td>Caron, Marietta, OH</td><td>6016-1</td><td></td></tr><tr><td>COMSOL Multiphysics</td><td>COMSOL, Burlington, MA</td><td>Ver. 4.3b</td><td>for numerical simulation of chemical gradients in the device</td></tr><tr><td>D-PBS</td><td>ThermoFisher Scientific,Waltham, MA</td><td>GIBCO 14190-144</td><td></td></tr><tr><td>Desicattor</td><td>A-VAC Industries, Anaheim, CA</td><td>35.10001.01</td><td></td></tr><tr><td>DMEM/F12+GlutaMax-1</td><td>ThermoFisher Scientific,Waltham, MA</td><td>GIBCO 10565-018</td><td></td></tr><tr><td>Fetal Bovine Serum</td><td>ThermoFisher Scientific,Waltham, MA</td><td>GIBCO 10082</td><td></td></tr><tr><td>Fibronectin from Human Plasma</td><td>Sigma-Aldrich, St. Louis, MO</td><td>F2006</td><td></td></tr><tr><td>Inverted Fluorescence Microscope</td><td>Leica Microsystems, Wetzlar, Germany</td><td>DMIL LED</td><td></td></tr><tr><td>Isopropyl Alcohol (IPA)</td><td>ECHO Chemical, Miaoli, Taiwan</td><td>CMOS112-00000-72EC</td><td></td></tr><tr><td>JuLi Smart Fluorescence Cell Imager</td><td>NanoEnTek, Seoul, Korea</td><td>DBJ01B</td><td></td></tr><tr><td>Mechanical Convention Oven</td><td>ThermoFisher Scientific,Waltham, MA</td><td>Lindberg Blue M MO1450C</td><td></td></tr><tr><td>NaOH</td><td>Showa Chemical Industry, Tokyo, Japan</td><td>1943-0150</td><td></td></tr><tr><td>Plasma tretment system</td><td>Nordson MARCH, Concord CA</td><td>PX-250</td><td>for oxygen plasma surface treatment</td></tr><tr><td>Polycarbonate (PC) film</td><td>Quantum Beam Technologies, Tainan Taiwan</td><td></td><td></td></tr><tr><td>Polydimehtylsiloxane (PDMS)</td><td>Dow Corning, Midland, MI</td><td>SYLGARD 184</td><td></td></tr><tr><td>Pyrogallol</td><td>Alfa Aesar, Ward Hill, MA</td><td>A13405</td><td></td></tr><tr><td>Removable Adhesive Putty</td><td>3M</td><td>860</td><td></td></tr><tr><td>Sorvall Legend Mach 1.6R Tabletop Centrifuge</td><td>ThermoFisher Scientific,Waltham, MA</td><td></td><td></td></tr><tr><td>Spin Coater</td><td>ELS Technology, Hsinchu, Taiwan</td><td>ELS 306MA</td><td></td></tr><tr><td>SU-8 2050</td><td>MicroChem, Westborough, MA</td><td>SU-8 2050</td><td></td></tr><tr><td>SU-8 Developer</td><td>MicroChem, Westborough, MA</td><td>Y020100</td><td></td></tr><tr><td>Surgical blade</td><td>Feather, Osaka, Japan</td><td>5005093</td><td>for PDMS cutting</td></tr><tr><td>Syringe Pump</td><td>Chemyx, Houston, TX</td><td>Fusion 400</td><td></td></tr><tr><td>T75 Cell Culture Flask</td><td>ThermoFisher Scientific,Waltham, MA</td><td>Nunc 156367</td><td></td></tr><tr><td>Trypan Blue Solution, 0.4%</td><td>ThermoFisher Scientific,Waltham, MA</td><td>15250061</td><td></td></tr><tr><td>Trypsin-EDTA</td><td>ThermoFisher Scientific,Waltham, MA</td><td>GIBCO 25200</td><td></td></tr><tr><td>Tygon PTFE Tubing</td><td>Saint-Gobain Performance Plastics, Akron, OH</td><td></td><td></td></tr><tr><td>Tygon Tubing</td><td>Saint-Gobain Performance Plastics, Akron, OH</td><td>621</td><td></td></tr></tbody></table>

polydimethylsiloxane-polycarbonate microfluidic devices for cell migration studies under perpendicular chemical and oxygen gradients

This paper reports a microfluidic device made of polydimethylsiloxane (PDMS) with an embedded polycarbonate (PC) thin film to study cell migration under combinations of chemical and oxygen gradients. Both chemical and oxygen gradients can greatly affect cell migration in vivo; however, due to technical limitations, very little research has been performed to investigate their effects in vitro. The device developed in this research takes advantage of a series of serpentine-shaped channels to generate the desired chemical gradients and exploits a spatially confined chemical reaction method for oxygen gradient generation. The directions of the chemical and oxygen gradients are perpendicular to each other to enable straightforward migration result interpretation. In order to efficiently generate the oxygen gradients with minimal chemical consumption, the embedded PC thin film is utilized as a gas diffusion barrier. The developed microfluidic device can be actuated by syringe pumps and placed into a conventional cell incubator during cell migration experiments to allow for setup simplification and optimized cell culture conditions. In cell experiments, we used the device to study migrations of adenocarcinomic human alveolar basal epithelial cells, A549, under combinations of chemokine (stromal cell-derived factor, SDF-1&#945;) and oxygen gradients. The experimental results show that the device can stably generate perpendicular chemokine and oxygen gradients and is compatible with cells. The migration study results indicate that oxygen gradients may play an essential role in guiding cell migration, and cellular behavior under combinations of gradients cannot be predicted from those under single gradients. The device provides a powerful and practical tool for researchers to study interactions between chemical and oxygen gradients in cell culture, which can promote better cell migration studies in more in vivo-like microenvironments.

Fabricated PDMS-PC hybrid microfluidic cell culture device. Fig. 1 shows a photo and an illustration of the microfluidic device. The bottom layer contains four levels of serpentine-shaped channels to generate solutions from reagents introduced from two separated inlets with six different mixing ratios. Theoretically, the six different mixing ratios are 1:0, 4:1, 3:2, 2:3, 1:4, and 0:1 (left:right) between the two solutions introduced from the inlets. The chemical gradients constructed by the six different mixing-ratio solutions can be generated in the cell culture chamber, located downstream. The top and bottom layers are separated by a PDMS membrane. In the top layer, the reagents for the oxygen scavenging chemical reaction are introduced into the microfluidic channel from two separate inlets. The reagents are mixed with each other for the reaction immediately before flowing on top of the cell culture chamber to scavenge the oxygen from the bottom channel, without direct chemical contact. The embedded PC film, with a smaller gas diffusion coefficient compared to PDMS, acts as a diffusion barrier that makes oxygen scavenging more efficient. Oxygen gradually diffuses back to the cell culture chamber through the PDMS in the downstream area to form an oxygen gradient along the flow direction. Since the oxygen scavenging chemical reaction is spatially confined, only local oxygen tensions are affected. As a result, the device can be utilized in a conventional cell incubator without altering its global oxygen tension. In the migration experiments, cells are seeded inside the cell culture chamber for observation. The growth medium and chemical reagents are introduced to the device using syringe pumps with precisely controlled flow rates.
Characterization of chemical and oxygen gradients generated inside the device. Due to the laminar flow nature of microfluidics, flow behaviors can be predicted using computational fluidic dynamics (CFD) simulation. In this paper, we constructed a 3D model and performed the simulation using a commercially available multiphysics modeling software. Fig. 2(a) shows a comparison between experimentally characterized fluorescein concentration profiles across the width of the cell culture chamber based on fluorescence intensity measurements and the numerical simulation results. The agreement between the experimental and simulation results suggests that the CFD model can well estimate the chemical gradients generated inside the device. Fig. 2(b) plots the simulated SDF-1&#945; gradient generated in the cell culture chamber. Fig. 3 shows the oxygen gradient characterization results by flowing the oxygen-sensitive fluorescence dye inside the cell culture chamber before the cell experiments. The result indicates that an oxygen gradient, ranging from about 1 to 16%, can be established using the aforementioned protocol.
Cell migration results. As a demonstration, we performed A549 cell migration studies under 4 combinations of chemokine (SDF-1&#945;) and oxygen gradients: (1) no chemokine and no oxygen gradients as a control, (2) with a chemokine gradient and without an oxygen gradient, (3) with an oxygen gradient and without a chemokine gradient, and (4) with both chemokine and oxygen gradients. Fig. 4 shows the photo of the entire experimental setup. The experiments were all performed in a conventional cell culture incubator with the entire setup (including the microfluidic devices, syringe pumps, and live cell imaging microscopes) placed inside it. The cell migration results are shown in Fig. 5. Fig. 5(a) shows the images collected during the experiments using the live cell imaging analyzer, and Fig. 5(b) and (c) plots the cell migration trajectories and average movements under the four combinations analyzed by the ImageJ software with the plugins. The results show that the average cell migration distance in the control approaches zero, which suggests random movement of the cells in the experiment. In contrast, with only the chemokine gradient, the average movement of the cells is towards the left, where the SDF-1&#945; concentration is higher. The results suggest the SDF-1&#945; chemotaxis behavior of A549 cells, which has been previously reported. In the experiment with only oxygen gradients, the average movement of the cells is upwards, where the oxygen tension is lower. More interestingly, in the experiment with perpendicular chemokine and oxygen gradients, the average movement of the cells is upwards and without any obvious movement in the horizontal direction (chemokine gradient direction).
<img alt="Figure 2" src="/files/ftp_upload/55292/55292fig1.jpg" /> 
Figure 1: Fabricated PDMS-PC microfluidic cell culture device. (a) The experimental photo of the fabricated device capable of reliably generating perpendicular chemical and oxygen gradients for cell migration studies. The chemical gradient channel is filled with blue and yellow food dyes to demonstrate the gradient generation inside the cell culture chamber. The oxygen gradient channel is filled with red food dye. The scale bar is 1 cm. (b) The schematic of the microfluidic device. The top layer is fabricated using PDMS with an embedded PC layer as a gas diffusion barrier for efficient oxygen gradient control inside the cell culture chamber. (c) The master molds for the fabrication of the top and bottom layers. <a href="http://cloudflare.jove.com/files/ftp_upload/55292/55292fig1large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" src="/files/ftp_upload/55292/55292fig2.jpg" /> 
Figure 2: Chemical gradient inside the microfluidic cell culture device. (a) Numerically simulated and experimentally characterized fluorescein concentration gradient inside the cell culture chamber across the width of the cell culture chamber (Y direction). The similarity between the simulated and experimentally measured gradients indicates that the simulation can well predict the chemical gradient. The figure inset shows the three-dimensional (3D) model constructed for the simulation. (b) Numerical simulation result of the SDF-1&#945; chemokine gradient across the width of the cell culture chamber for cell migration studies. <a href="http://cloudflare.jove.com/files/ftp_upload/55292/55292fig2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" src="/files/ftp_upload/55292/55292fig3.jpg" /> 
Figure 3: Oxygen gradient inside the microfluidic cell culture device. Experimentally measured oxygen gradients within the cell culture chamber along the flow direction. The gradients were estimated using the oxygen-sensitive fluorescence dye and image analysis. The gradients, from left to right of the chamber, are characterized, and the results show consistent gradient profiles across the width of the chamber.
<img alt="Figure 4" src="/files/ftp_upload/55292/55292fig4.jpg" /> 
Figure 4: Photos of the experimental setup. The entire setup, including microfluidic devices, syringe pumps, and a live cell imaging microscope, is placed inside a conventional cell culture incubator for optimized cell culture conditions during the experiments. <a href="http://cloudflare.jove.com/files/ftp_upload/55292/55292fig4large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 5" src="/files/ftp_upload/55292/55292fig5.jpg" /> 
Figure 5: Cell migration study results under perpendicular SDF-1&#945;&#8203; and oxygen gradients. (a) Images captured before and after the 12-h cell migration study. The cell migration paths can be analyzed from the captured time-lapsed images using the live cell imaging microscope. (b) The cell migration paths and the analyzed average migration movement from the captured images under 4 different gradient combinations: no gradient, only chemokine gradient, only oxygen gradient, and both chemokine and oxygen gradients. The images were captured every 15 min. The scale bar is 250 &#181;m. (c) Plots of the average cell migration distances in the perpendicular (oxygen gradient) and horizontal (chemokine gradient) directions under four different gradient combinations. The data are expressed as the mean &#177; SD, obtained from three independent experimental sets, and 10 cells were analyzed in each experiment. The statistical significantly different (unpaired Student&#39;s t-test, p &#60; 0.01) results are designated by different letters (a and b). <a href="http://cloudflare.jove.com/files/ftp_upload/55292/55292fig5large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>

Watch this Scientific Journal Video about Polydimethylsiloxane-polycarbonate Microfluidic Devices for Cell Migration Studies Under Perpendicular Chemical and Oxygen Gradients at JoVE.com

Polydimethylsiloxane-polycarbonate Microfluidic Devices for Cell Migration Studies Under Perpendicular Chemical and Oxygen Gradients

The control of chemical and oxygen gradients is essential for cell cultures. This paper reports a polydimethylsiloxane-polycarbonate (PDMS-PC) microfluidic device capable of reliably generating combinations of chemical and oxygen gradients for cell migration studies, which can be practically utilized in biological labs without sophisticated instrumentation.

This paper reports a microfluidic device made of polydimethylsiloxane (PDMS) with an embedded polycarbonate (PC) thin film to study cell migration under ...

polydimethylsiloxane-polycarbonate-microfluidic-devices-for-cell

Universidad de Cartagena UDEC

Research

JoVE Journal

Bioengineering

14.1K Views.  Academia Sinica. The control of chemical and oxygen gradients is essential for cell cultures. This paper reports a polydimethylsiloxane-polycarbonate (PDMS-PC) microfluidic device capable of reliably generating combinations of chemical and oxygen gradients for cell migration studies, which can be practically utilized in biological labs without sophisticated instrumentation.

Video: Polydimethylsiloxane-polycarbonate Microfluidic Devices for Cell Migration Studies Under Perpendicular Chemical and Oxygen Gradients

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 &mu;m 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&deg;C, 5% CO2). Therefore, this microfluidic device incorporated with microgrooved substrates could be useful for studying the cellular behavior and performing high-throughput drug screening.

We describe a protocol for the fabrication of microfluidic devices that can enable cell capture and culture. In this approach patterned microstructures such as grooves within microfluidic channels are used to create low shear stress regions within which cell can dock.

We describe a microfluidic device with microgrooved patterns for studying cellular behavior.  This microfluidic platform consists of a top fluidic channel ...

Biology

A Gradient-generating Microfluidic Device for Cell Biology

 The fabrication and operation of a gradient-generating microfluidic device for studying cellular behavior is described.  A microfluidic platform is an enabling experimental tool, because it can precisely manipulate fluid flows, enable high-throughput experiments, and generate stable soluble concentration gradients.  Compared to conventional gradient generators, poly(dimethylsiloxane) (PDMS)-based  microfluidic devices can generate stable concentration gradients of growth factors with well-defined profiles.  Here, we developed simple gradient-generating microfluidic devices with three separate inlets.  Three microchannels combined into one microchannel to generate concentration gradients.  The stability and shape of growth factor gradients were confirmed by fluorescein isothyiocyanate (FITC)-dextran with a molecular weight similar to epidermal growth factor (EGF).  Using this microfluidic device, we demonstrated that fibroblasts exposed to concentration gradients of EGF migrated toward higher concentrations.  The directional orientation of cell migration and motility of migrating cells were quantitatively assessed by cell tracking analysis.  Thus, this gradient-generating microfluidic device might be useful for studying and analyzing the behavior of migrating cells.

We describe a protocol for the microfabrication of the gradient-generating microfluidic device that can generate spatial and temporal gradients in well-defined microenvironment. In this approach, the gradient-generating microfluidic device can be used to study directed cell migration, embryogenesis, wound healing, and cancer metastasis.

 The fabrication and operation of a gradient-generating microfluidic device for studying cellular behavior is described.  A microfluidic platform is an ...

Evaluation of Cancer Stem Cell Migration Using Compartmentalizing Microfluidic Devices and Live Cell Imaging

In the last 40 years, the United States invested over 200 billion dollars on cancer research, resulting in only a 5% decrease in death rate. A major obstacle for improving patient outcomes is the poor understanding of mechanisms underlying cellular migration associated with aggressive cancer cell invasion, metastasis and therapeutic resistance1. Glioblastoma Multiforme (GBM), the most prevalent primary malignant adult brain tumor2, exemplifies this difficulty. Despite standard surgery, radiation and chemotherapies, patient median survival is only fifteen months, due to aggressive GBM infiltration into adjacent brain and rapid cancer recurrence2. The interactions of aberrant cell migratory mechanisms and the tumor microenvironment likely differentiate cancer from normal cells3. Therefore, improving therapeutic approaches for GBM require a better understanding of cancer cell migration mechanisms. Recent work suggests that a small subpopulation of cells within GBM, the brain tumor stem cell (BTSC), may be responsible for therapeutic resistance and recurrence. Mechanisms underlying BTSC migratory capacity are only starting to be characterized1,4.
Due to a limitation in visual inspection and geometrical manipulation, conventional migration assays5 are restricted to quantifying overall cell populations. In contrast, microfluidic devices permit single cell analysis because of compatibility with modern microscopy and control over micro-environment6-9.
We present a method for detailed characterization of BTSC migration using compartmentalizing microfluidic devices. These PDMS-made devices cast the tissue culture environment into three connected compartments: seeding chamber, receiving chamber and bridging microchannels. We tailored the device such that both chambers hold sufficient media to support viable BTSC for 4-5 days without media exchange. Highly mobile BTSCs initially introduced into the seeding chamber are isolated after migration though bridging microchannels to the parallel receiving chamber. This migration simulates cancer cellular spread through the interstitial spaces of the brain. The phase live images of cell morphology during migration are recorded over several days. Highly migratory BTSC can therefore be isolated, recultured, and analyzed further. 
Compartmentalizing microfluidics can be a versatile platform to study the migratory behavior of BTSCs and other cancer stem cells. By combining gradient generators, fluid handling, micro-electrodes and other microfluidic modules, these devices can also be used for drug screening and disease diagnosis6. Isolation of an aggressive subpopulation of migratory cells will enable studies of underlying molecular mechanisms.

A compartmentalizing microfluidic device for investigating cancer stem cell migration is described. This novel platform creates a viable cellular microenvironment and enables microscopic visualization of live cell locomotion. Highly motile cancer cells are isolated to study molecular mechanisms of aggressive infiltration, potentially leading to more effective future therapies.

In the last 40 years, the United States invested over 200 billion dollars on cancer research, resulting in only a 5% decrease in death rate. A major ...

Medicine

Creating Adhesive and Soluble Gradients for Imaging Cell Migration with Fluorescence Microscopy

Cells can sense and migrate towards higher concentrations of adhesive cues such as the glycoproteins of the extracellular matrix and soluble cues such as growth factors. Here, we outline a method to create opposing gradients of adhesive and soluble cues in a microfluidic chamber, which is compatible with live cell imaging. A copolymer of poly-L-lysine and polyethylene glycol (PLL-PEG) is employed to passivate glass coverslips and prevent non-specific adsorption of biomolecules and cells. Next, microcontact printing or dip pen lithography are used to create tracks of streptavidin on the passivated surfaces to serve as anchoring points for the biotinylated peptide arginine-glycine-aspartic acid (RGD) as the adhesive cue. A microfluidic device is placed onto the modified surface and used to create the gradient of adhesive cues (100% RGD to 0% RGD) on the streptavidin tracks. Finally, the same microfluidic device is used to create a gradient of a chemoattractant such as fetal bovine serum (FBS), as the soluble cue in the opposite direction of the gradient of adhesive cues.

A method for the assembly of adhesive and soluble gradients in a microscopy chamber for live cell migration studies is described. The engineered environment combines antifouling surfaces and adhesive tracks with solution gradients and therefore allows one to determine the relative importance of guidance cues.

Cells can sense and migrate towards higher concentrations of adhesive cues such as the glycoproteins of the extracellular matrix and soluble cues such as ...

Study of Cell Migration in Microfabricated Channels

The method described here allows the study of cell migration under confinement in one dimension. It is based on the use of microfabricated channels, which impose a polarized phenotype to cells by physical constraints. Once inside channels, cells have only two possibilities: move forward or backward. This simplified migration in which directionality is restricted facilitates the automatic tracking of cells and the extraction of quantitative parameters to describe cell movement. These parameters include cell velocity, changes in direction, and pauses during motion. Microchannels are also compatible with the use of fluorescent markers and are therefore suitable to study localization of intracellular organelles and structures during cell migration at high resolution. Finally, the surface of the channels can be functionalized with different substrates, allowing the control of the adhesive properties of the channels or the study of haptotaxis. In summary, the system here described is intended to analyze the migration of large cell numbers in conditions in which both the geometry and the biochemical nature of the environment are controlled, facilitating the normalization and reproducibility of independent experiments.

A quantitative method to study spontaneous migration of cells in a one-dimensional confined microenvironment is described. This method takes advantage of microfabricated channels and can be used to study migration of large number of cells under different conditions in single experiments.

The method described here allows the study of cell migration under confinement in one dimension. It is based on the use of microfabricated channels, which ...

A Microfluidic Technique to Probe Cell Deformability

Here we detail the design, fabrication, and use of a microfluidic device to evaluate the deformability of a large number of individual cells in an efficient manner. Typically, data for ~102 cells can be acquired within a 1 hr experiment. An automated image analysis program enables efficient post-experiment analysis of image data, enabling processing to be complete within a few hours. Our device geometry is unique in that cells must deform through a series of micron-scale constrictions, thereby enabling the initial deformation and time-dependent relaxation of individual cells to be assayed. The applicability of this method to human promyelocytic leukemia (HL-60) cells is demonstrated. Driving cells to deform through micron-scale constrictions using pressure-driven flow, we observe that human promyelocytic (HL-60) cells momentarily occlude the first constriction for a median time of 9.3 msec before passaging more quickly through the subsequent constrictions with a median transit time of 4.0 msec per constriction. By contrast, all-trans retinoic acid-treated (neutrophil-type) HL-60 cells occlude the first constriction for only 4.3 msec before passaging through the subsequent constrictions with a median transit time of 3.3 msec. This method can provide insight into the viscoelastic nature of cells, and ultimately reveal the molecular origins of this behavior.

We demonstrate a microfluidics-based assay to measure the timescale for cells to transit through a sequence of micron-scale constrictions.

Here we detail the design, fabrication, and use of a microfluidic device to evaluate the deformability of a large number of individual cells in an ...

Designing Microfluidic Devices for Studying Cellular Responses Under Single or Coexisting Chemical/Electrical/Shear Stress Stimuli

Microfluidic devices are capable of creating a precise and controllable cellular micro-environment of pH, temperature, salt concentration, and other physical or chemical stimuli. They have been commonly used for in vitro cell studies by providing in vivo like surroundings. Especially, how cells response to chemical gradients, electrical fields, and shear stresses has drawn many interests since these phenomena are important in understanding cellular properties and functions. These microfluidic chips can be made of glass substrates, silicon wafers, polydimethylsiloxane (PDMS) polymers, polymethylmethacrylate (PMMA) substrates, or polyethyleneterephthalate (PET) substrates. Out of these materials, PMMA substrates are cheap and can be easily processed using laser ablation and writing. Although a few microfluidic devices have been designed and fabricated for generating multiple, coexisting chemical and electrical stimuli, none of them was considered efficient enough in reducing experimental repeats, particular for screening purposes. In this report, we describe our design and fabrication of two PMMA-based microfluidic chips for investigating cellular responses, in the production of reactive oxygen species and the migration, under single or coexisting chemical/electrical/shear stress stimuli. The first chip generates five relative concentrations of 0, 1/8, 1/2, 7/8, and 1 in the culture regions, together with a shear stress gradient produced inside each of these areas. The second chip generates the same relative concentrations, but with five different electric field strengths created within each culture area. These devices not only provide cells with a precise, controllable micro-environment but also greatly increase the experimental throughput.

Micro-fabricated devices integrated with fluidic components provide an in vitro platform for cell studies mimicking the in vivo micro-environment. We developed polymethylmethacrylate-based microfluidic chips for studying cellular responses under single or coexisting chemical/electrical/shear stress stimuli.

Microfluidic devices are capable of creating a precise and controllable cellular micro-environment of pH, temperature, salt concentration, and other ...

A Microfluidic Device for Quantifying Bacterial Chemotaxis in Stable Concentration Gradients

Chemotaxis allows bacteria to approach sources of attractant chemicals or to avoid sources of repellent chemicals. Bacteria constantly monitor the concentration of specific chemoeffectors by comparing the current concentration to the concentration detected a few seconds earlier. This comparison determines the net direction of movement. Although multiple, competing gradients often coexist in nature, conventional approaches for investigating bacterial chemotaxis are suboptimal for quantifying migration in response to concentration gradients of attractants and repellents. Here, we describe the development of a microfluidic chemotaxis model for presenting precise and stable concentration gradients of chemoeffectors to bacteria and quantitatively investigating their response to the applied gradient. The device is versatile in that concentration gradients of any desired absolute concentration and gradient strength can be easily generated by diffusive mixing. The device is demonstrated using the response of Escherichia coli RP437 to gradients of amino acids and nickel ions.

This protocol describes the development of a microfluidic device for investigating bacterial chemotaxis in stable concentration gradients of chemoeffectors.

Chemotaxis allows bacteria to approach sources of attractant chemicals or to avoid sources of repellent chemicals. Bacteria constantly monitor the ...

Traction Microscopy Integrated with Microfluidics for Chemotactic Collective Migration

Cells change migration patterns in response to chemical stimuli, including the gradients of the stimuli. Cellular migration in the direction of a chemical gradient, known as chemotaxis, plays an important role in development, the immune response, wound healing, and cancer metastasis. While chemotaxis modulates the migration of single cells as well as collections of cells in vivo, in vitro research focuses on single-cell chemotaxis, partly due to the lack of the proper experimental tools. To fill that gap, described here is a unique experimental system that combines microfluidics and micropatterning to demonstrate the effects of chemical gradients on collective cell migration. Furthermore, traction microscopy and monolayer stress microscopy are incorporated into the system to characterize changes in cellular force on the substrate as well as between neighboring cells. As proof-of-concept, the migration of micropatterned circular islands of Madin-Darby canine kidney (MDCK) cells is tested under a gradient of hepatocyte growth factor (HGF), a known scattering factor. It is found that cells located near the higher concentration of HGF migrate faster than those on the opposite side within a cell island. Within the same island, cellular traction is similar on both sides, but intercellular stress is much lower on the side of higher HGF concentration. This novel experimental system can provide new opportunities to studying the mechanics of chemotactic migration by cellular collectives.

Collective cell migration in development, wound healing, and cancer metastasis is often guided by the gradients of growth factors or signaling molecules. Described here is an experimental system combining traction microscopy with a microfluidic system and a demonstration of how to quantify the mechanics of collective migration under biochemical gradient.

Cells change migration patterns in response to chemical stimuli, including the gradients of the stimuli. Cellular migration in the direction of a chemical ...

A Microphysiological System to Study Leukocyte-Endothelial Cell Interaction during Inflammation

Leukocyte-endothelial cell interactions play an important role in inflammatory diseases such as sepsis. During inflammation, excessive migration of activated leukocytes across the vascular endothelium into key organs can lead to organ failure. A physiologically relevant biomimetic microfluidic assay (bMFA) has been developed and validated using several experimental and computational techniques, which can reproduce the entire leukocyte rolling/adhesion/migration cascade to study leukocyte-endothelial cell interactions. Microvascular networks obtained from in vivo images in rodents were digitized using a Geographic Information System (GIS) approach and microfabricated with polydimethylsiloxane (PDMS) on a microscope slide. To study the effect of shear rate and vascular topology on leukocyte-endothelial cell interactions, a Computational Fluid Dynamics (CFD) model was developed to generate a corresponding map of shear rates and velocities throughout the network. The bMFA enables the quantification of leukocyte-endothelial cells interactions, including rolling velocity, number of adhered leukocytes in response to different shear rates, number of migrated leukocytes, endothelial cell permeability, adhesion molecule expression and other important variables. Furthermore, by using human-related samples, such as human endothelial cells and leukocytes, bMFA provides a tool for rapid screening of potential therapeutics to increase their clinical translatability.

In this protocol, a biomimetic microfluid assay, which can reproduce a physiologically relevant microvascular environment and reproduce the entire leukocyte adhesion/migration cascade, is employed to study leukocyte-endothelial cell interactions in inflammatory disease.

Leukocyte-endothelial cell interactions play an important role in inflammatory diseases such as sepsis. During inflammation, excessive migration of ...