The Organic Electrochemical Transistor is integrated with live cells and used to monitor ion flux across the gastrointestinal epithelial barrier. In this study, an increase in ion flux, related to disruption of tight junctions, induced by the presence of the calcium chelator EGTA (ethylene glycol-bis(beta-aminoethyl ether)-N,N,N’,N’-tetra acetic acid), is measured.
The gastrointestinal tract is an example of barrier tissue that provides a physical barrier against entry of pathogens and toxins, while allowing the passage of necessary ions and molecules. A breach in this barrier can be caused by a reduction in the extracellular calcium concentration. This reduction in calcium concentration causes a conformational change in proteins involved in the sealing of the barrier, leading to an increase of the paracellular flux. To mimic this effect the calcium chelator ethylene glycol-bis(beta-aminoethyl ether)-N,N,N',N'-tetra acetic acid (EGTA) was used on a monolayer of cells known to be representative of the gastrointestinal tract. Different methods to detect the disruption of the barrier tissue already exist, such as immunofluorescence and permeability assays. However, these methods are time-consuming and costly and not suited to dynamic or high-throughput measurements. Electronic methods for measuring barrier tissue integrity also exist for measurement of the transepithelial resistance (TER), however these are often costly and complex. The development of rapid, cheap, and sensitive methods is urgently needed as the integrity of barrier tissue is a key parameter in drug discovery and pathogen/toxin diagnostics. The organic electrochemical transistor (OECT) integrated with barrier tissue forming cells has been shown as a new device capable of dynamically monitoring barrier tissue integrity. The device is able to measure minute variations in ionic flux with unprecedented temporal resolution and sensitivity, in real time, as an indicator of barrier tissue integrity. This new method is based on a simple device that can be compatible with high throughput screening applications and fabricated at low cost.
The gastrointestinal epithelium is an example of barrier tissue, which controls the passage of molecules between different compartments of the body. The epithelium consists of elongated columnar cells joined together by complexes of proteins that provide a physical barrier1 against pathogens and toxins, while allowing the passage of water and nutrients required to sustain the body. This selectivity is due to the polarization of the epithelial cells, which creates two different membrane domains: the apical side of the cells exposed to the lumen and the basal side of the cells anchored on the underlying tissues2,3. Tight junctions (TJ) are complexes of proteins present at the apical portion of epithelial cells and are part of a larger complex known as the apical junction4. Ion flow across the barrier tissue may either go via the transcellular (through the cell) or via a paracellular (between two adjacent cells) pathway. The sum of the transport through both pathways is known as the transepithelial resistance. The apical junction is responsible for the regulation of ions and molecules passing across the barrier5,6 via a specific opening and closing function. A dysfunction or disruption of these protein complexes is often related to disease7-11. In addition, many enteric pathogens/toxins are known to specifically target this complex, thereby entering the body and leading to diarrhea, most likely as a consequence of massive dysregulation of ion/water flow across the barrier12-14. Barrier tissue may also be modified by changing the extracellular microenvironment. Cadherin is a critical protein for cell-cell adhesion, and is involved in the formation of the apical junction. Calcium is required for the correct structural conformation of Cadherin, and a decrease in extracellular calcium has been shown to result in the destruction of the cell-cell junction and a subsequent opening of the paracellular pathway between the cells15. In this study, EGTA (Ethylene glycol-bis(beta-aminoethyl ether)-N,N,N',N'-tetra acetic acid), a specific calcium chelator, was used to induce a breach in barrier tissue, as it has been shown to have a rapid and drastic effect on paracellular ion flow16,17. This calcium chelator was used on a confluent and differentiated monolayer of the Caco-2 cell-line. Cultured in cell culture inserts, this cell line is known to develop the characteristics of the gastrointestinal tract and is widely used by the pharmaceutical industry to test the absorption of drugs18,19.
Methods to monitor barrier tissue integrity are plentiful. These methods are often optical, relying on immunofluorescence staining of particular proteins known to be at the apical junction20, or relying on the quantification of a fluorescent tracer molecule that is normally impermeable to the barrier tissue21,22. However, label-free methods (i.e. without a fluorophore/chromophore) are preferable as the use of a label can incur artifacts, and often increases cost and assay time. Electrical, label-free monitoring of barrier tissue has recently emerged as a dynamic monitoring method23. For example recent technological advances in electrical impedance spectroscopy have allowed the development of a commercially available scanning apparatus24,25 that can measure transepithelial resistance (TER), a measurement of the ion conductance across the cell layer.
Organic electronics has created a unique opportunity to interface the world of electronics and biology26,27 28,29 by using conducting polymers that can conduct both electronic and ionic carriers. A new technique to detect breaches in barrier tissue using the OECT30-32 was recently introduced. This device was validated against existing techniques used to assess barrier tissue integrity, including immunofluorescence, permeability assays using Lucifer yellow, and impedance spectroscopy using the Cellzscope. In the case of all toxic compounds tested, the OECT was found to operate with equal or better sensitivity, and with increased temporal resolution, compared to the above techniques. In this device, PEDOT:PSS, a conducting polymer that has been shown to be stable and biocompatible33,34, is used as the active material in the transistor channel. The OECT is composed of drain and source electrodes on either side of a conducting polymer channel. This is then placed in contact with an electrolyte, which forms an integral part of the device. A gate electrode is immersed in the electrolyte (Figure 1), and when a positive gate voltage is applied at the gate, cations from the electrolyte are forced into the channel, thus dedoping the conducting polymer and resulting in a change in the source-drain current. The device is thus extremely sensitive to minute changes in ionic flux due to amplification by the transistor. A cell layer grown on a cell culture insert was placed between the gate electrode and the conducting polymer channel. The presence of an intact cell layer acts as barrier for the cations entering into the conducting polymer, therefore, in the presence of an intact monolayer, the drain current decreases (Figure 2: transition from region a to b). In the presence of a toxic compound, the barrier tissue will progressively lose its integrity, letting the cations enter into the polymer film and increasing the drain current (Figure 2: region c). With this technique, the breach in barrier tissue is seen by the modulation of the drain current, corresponding to the modulation of the flux across the monolayer. This device is able to measure minute variations in ionic flux with unprecedented temporal resolution and sensitivity in real time. This technology will be of interest in the domain of toxicology for drug testing, disease diagnostics or basic research as the barrier model can be easily adapted. This method will also help to reduce animal experimentation, as it allows the validation of in vitro models to replace in vivo testing.
1. PEDOT:PSS Solution Preparation
2. OECT Fabrication (Figure 3)
3. Device Assembly
4. Cell Culture
5. Measurements with OECT
6. Integrating Cells with OECT for Measurement
Note: Prior to the experiment, the integrity of the cell layer may be verified by measuring TER with an Impedance spectroscopy device. TER of each 3-week old Caco-2 cell insert should be above 400 Ω.cm2.
7. Preparation and Introduction of Toxic Compound
During the first step of measurement, the drain current may vary somewhat, but in most cases it should remain stable (Figure 2, section a). If the signal is not stable, the transistor should be discarded and replaced. This stability check also ensures that any initial losses in conductivity of the device do not affect the subsequent measurement. After several minutes of measurement, the insert with cells forming barrier tissue is placed on top of the channel. The drain current should immediately decrease (Figure 2, section b.). If the drain current does not decrease, this could imply that the cells have not correctly formed a barrier, or were damaged during manipulation, and the filter should be discarded and replaced. By adding a toxic compound to the barrier tissue, the modulation of the drain current should increase progressively or immediately, depending on the compound used and the concentration (Figure 2, section c.).
Data were collected using a sourcemeter and a customized acquisition program. From this program different parameters were obtained, which are run in a data analysis program to obtain the mid-modulation corresponding to each gate pulse. The mid modulation corresponds to the value of the current at the middle of the peak (Figure 4). The mid modulation values obtained during sensing of an intact monolayer were normalized to 0 while the mid modulation obtained after the scratch were normalized to 1. Normalized results are used to compare data from different devices (Figure 5). From this data the dose response of difference concentrations of toxic compound over time can be seen.
Figure 1. Schematic of an Organic Electrochemical Transistor integrated with cell culture insert a) from a side view. b) Top view of channel (grey) and contact (yellow) dimensions on a glass slide with a channel length of 6mm and channel width of 1 mm. This figure has been modified from Jimison30.
Figure 2. Overview of in situ measurement of drain current response to square gate pulses over time. Measurement conditions are: VDS = -0.2 V, VGS = 0.3 V, VGS on time = 2 sec, off time = 28 sec. a) Corresponds to the OECT operated before integration with cells, ensuring the stability of the device. b) Corresponds to the integration of the barrier tissue forming cells, again ensuring a stable signal before commencing testing of toxic compound. c) Corresponds to the addition of EGTA to the barrier tissue cells, note the evolution of the signal over time.
Figure 3. Fabrication processes of the OECT. Click here to view larger image.
Figure 4. OECT drain current response to a single square gate pulse. Measurement conditions are as follows: VDS = -0.2 V, VGS = 0.3 V, VGS on time = 2 sec, off time = 28 sec. a) OECT transient response before (dashed line) and after (blue line) the addition of barrier tissue forming cells grown on a filter. b) OECT transient response after the addition of toxic compound on a barrier tissue (orange line) and without barrier tissue (dashed line).
Figure 5. Typical normalized result From the OECT. The normalized response of the OECT on introduction of device (empty circle), cell layer (black cross), 5 mM EGTA (dark blue circle) and 10 mM EGTA (cyan circle) introduced at t = 0, were measured over a period of 50 min. Click here to view larger image.
This technique provides a novel method to integrate an organic electrochemical transistor with live cells to measure barrier tissue integrity. The main advantages of this technique are the rapidity and sensitivity, but also the low cost of the device for dynamic monitoring of barrier tissue.
As this method uses live cells, a critical point is to be sure to use a monolayer, which represents an intact barrier layer. The parameters of the barrier should be defined during the characterization of the cell line. It is therefore crucial not to damage the cell layer when the gate electrode is immersed in the electrolyte on top of the cell layer.
Another important point is the fabrication of the device; no leakage should occur between the edge of the PDMS and the plastic holder to avoid liquid volume variation. In order to achieve reproducible results, attention should be also given to the soldering of the wire, as burning the gold electrode will result in poor/no contact with the conducting polymer channel and so poor/no signal.
To facilitate the analysis and to obtain better results a few minutes delay between each step of the experiment should be allowed for the device to stabilize between steps. As a variation of the signal from device to device is observed, normalization of results is required to be able to compare the results of each experiment. However, in the future larger scale production of the device will allow greater device-device reproducibility.
The main limitation of the technique is the format, as for the moment only one sample can be measured. This will be solved soon by the development of a multiacquisition sensor and in the future the creation of a 96-well plate format. This will open the way for this technique for use in high throughput screening of barrier tissue. In parallel, planar devices are also under development to allow simultaneous optical and electronic measurements.
In summary, a novel device that can be fabricated at low cost that is capable of label-free monitoring of barrier tissue has been developed. This device shows greater sensitivity and higher temporal resolution than existing methods. The integration of in vitro models with devices such as the OECT can be a great alternative to animal testing for drug discover and toxicology.
The authors have nothing to disclose.
The authors of this paper do not have any competing financial interests.
CLEVIOS PH 1000 | HERAUS CLEVIOS | ||
AZ9260 resin | CIPEC SPECIALITIES | ||
Dodecylbenzenesulfonic acid (DBSA) | Acros Organic | ||
3-glycidoxypropyltrimethoxysilane (GOPS) | Sigma Aldrich | ||
24-well Suspended cell Culture insert Millicell PET 0.4 μm Millipore | Dominique dutscher | 51705 | |
24-well cell culture plate BD Falcon | Dominique dutscher | 51705 | |
STERICUP-GP PES 0.22 μM | Dominique dutscher | 51246 | |
ADVANCED DMEM Marque GIBCO | Fisher scientific | E3434T | |
FBS HEAT INACT. S.AMERICAN | Fisher scientific | E3387M | |
PENICILLIN STREPTOMYCIN | Fisher scientific | E3470C | |
GLUTAMAX | Fisher scientific | E3524T | |
TRYPSIN 0.05% EDTA | Fisher scientific | E3513N | |
EGTA (Ethylene glycol-bis(2-aminoethylether)-N,N,N′,N′-tetraacetic acid) | Sigma Aldrich | E4378 | |
ETHYLENE GLYCOL, ANHYDROUS, 99.8%, | Sigma aldrich | ||
Caco-2 cells | ATCC | ||
PDMS | Dow corning | SYLGARD 184 SILICONE ELASTOMER | |
Au (99.99%) | NEYCO | AU3X6 | |
Chromium (99.95%) | NEYCO | ||
Parylene C | Specialty Coating Systems | ||
Ag/AgCl wire | HARVARD APPARATUS | ||
Photoresist | CIPEC SPECIALITIES | Résine AZ9260 |