1. Fabricating a Prototype cDEP Microfluidic Device: Overview
Figure 1. Schematic of a low frequency continuous sorting device. The sample channel runs left to right and is 500 μm wide with sawtooth constrictions to 100 μm. The two pairs of fluidic electrode channels compose the source and sink electrodes, respectively, and are separated from the sample channel by a 20 μm thick PDMS barrier.
Figure 2. The fabrication process of a cDEP device. (a) For 60 sec, UV light selectively reacts with photoresist exposed through a mask pattern of the cDEP device geometry. (b) Photoresist is removed using developer. (c) Deep Reactive Ion Etching (DRIE) is used to etch 50 μm deep features, and 5 min of wet etching by tetramethylammonium hydroxide (TMAH) 25% at 70 °C is used to reduce roughness on the side walls. (d) A Teflon coating is added to improve device release from the wafer. (e) PDMS is poured onto the re-usable wafer stamp after degassing and cured for 45 min at 100 °F. (f) PDMS is removed from the wafer. PDMS and a clean glass slide are exposed to air plasma for 2 min and bonded together.
Figure 3. (a) The mask used for photolithography during the silicon wafer stamp fabrication, and (b) the finished PDMS-glass device with the sample and fluid electrode channels filled with green and red food coloring, respectively. See Figure 1 for dimensions. Click here to view larger figure.
2. Preparing a Cell Suspension in DEP Buffer
Note: Cell viability analysis by the trypan blue dye exclusion method showed a slight decrease in viability (from 95.1-91.6%) of early-stage MOSE (MOSE-E) cells suspended in DEP buffer at room temperature after 5 hr. It is predicted that a similar slight decrease in viability occurs for MOSE-L cells, indicating that cells should not be stored in DEP buffer long-term.
3. Loading the cDEP Microfluidic Chip
4. Characterizing Crossover Frequency of Cells using cDEP Chip
Figure 4. (a) Overall experimental setup for cDEP experiments. The cDEP chip is located on the platform of the inverted microscope. A camera sends images to the computer for recording. The syringe pump maintains a constant inlet flow. The function generator generates a signal which is stepped up by the high voltage amplifier and connected to the cDEP chip by wire electrodes. The oscilloscope monitors the signal sent to the chip. (b) Detail view of the cDEP chip and fluidic and electronic connections. Click here to view larger figure.
5. Image Processing for Characterizing Crossover Frequency
6. Varying the Experiment to Perform Cell Sorting or Enrichment
DEP should be observed qualitatively in the sample channel to confirm the device is operational when the electric field is present. One method to test for the presence of DEP is to adjust the frequency to values far from the crossover frequency where strong pDEP and nDEP are predicted (roughly >40 kHz to observe pDEP and <10 kHz to observe nDEP for most mammalian cancer cells in a buffer with conductivity of 100 μS/cm). It should be noted that inert microspheres exhibit pDEP below their crossover frequency and nDEP above their crossover frequency. For the sawtooth feature geometry presented here, pDEP should be seen for cells at the higher test frequency, indicated by the occurrence of pearl chaining and focusing of cells or particles at the sawtooth feature edge of the channel, while at the lower test frequency, nDEP should be apparent as cells are restricted to the region nearer the straight edge of the channel. At these low frequencies, cells may lyse due to electroporation, so the sample may appear to contain fewer cells, and those that are visible may appear enlarged or blurry if using an enzymatically-activated fluorescing dye. Verifying the frequencies at which pDEP and nDEP occur allows the determination of the crossover frequency as described in the protocol. For mammalian cancer cells, such as MOSE-L used here, we observed nDEP at 5 kHz (Figure 5a) and strong pDEP at 60 kHz (Figure 5b). MOSE-L cells had a diameter of 17.7±3.3 μm (n = 268 cells) and the beads have a 4 μm nominal diameter. A full analysis of the dielectric properties of MOSE-L cells compared to MOSE cells in earlier stages of progression can be found in the recent work by Salmanzadeh et al.33
If pDEP and nDEP are not observed at these extremes, various problems could be occurring. The sample conductivity may be too high due to contaminants or cell lysing. Insufficient electric field may be generated due to bubbles trapped in the fluid electrode channels, which prevent conduction of current to the portion of the channels bordering the sample channel. Unsteady flow may be caused by a bubble trapped in the syringe or inlet tubing, bubbles resulting from not keeping the device under vacuum for a sufficient time or not quickly filling the device upon removing from vacuum, leakage due to delamination of poorly bonded PDMS to the glass slide, tears in the barrier membrane due to excessive force exerted when filling the channels, or flow rates at the extremes of the pump operating range.
In addition to determining the crossover frequency of cells, this technique can be used to sort a mixture, illustrated here by a mixture of MOSE-L cells and beads. This example takes advantage of the negative dielectrophoresis (nDEP) exhibited by 4 μm beads at frequencies where MOSE-L cells experience positive dielectrophoresis (pDEP). We operated the device at 200 VRMS and 10 kHz (Figure 6a) and observed that both cells and beads were mixed as they experienced nDEP. At 50 kHz we observed movement of MOSE-L cells to the top of the channel, while beads were restricted to the lower portion of the channel, enabling separation of the mixture into two components (Figure 6b).
Figure 5. The position of MOSE-L cells is manipulated by changing the frequency of the applied electric field. The photos are taken at the final sawtooth feature in the sample channel and the fluidic electrodes are located at the corners on the right side. They are filled with PBS containing rhodamine B, which fluoresces to visualize the channels. (a) MOSE-L cells experience nDEP at 200 VRMS and 5 kHz. (b) MOSE-L cells experience pearl chaining and pDEP at 200 VRMS and 60 kHz. Click here to view larger figure.
Figure 6. A mixture of MOSE-L cells (green) and 4 μm beads (red) flow through the final sawtooth feature in the sample channel of a low frequency cDEP device. (a) At 200 V and 10 kHz cells and beads are mixed. Arrows point to faintly appearing cells that likely have died due to the low frequency conditions. (b) At 200 V and 50 kHz cells experience pDEP and move to the feature edge of the channel, while beads experience nDEP and remain confined to the region nearer the straight edge. Click here to view larger figure.
Name of Reagent/Material | Company | Catalog Number | Comments |
Polydimethylsiloxane (PDMS) | Dow Corning, Midland, MI,USA | Sylgard 184 | |
Glass slides | The Microscope Depot | 76079 | 2×3 inch-ground edges |
Microbore PTFE Tubing | Cole-Parmer Instrument Co, Vernon Hills, IL, USA | EW-06417-31 | Thin walled 20 gauge, 0.032″ID x 0.056″OD, 100 ft/roll |
Luer-slip plastic syringes | National Scientific company | S7510-1 | |
Needle tip | Howard Electronic instruments | JG20-1.0 | 20 Gauge 1.0″, ID=0.025″ OD=0.036″ |
D(+)-Sucrose | Fisher Scientific, Fair Lawn, NJ | S3-500 | |
D(+)-glucose, reagent ACS, anhydrous | Acros Organics N.V., Fair Lawn, NJ | AC410955000 | |
RPMI-1640 Medium | Quality Biological Inc. | 112-025-101 | |
Calcein AM, Molecular Probes | Invitrogen Corp. (life technologies), Carlsbad, CA, USA | C3100MP | excitation wavelength 488/emission wavelength 516 |
Rhodamine B, O | Science Lab | SLR1465-100G | excitation wavelength 540/emission wavelength 625 |
Phosphate buffered saline (10X) | Gbiosciences, St. Louis, MO | RC-147 | |
Leica, inverted light microscope | Leica Microsystems, Bannockburn, IL, USA | Leica DMI 6000B | |
Leica DFC420, color camera | Leica Microsystems, Bannockburn, IL, USA | Leica DFC420 | |
Function generator | GW Instek, Taipei, Taiwan | GFG-3015 | |
Wideband power amplifier | Amp-Line Corp., Oakland Gardens, NY, USA | AL-50HF-A | |
HFHV Output Transformer | AL-T50-V25/300-F100K-600K | ||
High voltage amplifier | Trek | Model 2205 | |
USB Modular Oscilloscope, 100 MHz | AgilentTechnologies | U2701A | |
Expanded Plasma Cleaner | Harrick Plasma | PDC-001/002 (115/230V) | air plasma |
Scotch Magic tape | 3M | any available width is sufficient | |
1.5 mm puncher | Harris Uni-Core | Z708836-25EA | |
.25% Trypsin-EDTA | Invitrogen | 25200-056 | |
FluoSpheres Sulfate Microspheres | Invitrogen | F8858 | 4.0 μm, red fluorescent (excitation wavelength 580/emission wavelength 605) |
AZ 9260 photoresist | AZ Electronic Materials | ||
AZ 400 K developer | AZ Electronic Materials | ||
Tetramethylammonium hydroxide (TMAH) 25% | provided by Virginia Tech cleanroom | ||
Teflon coating | applied using DRIE machine | ||
Silicon wafer | University Wafer | 452 | 100 mm diameter, 500 μm thickness, one side polished (SSP) |
Deep Reactive Ion Etching (DRIE) | Alcatrel | AMS SDE 100 |
Dielectrophoresis (DEP) is the phenomenon by which polarized particles in a non-uniform electric field undergo translational motion, and can be used to direct the motion of microparticles in a surface marker-independent manner. Traditionally, DEP devices include planar metallic electrodes patterned in the sample channel. This approach can be expensive and requires a specialized cleanroom environment. Recently, a contact-free approach called contactless dielectrophoresis (cDEP) has been developed. This method utilizes the classic principle of DEP while avoiding direct contact between electrodes and sample by patterning fluidic electrodes and a sample channel from a single polydimethylsiloxane (PDMS) substrate, and has application as a rapid microfluidic strategy designed to sort and enrich microparticles. Unique to this method is that the electric field is generated via fluidic electrode channels containing a highly conductive fluid, which are separated from the sample channel by a thin insulating barrier. Because metal electrodes do not directly contact the sample, electrolysis, electrode delamination, and sample contamination are avoided. Additionally, this enables an inexpensive and simple fabrication process.
cDEP is thus well-suited for manipulating sensitive biological particles. The dielectrophoretic force acting upon the particles depends not only upon spatial gradients of the electric field generated by customizable design of the device geometry, but the intrinsic biophysical properties of the cell. As such, cDEP is a label-free technique that avoids depending upon surface-expressed molecular biomarkers that may be variably expressed within a population, while still allowing characterization, enrichment, and sorting of bioparticles.
Here, we demonstrate the basics of fabrication and experimentation using cDEP. We explain the simple preparation of a cDEP chip using soft lithography techniques. We discuss the experimental procedure for characterizing crossover frequency of a particle or cell, the frequency at which the dielectrophoretic force is zero. Finally, we demonstrate the use of this technique for sorting a mixture of ovarian cancer cells and fluorescing microspheres (beads).
Dielectrophoresis (DEP) is the phenomenon by which polarized particles in a non-uniform electric field undergo translational motion, and can be used to direct the motion of microparticles in a surface marker-independent manner. Traditionally, DEP devices include planar metallic electrodes patterned in the sample channel. This approach can be expensive and requires a specialized cleanroom environment. Recently, a contact-free approach called contactless dielectrophoresis (cDEP) has been developed. This method utilizes the classic principle of DEP while avoiding direct contact between electrodes and sample by patterning fluidic electrodes and a sample channel from a single polydimethylsiloxane (PDMS) substrate, and has application as a rapid microfluidic strategy designed to sort and enrich microparticles. Unique to this method is that the electric field is generated via fluidic electrode channels containing a highly conductive fluid, which are separated from the sample channel by a thin insulating barrier. Because metal electrodes do not directly contact the sample, electrolysis, electrode delamination, and sample contamination are avoided. Additionally, this enables an inexpensive and simple fabrication process.
cDEP is thus well-suited for manipulating sensitive biological particles. The dielectrophoretic force acting upon the particles depends not only upon spatial gradients of the electric field generated by customizable design of the device geometry, but the intrinsic biophysical properties of the cell. As such, cDEP is a label-free technique that avoids depending upon surface-expressed molecular biomarkers that may be variably expressed within a population, while still allowing characterization, enrichment, and sorting of bioparticles.
Here, we demonstrate the basics of fabrication and experimentation using cDEP. We explain the simple preparation of a cDEP chip using soft lithography techniques. We discuss the experimental procedure for characterizing crossover frequency of a particle or cell, the frequency at which the dielectrophoretic force is zero. Finally, we demonstrate the use of this technique for sorting a mixture of ovarian cancer cells and fluorescing microspheres (beads).
Dielectrophoresis (DEP) is the phenomenon by which polarized particles in a non-uniform electric field undergo translational motion, and can be used to direct the motion of microparticles in a surface marker-independent manner. Traditionally, DEP devices include planar metallic electrodes patterned in the sample channel. This approach can be expensive and requires a specialized cleanroom environment. Recently, a contact-free approach called contactless dielectrophoresis (cDEP) has been developed. This method utilizes the classic principle of DEP while avoiding direct contact between electrodes and sample by patterning fluidic electrodes and a sample channel from a single polydimethylsiloxane (PDMS) substrate, and has application as a rapid microfluidic strategy designed to sort and enrich microparticles. Unique to this method is that the electric field is generated via fluidic electrode channels containing a highly conductive fluid, which are separated from the sample channel by a thin insulating barrier. Because metal electrodes do not directly contact the sample, electrolysis, electrode delamination, and sample contamination are avoided. Additionally, this enables an inexpensive and simple fabrication process.
cDEP is thus well-suited for manipulating sensitive biological particles. The dielectrophoretic force acting upon the particles depends not only upon spatial gradients of the electric field generated by customizable design of the device geometry, but the intrinsic biophysical properties of the cell. As such, cDEP is a label-free technique that avoids depending upon surface-expressed molecular biomarkers that may be variably expressed within a population, while still allowing characterization, enrichment, and sorting of bioparticles.
Here, we demonstrate the basics of fabrication and experimentation using cDEP. We explain the simple preparation of a cDEP chip using soft lithography techniques. We discuss the experimental procedure for characterizing crossover frequency of a particle or cell, the frequency at which the dielectrophoretic force is zero. Finally, we demonstrate the use of this technique for sorting a mixture of ovarian cancer cells and fluorescing microspheres (beads).