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SIMTech technical reports (STR_V10_N3_10_MMP) Volume 10 Number 3 Jul-Sep 2009 186 Electroosmosis flow (EOF) mobility measurement in polymer micro channels Z. F. Wang, Y. X. Wu1, and K. Puttachat 1 School of Engineering, Ecole Polytechnique Federale de Lausanne, Switzerland Abstract – The most popular microfluidic applica- tions are based on electrically moving separation in capillaries. Capillary electrophoresis (CE) is one of the fundamental methods for analysis using elec- troosmotic flow (EOF) and the mobility of charged species (ions) by attraction or repulsion in an electric field. Microchannels fabricated from various polymer manufacturing processes result in various CE proper- ties, especially the difference on EOF mobility, which determine the separation efficiency and other per- formance of the microfluidic device. In this report, we introduce the method and experimental setup of EOF mobility measurement of microchannel. Some meas- urement results of EOF mobility in polymer micro channels are also included. We prepare the test sam- ples from various fabrication methods, and the EOF measurement results reveal the effects of polymer manufacturing process towards CE property. Keywords: Microfluidics, Electroosmosis flow, Polymer microfabrication,Separation 1 BACKGROUND In the past decade, the field of microfluidics has been developed for most areas of interest in bio technology, medical science, and analytical chemistry. The most popular microfluidic applications are based on electrically moving separation in capillaries. Cap- illary electrophoresis is one of the fundamental methods for analysis using electroosmotic flow and the mobility of charged species (ions) by attraction or repulsion in an electric field. Microchip capillary electrophoresis offers faster and higher resolution separation. Instead of using glass, recently polymers were often employed as the base materials of the microchip device. It shows that many polymers are extremely suitable for mass- production using low-cost fabrica- tion methods such as molding, imprinting, and plasma etching or laser ablation. Furthermore, their flexibility for microfabrication is adequate for miniaturisation, and 3D-integration. The other characteristics such as the capability for surface modification, good optical transparency, and durability to acids also show several merit points for the analysis property of microfluidic chip. Elec- troosmotic flow (EOF) is the driving wheel of elec- trophoresis and the value of the EOF mobility, µEOF, is a crucial parameter for the electrophoretic experi- ments. In polymer microfluidic devices, the various polymer substrate materials exhibit different EOF mobility values. A reliable measurement of parameter µEOF is highly desirable for designing the micro cap- illary electrophoresis (µCE) based microfluidic de- vices. Moreover, the EOF mobility may also be af- fected by the manufacturing techniques applied in the device fabrication. For example, during various pat- terning processes, e.g. hot embossing, injection molding, laser cutting and micro milling, the polymer substrate experiences different pressure (or force), temperature profile and machine tool (or mold). Re- sulting channel surface may exhibit difference CE property and also vary in EOF reliability, which is equally important in configuring the CE-based mi- crofluidic devices. 2 OBJECTIVE This project is to set up the measurement tech- nique for EOF mobility of polymer micro channels, and examine the effects from various polymer manufacturing processes. By measuring the mobility of electroosmosis flow, the separation efficiency of microfluidic device can be well modelled, which is essential in design of microfluidic devices for separa- tion and diagnosis. 3 METHODOLOGY 3.1 EOF Mobility Measurement There are different ways to measure the EOF mobility. The most commonly used one is the Cur- rent-Monitoring method [1], which is an indirect method for measuring the average electroosmotic velocity in microchannels. In general, the EOF mobility is known as [2]: η ζεεμ r0EOF = (1) Here ε0, and εr are the permittivity of vacuum, and the dielectric constant respectively, ζ is the zeta potential of the capillary surface and η is viscosity of the solution. Z. F. Wang, Y. X. Wu, and K. Puttachat 187 A straight microchannel is filled with buffer so- lution which has low ionic concentration. Both ends of the capillary connect with reservoirs. An electrical field is applied into the microchannel. High concen- tration buffer is now loaded to reservoir at anode. By electroosmosis phenomenon, the ions migrate towards to cathode and gradually move to the other end of the reservoir. The total electrical conductivity of the mi- crochannel increase due to the increasing ion con- centration, and therefore the current being recorded between the two reservoirs will increase. The change of current across the two reservoirs is recorded through a data acquisition system as a func- tion of time. When the higher concentration buffer is completely driven to cathode, the current will reach a plateau value. The EOF mobility can be then derived from current-time response curve. This should be noted that hydraulic pressure has no interfere in this system. By ignoring the nonlinear characteristic which usually exhibits at the beginning stage, the mobility can be derived as below [2]: tV LL E v efft EOF ==μ (2) Here Lt and Leff are the total and effective lengths of the microchannel between the two reservoirs, re- spectively. V is the voltage which was applied across the distance of Lt, and t is the migration time of the marker of EOF travelling in the distance of Leff. In the current-monitoring method, t stands for the time the total current reaches plateau. It has been reported that the EOF mobility of different PMMA (Polymethyl Methacrylate) microfluidic chips were all about 1.1 x 10−4 cm2V−1s−1 [1]. EOF mobility can also be measured using Laser Induced Fluorescence (LIF) detection. The channel design in LIF measurement has two crossed channels. First channel is a short channel which uses for sample injection. The second channel is long channel which use for sample separation and detection. At first step, the sample, which added fluorescent, is loaded to a reservoir of injected channel, and it is driven by electroosmosis flow under high voltage. When sample is passing the cross junction, the electric filed is switched to the separation channel. Only sample in crossed area is driven to the separation channel under influence of electric filed. At the almost end of separation channel is focused with laser light, 493 nm in wave length, and a visible light sensor. Fluorescent was energised by laser and emitted a visible light. The EOF mobility can then be calculated ac- cording to Equation (2). The t is the migration time that the sample plug travels from the channel cross junction to the detection point, which distance is Leff. In this technical report, we only include the meas- urement results of current-voltage method. The value of EOF mobility is also varied through the change of buffer solution, e.g. pH and concentra- tion. Some published measurement results on PMMA, silica and PDMS microchannels are summarised in Table 2 as reference. Table 2. EOF mobility measurement in literature [3-7]. Buffer solution/ microchannel substrate EOF mobility (cm2V-1s-1) NH4Ac / PMMA 1.4~1.6 x 10-4 KCL / PMMA 1.0 x 10-4 1 x TAE / silica 4.9 x 10-4 1 x TBE / silica 3.1 x 10-4 Phosphate/ PMMA 2.83 x 10-4 BSA / PDMS 1.73 10-4 3.2 Experimental Setup Polymer chips with two microchannel designs are fabricated for the EOF mobility test. One design is with the straight channel, which is for the cur- rent-monitoring method. Another design comprises cross channels for the LIF measurement, which results are not included in this report. Two kinds of polymers are used as the substrate materials for fabricating microchannels. One is 1.5 mm-thick PMMA sheet (supplied by DAMA Enter- prise). Another is PDMS (Poly-dimethylsiloxane). The PMMA chips with microchannels are fabricated in two ways. One is hot embossing, which transfers the micro features from a mold to the PMMA sub- strate by applying heat and pressure. We use SpecacTM thermal press as the process tool. The mold is 4-inch single crystal silicon wafer, where the micro features are fabricated through deep reactive ion etching (DRIE) process. Other than hot embossing, we also use CO2 laser to cut the microchannels directly. After the channel patterning process, we laminate the PMMA chips using another piece of PMMA sheet through thermal diffusion bonding, or simply through adhesive tape, to encapsulate the channels. The PDMS chips are made from casting out of SU-8 photoresist, which is shaped through typical photolithography process. We use SlygardTM 184 kit, which contains a PDMS elastomer and a PDMS cur- ing agent, to form the PDMS prepolymer by mixing them in a ratio of 10:1, and degassing in vacuum oven. We then pour the prepolymer over the mold, which is the 4-inch silicon wafer being fabricated through DRIE process, and further degas the prepolymer in the vacuum oven for 30 min. After curing at 100ºC for 4 hours, the PDMS chip can be de-molded and ready for bonding process. We used three different covers to laminate the PDMS chips, e.g. PDMS sheet, glass plate, and adhesive tape. The tape we use is 3MTM8161, which has 25 µm ad- hesion layer. The PDMS-glass and PDMS-PMDS bonding are all done at room temperature. Electroosmosis flow (EOF) mobility measurement in polymer micro channels 188 TBE (Tris-Borate-EDTA) buffer, which is commonly used in DNA electrophoresis applications, was used in our CE experiments due to its high buff- ering capacity and low conductivity, especially its good electrical stability under high voltage [8], which is always required for generating electroosmosis flow. The high voltage source used in the CE meas- urement is a LabSmithTM-HVS448/3000V high volt- age sequencer. The current measurement is done using KeithleyTM 8800 source meter. A ZeissTM Ax- iovert40-CFL inverted microscope is set up as the test station (shown in Fig. 1.) The chip holder is machined with polycarbonate for housing the polymer chip during the test. The holder consists of two parts. The bottom one is holding the chip and the upper one is fixing the CE electrodes, which is made of 0.5mm diameter platinum wire (99.9%, from Sigma-Aldrich) and plastic cover. (a) The ZeissTM Axiovert40-CFL inverted microscope as the test station (b) The polycarbonate chipholder and CE electrodes Fig. 1. Experimental setup of EOF mobility measurement. NI-USB 6259 16-bit data acquisition (DAQ) card is used to control the CE driving voltage and collect the current measurement data. We use LabVIEWTM 8.5 to build the current-voltage EOF mobility meas- urement platform, which user interface has been shown in Fig. 2. The configuration for LIF method is also included in this LabVIEWTM platform. Fig. 2. LabviewTM interface for current-voltage measure- ment of EOF mobility. 4 RESULTS & DISCUSSION The micrographs of PMMA chip fabricated through hot embossing and laser cutting are shown in Fig. 3. The two kinds of chip have the identical single straight channel design. The length and width of the micro channel are 50 mm and 100 µm, respectively. From Fig. 3 we can find out that the hot embossing process offers a rectangular cross-section of channel and a smooth inner channel surface. While the laser cutting process generates micro channel with V-shape cross-section, and the inner channel surface appears to be much rougher than the embossed samples. (a) Top view of hot embossing PMMA chip (a) Cross-section of hot embossing PMMA chip Z. F. Wang, Y. X. Wu, and K. Puttachat 189 (c) Top view of laser cutting PMMA chip (d) Cross-section of laser cutting PMMA chip Fig. 3. Micrograph of channel. The patterned PMMA chips are then laminated through thermal diffusion bonding. Figure 4 shows some results from hot-embossed PMMA chips under various measurement conditions. In this current- voltage measurement, Lt and Leff are all around 50 mm long. The voltage across the capillary (channel) is 1,500 V. We found that the pre-treatment to the channel with NaOH before each use can significantly increase the EOF mobility and also make the meas- urement results stable. From Fig. 4 we can also find out that when using the buffer with higher concentra- tion, higher EOF mobility can be achieved. This may because that higher concentrated buffer generates more joule heat due to larger current, and leads to a lower viscosity [2], which raises the EOF velocity according to Eq. (1). We also compare the CE measurement results getting from the PMMA chips fabricated from hot embossing and laser cutting. As shown in Fig. 5, throughout the samples we measured, the laser cutting samples exhibit consistently lower EOF mobility comparing with the hot embossed samples. This dif- ference may mainly contribute from the different inner channel surface property, such as roughness and wettability. It’s obvious that these two patterning processes offer very different CE property to PMMA microfluidic chips. Fig. 4. EOF mobility measurement for PMMA channel. Fig. 5. EOF mobility measurement of PMMA chips: hot embossing vs laser cutting; both chips were thermal bonded. We use the PDMS chips to examine the effects of lamination technique on the EOF mobility. As men- tioned earlier, after fabricating the channels, the PDMS chips are bonded with another piece of PDMS, glass sheet, and adhesive tape, respectively. The channel design is the same as we use in PMMA chips. 1,500 V EOF driving voltage is applied and 1 x TBE buffer is used. Figure 6 shows the measurement re- sults from the PDMS chips with the 3 bonding covers. Fig. 6. EOF mobility of PDMS chip with various bonding techniques. The average EOF mobility for these 3 kinds of chip are 2.21 x 10-4 cm2V-1s-1, 1.68 x 10-4 cm2V-1s-1 and 2.84 x 10-4 cm2V-1s-1, respectively. The results show the clear effects of bonding technique on CE property. The tape-bonded PDMS chips exhibit very much higher EOF velocity, and the PDMS-glass con- figuration gives the lowest EOF mobility. Electroosmosis flow (EOF) mobility measurement in polymer micro channels 190 5 CONCLUSION Through the EOF mobility measurement of mi- crochannels in PMMA and PDMS microfluidic de- vices, we find out that the manufacturing process varies the results significantly. As the structuring process, laser cutting contributes much lower EOF mobility comparing with hot embossing. This may due to the poor inner channel surface finishing gen- erated through laser process. We also examine the effects of various bonding techniques on CE property of PDMS chips. The results show that the channels covered by adhesive tape exhibit the highest EOF mobility, followed by the glass covered chips and PDMS covered ones, respectively. 6 INDUSTRIAL SIGNIFICANCE Through this research, the effects of some poly- mer manufacturing process on µCE property are dis- covered throughthe EOF mobility measurement. The results are useful in building up the design for per- formance library of polymer microfluidic devices manufacturing. The µCE property of the polymer micro channels would then be well controlled and the separation efficiency could be designed accordingly. REFERENCES [1] X.H. Huang, M.J. Gordon and R.N. Zare, “Cur- rent-monitoring method for measuring the electroos- motic flow rate in capillary zone electrophoresis”, Anal. Chem., vol. 60(17), pp. 1837-1838, 1988. [2] A. S. Rathore, A. Guttman, “Electrokinetic Phenomena; Principles and applications”, in Analytical chemistry and microchip Technology, Marcel Dekker Inc., New York, pp. 141-165, 2004. [3] X. Ren, M. Bachman, C.E. Sims, G.P. Li, N.L. All- britton, “Electroosmotic Properties of Microfluidic Channels Composed of Poly(dimethylsiloxane)”, J. Chromat. B., vol. 762(2), pp. 117-25, 2001. [4] R. Chen, H. Guo, Y. Shen, Y. Hu and Y. Sun, “De- termination of EOF of PMMA microfluidic chip by indirect laser-induced fluorescence detection”, Sens. Actuator A, 2006, vol. 114(2), pp. 1100-1107, 2006. [5] D. Sinton, C.E. Canseco, L. Ren and D. Li, “Direct and Indirect Electroosmotic Flow Velocity Measurements in Microchannels”, J. Colloid Interface Sci., vol. 254(1), pp. 184-189, 2002. [6] N. Vourdas, A. Tserepi, A.G. Boudouvis and E. 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