The authors would like to thank the technician Agnes M&#252;ller-Schr&#246;er for her valuable contribution. This work was partly performed at Helmholtz Nanoelectronic Facility (HNF) at Forschungszentrum J&#252;lich GmbH. The authors are grateful for the generous help and support.

1. Wafer Fabrication
<ol>
	<li>Design the microfluidic device containing inlets, outlets, main channels and the PLBRs (Figure 1A) using CAD software.</li>
	<li>The design presented in this protocol (Figure 2) consists of two seeding inlets, a gradient generator for mixing of two different substrates, one outlet, and six arrays of PLBRs. Each array contains 5 PLBRs, resulting in 30 parallel PLBRs inside one microfluidic device.</li>
	<li>Create a lithography photomask containing the desired chip layouts (Figure 1B). The photomask was produced in-house by electron beam writing with submicron resolution. The mask used was composed of a chromium layer on a 5 in2&#160;glass plate. 
	Note: perform all following steps under cleanroom class 100 conditions or better (a process flowchart is shown in Figures 3A and 3B).</li>
	<li>Clean a 4 in&#160;silicon wafer with piranha (10:1 ratio of sulfuric acid and hydrogen peroxide) and hydrofluoric acid for several minutes (Caution: hazardous chemicals). Rinse with deionized (DI) water for approximately 10 sec.</li>
	<li>Dehydrate wafer for 20 min at 200 &#176;C.</li>
	<li>Spin coat 1 &#181;m SU-8 2000.5 photoresist onto the wafer (1st layer) (4 ml resist, spin 10 sec with, v = 500 rpm, and a = 100 rpm/sec, spin 30 sec with v = 1,000 rpm and a = 300 rpm/sec).</li>
	<li>Place the coated wafer on a hotplate at 95 &#176;C to drive off excess solvent (1.5 min at 65 &#176;C, 1.5 min at 95 &#176;C, and 1 min at 65 &#176;C; ideally use two hotplates).</li>
	<li>Insert 1st layer photomask (here the trapping regions of the picoliter reactors) and wafer inside the mask aligner and expose wafer to 350-400 nm (vacuum contact, 64 mJ/cm&#178;, t = 3 sec, I = 7 mW/cm&#178;).</li>
	<li>Perform post exposure bake on a hotplate at 95 &#176;C to initiate the polymerization of SU-8 (1 min at 65 &#176;C, 1 min at 95 &#176;C, and 1 min at 65 &#176;C). Note: after this step the structures in the SU-8 layer can be seen.</li>
	<li>Place the wafer in a SU-8 developer bath for 1 min and transfer the wafer into a second container with fresh SU-8 developer for few seconds.</li>
	<li>Rinse the wafer in isopropanol to remove SU-8 developer and dry wafer using nitrogen flow of wafer spinner.</li>
	<li>Hard bake the wafer for 10 min at 150 &#176;C.</li>
	<li>Spin coat 9 &#181;m SU-8 2010 photoresist onto the wafer (2ndlayer) (dispense 4 ml resist, spin 10 sec with v = 500 rpm, a = 100 rpm/sec, and spin 30 s with v = 4,000 rpm, a = 300 rpm/sec).</li>
	<li>Place the wafer with SU-8 on a hotplate at 95 &#176;C to drive off excess solvent (15 min at 65 &#176;C, 45-60 min at 95 &#176;C, and 10 min at 65 &#176;C). Note: attention has to be paid to wrinkles and bubbles. If the wafer is heated to fast to 95 &#176;C, evaporated solvent may be encapsulated in tiny gas bubbles.</li>
	<li>Insert photomask with the desired layout (here main channels for nutrient supply) and the wafer into the mask aligner and expose to 350-400 nm (hard contact, 64 mJ/cm&#178;, t = 10 sec, I = 7 mW/cm&#178;)</li>
	<li>Perform post exposure bake on a hotplate at 95 &#176;C to finalize the polymerization of SU-8 (5 min at 65 &#176;C, 3:30 min at 95 &#176;C, 3 min at 65 &#176;C). Note: after this step the structures in the SU-8 layer can be seen.</li>
	<li>Place the wafer in a SU-8 developer bath for 45 sec, transfer the wafer into a second container with fresh SU-8 developer and develop for 60 sec.</li>
	<li>Rinse the wafer 20 sec with isopropanol to remove any SU-8 developer residue and dry wafer using pressured nitrogen.</li>
	<li>Finally hard bake the wafer at 150 &#176;C. As a result the final wafer (Figure 1C) is obtained, which will be used as master mold for PDMS molding.</li>
	<li>Perform profilometer measurements (Figure 3C) to validate SU-8 structure heights. Note: inaccuracies in structure height may results in inefficient cell trapping or loss of cells during cultivation.</li>
</ol>
2. Polydimethylsiloxane Chip Fabrication
Note: All following steps should be ideally performed under laminar-flow conditions to prevent dust particles interfering with the fabrication procedure (A&#160;process flowchart is shown in Figure 4).
<ol>
	<li>Prepare a mixture of polydimethylsiloxane (PDMS) base and curing agent in a 10:1 ratio. Mix carefully until a homogenous solution is achieved which looks opaque. Prepare as much as required for the desired layer height (here 3 mm).</li>
	<li>Degas the PDMS mixture for approximately 30 min under slight vacuum until all bubbles have disappeared.</li>
	<li>Prepare molding device (or Petri dish) with appropriate SU-8 wafer and pour the PDMS mixture into it (Figure 1D).</li>
	<li>Bake the PDMS for 3 hr&#160;at 80 &#176;C in the oven.</li>
	<li>Carefully peel off the PDMS slab from the wafer. Cut the slab into single chips using a clean and sharp scalpel.</li>
	<li>Wash the chips in a n-pentane bath for 90 min, followed by two acetone washing baths (90 min each). Dry the chips overnight to remove any solvent residue. Caution: perform the PDMS washing under a fume hood. Note: during the n-pentane wash, monomers and dimers are removed from the cured PDMS and the chip size may temporarily&#160;double during washing procedure.</li>
	<li>Store the microfluidic PDMS chips in close containers until the final experiment.</li>
	<li>Just before the experiment, punch the inlet and outlet holes into the PDMS chip using a needle (or hole-puncher) with a slightly smaller diameter than the connectors that are used to connect tubing with PDMS chip.</li>
	<li>Clean the microfluidic PDMS chip carefully with isopropanol and use scotch tape to remove any dust particles which might stick on the structured PDMS side. Use the scotch tape several times until no particle can be seen on the chip.</li>
	<li>Clean a 170 &#181;m thin glass slide with acetone and isopropanol successively. Finally clean with deionized water and dry with pressurized nitrogen.</li>
	<li>Before plasma-activation, warm up the plasma cleaner and run the plasma for approximately 300 sec. Plasma-oxidize glass slide and PDMS chip (Power 50 W, Time = 25 sec, oxygen flow rate = 20 sccm).</li>
	<li>Align the PDMS and glass chip before bonding. Finally, place the PDMS chip carefully onto the glass slide (Figure 1E). PDMS and glass will bond within seconds. Note: do not push with tweezers onto the top of the PDMS chip during the bonding process. This may lead to so called roof-collapsing of the channels and small structures.</li>
	<li>In order to strengthen the bond, bake the final PDMS-glass chip for 10 sec at 80 &#176;C.</li>
</ol>
3. Preparation of the Bacterial Culture
Note: All cultivations should be prepared in sterile filtered medium to prevent accumulation of undesired particles, which may interfere during cultivation.
<ol>
	<li>Use an agar plate containing the desired organisms (here, C. glutamicum ATCC 13032) and inoculate one colony into 20 ml of fresh BHI medium, incubate overnight (&#8776; 8-14 hr) at 30 &#176;C on a rotary shaker (120 rpm).</li>
	<li>Transfer 10 &#181;l of the preculture into the desired medium (here CGXII21) which will be used during microfluidic cultivation and let the cell grow overnight at 30 &#176;C on a rotary shaker (120 rpm).</li>
	<li>Transfer the desired amount of cell suspension (between 10-500 &#181;l, depending on the start of the experiment) into the desired medium (here CGXII21) which will be used during microfluidic cell cultivation. Note: the best is to use cells from the early logarithmic phase for seeding. For C. glutamicum&#160;culture the best optical density (OD600) for seeding was between 0.5-2.</li>
	<li>Transfer 1 ml of the bacterial culture into a sterile 2 ml tube. Note: this should be done right after the microfluidic PDMS chip was assembled to minimize transfer time between shake flask and microfluidic cultivation. Typically the transfer time is around 15 min&#160;and should be kept as small as possible to prevent impact on metabolism caused by oxygen limitation and temperature changes.</li>
</ol>
4. Experimental Setup
Note: All steps are performed with an inverted microscope.
<ol>
	<li>Start microscope incubator 2 hrs before the experiment to warm-up the system. Note: the microscopy should be equipped with a full-size incubator to control temperature and if desired gas flow. Additional humidity control is not necessary since the chip system is continuously infused with media.</li>
	<li>Open incubator system, select the desired objective and if required add immersion oil onto the objective.</li>
	<li>Mount the chip inside the chip holder. If required fix the glass plate with adhesive tape in order to avoid chip any movement during stage operation.</li>
	<li>Center the sample on the microscope and focus onto the PLBR arrays.</li>
	<li>Connect inlets and outlets with appropriate tubing (Figure 1F). Connect tubing to a waste reservoir. A representative chip can be seen in Figure 4D.</li>
	<li>Insert syringes into pumps and start media flow. Use medium, buffer or if necessary coating solution and rinse the microfluidic channels for approximately 1 hr. Note: coating solution is used to coat channel walls to prevent unspecific cell adhesion.</li>
	<li>For E. coli, 0.1% solution of BSA is used to coat the channel walls. For C. glutamicum no coating is necessary. After the coating procedure flush the chip with medium prior cell seeding.</li>
	<li>Before cell seeding and cultivation, check that no leakage occurs and that the temperature is constant.</li>
</ol>
5. Seeding of Bacterial Cells into the Microfluidic Device
<ol>
	<li>Make sure the desired bacteria solutions are available in appropriate syringes connected to tubing.</li>
	<li>Disconnect buffer or coating solution and connect the cell suspension to the chip. To minimize death volume, undesired air bubbles and to reduce experimental time, change the complete needle as well as tubing, rather than only the syringes.</li>
	<li>Infuse the cell suspension into the channels at a volumetric flow rate of 200 nl/min until most of the PLBRs are filled with the desired amount of cells (Figure 5A). Note: optimal seeding results depend on the bacterial strain, OD600, and growth medium of the preculture. These parameters have to be adapted to increase trapping efficiency and time until a sufficient number of cells are trapped in the reactor structures. For C. glutamicum, typically a cell suspension of OD600 0.5-2 was used; for E. coli&#160;the OD600&#160;was between 0.5-1.</li>
	<li>If only a small number of PLBRs are filled, increase the flow rate to 800-1,200 nl/min.</li>
	<li>Disconnect the cell suspension and connect the growth medium to the chip (Figure 5B). Make sure that no air bubble is introduced during the medium change. Perfuse with fresh growth media at 100 nl/min.</li>
</ol>
6. Time-lapse Imaging
<ol>
	<li>Select specific PLBRs for time-lapse imaging. Typically PLBRs are chosen that contain a single mother cell at the beginning of an experiment. The number of regions of interest that can be investigated in one experiment depends on the desired frame rate and microscopic setup.</li>
	<li>Select an appropriate frame rate depending of number of PLBRs. Make sure that the microscope can handle the desired amount of ROIs in the time lapse interval.</li>
	<li>Choose appropriate filter sets (here YFP). Automatically close the shutter during stage movement and after each time-lapse measurement to prevent chromophore bleaching.</li>
	<li>Configure the time-lapse microscopy sequence and start the experiment.</li>
	<li>After all PLBRs are overgrown, the experiment can be stopped, the microfluidic PDMS chip can be discarded and the experiment can be evaluated.</li>
</ol>
7. Analysis
Note: The following steps or parts of the procedure can be performed manually or by image analysis programs such as ImageJ,&#160;etc.
<ol>
	<li>Determine PLBRs of interest where the cultivation fulfills all desired criteria, e.g.&#160;number of mother cells, position of the mother cells, etc.</li>
	<li>To determine the growth rate of one microcolony count the number of cells in each time frame.</li>
	<li>Calculate the maximum growth rate by plotting time vs. ln (cell number). The slope of the plot represents the growth rate in [1/hr] (see Figure 6).</li>
	<li>Fluorescence data analysis strongly depends on the performed experiment. In this report, an example was chosen to illustrate colony-to-colony and cell-to-cell heterogeneity between different isogenic microcolonies (see Figure 7).</li>
</ol>

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<li>Grunberger, A., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((A+disposable+picolitre+bioreactor+for+cultivation+and+investigation+of+industrially+relevant+bacteria+on+the+single+cell+level%5BTitle%5D)+AND+%22Lab+Chip%22%5BJournal%5D)">A disposable picolitre bioreactor for cultivation and investigation of industrially relevant bacteria on the single cell level.</a> Lab Chip. 12, 2060-2068 (2012).</li>
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</ol>

The authors have nothing to disclose.

We have described the fabrication, experimental setup and related operation procedures of a microfluidic PDMS device containing several (PLBRs) for single-cell analysis of bacteria.
Microfabrication using soft lithography techniques allows fast adjustments of device dimensions for various sizes and bacteria morphologies. Currently we are optimizing the picoliter bioreactor regarding the cultivation of different microbial organisms and cultivation throughput. In order to increase the trapping efficiency, also the reactor geometry is under optimization. Figure 8 shows four new PLBR devices that are currently validated. In all figures the seeding channel was redesigned with regards to width and shape. In practice, this seems to have an effect on the number of cells that are trapped, but needs further investigations. Significant improvements regarding the trapping efficiency were also achieved by the incorporation of additional overflow channels leading to higher convectional flow through the reactor and more cells being trapped. However, at the same time one increases the risk to wash out cells during cultivation.
The device is an interesting alternative to macroscale cultivations that have been used for decades to investigate growth and production processes on single-cell level. However, it has some important requirements: For parallel monitoring of several picoliter bioreactors a high resolution and fully motorized microscopic setup with focus drift compensation is mandatory. In addition an incubation system is needed to maintain the desired cultivation temperature constant throughout the measurements.
We achieve a 95% success rate in device fabrication. Main problems are related to inefficient PDMS-glass bonding, PDMS roof collapse, or fluid leakage (see Table 1 for troubleshooting of most occurring problems). Although the experimental work is done partially under nonsterile conditions, we rarely see contamination during experiments, due the closed fluidic system. PDMS microfluidic devices are optically transparent, therefore, can be used for high resolution in vivo imaging. Although PDMS seems to be perfect for the application, it has a high affinity for hydrophobic molecules, making the use of solvents which are widely used in whole cell biocatalytic processes limited. However, suitable coatings are available to adapt the protocol to these kinds of applications.
The proposed PLBR is well suited for spatio-temporal analysis of cellular and even subcellular events of various kinds of bacteria. A major advantage of the present approach lies in the ability to quantify microcolony growth directly in contrast to conventional methods. Furthermore, the PLBR allows for culturing under defined and constant conditions. Because the system facilitates the use of small amounts of reagents or materials it carries the advantages of being inexpensive, customizable and amenable to high throughput. In traditional methods average values of the whole population are considered when analyzing microbial cultivation. Furthermore, existing methods need manual sampling which can lead to degradation of samples and thus to errors in the measurement. The PLBR offers new perspectives for bioprocess development and population heterogeneity analysis in microbiology. The PLBR is a promising tool for various applications within bioprocess development and could be applied in various fields of research, e.g.&#160;analysis of cell-to-cell heterogeneity, analysis of specific cell clusters within cell-lineages, screening of microbial production strains and real-time investigation of cell phenotypes.

Time-lapse microscopy is a powerful tool for studying living cells in vivo1. Meanwhile commercially available fully automated microscopy platforms including thermally induced focus drift compensation are commonly applied in biological research to study time-dependent phenomena, ranging from cancer and neuron cell research over tissue engineering and dynamic studies with single yeast or bacterial cells2-6.
Typically transparent well plates, agar-pads, or simply microscopy slides are applied to provide cell culture environments during time-lapse imaging7. Even though suitable for certain research, these simple systems have very limited control over environmental conditions and do not allow for more complex perturbations or well defined and fast medium changes. Disposable microfluidic chip devices produced by mass production have been introduced to the market recently but are mostly tailored towards larger eukaryotic cell types4. Although growth can be followed, well defined growth investigations concerning, e.g.&#160;precise cell trapping, colony size, growth direction, and the ability for cell removal are limited. Microfluidic habitats and reactors, in which bacteria cells are cultured in 3D environments have been developed8-10, have drawbacks when dealing with quantitative studies at the single-cell level. While overall population heterogeneity can be analyzed, many cell parameters cannot be determined accurately with single-cell resolution since growth is not restricted to monolayers.
This limitation triggered the development of microsystems enabling the cultivation of cells in well-defined channels and habitats with cells growing in flat monolayers with single cell resolution and especially tight control over media supply and environmental conditions6,11,12.&#160;Few examples of microfluidic systems for the cultivation of bacterial cells have been demonstrated12-14. Bacteria typically exhibit very fast growth rates and require microfluidic structures in the range of few micrometers and below, especially when cell monolayers are desired for microscopy. Keymer et al. demonstrated growth and spreading of E. coli strains in microfabricated landscapes15,16. Since they were interested in population dynamics they did not investigate with single-cell resolution.
We have developed the picoliter bioreactor (PLBR)13, which is currently applied to investigate various biotechnological performance indicators such as growth17 and fluorescence coupled productivity analysis on single-cell level18,19. The present microfluidic device allows environmental reactor control at a defined culture volume of approximately one picoliter and continuous single-cell observation simultaneously. In comparison to open monolayer box systems11,14, where one or two sides are open to the media supply channel, the PLBR allows for controlled trapping and culturing. The design permits long term cultivation of bacteria without the risk of several adjacent colonies forming one large population. Furthermore, the system incorporates cultivation regions of 1 &#181;m height (in the order of the cell diameter) to restrict bacteria growth to cell monolayers. In contrast, the supply channels are 10 fold deeper to minimize hydraulic resistance.
In comparison to miniaturized batch cultivation systems20&#160;the present system allows the cultivation with constant environmental parameters due to continuous media flow. Furthermore, environmental parameters such as medium composition, temperature, flow rates and gas exchange can be easily controlled and changed within seconds. This allows for specific investigations of cellular response to environmental changes concerning for example nutrient availability or stress stimuli. The demand for reduced media volumes, namely in the range of few microliters only, enable researchers to perform novel studies, e.g. the perturbation of cells during time-lapse imaging with supernatant of large-scale experiments unraveling cell response under these specific environmental conditions17. The picoliter bioreactor provides researchers with a robust system that tightly controls biophysical conditions and is operated using high precision syringe pumps and automated bright field and fluorescence microscopy for time-lapse imaging. Here, we report a complete protocol including device design, fabrication, and exemplary applications.

<table><tbody><tr><td>Silicon wafer 100 mm diameter, P/BOR &amp;lt;100&gt;</td><td>Si-MAT, Silicon Materials, Germany</td><td></td><td></td></tr><tr><td>Photoresist SU-8 2000.5</td><td>Micro Resist Technology GmbH, Germany</td><td></td><td></td></tr><tr><td>Photoresist SU-8 2010</td><td>Micro Resist Technology GmbH, Germany</td><td></td><td></td></tr><tr><td>SU-8 Developer mr DEV- 600</td><td>Micro Resist Technology GmbH, Germany</td><td></td><td></td></tr><tr><td>Polydimethylsiloxane (PDMS) Sylgard 184 Silicone Elastomer Kit</td><td>Dow Corning; Farnell GmbH, Germany</td><td></td><td></td></tr><tr><td>Dispensing needles Precision Tips&amp;nbsp; 27 G; ID = 0.2 mm, OD = 0.42 mm</td><td>Nordson EFD Deutschland, Germany</td><td></td><td></td></tr><tr><td>Glass plates D263 T eco, 30 mm x 25 mm x 0.17 mm</td><td>Schott AG, Germany</td><td></td><td></td></tr><tr><td>Hole puncher AKA 5130-B-90</td><td>Harris Uni-Core</td><td></td><td></td></tr><tr><td>Tubing Tygon S-54-HL, ID = 0.25 mm, OD = 0.76 mm</td><td>Saint Gobain; VWR International GmbH, Germany</td><td></td><td></td></tr><tr><td>Disposable Syringes &amp;ndash; Omnifix Spritzen BRAUN Omnifix 40 Duo, 1 ml</td><td>B. Braun Melsungen AG, Germany</td><td>552-183143</td><td></td></tr><tr><td>Syringes, 1 ml sterile glass syringes</td><td>INNOVATIVE LABOR SYSTEME GMBH (ILS), Germany</td><td></td><td></td></tr><tr><td colspan="4">Chemicals</td></tr><tr><td>(NH&lt;sub&gt;4&lt;/sub&gt;)&lt;sub&gt;2&lt;/sub&gt;SO&lt;sub&gt;4&lt;/sub&gt;</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>Urea</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>KH&lt;sub&gt;2&lt;/sub&gt;PO&lt;sub&gt;4&lt;/sub&gt;</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>K&lt;sub&gt;2&lt;/sub&gt;HPO&lt;sub&gt;4&lt;/sub&gt;</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>MgSO&lt;sub&gt;4&lt;/sub&gt;&amp;bull;7H&lt;sub&gt;2&lt;/sub&gt;O</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>MOPS</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>FeSO&lt;sub&gt;4&lt;/sub&gt;&amp;bull;7H&lt;sub&gt;2&lt;/sub&gt;O</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>MnSO&lt;sub&gt;4&lt;/sub&gt;&amp;bull;H&lt;sub&gt;2&lt;/sub&gt;O</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>ZnSO&lt;sub&gt;4&lt;/sub&gt;&amp;bull;7H&lt;sub&gt;2&lt;/sub&gt;O</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>CuSO&lt;sub&gt;4&lt;/sub&gt;</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>NiCl&lt;sub&gt;2&lt;/sub&gt;&amp;bull;6H&lt;sub&gt;2&lt;/sub&gt;O</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>CaCl&lt;sub&gt;2&lt;/sub&gt;</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>Biotin</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>Procatechuic acid</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>Glucose-Monohydrate</td><td>Carl Roth GmbH + Co. KG, Germany</td><td></td><td></td></tr><tr><td>BHI</td><td>Becton, Dickinson</td><td></td><td></td></tr><tr><td colspan="4">Cells</td></tr><tr><td>&lt;em&gt;Corynebacterium glutamicum&lt;/em&gt; ATTC 13032</td><td>DSMZ; Leibniz-Institut DSMZ - Deutsche Sammlung von Mikroorganismen und Zellkulturen GmbH, Germany</td><td></td><td></td></tr><tr><td>&lt;em&gt;Escherichia coli&lt;/em&gt; MG 1655</td><td>DSMZ; Leibniz-Institut DSMZ - Deutsche Sammlung von Mikroorganismen und Zellkulturen GmbH, Germany</td><td></td><td></td></tr><tr><td colspan="4">Equipment</td></tr><tr><td>Wafer Cleaner SSEC 3300</td><td>Solid State Equipment LLC</td><td></td><td></td></tr><tr><td>Spin Coater SPIN150 -NPP</td><td>SPS Europe B.V.</td><td></td><td></td></tr><tr><td>Mask Aligner MA-6</td><td>Karl Suess</td><td></td><td></td></tr><tr><td>Hot Plate HP30A - 2</td><td>Torrey Pines Scientific</td><td></td><td></td></tr><tr><td>Laboratory oven Memmert UN 200</td><td>Memmert</td><td></td><td></td></tr><tr><td>Plasma Cleaner FEMTO</td><td>Diener Electronics, Germany</td><td></td><td></td></tr><tr><td>neMESYS syringe pumps</td><td>Cetoni GmbH, Germany</td><td></td><td></td></tr><tr><td>Magnetic stirrer CB 162</td><td>Stuart</td><td>VWR 442-0304</td><td></td></tr><tr><td>Microscope Nikon Eclipse Ti</td><td>Nikon Microscopy</td><td></td><td></td></tr><tr><td>Microscope incubuator</td><td>Pecon GmbH, Germany</td><td></td><td></td></tr><tr><td>Centrifuge minispin plus &amp;ldquo;black line&amp;rdquo;</td><td>Eppendorf</td><td>9776501</td><td></td></tr><tr><td>Photometer BioPhotometer plus&amp;nbsp;</td><td>Eppendorf</td><td>6132000008</td><td></td></tr><tr><td>Shake flask shaker/incubator 3031</td><td>GFL - Gesellschaft f&amp;uuml;r Labortechnik mbH, Germany</td><td></td><td></td></tr><tr><td>Profilometer, Dektak 150 Stylus Profiler</td><td>Veeco</td><td></td><td></td></tr></tbody></table>

microfluidic picoliter bioreactor for microbial single-cell analysis: fabrication, system setup, and operation

In this protocol the fabrication, experimental setup and basic operation of the recently introduced microfluidic picoliter bioreactor (PLBR) is described in detail. The PLBR can be utilized for the analysis of single bacteria and microcolonies to investigate biotechnological and microbiological related questions concerning, e.g.&#160;cell growth, morphology, stress response, and metabolite or protein production on single-cell level. The device features continuous media flow enabling constant environmental conditions for perturbation studies, but in addition allows fast medium changes as well as oscillating conditions to mimic any desired environmental situation. To fabricate the single use devices, a silicon wafer containing sub micrometer sized SU-8 structures served as the replication mold for rapid polydimethylsiloxane casting. Chips were cut, assembled, connected, and set up onto a high resolution and fully automated microscope suited for time-lapse imaging, a powerful tool for spatio-temporal cell analysis. Here, the biotechnological platform organism Corynebacterium glutamicum&#160;was seeded into the PLBR and cell growth and intracellular fluorescence were followed over several hours unraveling time dependent population heterogeneity on single-cell level, not possible with conventional analysis methods such as flow cytometry. Besides insights into device fabrication, furthermore, the preparation of the preculture, loading, trapping of bacteria, and the PLBR cultivation of single cells and colonies is demonstrated. These devices will add a new dimension in microbiological research to analyze time dependent phenomena of single bacteria under tight environmental control. Due to the simple and relatively short fabrication process the technology can be easily adapted at any microfluidics lab and simply tailored towards specific needs.

Device Fabrication
The microfluidic PLBR system is fabricated by one layer of PDMS bonded onto a thin glass chip suited for high resolution microscopy. The fabrication consists of two main steps: firstly the fabrication of the replication master (Figures 1A, 1B,&#160;and 1C) and secondly the chip fabrication (Figures 1D, 1E, and 1F). According to the protocol, standard photolithographic microfabrication techniques are used to create the master mold. Laboratories without clean room facility can acquire commercially available customized SU-8 master molds. Using repetitive PDMS molding (Figures 1A, 1B, and 1C) hundreds of disposable chips can be produced. PDMS molding and chip assembly can be done in any lab and do not require clean room facilities, however, laminar airflow workplaces are favorable.
The process starts with the design of the microfluidic chip system. Typically CAD software is used to design the microfluidic chip (Figure 1A). After CAD, a mask is generated by an e&#8212;beam writer (Figure 1B) with submicron resolution. In the present study a 5 in&#160;chromium mask was created which was used for the SU-8 wafer lithography. The final silicon&#8212;SU&#8212;8 wafer is used for PDMS molding (Figure 1D). After a baking step the PDMS slab is cut into chips which are irreversibly bonded onto the glass slides (Figure 1E). Finally the tubing is connected (Figure 1F).
Figure 2 shows the design of the microfluidic system in detail. It consists of two seeding inlets, a gradient generator for mixing of different substrates or media and one outlet. The main channels have a dimension of 50 &#181;m x 10 &#181;m (W x H). Each device consists of six arrays of PLBRs, containing 5 PLBRs each. This results in 30 parallelized reactors inside one microfluidic device.
Figure 3&#160;illustrates the replication master production. As described in detail in the protocol, a first SU-8 layer is fabricated by SU-8 lithography (Figure 3A). A similar procedure is applied for the second layer (Figure 3B). To check the channel geometry we investigated the height of the PLBRs and main channels using a profilometer. In the example shown in Figure 3C, the first layer (the cultivation layer) was measured. Here the layer shows a consistent height of 1,200 nm, suitable for the cultivation of C. glutamicum in BHI medium.
Figure 4 illustrates the PDMS molding procedure starting with PDMS mixing (Figure 4A) followed by the molding process (Figure 4B) and finally the bonding step (Figure 4C). Figure 4D shows the final microfluidic chip incorporating the 170 &#181;m thick glass plate, PDMS chip (3 mm in height) with inlets and outlets and steel needles connected to tubing. After the experiment the chip can be disposed and no extensive cleaning is necessary. Furthermore, it is easy to assemble and handle. No complex and difficult filling procedure is necessary.
Device Principle
Figure 5 shows the working principle of the reactor system. Cells are infused into the microfluidic device and individual cells remain trapped inside the PLBR simply by cell-wall interactions. Due to the difference in hydrodynamic resistance of channel and PLBR, only minimal flow occurs inside the PLBR. After seeding of the PLBR (Figure 5A), the growth and observation phase is initiated with a change from bacteria solution to growth medium (Figure 5B). After the PLBRs are overgrown (Figure 5C) the experiment is typically stopped and time-lapse images can be analyzed. For the trapping mechanisms and flow profile within the PLBR the reader is referred to Gr&#252;nberger et al.13&#160;for more details.
Growth Rate Analysis
The present system can be applied to study various bacterial species with respect to different biological parameters such as growth, morphology, or a fluorescent signal. In a first example C. glutamicum, an industrially relevant production organism was cultured under standard cultivation conditions (T=30 &#176;C, CGXII medium21). Figure 6A shows the growth curves derived from three isogenic microcolonies. Exponential growth is maintained until the PLBRs are filled indicating that no nutrient limitation occurs.&#160;Figure 6B displays four DIC time-lapse microscopy images of a growing C. glutamicum colony.
Fluorescence Analysis
For single-cell fluorescence microscopy, researchers often make use of specific fluorescent proteins, for example GFP or derivatives, to couple a specific phenotype of interest to a measurable output (a fluorescent signal). To demonstrate the applicability of the PBLR for fluorescence based time-lapse studies, we investigated the fluorescence emission of a C. glutamicum strain producing a plasmid-encoded YFP-TetR fusion protein under control of the Ptac promoter (pEKEx2-yfp-tetR)18,22. In the presence of low inducer (IPTG) concentrations, expression from Ptac is known to lead to significant cell-to-cell variation in isogenic bacterial populations. Starting from one preculture, the growth and single cell fluorescence was followed for several isogenic microcolonies. As it can be seen in Figure 7, we observed phenotypic heterogeneity between different microcolonies and heterogeneity at the single-cell level within colonies starting from one mother cell. One colony (Figure 7B, PLBR 1) showed almost no fluorescence emission, whereas cells of PLBR 2 exhibited a low fluorescence emission due to basal yfp-tetR expression from the Ptac promoter. In PLBR 3 fluorescence emission was considerable strong compared to the other colonies and a broad distribution of the population was observed. This example demonstrates the applicability of the PBLR for time-lapse fluorescence microscopy studies. In comparison to flow cytometry, in which the fluorescence of single cells can be determined at one time point, the present systems allows the tracking of cells and the study of single-cell fluorescence in real time over many generations.
<img alt="Figure 1" fo:content-width="5in" fo:src="/files/ftp_upload/50560/50560fig1highres.jpg" src="/files/ftp_upload/50560/50560fig1.jpg" /> 
Figure 1.&#160;Overview of PLBR chip production process. Master mold fabrication: starting with (A) Design, (B) Lithography mask fabrication, and (C) Wafer production. PDMS-glass chip production: starting with (D) of PDMS molding followed by (E) glass and PDMS bonding and (F) final chip assembly.
<img alt="Figure 2" fo:content-width="5in" fo:src="/files/ftp_upload/50560/50560fig2highres.jpg" src="/files/ftp_upload/50560/50560fig2.jpg" /> 
Figure 2.&#160;Design of the PLBR chip. (A) CAD drawing of the whole microfluidic chip; (B) Magnification of selected layout positions: The layout contains two medium inlets (a1), a gradient generator with mixing channels (a2) and 6 parallel PLBR arrays (b1).&#160;b2 shows one PLBR, which is embedded in a fluid channel with a width of 100 &#181;m. The PLBR has an inner diameter of 40 &#181;m and nutrient channels with 2 &#181;m in width. The seeding inlet has a length of 40 &#181;m. Pink color represents the first layer (trapping and cultivation region) and blue color represents the second layer (fluid transport).
<img alt="Figure 3" fo:content-width="5in" fo:src="/files/ftp_upload/50560/50560fig3highres.jpg" src="/files/ftp_upload/50560/50560fig3.jpg" /> 
Figure 3.&#160;Illustration of two layer wafer fabrication process. (A) Fabrication of the first layer containing trapping structures; (B) Fabrication of the second layer containing fluid channels, inlets and outlets; (C) Representative surface profiles of the first layer. In this case the height of the first layer was 1,200 nm and is used for the cultivation of C. glutamicum in complex medium.
<img alt="Figure 4" fo:content-width="5in" fo:src="/files/ftp_upload/50560/50560fig4highres.jpg" src="/files/ftp_upload/50560/50560fig4.jpg" /> 
Figure 4.&#160;Device fabrication and representative chip. Illustration of the PDMS molding process: (A) PDMS mixing and degassing; (B) PDMS molding; (C) mold release, cutting and chip bonding. Final chip (Reproduced with permission of the Royal Society of Chemistry13): (D) photograph of the PDMS chip with 2 inlets and 1 outlet; (E) CAD image of six parallel arrays containing 5 PLBRs each; (F) SEM image of one PLBR.
<img alt="Figure 5" fo:content-width="5in" fo:src="/files/ftp_upload/50560/50560fig5highres.jpg" src="/files/ftp_upload/50560/50560fig5.jpg" /> 
Figure 5.&#160;Working principle of the PLBR system. (A) Seeding phase; (B) Growth phase of the bacterial microcolonies; (C) Overflow phase. Reproduced with permission of the Royal Society of Chemistry13.&#160;<a href="http://dx.doi.org/10.1039/C2LC40156H">http://dx.doi.org/10.1039/C2LC40156H</a>.
<img alt="Figure 6" fo:content-width="5in" fo:src="/files/ftp_upload/50560/50560fig6highres.jpg" src="/files/ftp_upload/50560/50560fig6.jpg" /> 
Figure 6.&#160;Growth rate determination of C. glutamicum WT microcolonies. (A) Growth plot of three PLBR cultivations and resulting exponential curves (Parts reproduced with permission of the Royal Society of Chemistry)13.&#160;<a href="http://dx.doi.org/10.1039/C2LC40156H">http://dx.doi.org/10.1039/C2LC40156H</a>. (B) Time-lapse images of a growing C. glutamicum colony.
<img alt="Figure 7" fo:content-width="5in" fo:src="/files/ftp_upload/50560/50560fig7highres.jpg" src="/files/ftp_upload/50560/50560fig7.jpg" /> 
Figure 7.&#160;PBLR-based analysis of population heterogeneity. Shown is C. glutamicum expressing an yfp-tetR fusion under the control of the Ptac promoter (pEKEx2-yfp-tetR) in the absence of the inducer IPTG. (A) Experimental workflow; (B) Three isogenic microcolonies showing colony-to-colony heterogeneity and cell-to-cell heterogeneity; (C) Distribution of single-cell fluorescence within the respective microcolonies.
<img alt="Figure 8" fo:content-width="5in" fo:src="/files/ftp_upload/50560/50560fig8highres.jpg" src="/files/ftp_upload/50560/50560fig8.jpg" /> 
Figure 8.&#160;Scanning electron images of different PLBRs. SEM images showing seeding inlets for the optimization of trapping efficiency. (A) Lager seeding inlets (B) Smaller seeding inlets (C) Larger &#8220;open&#34; seeding inlets (D) Two seeding inlets.
<table border="0" cellpadding="0" cellspacing="0" width="1276">
	<colgroup>
		<col span="4" />
	</colgroup>
	<tbody>
		<tr height="21">
			<td>Step</td>
			<td>Problem</td>
			<td>Possible Reason</td>
			<td>Solution</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Wafer Fabrication</td>
			<td>Trapped air bubbles in SU-8 during soft bake</td>
			<td>Increase of temperature to fast</td>
			<td>Bake at 95 &#176;C and 65 &#176;C several times</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Wafer Fabrication</td>
			<td>Disappearing and broken SU-8 structures</td>
			<td>Not optimal fabrication procedure; mechanical stress in SU-8 structures</td>
			<td>Optimize parameter such as baking time, exposure time</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Wafer Fabrication</td>
			<td>SU-8 layers to low or high or uneven layer thickness</td>
			<td>Problem during spin coating</td>
			<td>Check spin-coater parameters and wafer chuck</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Chip Bonding and Assembly&#160;</td>
			<td>Collapsing PLBRs</td>
			<td>PDMS bonding parameters not optimal&#160;</td>
			<td>Adjust power, plasma exposure time. and baking time after bonding</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Chip Bonding and Assembly</td>
			<td>Dirty structures and particles in the PLBRs</td>
			<td>Chip was not properly cleaned</td>
			<td>Apply scotch-tape for surface cleaning&#160;</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Chip Bonding and Assembly</td>
			<td>Insufficient PDMS-glass bonding</td>
			<td>Bonding parameters not optimal or insufficient cleaning&#160;</td>
			<td>Check settings of oxygen plasma</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Microfluidic Experiment</td>
			<td>Fluid leakage</td>
			<td>Inlet/outlet hole was not properly punched&#160;</td>
			<td>Optimize hole punching process</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Microfluidic Experiment</td>
			<td>Many small PDMS particles during filling</td>
			<td>Hole was not properly punched&#160;</td>
			<td>Optimize hole punching process</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Microfluidic Experiment, Biological Aspect</td>
			<td>No cell growth</td>
			<td>Solvent residue from cleaning procedure</td>
			<td>Flush chip more extensively prior cell loading or let solvent evaporate prior bonding</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Microfluidic Experiment, Biological Aspect</td>
			<td>Changing growth rates</td>
			<td>Various reasons</td>
			<td>Check preculture and temperature</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Microfluidic Experiment, Biological Aspect</td>
			<td>Cell morphology changes during cultivation</td>
			<td>Nutrient limitations or temperature shift</td>
			<td>Check incubator and flow</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Microfluidic Experiment, Technical &#160;Aspect</td>
			<td>Drift in position during time lapse microscopy</td>
			<td>Temperature fluctuations</td>
			<td>Check temperature profile prior experiments until no oscillation</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Microfluidic Experiment, Technical &#160;Aspect</td>
			<td>Loss of cells during cultivation</td>
			<td>Slightly to high reactor height&#160;</td>
			<td>Optimize reactor height</td>
		</tr>
		<tr height="20">
			<td height="20" style="height:20px;">Microfluidic Experiment, Technical &#160;Aspect</td>
			<td>No trapping</td>
			<td>Too low reactor height&#160;</td>
			<td>Optimize reactor height</td>
		</tr>
	</tbody>
</table>
Table 1.&#160;Troubleshooting. This table summarizes critical aspects, common mistakes, and possible solutions during experimental work.

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Recent advances in mammalian, insect, and stem cell cultivation and scale-up have created tremendous opportunities for new therapeutics and personalized medicine innovations. However, translating these advances into therapeutic applications will require in vitro systems that allow for robust, flexible, and cost effective bioreactor systems. There are several bioreactor systems currently utilized in research and commercial settings; however, many of these systems are not optimal for establishing, expanding, and monitoring the growth of different cell types. The culture parameters most challenging to control in these systems include, minimizing hydrodynamic shear, preventing nutrient gradient formation, establishing uniform culture medium aeration, preventing microbial contamination, and monitoring and adjusting culture conditions in real-time. Using a pneumatic single-use bioreactor system, we demonstrate the assembly and operation of this novel bioreactor for mammalian cells grown on micro-carriers. This bioreactor system eliminates many of the challenges associated with currently available systems by minimizing hydrodynamic shear and nutrient gradient formation, and allowing for uniform culture medium aeration. Moreover, the bioreactor&#8217;s software allows for remote real-time monitoring and adjusting of the bioreactor run parameters. This bioreactor system also has tremendous potential for scale-up of adherent and suspension mammalian cells for production of a variety therapeutic proteins, monoclonal antibodies, stem cells, biosimilars, and vaccines.

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Recent advances in mammalian, insect, and stem cell cultivation and scale-up have created tremendous opportunities for new therapeutics and personalized ...

A Microfluidic Platform for High-throughput Single-cell Isolation and Culture

Studying the heterogeneity of single cells is crucial for many biological questions, but is technically difficult. Thus, there is a need for a simple, yet high-throughput, method to perform single-cell culture experiments. Here, we report a microfluidic chip-based strategy for high-efficiency single-cell isolation (~77%) and demonstrate its capability of performing long-term single-cell culture (up to 7 d) and cellular heterogeneity analysis using clonogenic assay. These applications were demonstrated with KT98 mouse neural stem cells, and A549 and MDA-MB-435 human cancer cells. High single-cell isolation efficiency and long-term culture capability are achieved by using different sizes of microwells on the top and bottom of the microfluidic channel. The small microwell array is designed for precisely isolating single-cells, and the large microwell array is used for single-cell clonal culture in the microfluidic chip. This microfluidic platform constitutes an attractive approach for single-cell culture applications, due to its flexibility of adjustable cell culture spaces for different culture strategies, without decreasing isolation efficiency.

Here, we present a protocol for isolating and culturing single cells with a microfluidic platform, which utilizes a new microwell design concept to allow for high-efficiency single cell isolation and long-term clonal culture.

高通量单细胞的分离和文化的微流体平台

Studying the heterogeneity of single cells is crucial for many biological questions, but is technically difficult. Thus, there is a need for a simple, yet ...

Window on a Microworld: Simple Microfluidic Systems for Studying Microbial Transport in Porous Media

Microbial growth and transport in porous media have important implications for the quality of groundwater and surface water, the recycling of nutrients in the environment, as well as directly for the transmission of pathogens to drinking water supplies. Natural porous media is composed of an intricate physical topology, varied surface chemistries, dynamic gradients of nutrients and electron acceptors, and a patchy distribution of microbes. These features vary substantially over a length scale of microns, making the results of macro-scale investigations of microbial transport difficult to interpret, and the validation of mechanistic models challenging. Here we demonstrate how simple microfluidic devices can be used to visualize microbial interactions with micro-structured habitats, to identify key processes influencing the observed phenomena, and to systematically validate predictive models. Simple, easy-to-use flow cells were constructed out of the transparent, biocompatible and oxygen-permeable material poly(dimethyl siloxane). Standard methods of photolithography were used to make micro-structured masters, and replica molding was used to cast micro-structured flow cells from the masters. The physical design of the flow cell chamber is adaptable to the experimental requirements: microchannels can vary from simple linear connections to complex topologies with feature sizes as small as 2 &mu;m. Our modular EcoChip flow cell array features dozens of identical chambers and flow control by a gravity-driven flow module. We demonstrate that through use of EcoChip devices, physical structures and pressure heads can be held constant or varied systematically while the influence of surface chemistry, fluid properties, or the characteristics of the microbial population is investigated. Through transport experiments using a non-pathogenic, green fluorescent protein-expressing Vibrio bacterial strain, we illustrate the importance of habitat structure, flow conditions, and inoculums size on fundamental transport phenomena, and with real-time particle-scale observations, demonstrate that microfluidics offer a compelling view of a hidden world.

Microfluidic devices can be used to visualize complex natural processes in real time and at the appropriate physical scales. We have developed a simple microfluidic device that mimics key features of natural porous media for studying growth and transport of bacteria in the subsurface.

窗口上的一个微观世界：简单的微流体系统为研究多孔介质中的微生物运输

Microbial growth and transport in porous media have important implications for the quality of groundwater and surface water, the recycling of nutrients in ...

生物学

Live Cell Analysis of Shear Stress on Pseudomonas aeruginosa Using an Automated Higher-Throughput Microfluidic System

A higher-throughput microfluidic in vitro bioreactor coupled with fluorescence microscopy has been used to study bacterial biofilm growth and morphology, including Pseudomonas aeruginosa (P. aeruginosa). Here, we will describe how the system can be used to study the growth kinetics and the morphological properties such as the surface roughness and textural entropy of P. aeruginosa strain PA01 that expresses an enhanced green fluorescent protein (PA01-EGFP). A detailed protocol will describe how to grow and seed PA01-EGFP cultures, how to set up the microscope and autorun, and conduct the image analysis to determine growth rate and morphological properties using a variety of shear forces that are controlled by the microfluidic device. This article will provide a detailed description of a technique to improve the study of PA01-EGFP biofilms which eventually can be applied towards other strains of bacteria, fungi, or algae biofilms using the microfluidic platform.

Live Cell Analysis of Shear Stress on Pseudomonas aeruginosa Using an Automated Higher-Throughput Microfluidic System

Here, we describe the use of a higher-throughput microfluidic bioreactor coupled with a fluorescent microscope for the analysis of shear stress effects on Pseudomonas aeruginosa biofilms expressing green fluorescent proteins, including instrument set up, the determination of biofilm coverage, growth rate, and morphological properties.

利用自动高通量微流控系统对铜绿假单胞菌剪切应力的活细胞分析

A higher-throughput microfluidic in vitro bioreactor coupled with fluorescence microscopy has been used to study bacterial biofilm growth and morphology, ...

Establishing Single-Cell Based Co-Cultures in a Deterministic Manner with a Microfluidic Chip

Cell co-culture assays have been widely used for studying cell-cell interactions between different cell types to better understand the biology of diseases including cancer. However, it is challenging to clarify the complex mechanism of intercellular interactions in highly heterogeneous cell populations using conventional co-culture systems because the heterogeneity of the cell subpopulation is obscured by the average values; the conventional co-culture systems can only be used to describe the population signal, but are incapable of tracking individual cells behavior. Furthermore, conventional single-cell experimental methods have low efficiency in cell manipulation because of the Poisson distribution. Microfabricated devices are an emerging technology for single-cell studies because they can accurately manipulate single cells at high-throughput and can reduce sample and reagent consumption. Here, we describe the concept and application of a microfluidic chip for multiple single-cell co-cultures. The chip can efficiently capture multiple types of single cells in a culture chamber (~46%) and has a sufficient culture space useful to study the cells&#39; behavior (e.g., migration, proliferation, etc.) under cell-cell interaction at the single-cell level. Lymphatic endothelial cells and oral squamous cell carcinoma were used to perform a single-cell co-culture experiment on the microfluidic platform for live multiple single-cell interaction studies.

This report describes a microfluidic chip-based method to set up a single cell culture experiment in which high-efficiency pairing and microscopic analysis of multiple single cells can be achieved.

使用微流体芯片以确定性方式建立基于单细胞的共培养物

Cell co-culture assays have been widely used for studying cell-cell interactions between different cell types to better understand the biology of diseases ...

Generation of Dynamical Environmental Conditions using a High-Throughput Microfluidic Device

Mimicking in vivo environmental conditions is crucial for in vitro studies on complex life machinery. However, current techniques targeting live cells and organs are either highly expensive, like robotics, or lack nanoliter volume and millisecond time accuracy in liquid manipulation. We herein present the design and fabrication of a microfluidic system, which consists of 1,500 culture units, an array of enhanced peristaltic pumps and an on-site mixing modulus. To demonstrate the capacities of the microfluidic device, neural stem cell (NSC) spheres are maintained in the proposed system. We observed that when the NSC sphere is exposed to CXCL in day 1 and EGF in day 2, the round-shaped conformation is well maintained. Variation in the input order of 6 drugs causes morphological changes to the NSC sphere and the expression level representative marker for NSC stemness (i.e., Hes5 and Dcx). These results indicate that dynamic and complex environmental conditions have great effects on NSC differentiation and self-renewal, and the proposed microfluidic device is a suitable platform for high throughput studies on the complex life machinery.

We present a microfluidic system for high throughput studies on complex life machinery, which consists of 1500 culture units, an array of enhanced peristaltic pumps and an on-site mixing modulus. The microfluidic chip allows for the analysis of the highly complex and dynamic micro-environmental conditions in vivo.

使用高通量微流体设备生成动态环境条件

Mimicking in vivo environmental conditions is crucial for in vitro studies on complex life machinery. However, current techniques targeting live cells and ...

Multi-Stream Perfusion Bioreactor Integrated with Outlet Fractionation for Dynamic Cell Culture

Certain cell and tissue functions operate within the dynamic time scale of minutes to hours that are poorly resolved by conventional culture systems. This work has developed a low-cost perfusion bioreactor system that allows culture medium to be continuously perfused into a cell culture module and fractionated in a downstream module to measure dynamics on this scale. The system is constructed almost entirely from commercially available parts and can be parallelized to conduct independent experiments in conventional multi-well cell culture plates simultaneously. This video article demonstrates how to assemble the base setup, which requires only a single multichannel syringe pump and a modified fraction collector to perfuse up to six cultures in parallel. Useful variants on the modular design are also presented that allow for controlled stimulation dynamics, such as solute pulses or pharmacokinetic-like profiles. Importantly, as solute signals travel through the system, they are distorted due to solute dispersion. Furthermore, a method for measuring the residence time distributions (RTDs) of the components of the perfusion setup with a tracer using MATLAB is described. RTDs are useful to calculate how solute signals are distorted by the flow in the multi-compartment system. This system is highly robust and reproducible, so basic researchers can easily adopt it without the need for specialized fabrication facilities.

This paper presents a method to construct and operate a low-cost, multichannel perfusion cell culture system for measuring the dynamics of secretion and absorption rates of solutes in cellular processes. The system can also expose cells to dynamic stimulus profiles.

多流灌注生物反应器集成了出口分馏功能，用于动态细胞培养

Certain cell and tissue functions operate within the dynamic time scale of minutes to hours that are poorly resolved by conventional culture systems. This ...

Automated and High-throughput Microbial Monoclonal Cultivation and Picking Using the Single-cell Microliter-droplet Culture Omics System

Pure bacterial cultures are essential for the study of microbial culturomics. Traditional methods based on solid plates, well plates, and micro-reactors are hindered by cumbersome procedures and low throughput, impeding the rapid progress of microbial culturomics research. To address these challenges, we had successfully developed the Single-cell Microliter-droplet Culture Omics System (MISS cell), an automated high-throughput platform that utilizes droplet microfluidic technology for microbial monoclonal isolation, cultivation, and screening. This system can generate a large number of single-cell droplets and cultivate, screen, and collect monoclonal colonies in a short time, facilitating an integrated process from microbial isolation to picking. In this protocol, we demonstrated its application using the isolation and cultivation of human gut microbiota as an example and compared the microbial isolation efficiency, monoclonal culture performance, and screening throughput using the solid-plate culture method. The experimental workflow was simple, and reagent consumption was very low. Compared to solid-plate culture methods, the MISS cell could cultivate a greater diversity of gut microbiota species, offering significant potential and value for microbial culturomics research.

This protocol describes how to use the Single-cell Microliter-droplet Culture Omics System (MISS cell) to perform microbial monoclonal isolation, cultivation, and picking. The MISS cell achieves an integrated workflow based on droplet microfluidic technology, which offers excellent droplet monodispersity, high parallel cultivation, and high-throughput biomass detection.

使用单细胞微升液滴培养组学系统的自动化和高通量微生物单克隆培养和挑取

Pure bacterial cultures are essential for the study of microbial culturomics. Traditional methods based on solid plates, well plates, and micro-reactors ...

Bioreactor Assembly for Continuous Culture of Complex Fecal Communities

The microbiota, especially bacteria, respond to various environmental exposures such as micro and macronutrients, pharmacological compounds, and inflammatory mediators, which dynamically alter community composition and microbial metabolic output. Understanding how physiological culture conditions affect microbial communities and diversity and their metabolic capacity will contribute important knowledge of their impact on health and diseases. Here, we present a protocol adapted from the template published by Auchtung et al. to create mini-bioreactor arrays that can cultivate complex fecal communities, define bacterial consortiums or single strains under precise conditions, including nutrient availability, temperature, flow rate, pH, and oxygen content. We describe the process for building the mini-bioreactor system, including adaptations to improve limitations in the published protocol. We also discuss the setup of the mini-bioreactor system under anaerobic conditions with the use of MEGA media (adapted from Han et al.), which is a rich media supporting the growth of diverse bacteria. We describe the inoculation of gut humanized mouse fecal samples into the mini-bioreactor system, followed by the establishment of complex community cultures within the mini-bioreactor system, which can be grown under continuous flow with aseptic sampling to monitor community composition. This system is adaptable to dietary changes and other cultural modifications. The techniques described here allow for the characterization of diverse, fastidious fecal communities under dynamic conditions or in response to perturbation in isolation from host-derived factors.

This protocol details the assembly of mini-bioreactor arrays to be utilized for continuous flow culture of complex fecal communities under anaerobic conditions. We also discuss the methods for assembly, inoculation, and sampling of the reactors for further analysis.