In this protocol the fabrication, setup and basic operation of a microfluidic picoliter bioreactor (PLBR) for single-cell analysis of prokaryotic microorganisms is introduced. Industrially relevant microorganisms were analyzed as proof of principle allowing insights into growth rate, morphology, and phenotypic heterogeneity over certain time periods, hardly possible with conventional methods.
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. 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 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.
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. 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. 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 µm 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 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.
1. Wafer Fabrication
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 process flowchart is shown in Figure 4).
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.
4. Experimental Setup
Note: All steps are performed with an inverted microscope.
5. Seeding of Bacterial Cells into the Microfluidic Device
6. Time-lapse Imaging
7. Analysis
Note: The following steps or parts of the procedure can be performed manually or by image analysis programs such as ImageJ, etc.
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, 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—beam writer (Figure 1B) with submicron resolution. In the present study a 5 in chromium mask was created which was used for the SU-8 wafer lithography. The final silicon—SU—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 µm x 10 µm (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 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 µm 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 Grünberger et al.13 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 °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. 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.
Figure 1. 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.
Figure 2. 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). b2 shows one PLBR, which is embedded in a fluid channel with a width of 100 µm. The PLBR has an inner diameter of 40 µm and nutrient channels with 2 µm in width. The seeding inlet has a length of 40 µm. Pink color represents the first layer (trapping and cultivation region) and blue color represents the second layer (fluid transport).
Figure 3. 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.
Figure 4. 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.
Figure 5. 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. https://dx-doi-org.vpn.cdutcm.edu.cn/10.1039/C2LC40156H.
Figure 6. 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. https://dx-doi-org.vpn.cdutcm.edu.cn/10.1039/C2LC40156H. (B) Time-lapse images of a growing C. glutamicum colony.
Figure 7. 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.
Figure 8. 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 “open" seeding inlets (D) Two seeding inlets.
Step | Problem | Possible Reason | Solution |
Wafer Fabrication | Trapped air bubbles in SU-8 during soft bake | Increase of temperature to fast | Bake at 95 °C and 65 °C several times |
Wafer Fabrication | Disappearing and broken SU-8 structures | Not optimal fabrication procedure; mechanical stress in SU-8 structures | Optimize parameter such as baking time, exposure time |
Wafer Fabrication | SU-8 layers to low or high or uneven layer thickness | Problem during spin coating | Check spin-coater parameters and wafer chuck |
Chip Bonding and Assembly | Collapsing PLBRs | PDMS bonding parameters not optimal | Adjust power, plasma exposure time. and baking time after bonding |
Chip Bonding and Assembly | Dirty structures and particles in the PLBRs | Chip was not properly cleaned | Apply scotch-tape for surface cleaning |
Chip Bonding and Assembly | Insufficient PDMS-glass bonding | Bonding parameters not optimal or insufficient cleaning | Check settings of oxygen plasma |
Microfluidic Experiment | Fluid leakage | Inlet/outlet hole was not properly punched | Optimize hole punching process |
Microfluidic Experiment | Many small PDMS particles during filling | Hole was not properly punched | Optimize hole punching process |
Microfluidic Experiment, Biological Aspect | No cell growth | Solvent residue from cleaning procedure | Flush chip more extensively prior cell loading or let solvent evaporate prior bonding |
Microfluidic Experiment, Biological Aspect | Changing growth rates | Various reasons | Check preculture and temperature |
Microfluidic Experiment, Biological Aspect | Cell morphology changes during cultivation | Nutrient limitations or temperature shift | Check incubator and flow |
Microfluidic Experiment, Technical Aspect | Drift in position during time lapse microscopy | Temperature fluctuations | Check temperature profile prior experiments until no oscillation |
Microfluidic Experiment, Technical Aspect | Loss of cells during cultivation | Slightly to high reactor height | Optimize reactor height |
Microfluidic Experiment, Technical Aspect | No trapping | Too low reactor height | Optimize reactor height |
Table 1. Troubleshooting. This table summarizes critical aspects, common mistakes, and possible solutions during experimental work.
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. 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.
The authors have nothing to disclose.
The authors would like to thank the technician Agnes Müller-Schröer for her valuable contribution. This work was partly performed at Helmholtz Nanoelectronic Facility (HNF) at Forschungszentrum Jülich GmbH. The authors are grateful for the generous help and support.
Silicon wafer 100 mm diameter, P/BOR <100> | Si-MAT, Silicon Materials, Germany | ||
Photoresist SU-8 2000.5 | Micro Resist Technology GmbH, Germany | ||
Photoresist SU-8 2010 | Micro Resist Technology GmbH, Germany | ||
SU-8 Developer mr DEV- 600 | Micro Resist Technology GmbH, Germany | ||
Polydimethylsiloxane (PDMS) Sylgard 184 Silicone Elastomer Kit | Dow Corning; Farnell GmbH, Germany | ||
Dispensing needles Precision Tips 27 G; ID = 0.2 mm, OD = 0.42 mm | Nordson EFD Deutschland, Germany | ||
Glass plates D263 T eco, 30 mm x 25 mm x 0.17 mm | Schott AG, Germany | ||
Hole puncher AKA 5130-B-90 | Harris Uni-Core | ||
Tubing Tygon S-54-HL, ID = 0.25 mm, OD = 0.76 mm | Saint Gobain; VWR International GmbH, Germany | ||
Disposable Syringes – Omnifix Spritzen BRAUN Omnifix 40 Duo, 1 ml | B. Braun Melsungen AG, Germany | 552-183143 | |
Syringes, 1 ml sterile glass syringes | INNOVATIVE LABOR SYSTEME GMBH (ILS), Germany | ||
Chemicals | |||
(NH4)2SO4 | Carl Roth GmbH + Co. KG, Germany | ||
Urea | Carl Roth GmbH + Co. KG, Germany | ||
KH2PO4 | Carl Roth GmbH + Co. KG, Germany | ||
K2HPO4 | Carl Roth GmbH + Co. KG, Germany | ||
MgSO4•7H2O | Carl Roth GmbH + Co. KG, Germany | ||
MOPS | Carl Roth GmbH + Co. KG, Germany | ||
FeSO4•7H2O | Carl Roth GmbH + Co. KG, Germany | ||
MnSO4•H2O | Carl Roth GmbH + Co. KG, Germany | ||
ZnSO4•7H2O | Carl Roth GmbH + Co. KG, Germany | ||
CuSO4 | Carl Roth GmbH + Co. KG, Germany | ||
NiCl2•6H2O | Carl Roth GmbH + Co. KG, Germany | ||
CaCl2 | Carl Roth GmbH + Co. KG, Germany | ||
Biotin | Carl Roth GmbH + Co. KG, Germany | ||
Procatechuic acid | Carl Roth GmbH + Co. KG, Germany | ||
Glucose-Monohydrate | Carl Roth GmbH + Co. KG, Germany | ||
BHI | Becton, Dickinson | ||
Cells | |||
Corynebacterium glutamicum ATTC 13032 | DSMZ; Leibniz-Institut DSMZ – Deutsche Sammlung von Mikroorganismen und Zellkulturen GmbH, Germany | ||
Escherichia coli MG 1655 | DSMZ; Leibniz-Institut DSMZ – Deutsche Sammlung von Mikroorganismen und Zellkulturen GmbH, Germany | ||
Equipment | |||
Wafer Cleaner SSEC 3300 | Solid State Equipment LLC | ||
Spin Coater SPIN150 -NPP | SPS Europe B.V. | ||
Mask Aligner MA-6 | Karl Suess | ||
Hot Plate HP30A – 2 | Torrey Pines Scientific | ||
Laboratory oven Memmert UN 200 | Memmert | ||
Plasma Cleaner FEMTO | Diener Electronics, Germany | ||
neMESYS syringe pumps | Cetoni GmbH, Germany | ||
Magnetic stirrer CB 162 | Stuart | VWR 442-0304 | |
Microscope Nikon Eclipse Ti | Nikon Microscopy | ||
Microscope incubuator | Pecon GmbH, Germany | ||
Centrifuge minispin plus “black line” | Eppendorf | 9776501 | |
Photometer BioPhotometer plus | Eppendorf | 6132000008 | |
Shake flask shaker/incubator 3031 | GFL – Gesellschaft für Labortechnik mbH, Germany | ||
Profilometer, Dektak 150 Stylus Profiler | Veeco |