A lab-on-a-chip for hypoxic patch clamp measurements combined with optical tweezers and spectroscopy- first investigations of single biological cells
© Alrifaiy et al.; licensee BioMed Central Ltd. 2015
Received: 29 August 2014
Accepted: 17 March 2015
Published: 18 April 2015
The response and the reaction of the brain system to hypoxia is a vital research subject that requires special instrumentation. With this research subject in focus, a new multifunctional lab-on-a-chip (LOC) system with control over the oxygen content for studies on biological cells was developed. The chip was designed to incorporate the patch clamp technique, optical tweezers and absorption spectroscopy. The performance of the LOC was tested by a series of experiments. The oxygen content within the channels of the LOC was monitored by an oxygen sensor and verified by simultaneously studying the oxygenation state of chicken red blood cells (RBCs) with absorption spectra. The chicken RBCs were manipulated optically and steered in three dimensions towards a patch-clamp micropipette in a closed microfluidic channel. The oxygen level within the channels could be changed from a normoxic value of 18% O 2 to an anoxic value of 0.0-0.5% O 2. A time series of 3 experiments were performed, showing that the spectral transfer from the oxygenated to the deoxygenated state occurred after about 227 ± 1 s and a fully developed deoxygenated spectrum was observed after 298 ± 1 s, a mean value of 3 experiments. The tightness of the chamber to oxygen diffusion was verified by stopping the flow into the channel system while continuously recording absorption spectra showing an unchanged deoxygenated state during 5400 ± 2 s. A transfer of the oxygenated absorption spectra was achieved after 426 ± 1 s when exposing the cell to normoxic buffer. This showed the long time viability of the investigated cells. Successful patching and sealing were established on a trapped RBC and the whole-cell access (Ra) and membrane (Rm) resistances were measured to be 5.033 ± 0.412 M Ω and 889.7 ± 1.74 M Ω respectively.
KeywordsMicrofluidic system Hypoxia Patch clamp Optical tweezers Absorption spectroscopy Oxygen sensor
The patch clamp technique  is a significant tool in electrophysiology for high resolution investigations of the ionic current activities through the membrane of living biological cells. The technique provides critical insight into wide ranging applications in the fields of neuroscience, biology, pharmacology, and many other related biomedical research disciplines. The electrophysiological activity of individual biological cells are measured and analyzed by high-resolution current-, and voltage recordings of whole cells, through single ion channels or removed cellular patches. In patch clamp experiments the biological cells are exposed to fast changing environmental stimuli created by an open perfusion system. The electrical signaling activity across the plasma membrane of the cell is recorded through an electrode placed in the extracellular environment close to the cell and another recording electrode that is placed in the micro-pipette of borosilicate glass. The tip of the pipette is patched to the cell membrane to perform recordings on the cell under varying stimuli. Patch clamp is one of the most challenging methods in daily laboratory work. The technique needs highly sensitive equipment and operators must have high experimental skills.
Many attempts have been made to modify the traditional patch clamp technique . Planar patch clamp  is the most reported one; it bases on planar microfluidic chip substrates of 1-2 micro-sized holes for capturing the cells from suspension by means of suction. The cells are sealed to the substrate by applying suction pulses or pore-forming compounds for whole cell and perforated patch recordings respectively. The benefits are the multiple cell recordings by arrays of apertures, lower cost and data throughput. The main challenges associated with planar platforms are the lower data quality outputs by a reduced electrical seal between the recording substrate and the cellular membrane . Another challenge is that the G Ω-seal created here is formed as cell membrane-substrate resistive interaction, which requires improvements for measurements associated with low-noise, high-quality recordings and high temporal resolution .
Even though the planar platforms overcome some key challenges, the conventional patch clamp technique still enables the best temporal resolution, voltage control and direct measurements. The high level of flexibility and experimental possibilities for environmental exchange are valuable, necessary and usually optimized related to the nature of experiments.
Most electrophysiological studies on oxygen deprivation, e.g. stroke, are carried out either by inducing a chemical oxygen shortage or by flushing cells or tissue with oxygen free solutions in open systems. In both ways, the effective oxygen content in-situ cannot be sufficiently controlled due to the diffusion of ambient oxygen and often the oxygen content is close to the one present in vivo (about 6%) [6-9]. However, those estimations are away from providing an accurate value of the oxygenation states of the investigated cells. Many studies demonstrate the need of environmentally controlled LOC systems for biological applications . LOC devices offer important features for precise control of the amount and the dynamics of reagents within micro-sized fluidic channels connected to reservoirs, inlets and outlets. Those systems are usually fabricated in optically transparent materials [11,12], suitable for most types of optical microscopes and can be combined with other optical techniques. LOC devices, as essential tools for spatial and temporal control of cells and fluids on the micro-sized level, have been used for precisely controlled oxygen micro-environmental conditions such as gas mixing and chemical de-oxygenation [13-20]. For instance, PolyDiMethylSiloxane (PDMS)-based LOC, established on exchangeable passive diffusion of oxygen and nitrogen, have been used in hypoxic cell investigation to control oxygen concentration gradients [21-23]. However, the regulation and the generation of oxygen gradients through electrolysis in LOC for various cell assays are challenging due to the complexity to incorporate gas sources, device manufacturing and the possible impact on the well-being of the investigated cells [24-26]. Other studies that rely on oxygen content variations during cell culturing in LOCs include cell-based assays [27-31], bioreactors [32-34], and tissue engineering . Furthermore, LOC based oxygenation methods have been reported to use and treat the medium as the oxygen source [36-39]. However, the passive diffusion method is not sufficient for the demand of dense cell cultures due to the low solubility of oxygen in aqueous solutions and hence the long term diffusion time. Additionally, the devices are mainly produced of PDMS having a high oxygen permeability . Hence, full anoxic conditions cannot be established.
Innovative design is required to modify the conventional patch-clamp technique in which a micropipette is steered in three dimensions (3D) for precise attachment to the cell membrane for patching in a closed system. The promising approach presented here is to achieve control of the gaseous surroundings of the investigated cells by a gas-tight LOC system of Plexiglas with an integrated pipette for patch clamp experiments. The positioning of an individual cell in 3D within the closed micro-channel system is enabled by optical tweezers , an excellent tool to trap and manipulate biological cells. Optical tweezers use light radiation forces to trap and steer small dielectric objects in three dimensions . Experimentally, a stable optical trap is achieved by focusing a laser beam strongly through a high-numerical aperture (NA) microscope objective onto the sample. The trapped object is usually manipulated by moving the trap and/or the sample stage to the desired position.
Previously, we presented a LOC that had the capability of steering a biological cell towards a micropipette. However, the system allowed only for chemical oxygen deprivation by adding natrium dithionte and no strong cell-membrane seals, necessary for patch-clamp experiments, could be performed .
The aim of this study was to design, develop and manufacture a LOC device for electrophysiological and spectroscopic studies on viable optically trapped biological cells demanding complete oxygen level control. The oxygen level was monitored by an integrated oxygen sensor.
We present a prototype of a new developed gas-tight multifunctional LOC system for hypoxic investigations on biological cells. The PolyMethylMethAcrylate (PMMA)-based LOC was manufactured by using Computer Numerical Control (CNC) machine for simplicity and to enable quick reproducibility in shorter time and lower cost. The gas-tight efficiency and flexibility of LOC were facilitated by a new design of microfluidic channels, a novel fastening technique and smart Micro-to-Macro interconnections between the microfluidic channels and the exterior techniques, as compared to our previous work . The viability of the cells was improved by efficient cell transport into the LOC using shorter transport pathways, effective design of the channel system and enhanced fluid flow. A new concept was developed to insert the patch clamp pipette to the LOC by replacing the hollow screw, used in our previous study . The new method enabled a precise steering of the pipette into the LOC by an attached single-axel micrometer differential drive, fitted together with the LOC as a platform, placed on the stage of the microscope.
Materials and methods
Biological samples and experimental buffer solutions
RBCs from chicken (Fitzgerald Industries International, USA) were used as a sample model in this study. The cells were pre-treated by washing, brief exposure to glutaraldehyde buffer solution and exhaustive washing in saline solution before suspension in saline solution with 0.1% sodium azide. The cells were then incubated at 4°C to ensure a steady state related to ion and water contents before experimental treatment. The sample consisted of 0.05 ml RBCs diluted in 2 ml Extracellular (EC) solution at pH 7.0 and 22°C.
Extracellular physiological solution (EC) of 150 mM KCl, 10 mM CaCl 2, 5 mM MgCl 2, 1 mM MES was titrated to pH 7.0 with Tris base (Sigma Aldrich, Germany) and used as bath medium for flushing the cells.
Intracellular solution (IC) containing 195 mM KCl, 1 mM EGTA, 0.15 mM CaCl 2, 4 mM MgCl 2, 4 mM ATP, titrated to pH 7.0 with KOH was used as pipette-filling solution. The deoxygenated EC solution was prepared by purging the solution with nitrogen gas (AGA AB, Sweden). Prior to the experiment, the nitrogen flow rate was controlled and the rate of oxygen level was measured continuously by an oxygen sensor system of a fiber optics probe (FOXY, AL3000, Ocean Optics, USA) connected through MultiFrequency Phase Fluorometer (MFPF, ocean optics, USA). All solutions were prepared in bottles and sucked into the syringes of a peristaltic pump system (HPLC, K-501, Germany) and a programmable pump system (neMESYS, Cetoni, Germany).
Optical tweezers  were built upon an near infrared (NIR)-diode laser (Renishaw, UK), with a square beam profile (size 5 mm) operating at 830 nm ± 1 nm with an average power of 300 mW ± 30 mW. The power at the sample was about 148 mW. The wavelength of the laser (830 nm) was chosen to minimize heating and photodamage of the sample . All equipment was mounted on a XYZ-translation stage (Thorlabs Inc., USA) to ensure precise alignment. The beam of the trapping laser was steered through a system of mirrors (Thorlabs Inc., USA) into the microscope oil immersion objective (100 ×, 1.4 NA, Olympus, Japan) through a dichroic mirror (Chroma Technology, USA). The intensity profile of the laser beam overfilled the back focal plane of the objective; hence no beam expansion was necessary. The optical trap, situated at the focal distance of the microscope objective, was aligned to the centre of the field-of-view of the Charge Coupled Device (CCD) camera of the microscope.
Structural design of LOC and integrations
Optical absorbance measurement’s instrumentation
The oxygenated and deoxygenated conditions of the trapped RBC were monitored by an integrated spectrometer for absorption spectroscopy in the visible region (Ocean Optics, HR4000, USA). The visible light from the microscope passing through the sample and the dichroic mirror was split by a beam splitter; a fraction of 20% of light was guided to the camera on the left hand side of the microscope and 80% was guided to the right hand side port of the microscope to the spectrometer, see Figure 1. The optical fiber, with a core size diameter of 50 μm, was aligned precisely onto the center of the right-hand side-port of the microscope to collect the transmitted light. The absorption spectra were binomially smoothed by a data-analyzing software program (IGOR Pro, USA). The region from 520 - 600 nm was used to study the typical spectral peaks of the Q-bands of the oxygenated and deoxygenated states of haemoglobin (Hb) . The built in function “Binomial smoothing” as a Gaussian filter was applied to reduce the variability of data as well as to present clear and noise-free spectra . We were careful to ensure that the peaks at 540 nm, 575 nm and 553 nm were not changed in both cases before and after using the smoothing operation.
Patch clamp  was used to register the electrical activity across the plasma membrane of an optically trapped chicken RBC. An electrode was placed in one inlet of the LOC and a recording electrode was placed in the micro-pipette to record the electric signals. Signals were recorded using an amplifier (EPC-7, HEKA elektronik, Germany), a Digidata 1200 interface and software program pClamp 7 (Axon Instruments, Union City, CA, USA). Patch clamp pipettes were pulled from borosilicate glass capillaries of 1.5 mm (OD), 1.16 mm (ID) (PG150T-10, Harvard apparatus, USA) in two steps using a vertical Needle/Pipette Puller (David Kopf Instruments, Model 750, Tujunga, CA, USA). First, the capillary was thinned over a length of 7-10 mm to obtain a minimum diameter of 150 μm. The capillary was then recentred related to the heating filament of the puller. In the second step the thinned pipette was pulled until break to produce two pipettes with tips of about 1-2 μm. For this experimental purpose, the puller was adjusted to produce one pipette of good quality to fill out the required properties, i.e., tip’s diameter and taper’s length to be used for experimentation.
The oxygen sensor system
The oxygen content was measured through a fibre optic oxygen sensor probe, (FOXY probe, ocean optics, USA), connected to a MultiFrequency Phase Fluorometer (Ocean Optics, Florida, USA). The oxygen sensor was pre-calibrated by curves generated from standards concentration values of O 2 dissolved in anoxic and normoxic solutions. The second order polynomial algorithm was used for better curve fitting and for accurate oxygen measurements in a broad oxygen concentration range. The continuous visualization of the O 2-concentration values were achieved by a software program (OOISensors Oxygen Measurement Software, Ocean Optics, USA) installed on a personal computer (PC) connected to the oxygen sensor system, see Figure 1 above.
Experimental results and discussions
In a first step, the LOC was manufactured as described in the section of Materials and Methods. To enable the measurements under full control of the environment, a novel approach in the fabrication process was introduced to achieve good quality fastening of the LOC by using the capillary effect. This was performed by using a rectangular cover glass that was attached to the LOC with a UV curable adhesive material, characterized with low viscosity, high optical transparency and high biocompatibility (USP Class VI).
The gas-tight microfluidic chip including the integrated micropipette was positioned on the microscope stage and connected to the pump systems for the insertion of RBCs and for the flow of the solutions of different oxygen contents, see Figure 3.
The micropipette was carefully inserted, through the diagonal hole in the LOC, into the intersection-zone within the microfluidic channel and monitored visually. The selected RBCs were introduced to the microfluidic channel system in a low flow rate (0.1 μl/s) to enable the monitoring and selection of an RBC for experiments. The RBCs were trapped by optical tweezers and optically steered within the microfluidic channels towards the interaction-zone, while the trapping dynamics were recorded in real time with the CCD-camera of the microscope. The optical trapping and steering of RBCs has been presented previously in ref . The LOC including the integrated micropipette was precisely moved in 3D related to the fixed trap. The trapped RBC was steered to the interaction zone of the channel where the tip of the patch clamp micropipette was located. The micropipette was moved exactly towards the cell to place the tip onto the membrane of the cell. This experiment was performed for 13 times prior to the patch clamp experiments to ensure the functionality of the design.
To verify the gas-tight functionality of the microfluidic chip, the oxygen content was measured by an oxygen sensor while absorption spectra were taken in the visible region. The oxygen sensor measured values from 18% oxygen in normal EC solution that gradually declined down to 0-0.5% oxygen when deoxygenated-buffer solution (0% O 2) was purged into the channel system. The Experiments were performed under real physiological oxygen transition compared to our earlier study  in which hypoxia was generated chemically by adding natrium dithionite .
The oxygen content within the channel vs. the time series of the numbered spectra that presented in Figure 6
Absorption spectra (No. in Figure 6)
O 2 -Concentrations (%)
17.83 ± 0.14
27 ± 0.5
13.030 ± 0.100
83 ± 0.5
10.720 ± 0.180
128 ± 1
9.607 ± 0.016
195 ± 1
6.430 ± 0.030
191 ± 1
4.465 ± 0.026
227 ± 1
3.481 ± 0.014
255 ± 1
2.941 ± 0.018
282 ± 1
0.103 ± 0.006
298 ± 1
0.017 ± 0.016
5400 ± 2
0.023 ± 0.008
5828 ± 2
13.650 ± 0.160
The successful tests of the gas-tight functionality within the LOC showed the capability of the LOC to perform electrophysiological measurements on the trapped cell. Long patch pipettes with open-tip resistances of 8-10 M Ω were used for sealing onto the RBC plasma membrane. A patch clamp pipette was moved slowly towards the optically trapped cell to ensure near contact between the tip of the pipette and the membrane of the cell. The changes in pipette and access resistances were measured prior to the seal formation. Once the pipette attached the membrane of the cell, the positive pressure was released and followed by the application of gentle suction (negative pressure) on the solution within the pipette to create a high seal resistance. Many RBCs were trapped and patched successfully whereas the highest whole-cell access (Ra) and membrane (Rm) resistances obtained were 5.033 ± 0.412 M Ω and 889.7 ± 1.74 M Ω. The main focus of this paper was to present a gas-tight LOC that meets all the requirements to enable patch clamp experiment under hypoxic condition. Complete patch clamp experiments on other types of biological cells (related to the projects) during hypoxia will be presented in the future. Compared to our earlier study , the LOC was used for experiments under physiological conditions and the viability of the cells was improved by efficient cell transport into the LOC using shorter transport pathways and efficient design of the channel system and enhanced fluid flow.
In conclusion, we have demonstrated a concept of a low-cost, multi-use and high performance functionality of gas-tight PMMA based LOC for patch clamp investigations on single cells with precise control of hypoxic and anoxic conditions obtained by exchangeable oxygen contents. The LOC presented here provides an alternative to the traditional open system that is conventionally used in patch clamp experiments. The pump systems enabled the best infusion of RBCs and buffer solutions into the microfluidic channels by flow rates lower than 0.5 μl/s. The time series of the absorption spectra showed that the RBCs were viable for an experimental time more than 90 minutes and that the LOC delivered full control over the oxygen content. The measurements of the oxygen content within the LOC as well as the acquired absorption spectra of the patched RBC could to a high grade verify that the chip could be used for hypoxic and normoxic electrophysiological investigations. The resistance measurements of the sealed patch showed the proof of concept that this system could be used in the future to perform a full protocol of patch clamp measurements on different biological cells under controlled environments.
An improvement may be executed such as using absorption spectroscopy to investigate and evaluate the quantitative oxygenation status within the chamber. Another improvement is to incorporate control over temperature or pressure. The presented LOC shows a useful functionality to measure cell mechanics such as sheer stress under environmental changes. Furthermore, the gas-tight functionality and feasible control of the gaseous environments within the chip could be used to provide rapid and direct insight into the behavior and growth of anaerobic microorganisms. The presented LOC may also be useful for studying the effect of changing chemical and physical conditions on the morphology and function of biological cells in environmental gradients.
The authors would like to thank EU Structural Fund - Objective 2 Norra Norrland, the Swedish Research Council and the Kempe Foundation for supporting this work.
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