Effects of Dielectrophoresis on Growth, Viability and Immuno-reactivity of Listeria monocytogenes
© Yang et al; licensee BioMed Central Ltd. 2008
Received: 30 November 2007
Accepted: 16 April 2008
Published: 16 April 2008
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© Yang et al; licensee BioMed Central Ltd. 2008
Received: 30 November 2007
Accepted: 16 April 2008
Published: 16 April 2008
Dielectrophoresis (DEP) has been regarded as a useful tool for manipulating biological cells prior to the detection of cells. Since DEP uses high AC electrical fields, it is important to examine whether these electrical fields in any way damage cells or affect their characteristics in subsequent analytical procedures. In this study, we investigated the effects of DEP manipulation on the characteristics of Listeria monocytogenes cells, including the immuno-reactivity to several Listeria- specific antibodies, the cell growth profile in liquid medium, and the cell viability on selective agar plates. It was found that a 1-h DEP treatment increased the cell immuno-reactivity to the commercial Listeria species-specific polyclonal antibodies (from KPL) by ~31.8% and to the C11E9 monoclonal antibodies by ~82.9%, whereas no significant changes were observed with either anti-InlB or anti-ActA antibodies. A 1-h DEP treatment did not cause any change in the growth profile of Listeria in the low conductive growth medium (LCGM); however, prolonged treatments (4 h or greater) caused significant delays in cell growth. The results of plating methods showed that a 4-h DEP treatment (5 MHz, 20 Vpp) reduced the viable cell numbers by 56.8–89.7 %. These results indicated that DEP manipulation may or may not affect the final detection signal in immuno-based detection depending on the type of antigen-antibody reaction involved. However, prolonged DEP treatment for manipulating bacterial cells could produce negative effects on the cell detection by growth-based methods. Careful selection of DEP operation conditions could avoid or minimize negative effects on subsequent cell detection performance.
Listeria monocytogenes is considered as one of the most hazardous, potentially life-threatening, human foodborne pathogens. It can contaminate many food products, such as milk, cheese, ice cream, raw vegetables, poultry products, and meats. The Centers for Disease Control and Prevention (CDC) estimates that there are 2,500 illnesses with 500 deaths associated with listeriosis in the United States each year . The development of rapid, sensitive, simple and cost effective methods to detect this pathogen is extremely important in implementing an effective response to the prevention of foodborne diseases. Conventional microbiological methods are time-consuming, largely because they require several enrichment and separation steps (e.g. pre-enrichment, selective enrichment) to grow cells to detectable concentrations. Many recently developed rapid methods have sought to accelerate or eliminate traditional growth-based enrichment steps by using newly discovered concentration or separation methods that are not limited by bacterial growth. These methods include membrane filtration, magnetic separation, dielectrophoresis, and electrophoresis to concentrate bacteria cells . Among these, dielectrophoresis (DEP) has been proven especially suitable for manipulation, concentration, and separation of biological cells in micro-scaled devices, and has great potential to be integrated with various detection methods [3, 4].
where, and are complex permittivities of the particle and the medium respectively, with σ the conductivity, ε the permittivity, ω the angular frequency of the applied electrical field, and . The frequency dependence of Re[f CM (ω)] indicates that the force acting on the particle varies with the frequency. Depending on the relative polarizability of the particle with respect to the surrounding medium, the particle will be induced to move either towards a region where the electrical field gradients are the strongest (Re[f CM ] > 0) (positive DEP), or towards a region where the electrical field gradients are the weakest (Re[f CM ] < 0) DEP (negative DEP).
As most biological cells behave as dielectrically polarized particles in a non-uniform electrical field, they can be manipulated by DEP for various applications. Well demonstrated applications of DEP for manipulation of cells are the separations of different types of cells based on the differences in the dielectrical polarizabilities among these cell types . Examples of these applications include the separation of viable and nonviable yeast cells [10, 11], cancer cells and normal cells [12–15], CD34+ cells and blood stem cells , individual neurons , the trapping of viruses from fluid , and the separation and detection of bacterial cells [3, 19–23].
DEP has been employed to manipulate Listeria cells for separation, concentration, and/or detection purposes. Li and Bashir  reported a DEP-based separation method to separate live and heat-killed Listeria monocytogenes cells in a static solution on microfabricated interdigitated electrodes. The separation was based on the large difference in dielectrical properties between live and dead cells. DEP has afforded the development of advanced lab-on-a-chip devices by integrating its multi-functions (concentration and separation) with different analytical detection technologies . Gomez et al.  developed the on-chip impedance microbiology to detect Listeria cells. Live Listeria cells in the fluid were successfully concentrated into an ultra-small volume (400 pl) in a micro-device by DEP, and were followed by impedance detection of bacterial growth. The concentration factor of the chip was between 104 to 105 when the cells in an original sample volume of 40 μl were concentrated into the 400 pl chamber. Such a DEP concentration step eliminated the need for lengthy bacterial population enrichment steps using conventional cell culture methods, and drastically reduced the total assay time. Yang et al.  employed DEP to collect and concentrate Listeria monocytogenes cells in a microfluidic channel and combined it with antibody-based capture of cells in the microfluidic device. The device utilized an interdigitated microelectrode embedded in the microfluidic channel for DEP collection of cells. Monoclonal anti-Listeria monocytogenes antibodies were immobilized on the microelectrode surface which provided selective capture of Listeria monocytogenes cells. DEP served to concentrate Listeria cells at the locality of the electrodes, and to make cells in close contact with antibodies immobilized on the channel and electrode surfaces, which in combination dramatically improved the capture efficiency of antibodies to cells in the microfluidic device. Such a DEP microfluidic device was particularly useful for trapping and detecting low concentrations of cells.
DEP has also been widely used to characterize and/or detect other microorganisms. Lapizco-Encinas et al.  reported a DEP method to concentrate and remove microbes (Bacillus subtilis spores, Tobacco Mosaic Virus, Escherichia coli cells) from water. Suehiro et al.  combined DEP with the impedance method to selectively detect E. coli. After dielectrophoretic trapping of bacteria, antibodies were added to agglutinate target bacteria. Agglutinated bacteria whose apparent size increased experienced greater DEP forces and were thus trapped in the gap of the electrodes, while other non-agglutinated non-target bacterial cells were washed out in the wash steps. They also immobilized anti-E. coli antibodies onto the electrode surfaces so that only antibody-specific bacteria would be bound to the electrode. Cells were collected by DEP in the gaps between the electrodes, and then impedance changes due to the captured cells were monitored . The same group reported an improved DEP impedance method to detect E. coli by combining DEP with electropermeabilization (EP) . E. coli cells in suspension were captured onto an interdigitated microelectrode array by positive DEP. EP was then performed by applying a high AC electrical field to the trapped bacteria which led to intracellular ion release through damaged cell membranes, and caused an increase in conductance. Using this method, 102 cfu/ml of E. coli was detected in 3 h.
These studies have demonstrated that DEP is a useful technique to develop advanced multifunctional detection methods for rapid detection of microorganisms. In these detection methods, cells are manipulated by DEP prior to various detection steps, which may involve antibody-based immunoreaction, bacterial growth/metabolism, or DNA analysis. Since cells are exposed to AC electrical fields during DEP manipulation, it is imperative to examine whether such electrical field exposure induces undesirable effects on the cells which may affect the analytical performance in these subsequent detection procedures. A number of studies have shown that pulse and DC electrical fields applicable to electroporation and cell fusion can seriously alter the characteristics of mammalian cells. These effects include alteration in cell membrane potentials and cell membrane structures [29–31], cell deformation [29, 31–33], and increases in cell membrane permeability [32–34]. Wang et al.  studied the effects of AC field exposure on the viability and proliferation of mammalian cells in DEP manipulation, and found that extended lag phases in cell growth following electrical field exposure were due to toxic reactions of cells with electrochemical species produced at the electrodes. However, other studies have reported that DEP treatment has no serious effect on cells. For instance, Huang et al.  found that DEP forces had little effect on cell survival or stress by analyzing the expression of the stress-related gene c-fos. A number of studies showed that DEP did not cause major damages to various types of cells, including erythrocytes [36, 37], yeast cells , and CD34+ cells . Some other studies have reported that DEP treatment's effect largely depends on the experimental conditions. Wang et al.  and Altomare et al.  examined the effects of experimental DEP on tumor cell growth kinetics and their ability to undergo differentiation. They concluded that DEP induced effects on tested tumor cells depended on the buffer used in the experiments. However, these studies have been mostly focused on mammalian cells; little has been done to study the DEP effects on bacterial cells. In our previous study, we found that the expression of L. monocytogenes antigens that are specific for C11E9 monoclonal antibody increased ~2–3 folds after Listeria cells were manipulated by DEP .
In this study, we investigated the effects of DEP on the immuno-reactivity of Listeria monocytogenes cells to several anti-Listeria antibodies using enzyme-linked immunosorbant assays (ELISA), on the cell growth profile in liquid medium, and on the cell viability on selective agar plates. These cell characteristics are commonly used in various detection techniques, such as antibody-based tests and growth-based tests, to detect bacterial cells. The results from this study are useful for the selection of experimental DEP conditions for concentration and manipulation of Listeria cells to avoid or minimize possible negative effects in integrated detection methods.
Listeria monocytogenes V7 culture, a milk isolate of serovar 1/2a was grown in brain heart infusion (BHI) broth at 37°C for 16–18 h in a shaker incubator with a constant agitation at 140 rpm. The cells were pelleted by centrifugation (Eppendorf, Westbury, NY)) at 6,000 × g for 5 min and resuspended in sterilized deionized (DI) water. The cell numbers were determined by surface plating 0.1 ml of appropriate dilutions onto modified oxford agar (MOX) (Difco, Sparks, MD). Colonies were counted after incubation of the plates at 37°C for 24 h. The concentration of cells in the culture averaged about 109 colony forming units per milliliter (cfu/ml).
L. monocytogenes cells were stained with 3,3'-dihexyloxacarbocyanine iodide (DiOC6(3)) dye (green) (Molecular Probes, Eugene, OR) for visualization purposes under a fluorescence microscope. All stained bacteria suspensions were washed and centrifuged with DI water for 4 to 5 times to remove excess dye molecules. Serial dilutions were prepared in DI water for further applications when needed.
For DEP treatment, 50 μl of L. monocytogenes cells (108–109 cfu/ml) was introduced into the chamber, and a glass cover was used to cover the chamber to prevent evaporation. The chamber was allowed to sit for at least 2 h at room temperature to let the bacterial cells settle on the surfaces of the electrodes. An Agilent 33120A arbitrary waveform generator (Agilent Technologies, Inc., Palo Alto, CA) was used to apply a sinusoidal voltage to the DEP electrodes at 20 Vpp with different frequencies for desired test periods. For control experiments, the same number of cells were processed in the same way but no DEP voltage was applied. Then the DEP-treated and -untreated cells were examined in parallel for their reactivity to different antibodies using ELISA methods, their growth profile using real time pH measurements, and their viability using conventional plating methods.
Aliquots of 50 μl (109 cfu/ml) of DEP-treated and -untreated Listeria cells were dispensed into the wells of a flat-bottomed 96-well microtiter plates (1B Immulon, ThermoLabsystems, Milford, MA). The plate was incubated overnight at 4°C and the wells were washed with phosphate buffered saline (PBS) containing 0.5% Tween 20 (PBST, pH 7.4) to remove unbound cells. Mouse anti-Listeria monoclonal antibody C11E9 (MAb-C11E9) (0.02 mg/ml) , rabbit polyclonal antibody Lm404 (PAb Lm404), rabbit polyclonal antibody C639 (PAb C639) ; and horseradish peroxidase (HRP) conjugated anti-Listeria polyclonal antibody from KPL (cat# 04-90-90, KPL Inc., Gaithersburg, MD) were used to study the reactivity of the cells to these antibodies. C11E9 belongs to the IgG2b subclass and reacts with 5 different surface antigens with a major reactive antigen being the 66-kDa N-acetylmuramidase . PAb Lm404 and PAb C639 react with Internalin B (inlB) and Actin polymerization protein A (ActA) on Listeria cell surfaces . These antibodies were added to the bacteria-coated wells, and the plate was incubated for 1 h at 37°C, with constant shaking. After washing three times with PBST to remove unbound antibodies, 100 μl (1:5000) of HRP-conjugated anti-mouse (for C11E9) or anti-rabbit (for PAb Lm404 and PAb C639) secondary antibody (Jackson Immuno Research Laboratories, Westgrove, PA) was added to each well. After washing three times with PBST, the substrate O-phenylene diamine (OPD) (Sigma, St. Louis, MO) was added to those wells to develop color products for absorbance measurements. The wells containing KPL anti-Listeria antibody were developed by directly adding the OPD substrate solution, since the KPL antibody was HRP conjugated. The reactions were stopped after 15 min by adding 100 μl 0.1 M HCl into each well. The absorbance of each well was read at 490 nm using an ELISA reader (Bio-Rad, Hercules, CA).
The pH measurement procedure was similar to that of our previous study . Aliquots of 50 μl of DEP-treated or -untreated sample were introduced into 15 ml of the BioV LCGM™ growth medium (BioVitesse, Inc., San Jose, CA)  in a 50 ml centrifuge tube (Becton Dickinson Labware, Franklin Lakes, NJ). The tube was then placed in an incubator (Lab-Line Instruments, Inc. Melrose Park, IL) and kept at 37 ± 0.5°C. The pH of the sample was measured using a pH probe (Serial No. JC05708, Jenco, San Diego, CA) immersed in the medium. pH data was collected every 5 min during the growth of L. monocytogenes within a total testing period of 18 h. pH growth curves were obtained by plotting the pH value as a function of growth time.
The DEP-treated or -untreated cells were serially diluted with DI water. The viable cell numbers were determined by surface plating appropriate dilutions onto MOX agar. MOX agar is a selective growth medium for Listeria cells, to which antibiotic agents are added to suppress the growth of other competing microflora. Thus, in the presence of these selective agents, the injured or stressed cells are unable to grow and form characteristic colonies on this agar. The difference in the number of colony-forming units of DEP-treated and -untreated samples indicates the number/percentage of the injured or stressed cells due to cell exposure to the DEP electrical field.
The bright field and fluorescence images were taken on a Nikon ECLIPSE E600FN fluorescence microscope (Japan) attached with a CCD camera (Pixera, Los Gatos, CA). Fluorescence images were taken using the FITC (Fluorescin isothiocyanate) – specific filter.
Listeria cells collected on the chip by DEP were air-dried overnight at room temperature. The chip was directly imaged using a Hitachi S 4800 FESEM microscope (Tokyo, Japan) without coating. Acceleration voltage was kept constant at 2.0 kV. Images were acquired digitally using Quartz PCI v.7 software (Hitachi High-Technologies Canada, Inc. Resdale, Ontario, Canada).
Significant differences were determined by the standard ANOVA and Tukey's-test, using SAS 9.1 software (SAS Institute Inc., Cary, NC).
The main component of any dielectrophoresis system is formed by the electrodes on which the AC electrical field is applied. The electrode configuration which determines the generated non-uniform electrical field is one of the important factors for efficient dielectrophoretic collection of biological cells. Many different electrode configurations have been reported to realize desirable cell trapping in micro-scale dielectrophoresis systems. Electrode structures made from thin wires, such as cone-plate electrodes [44, 45], simple pin-plate structures , and four-pole electrodes , have been used for dielectrophoretic characterization of cells. More recently, different microfabricated electrodes have played a major role in dielectrophoresis devices. Examples include planar polynomial microelectrodes arrays for trapping different types of cells at different locations by using positive and negative DEP , various three-dimensional microelectrode arrays for cell position, more complex 3-D extruded quadrupole structures for trapping single cells and particles [48–50], and a novel "points-and-lid" microelectrode system for DEP registration of single mammalian cells to a microelectrode .
The planar interdigitated array (IDA) microelectrode (shown in Fig. 1a) is perhaps the simplest electrode structure that has been used successfully in DEP manipulation of bacteria cells. Such a microelectrode can be readily integrated with micro-fluidic channels. Fig. 1b shows the schematic of the electrical field generated by the IDA electrodes. The electrical field has its maximum gradient and strength at the edges of the digit electrodes and the minimum at the centers of the digit electrodes and the gaps between the digit electrodes. When cells are placed in this non-uniform electrical field, they will experience positive DEP or negative DEP depending on the DEP operation frequency and the relative polarizability of the cells with respect to the medium (Fig. 1b). Positive DEP forces will direct cells to the edges of these digit electrodes where the electrical field is stronger, while negative DEP will move cells towards the centers of the digit electrodes or the gaps between the electrodes where the electrical field is weaker.
For DEP manipulation of biological cells, cells are usually suspended in low conductivity buffers. Buffers for suspending mammalian cells usually contain different sugars, such as a Tris-Boric acid-EDTA buffer supplemented with 250 mM sucrose having a conductivity of ~10 μS/cm , and another buffer consisting of 8.5% (w/v) sucrose plus 0.3% (w/v) dextrose having a conductivity of 50 μS/cm . Deionized (DI) water is often used for suspending bacterial cells for DEP manipulation [9, 24–26]. In this study, we used DI water to suspend Listeria cells for all the experiments. DI water has its conductivity in a range from 1–2 μS/cm to about 10–15 μS/cm. In DEP manipulation, most likely, at low frequencies, the electrical field is mainly dropped across the outermost membranes of the cells. The cells behave as poorly conductive spheres [6, 9]. As the frequency increases, the applied field gradually penetrates into the cells. The cells then behave as more conductive spheres with high permittivity of the cell interior . At low frequency (ω <<σ/ε), Eq. 2 can be approximated by :
f CM = (σ p - σ m )/(σ p + 2σ m ) (3)
While at high frequency (ω >> σ/ε):
f CM = (ε p - ε m )/(ε p + 2ε m ) (4)
Thus it is possible that cells exhibit negative DEP at low frequency if σp <σm, (Re[fCM] < 0 in Eq. 1) and positive DEP at high frequency if εp > εm (Re[fCM] < 0 in Eq. 1). It is also known that in positive DEP, cells are collected at the electrode edges where electrical field is the strongest. One can imagine that cells experiencing positive DEP at higher frequencies would more likely be affected by the electrical field compared with cells experiencing negative DEP at lower frequencies.
In practice, when DEP is used to concentrate or capture cells in micro-fluidic devices for subsequent detection, higher frequencies and voltages are usually required to achieve efficient capture of bacterial cells from the flow. Gomez et al.  reported that an AC signal at 3 MHz and 20 Vpp were needed to maximize the DEP forces acting on L. innocua cells to capture them from the Luria-Bertani broth. Yang et al.  reported that L. monocytogenes cells in the flow of DI water were captured by DEP at a frequency of 1 MHz and 20 Vpp. Verduzco-Luque et al.  used DEP to manipulate cells to make biofilms. They showed that Saccharomyces pombe cells suspended in DI water were oriented at right angles to the electrical field at 80 MHz and 3.5 Vpp. Patterning of 3T3 mouse fibroblast cells suspended in a 480 mM mannitol solution into the gaps between microelectrodes was achieved by positive DEP at 1 MHz and 20 Vpp . Suehiro et al.  used IDA microelectrodes to trap E. coli cells using DEP at 100 kHz and 5 Vpp onto the electrode surfaces for impedance measurements. Considering the DEP parameters used in these studies and the effectiveness of DEP manipulation of Listeria cells in microfluidic and/or non-fluidic devices, we selected DEP at 5 MHz and 20 Vpp for manipulation of Listeria cells in microdevices, and examined the effects of DEP on the immuno-reactivity of Listeria cells to several Listeria- specific antibodies, on cell growth profile in LCGM medium, and on cell viability on MOX agar plates.
Many rapid methods for bacteria detection, such as traditional ELISA or derived ELISA methods, and more recently developed biosensor methods, use an antibody-cell bioaffinity reaction in a sandwich immunoassay format, which involves the formation of immuno-complexes consisting of immobilized antibodies, captured target bacteria and enzyme-labeled antibodies. Most microchip-based methods that use DEP as a concentration step use antibodies to selectively capture target bacterial cells. Therefore, it is logical to examine whether DEP treatment affects the immuno-reactivity of the cells to those antibodies. In our previous study, we found that the number of C11E9 monoclonal antibody binding sites on Listeria cells increased from ~5 binding sites per cell to ~10 binding sites per cell upon the DEP treatment when analyzed by SEM .
In this study, using ELISA methods, we examined the reactivity of DEP-treated and -untreated Listeria cells to monoclonal C11E9 antibody, polyclonal anti-Internalin B (InlB) antibody, polyclonal anti-Actin polymerization protein A (ActA) antibody, and a commercial polyclonal anti-Listeria antibody (KPL). InlB and ActA are two major virulence proteins in L. monocytogenes that are expressed on the cell surface. These proteins are required for L. monocytogenes' entry and intracellular movement inside eukaryotic cells, respectively, and are credible targets for detection of pathogenic L. monocytogenes. Previous studies have shown that the reactivity of Listeria cells to these antibodies was affected by changes in environmental conditions [40, 41, 58, 59], thus influencing the performance of detection of Listeria cells using these antibodies. For example, Geng et al.  reported that the reactivity of L. monocytogenes cells to a polyclonal antibody and the monoclonal C11E9 antibody was related to the types of growth medium in which the cells were grown. L. monocytogenes subjected to stress (acid, cold, heat, and salt) and then grown in a buffered Listeria enrichment broth (BLEB) had the greater immuno-reactivity to anti-Listeria polyclonal antibody, while those grown in Listeria repair broth (LRB) had the greater immuno-reactivity to MAb C11E9. They also found that heat or osmotically stress environments reduced the reactivity of L. monocytogenes cells to MAb C11E9 and EM-7G1 antibodies , thus affected the detection of L. monocytogenes using these antibodies. Therefore, understanding the influence of DEP on the immuno-reactivity of Listeria cells is essential to the selection and integration of the best detection antibodies for further applications.
None of the antibodies tested in this study displayed any significant decrease in the ELISA signals, suggesting that the use of DEP as a tool to manipulate bacterial cells in micro-devices or other biosensors would not affect the subsequent immuno-based detection of Listeria. On the contrary, DEP can sometimes enhance the signals of immuno-based detection using some antibodies, e.g. C11E9 and KPL antibodies to Listeria cells.
A number of recently developed methods for rapid detection of bacteria are growth-based methods in which cell growth is a requirement of the detection procedure, such as impedance measurements [60, 61], pH and conductivity dual measurements , and electrochemical measurements of oxygen consumption . In these methods, regardless of the type of the signals, the detection or the quantification of bacterial concentration in a sample is based on the metabolic activity of the cells which produces a detectable signal. One of the most attractive advantages of these growth based methods is that they allow us to distinguish between viable and dead cells. Recent advances in microfabrication technologies have enabled scientists to fabricate micro-devices and have promoted these growth based methods to a more sensitive micro-chip-based stage. For example, a technique of "Impedance microbiology-on-a-chip" has been demonstrated by Gomez and coworkers . The basic idea was to confine a few live bacterial cells into a small volume on the order of nano- to pico- liters, so that the metabolism of a few live cells in a low conductivity buffer could be rapidly detected by impedance measurement. DEP has been proven to be an effective approach to confine a few live cells into such micro-chips. However, this approach brought our attention to the possible effects of DEP treatment on cell growth profile in liquid medium.
As shown in Fig. 5 (panel A), the Listeria cell sample treated by DEP at 5 MHz and 20 Vpp for 1 h has the same growth profile as the control sample, indicating that the 1h DEP treatment did not cause any significant change in cell growth profile in the LCGM medium. However, as seen in Fig. 5 (panel B and C), prolonged DEP treatments (4h and overnight) cause shifts in the pH-growth curves in comparison with those of control samples. The detection times of the samples treated with DEP for 4h or overnight were delayed by 1–2 h compared to the control samples without DEP treatments. The delays in the detection times implies that there were fewer viable cells or more damaged cells in the samples after prolonged (4h or longer) DEP treatment. The population of damaged cells may include the stressed cells, slow-growing cells, severely damaged and non-growing cells, and possibly dead cells. It is suspected that many membrane enzymes may absorb and transduce energy from the oscillating field during the exposure of cells to AC electrical fields . This alteration may cause cell damage, cell stress, slow cell growth, and even cell death. Other possible alterations, such as cell membrane potential and structure changes, deformation, and increased membrane permeability, as mentioned above, may in combination affect cell growth. Studies have shown that exposure of 3T3 fibroblast cells to a high frequency field (1–40 MHz) extended cell cycle time from 18 h to 26 h [63, 64]. We can also see in Fig. 5 (panel D) that the pH growth curve of the sample with DEP treatment at 15 MHz and 20 Vpp is the same as the control sample, indicating that the treatment of DEP at 15 MHz and 20 Vpp for 1 h did not cause any change in cell growth. These results suggest that the duration of DEP treatment, rather than the frequency of the DEP voltage, is a factor that induces the damages in cells. Therefore, DEP manipulation of bacterial cells for short durations (less than 1 h) is recommended when the cells will be analyzed by subsequent cell growth procedures.
Viable cell numbers of the tested samples before and after DEP treatment determined by plate counting on MOX plates, along with the calculated percentage differences.
Cell number before DEP treatment (in 50 μl)
Cell number after DEP treatment (in 50 μl)
(2.60 ± 0.99) × 108
(6.30 ± 0.71) × 107
(4.60 ± 0.61) × 108
(4.70 ± 1.41) × 107
(4.75 ± 1.27) × 108
(2.05 ± 0.87) × 108
(1.60 ± 0.41) × 108
(3.30 ± 0.64) × 107
It is believed that at such high frequency, the electrical field could penetrate to the interior of the cell as they experience positive DEP in DI water. It is reported that cells could be lysed by electroporation and/or electrofusion if the induced membrane potential exceeds ~1 V (Pethig, 1991). For cells with a radius of around 2.5–5 μm, an applied electrical field lower than about 1–3 × 105 V/m would not produce such effects . In our experiments, the calculated maximum electrical field was about 8 × 105 V/m (20 V/25 μm), but we did not observe any cell lyses under the experimental condition, which may be due to the difference in cell types.
The results in growth profile tests and viability tests showed that long duration of cell exposure to DEP electrical fields could cause bacterial cell damage and affected cell growth and viability, which could induce undesirable effects on cell growth-based detection methods (delays in detection time, decreases in viable cell number). These findings suggested that experimental conditions of DEP should be taken into consideration to avoid or minimize negative effects on subsequent cell detection performance.
In this study, we investigated the effects of DEP on the immuno-reactivity to different antibodies, growth profile, and cell viability. The immuno-reactivity tests using ELISA showed that the immuno-reactivity to KPL anti-Listeria antibodies and to C11E9 monoclonal antibodies was enhanced after DEP treatment, whereas the immuno-reactivity to other two antibodies (PAb Lm404 and PAb C639) showed no significant change. DEP treatment of 1 h (5 MHz or 15 MHz and 20 Vpp) caused no change in Listeria growth profiles in LCGM medium; however, longer treatment time (4 h or longer) did cause shifts in the pH-based growth curve, which was due to the reduced number of viable cells in the DEP-treated samples. It was found that 56.8–86.7% of cells in a population of 108 cfu/ml were injured by a 4 h DEP treatment at 5 MHz and 20 Vpp and were unable to form colonies on MOX selective agar plates. These results suggest that prolonged DEP treatment/operation for manipulating bacterial cells could produce negative effects on cell detection, particularly when it is used as a pre-concentration step prior to growth-based detection. For immuno-based detection, DEP manipulation may or may not affect the final detection signal depending on the type of antigen-antibody involved. It should be noted, however, that other alterations (from gene expression to cell morphology) may occur to DEP manipulated cells and may affect other biological functions of the cells; other factors such as medium conductivity and electrode materials may possibly affect the extent of DEP effects on cell functions; and these remained to be elucidated.
Biomedical and Biological Micro-Electro-Mechanical Systems (MEMS) technology has shown tremendous potentials in the development of new devices and sensors with scales and dimensions similar to biological species for a variety of applications in diagnostics, sensing and characterization of biological entities. DEP technique has been proven to be a powerful tool for manipulating biological entities in such engineering microfabricated microdevices. The integration of DEP will advance the performance of various biosensors, microfluidic chips, and lab-on-a-chip devices by providing multi-functions such as cell concentration, separation or sorting, and enhancement of immunoreaction in these microdevices. This study brings attention to the need for careful selection of DEP conditions for manipulation of biological entities to avoid or minimize possible negative effects on biological detection in DEP integrated microdevices.
LY acknowledges the research support from Faculty Scholarly/Creative Productivity Initiative at North Carolina Central University. RB and AKB acknowledge the research support through a cooperative agreement with the Agricultural Research Service of the United States Department of Agriculture, project number 1935-42000-035.
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