This work was sponsored by the National Natural Science Foundation of China (51375176); the Guangdong Provincial Natural Science Foundation of China (2014A030313264); and the Science and Technology Planning Project of Guangdong Province, China (2014B010126003).

Caution: Please consult all relevant material safety data sheets (MSDS) before use. Acetone is highly flammable and can cause irritation to the eyes and respiratory tract. The voltage involved is as high as several thousand volts; hence, electrical sparks are expected when conducting the experiment. Carry out the experiments in a room with good ventilation to avoid explosions and fire from the sparks.
1. Fabrication of the Plates and Holder
NOTE: In this work, the electrode plates and holder are fabricated by a production line in a factory. Only the material and the parameters of all parts in this paper will be introduced due to the complicated processes.
<ol>
	<li>Material and size of the electrode plate
	<ol>
		<li>Fabricate the electrode plates using 1.4 mm FR-4 CCL with a thin copper layer of 35 &#181;m. See Figure 1 for detailed parameters of the electrode plate.</li>
	</ol>
	</li>
	<li>Parameters of the electrodes
	<ol>
		<li>Order the electrode plates from the factory. See Figure 2 for more details.</li>
	</ol>
	</li>
	<li>Inspection of the electrode plate
	<ol>
		<li>After the preparation of the electrode plate, use an electron microscope to inspect the electrodes for any noticeable flaws under 100X and 300X magnification. Note that any tiny defects on the surface of the electrodes can cause short-circuiting, as shown in Figure 3.</li>
		<li>Inspect and measure the electrode width and spacing to determine whether the dimension accuracy meets the requirement.</li>
		<li>Test the plate with an amperemeter to see if an electrical short-circuit occurs.</li>
	</ol>
	</li>
	<li>Preparation of the chamber plate
	<ol>
		<li>Cut some silicone membrane to the same size as the electrode plate, as shown in Figure 4. Choose silicone membranes with different thicknesses to make chamber plates with different heights.</li>
		<li>Use a special punching tool to punch the chamber hole, as shown in Figure 5.</li>
	</ol>
	</li>
	<li>Processing of the holder
	<ol>
		<li>Order the holder from a factory. The detailed parameters are shown in Figure 6.</li>
	</ol>
	</li>
	<li>Fabrication of the cover plate
	<ol>
		<li>Drill two holes on the top of the cover plate using a drilling machine to install the inlet and outlet tubes. See Figure 7 for their positions and sizes.</li>
	</ol>
	</li>
</ol>
2. Assembly of the Micropump
<ol>
	<li>Use acetone to wash all the plates, the holder, the inlet and outlet tubes, and other tools used in the experiments. Put these tools and plates inside a beaker and then pour enough 99.5% acetone to immerse them. Put the beaker inside the ultrasonic washer. Turn on the ultrasonic washer and set the timer to 5 min.</li>
	<li>Insert the inlet and outlet stainless-steel tubes into the two holes on the cover plate.</li>
	<li>Place a chamber plate made of silicone membrane on the electrode plate and then cover it with the cover plate.</li>
	<li>Stack and align the cover plate, the chamber plate, and the electrode plate from top to bottom and insert the aligned plates into the holder.
	<ol>
		<li>Use an M5 bolt to fix the plates inside the holder. See the explosion view and normal view of the assembled micropump, as shown in Figure 8 and Figure 9, respectively.</li>
		<li>Press the plates together by tightening the bolts. 
		NOTE: The tubes and the cavity on the chamber plate will form a passage for the working liquid. The elastic chamber plate can also seal off the gap between plates to prevent liquid from flowing out. See the explosion view and the normal view of the assembled micropump in Figure 8 and Figure 9, respectively.</li>
	</ol>
	</li>
	<li>Use two polyurethane hoses with external diameters of 4 mm and internal diameters of 2 mm to connect the inlet and outlet stainless-steel tubes.</li>
	<li>Connect an amperemeter, a 500 V DC power source, and the micropump in series. Insert a 1 mA fuse between the amperemeter and the power source to protect the amperemeter in case the micropump is shorted.</li>
	<li>Insert the inlet hose into a 50 mL beaker with 20-30 mL of acetone inside. 
	NOTE: Figure 10 shows the completed platform.</li>
</ol>
3. Experimental Procedure
<ol>
	<li>Preparatory work before the experiment
	<ol>
		<li>Use a cylinder to inject acetone to fill up the micropump. After the liquid level reaches the outlet hose, continue to inject 10 mL of acetone inside until all bubbles are pushed away from the chamber. 
		NOTE: It is impossible to see if there are any bubbles left inside the chamber because the cover plate and the electrode plate are not transparent. Continuously injecting acetone helps to remove bubbles, but it cannot guarantee that no bubbles are left inside the micropump. Bubbles may block the passage of liquid, or they may short the circuits and cause a micro-explosion inside the micropump, which will burn the electrodes. The effect of bubbles on the pump operation is not totally clear yet, but the breakdowns they cause have been observed several times.</li>
		<li>Pour 20-30 mL of acetone into the beaker and put the inlet hose inside the beaker. Ensure that the liquid level is at least 5 mm higher than the inlet so that acetone can flow into the pump and no air can be sucked into the micropump chamber.</li>
	</ol>
	</li>
	<li>Static pressure test
	<ol>
		<li>Attach the outlet hose to a small frame so that the hose can remain straight and vertical. Put a ruler alongside the outlet hose to measure the liquid level.</li>
		<li>Connect the micropump to the power source.</li>
		<li>Start the test by pressing the switch and then mark down the initial liquid level.</li>
		<li>After the liquid level becomes stable, record the time, the final liquid level, and the electric current.</li>
		<li>Continue to record the liquid level and the current every 10 s until the micropump breaks down.</li>
	</ol>
	</li>
	<li>Flow rate test
	<ol>
		<li>Use a large measuring cylinder to collect the liquid coming out of the outlet hose. Be sure to fix the outlet hose so that the end remains at the same altitude as the liquid level in the beaker.</li>
		<li>Connect the micropump to the power source.</li>
		<li>Start the test by pressing the switch and then mark down the initial liquid level.</li>
		<li>As the liquid starts to flow out of the outlet hose, record the volume of acetone inside the measuring cylinder every 10 s. As the experiment goes on, add acetone to the beaker to maintain the liquid level.</li>
	</ol>
	</li>
	<li>Reliability test
	<ol>
		<li>Use the average working time to evaluate the reliability of the pump. During the flow rate test and the static pressure test, record the operation time before the pump breaks down. Record the detailed phenomena of each breakdown during the experiment and inspect the electrode plate surface afterwards for further analysis.</li>
	</ol>
	</li>
</ol>

<ol><li>Kazemi, P. Z., Selvaganapathy, P. R., Ching, C. <a target="_blank" href="https://www-sciencedirect-com.remotexs.ntu.edu.sg/science/article/pii/S0304388610000719">Effect of micropillar electrode spacing on the performance of electrohydrodynamic micropumps.</a> J Electrostat. 68 (4), 376-383 (2010).</li>
<li>Kano, I., Nishina, T. <a target="_blank" href="http://ieeexplore.ieee.org/document/6074271/">Effect of electrode arrangements on EHD conduction pumping.</a> IEEE Trans Ind Appl. 49 (2), 679-684 (2013).</li>
<li>Laser, D. J., Santiago, J. G. <a target="_blank" href="http://microfluidics.stanford.edu/Publications/Micropumps_Cooling/Laser%20Review%20of%20Micropumps%20in%20JMM.pdf">A review of micropumps.</a> J Micromech Microeng. 14 (6), R35(2004).</li>
<li>Fylladitakis, E. D., Theodoridis, M. P., Moronis, A. X. <a target="_blank" href="http://ieeexplore.ieee.org/document/6714477/">Review on the history, research, and applications of electrohydrodynamics.</a> IEEE Trans Plasma Sci. 42 (2), 358-375 (2014).</li>
<li>Yazdani, M., Seyed-Yagoobi, J. <a target="_blank" href="http://www.electrostaticanswers.com/2009ESJC/Session01/2009%20Yazdani%20Effects%20of%20Charges%20Mobility%20-%20Dielectric%20Liquid%20Flow.pdf">Effect of Charge Mobility on Electric Conduction
Driven Dielectric Liquid Flow.</a> Electrostatics Joint Conf. , (2009).</li>
<li>Gharraei, R., Esmaeilzadeh, E., Hemayatkhah, M., Danaeefar, J. <a target="_blank" href="https://www-sciencedirect-com.remotexs.ntu.edu.sg/science/article/pii/S0304388610001373">Experimental investigation of electrohydrodynamic conduction pumping of various liquids film using flush electrodes.</a> J Electrostat. 69 (1), 43-53 (2011).</li>
<li>Gharraei, R., Esmaeilzadeh, E., Nobari, M. R. H. <a target="_blank" href="https://link-springer-com.remotexs.ntu.edu.sg/article/10.1007/s00162-013-0304-3">Numerical investigation of conduction pumping of dielectric liquid film using flush-mounted electrodes.</a> Theor Comp Fluid Dyn. 28 (1), 89(2014).</li>
<li>Jeong, S. -I., Seyed-Yagoobi, J. <a target="_blank" href="https://www-sciencedirect-com.remotexs.ntu.edu.sg/science/article/pii/S030438860200058X">Experimental study of electrohydrodynamic pumping through conduction phenomenon.</a> J Electrostat. 56 (2), 123-133 (2002).</li>
<li>Seyed-Yagoobi, J. <a target="_blank" href="https://www-sciencedirect-com.remotexs.ntu.edu.sg/science/article/pii/S0304388605000616">Electrohydrodynamic pumping of dielectric liquids.</a> J Electrostat. 63 (6), 861-869 (2005).</li>
<li>Hojjati, M., Esmaeilzadeh, E., Sadri, B., Gharraei, R. <a target="_blank" href="https://www-sciencedirect-com.remotexs.ntu.edu.sg/science/article/pii/S092777571100642X">Electrohydrodynamic conduction pumps with cylindrical electrodes for pumping of dielectric liquid film in an open channel.</a> Colloid Surface A. 392 (1), 294-299 (2011).</li>
<li>Yazdani, M., Seyed-Yagoobi, J. <a target="_blank" href="http://heattransfer.asmedigitalcollection.asme.org/article.aspx?articleid=1449435">Numerical investigation of electrohydrodynamic-conduction pumping of liquid film in the presence of evaporation.</a> J Heat Trans-T ASME. 131 (1), 011602(2009).</li>
<li>Vafaie, R. H., Ghavifekr, H. B., Lintel, H., Brugger, J., Renaud, P. <a target="_blank" href="http://onlinelibrary.wiley.com/doi/10.1002/elps.201500404/abstract">Bi-directional AC electrothermal micropump for on-chip biological applications.</a> Electrophoresis. 37 (5-6), 719-726 (2016).</li>
<li>Pearson, M. R., Seyed-Yagoobi, J. <a target="_blank" href="http://heattransfer.asmedigitalcollection.asme.org/article.aspx?articleid=1738568">Experimental Study of Linear and Radial Two-Phase Heat Transport Devices Driven by Electrohydrodynamic Conduction Pumping.</a> J Heat Trans-T ASME. 137 (2), 022901(2015).</li>
</ol>

The authors have nothing to disclose.

One of the critical steps within the protocol is to inspect the electrode plate carefully. Small burrs on the edge of an electrode can result in a short-circuit, and surface integrity can greatly affect pump performance. The cleaning of the electrode plate and holder is also very important. The electrode chamber height is less than 1 mm, so small dust particles may block the working liquid flow and cause a short-circuit. Before the test, injecting acetone into the chamber can remove the bubbles outside of the chamber.
The performance of the micropump can be severely influenced by the height of chamber. To eliminate such influence, the elastic chamber plate can be replaced by harder material.
There are a few limitations to the technique. First, the electrode height is determined by the metal layer on the FR-4 CCL. It is relatively high, which affects the flow of liquid to some extent. Second, by using silicone membrane as the chamber plate, the sealability of the chamber is improved. However, the elasticity of silicone can cause some deviation in chamber height. Finally, the electrode width and electrode spacing are limited by the technique itself, which makes achieving higher electric field strength much more difficult than with other technique.
Unlike photolithography and other high-precision fabrication techniques, using FR-4 CCL with this electrode fabrication process is relatively simpler and cheaper. On the other hand, the required electric voltage in this work is much lower. Pearson and Seyed-Yagoobi13 have proposed a ring electrode and perforated electrode design that requires 5 kV of DC voltage for the pump to work, while in this work, the power source is only 500 V.
This micropump can be used to loop a heat pipe, especially a long heat pipe that requires a driving force other than capillary force. Inserting one or multiple electrode plates inside the heat pipe can provide enough driving force for the dielectric coolant to travel from the cold end to the hot end. A similar function can also be achieved by an annular electrode fabricated on soft, insulated material with a metal substrate.

Micropumps can drive liquid flow on a much smaller scale than most pumps. In recent years, various driving schemes have been applied successfully to microfluidic systems1,2,3,4,5. The electrohydrodynamic (EHD) pump can exert forces directly on the liquid, without any moving parts, which makes it simpler and easier to fabricate6. According to the charge types, EHD pumps can be classified as injection pumps, induction pumps, or conduction pumps. Induction pumps do not work on isothermal liquids, while injection pumps change the liquid conductivity. Because they lack such problems, conduction pumps are more stable and have a wider application.
The conduction pump is based on the mismatch of the dissociation and recombination rates of liquid molecules. Normally, the dissociation and recombination process can be expressed as follows7,8: 
<img alt="Equation" src="/files/ftp_upload/55867/55867eq1.jpg" /> 
where the recombination rate kr is constant while the dissociation rate kd is a function of the electric field strength. When the electric field strength reaches a certain value, the dissociation rate will exceed the recombination rate. Then, more and more free charges travel to the two electrodes of opposite polarity, and heterocharge layers form. These heterocharge layers are the key to the pump, as the movement of the charges pushes the liquid molecules forward. Therefore, net body force can be generated in the liquid within the chamber using asymmetric electrodes or the mismatch of the mobility of positive and negative ions9,10,11,12.
This work introduces a new way of fabricating a symmetric planar electrode plate for a conduction pump. The electrode plate is prepared on FR-4 CCL, and the pump chamber is prepared by micromachining. The fabrication processes are relatively simpler and more convenient than those of other manufacturing methods, such as nanolithography. A testing platform is set up to investigate the performance of the conduction micropump under different conditions. Furthermore, the reliability of the conduction micropump is also investigated under different circumstances.

<table><tbody><tr><td>Amperemeter</td><td>-</td><td>85C1-MA</td><td></td></tr><tr><td>DC high voltage power supply</td><td>NanTong Jianuo electric device company</td><td>GY-WY500-1</td><td></td></tr><tr><td>Fuse</td><td>-</td><td>-</td><td></td></tr><tr><td>Ultrasonic cleaner</td><td>Derui ultrasonic device company</td><td>-</td><td></td></tr><tr><td>Soldering iron</td><td>-</td><td>-</td><td></td></tr></tbody></table>

a performance-testing platform for a conduction micropump with an fr-4 copper-clad electrode plate

Here, a conduction micropump with symmetric planar electrode pairs prepared on flame-retardant glass-reinforced epoxy (FR-4) copper-clad laminate (CCL) is fabricated. It is used to investigate the influence of chamber dimensions on the performance of a conduction micropump and to determine the reliability of the conduction pump when acetone is used as the working fluid. A testing platform is set up to evaluate conduction micropump performance under different conditions. When the chamber height is 0.2 mm, the pump pressure reaches its peak value.

As shown in Figure 11, the pump pressure and its increasing rate rise when the voltage increases. When the voltage reaches 500 V, the pump pressure reaches 1,100 Pa.
The pump static pressure rises with the pump chamber height increasing when the chamber height is under 0.2 mm. The pump performance reaches its highest point when the chamber height is 0.2 mm. Then, the static pressure drops when the chamber height continues to increase. It is believed that 0.2 mm is the best value for the chamber height. The results are shown in Figure 12.
By increasing the chamber length, the static pressure rises, with a big slope until a chamber length of 23 mm and a smaller slope, indicating a gradual rise, afterwards. The variation tendency of the pump pressure is shown in Figure 13.
As shown in Figure 14, there is a slight decrease in the static pressure versus chamber width curve when the chamber width increases from 2 mm to 3 mm. Afterwards, the static pressure remains at a certain level as the chamber width increases.
During testing, the micropump breaks down frequently after working for 10-90 min. After working for a certain amount of time, the pump pressure continues to drop until breakdown occurs. However, the performance of the pump pressure can be restored when new acetone is added to the beaker.
When there are bubbles inside the pump, the pump pressure will not rise as high as it normally does because the passage of working liquid is blocked by the bubbles. If the plates are not sufficiently cleaned, meaning that there is still dust or other contamination, the pump will easily get shorted when these particles travel to the gap between electrodes. When the pump gets shorted, the electric current will rise very fast and burn the electrodes.
<img alt="Figure 1" class="xfigimg" src="/files/ftp_upload/55867/55867fig1.jpg" /> 
Figure 1: Size of the electrode plate. The electrode plate, chamber plate, and cover plate are of the same size. Their widths are 9 mm and their lengths are 40 mm. The holes for soldering the wire have a diameter of 1.6 mm. Order the electrode plates from the factory with these parameters and check the plate size afterwards to make sure that they can fit inside the holder. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig1large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" class="xfigimg" src="/files/ftp_upload/55867/55867fig2.jpg" /> 
Figure 2: Dimensions of the electrodes. The electrode plates have 23 pairs of electrodes, with an electrode width of 300 &#181;m, an electrode spacing of 200 &#181;m, a width gap between the two electrode pairs of 400 &#181;m, and an electrode end spacing of 600 &#181;m. The electrode spacing is the most important parameter, as it determines the electric field strength. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" class="xfigimg" src="/files/ftp_upload/55867/55867fig3.jpg" /> 
Figure 3: Tiny defects on the surface of electrodes and the damage from short circuits. Rags and surface pits are the typical defects of the electrodes. The pits in (a) have caused a severe breakdown. Some of the electrodes in (b) burn under high electric field strength. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig3large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" class="xfigimg" src="/files/ftp_upload/55867/55867fig4.jpg" /> 
Figure 4: Chamber plate dimensions. The width and length of the plate are 9 mm and 40 mm, respectively. The thickness of the plate is 0.3 mm in these tests. The dimension accuracy is 0.1 mm. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig4large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 5" class="xfigimg" src="/files/ftp_upload/55867/55867fig5.jpg" /> 
Figure 5: Picture of the special hole punch. The special punching tool is customized for cutting the cavity on the chamber plate. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig5large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 6" class="xfigimg" src="/files/ftp_upload/55867/55867fig6.jpg" /> 
Figure 6: The engineering drawing of the holder. The 3 mm opening on the top is for the inlet and outlet stainless-steel tubes. The thickness of all walls is 2 mm, and the overall size of the holder is 14 x 37.5 x 9 mm3. The 2.4 mm wall on the left is for holding the position of the electrode plate, cover plate, and chamber plate. On the bottom of the holder, there is an M5 threaded hole for a fastening bolt. The dimension accuracy of the holder is 0.1 mm, which is not very high. Make sure that the electrode plate can fit inside. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig6large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 7" class="xfigimg" src="/files/ftp_upload/55867/55867fig7.jpg" /> 
Figure 7: The parameters of the cover plate. The material of the cover plate is also FR4. Two stainless-steel tubes are inserted into the hole to provide inlet and outlet passage for the working liquid. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig7large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 8" class="xfigimg" src="/files/ftp_upload/55867/55867fig8.jpg" /> 
Figure 8: Explosion view of the micropump. From top to bottom are the inlet and outlet tubes, the cover plate, the chamber plate, the electrode plate, and the fastening bolt. The tubes and the cavity on the chamber plate form a liquid passage for the working liquid. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig8large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 9" class="xfigimg" src="/files/ftp_upload/55867/55867fig9.jpg" /> 
Figure 9: Rendered image of the assembled micropump. After fastening the bolt, all plates are pressed together, and the hole on the chamber plate is the only space for liquid to flow through. The elastic chamber plate can also seal off the gap between plates to prevent liquid from flowing out. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig9large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 10" class="xfigimg" src="/files/ftp_upload/55867/55867fig10.jpg" /> 
Figure 10: The picture of the micropump experiment platform. The bottle that contains acetone can be replace by a beaker, but it is safer to cover the beaker with thin film to prevent the acetone from volatilizing too much. The power source, the amperemeter, and the pump are connected in series. The outlet hose can be also replaced by a glass tube. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig10large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 11" class="xfigimg" src="/files/ftp_upload/55867/55867fig11v2.jpg" /> 
Figure 11: The relationship between the voltage and the pump pressure. The pump pressure and its increasing rate rises when the voltage increases. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig11v2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 12" class="xfigimg" src="/files/ftp_upload/55867/55867fig12v2.jpg" /> 
Figure 12: The relationship between the chamber height and the pump performance. The pump performance first increases then drops when the chamber height increases from 0.1 mm to 0.5 mm. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55867/55867fig12v2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 13" class="xfigimg" src="/files/ftp_upload/55867/55867fig13v2.jpg" /> 
Figure 13: The relationship between the chamber length and the pump performance. The pump performance rises when the length increases.
<img alt="Figure 14" class="xfigimg" src="/files/ftp_upload/55867/55867fig14v2.jpg" /> 
Figure 14: The relationship between the chamber width and the pump performance. The pump pressure remains the same when the chamber width increases.

Watch this Scientific Journal Video about A Performance-testing Platform for a Conduction Micropump with an FR-4 Copper-clad Electrode Plate at JoVE.com

A Performance-testing Platform for a Conduction Micropump with an FR-4 Copper-clad Electrode Plate

This paper presents a protocol for the fabrication of a conduction micropump using symmetric planar electrodes on flame-retardant glass-reinforced epoxy (FR-4) copper-clad laminate (CCL) to test the influence of chamber dimensions on the performance of a conduction micropump.

Here, a conduction micropump with symmetric planar electrode pairs prepared on flame-retardant glass-reinforced epoxy (FR-4) copper-clad laminate (CCL) is ...

a-performance-testing-platform-for-conduction-micropump-with-an-fr-4

Nanyang Technological University

Research

JoVE Journal

Bioengineering

5.9K Views.  South China University of Technology. Dit document stelt een protocol voor de fabricage van een geleiding micropump met symmetrische vlakke elektroden op vlamvertragend glas-versterkt epoxy (FR-4) koper-geklede laminaat (CCL) voor het testen van de invloed van de afmetingen van de kamer op de prestaties van een geleiding micropump.

Video: A Performance-testing Platform for a Conduction Micropump with an FR-4 Copper-clad Electrode Plate

Hollow Microneedle-based Sensor for Multiplexed Transdermal Electrochemical Sensing

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High Throughput Microfluidic Rapid and Low Cost Prototyping Packaging Methods

In this work, 3 different packaging and assembly techniques are presented. They can be classified into two categories: one-time use and reusable packaging techniques.
The one-time use packaging technique employs UV-based and temperature curing epoxies to connect microtubes to access holes, wire-bonding for integrated circuit connections, and silver epoxy for electrical connections. This method is based on a robust assembly technique that can support relatively high pressure close to 1 psi and does not need any support to strengthen the microfluidic architecture.
Reusable packaging techniques consist of PDMS-based microtube interconnectors and anisotropic adhesive films for electrical connections. These devices are more sensitive and fragile. Consequently, Plexiglas support is added to the microfluidic structure to improve the electrical contact when anisotropic adhesive films are used, and also to strengthen the microfluidic architecture. In addition, a micromanipulator is needed to maintain tubes while using a thin PDMS layer to connect them to the access holes. Different PDMS layer thicknesses, ranging from 0.45-3 mm, are tested to compare the best adherence versus injection rates. Applied injection rates are varied from 50-300 &#956;l/hr for 0.45-3 mm PDMS layers, respectively. These techniques are mainly applicable for low-pressure applications. However, they can be extended for high-pressure ones through plasma-oxygen process to permanently seal the PDMS to glass substrates. The main advantage of this technique, besides the fact that it is reusable, consists of keeping the device observable when the microchannel length is very short (in the range of 3 mm or lower).

In this article we describe different techniques for microfluidic rapid prototyping platforms. The proposed techniques are based on ultraviolet (UV) sensitive and temperature curing epoxies, polydimethylsiloxane (PDMS) based tubing, wire-bonding, and anisotropic adhesive films. The assembling procedures presented are developed for both one-time use devices as well as reusable microfluidic systems.

In this work, 3 different packaging and assembly techniques are presented. They can be classified into two categories: one-time use and reusable packaging ...

A Microfluidic Platform for Precision Small-volume Sample Processing and Its Use to Size Separate Biological Particles with an Acoustic Microdevice

A major advantage of microfluidic devices is the ability to manipulate small sample volumes, thus reducing reagent waste and preserving precious sample. However, to achieve robust sample manipulation it is necessary to address device integration with the macroscale environment. To realize repeatable, sensitive particle separation with microfluidic devices, this protocol presents a complete automated and integrated microfluidic platform that enables precise processing of 0.15&#8211;1.5 ml samples using microfluidic devices. Important aspects of this system include modular device layout and robust fixtures resulting in reliable and flexible world to chip connections, and fully-automated fluid handling which accomplishes closed-loop sample collection, system cleaning and priming steps to ensure repeatable operation. Different microfluidic devices can be used interchangeably with this architecture. Here we incorporate an acoustofluidic device, detail its characterization, performance optimization, and demonstrate its use for size-separation of biological samples. By using real-time feedback during separation experiments, sample collection is optimized to conserve and concentrate sample. Although requiring the integration of multiple pieces of equipment, advantages of this architecture include the ability to process unknown samples with no additional system optimization, ease of device replacement, and precise, robust sample processing.

This protocol describes a system architecture for performing automated small volume (0.15&#8211;1.5 ml) particle separations using a microfluidic device, and discusses methods to optimize acoustofluidic device performance and operation.

A major advantage of microfluidic devices is the ability to manipulate small sample volumes, thus reducing reagent waste and preserving precious sample. ...

Fabrication and Characterization of Thickness Mode Piezoelectric Devices for Atomization and Acoustofluidics

We present a technique to fabricate simple thickness mode piezoelectric devices using lithium niobate (LN). Such devices have been shown to atomize liquid more efficiently, in terms of &#64258;ow rate per power input, than those that rely on Rayleigh waves and other modes of vibration in LN or lead zirconate titanate (PZT). The complete device is composed of a transducer, a transducer holder, and a &#64258;uid supply system. The fundamentals of acoustic liquid atomization are not well known, so techniques to characterize the devices and to study the phenomena are also described. Laser Doppler vibrometry (LDV) provides vibration information essential in comparing acoustic transducers and, in this case, indicates whether a device will perform well in thickness vibration. It can also be used to &#64257;nd the resonance frequency of the device, though this information is obtained more quickly via impedance analysis. Continuous &#64258;uid atomization, as an example application, requires careful &#64258;uid flow control, and we present such a method with high-speed imaging and droplet size distribution measurements via laser scattering.

Fabrication of piezoelectric thickness mode transducers via direct current sputtering of plate electrodes on lithium niobate is described. Additionally, reliable operation is achieved with a transducer holder and &#64258;uid supply system and characterization is demonstrated via impedance analysis, laser doppler vibrometry, high-speed imaging, and droplet size distribution using laser scattering.

We present a technique to fabricate simple thickness mode piezoelectric devices using lithium niobate (LN). Such devices have been shown to atomize liquid ...

Engineering

Dry Film Photoresist-based Electrochemical Microfluidic Biosensor Platform: Device Fabrication, On-chip Assay Preparation, and System Operation

In recent years, biomarker diagnostics became an indispensable tool for the diagnosis of human disease, especially for the point-of-care diagnostics. An easy-to-use and low-cost sensor platform is highly desired to measure various types of analytes (e.g., biomarkers, hormones, and drugs) quantitatively and specifically. For this reason, dry film photoresist technology - enabling cheap, facile, and high-throughput fabrication - was used to manufacture the microfluidic biosensor presented here. Depending on the bioassay used afterwards, the versatile platform is capable of detecting various types of biomolecules. For the fabrication of the device, platinum electrodes are structured on a flexible polyimide (PI) foil in the only clean-room process step. The PI foil serves as a substrate for the electrodes, which are insulated with an epoxy-based photoresist. The microfluidic channel is subsequently generated by the development and lamination of dry film photoresist (DFR) foils onto the PI wafer. By using a hydrophobic stopping barrier in the channel, the channel is separated into two specific areas: an immobilization section for the enzyme-linked assay and an electrochemical measurement cell for the amperometric signal readout.
The on-chip bioassay immobilization is performed by the adsorption of the biomolecules to the channel surface. The glucose oxidase enzyme is used as a transducer for electrochemical signal generation. In the presence of the substrate, glucose, hydrogen peroxide is produced, which is detected at the platinum working electrode. The stop-flow technique is applied to obtain signal amplification along with rapid detection. Different biomolecules can quantitatively be measured by means of the introduced microfluidic system, giving an indication of different types of diseases, or, in regard to therapeutic drug monitoring, facilitating a personalized therapy.

A microfluidic biosensor platform was designed and fabricated using low-cost dry film photoresist technology for the rapid and sensitive quantification of various analytes. This single-use system allows for the electrochemical readout of on-chip-immobilized enzyme-linked assays by means of the stop-flow technique.

In recent years, biomarker diagnostics became an indispensable tool for the diagnosis of human disease, especially for the point-of-care diagnostics. An ...

Fabrication and Validation of an Organ-on-chip System with Integrated Electrodes to Directly Quantify Transendothelial Electrical Resistance

Organs-on-chips, in vitro models involving the culture of (human) tissues inside microfluidic devices, are rapidly emerging and promise to provide useful research tools for studying human health and disease. To characterize the barrier function of cell layers cultured inside organ-on-chip devices, often transendothelial or transepithelial electrical resistance (TEER) is measured. To this end, electrodes are usually integrated into the chip by micromachining methods to provide more stable measurements than is achieved with manual insertion of electrodes into the inlets of the chip. However, these electrodes frequently hamper visual inspection of the studied cell layer or require expensive cleanroom processes for fabrication. To overcome these limitations, the device described here contains four easily integrated electrodes that are placed and fixed outside of the culture area, making visual inspection possible. Using these four electrodes the resistance of six measurement paths can be quantified, from which the TEER can be directly isolated, independent of the resistance of culture medium-filled microchannels. The blood-brain barrier was replicated in this device and its TEER was monitored to show the device applicability. This chip, the integrated electrodes and the TEER determination method are generally applicable in organs-on-chips, both to mimic other organs or to be incorporated into existing organ-on-chip systems.

This publication describes the fabrication of an organ-on-chip device with integrated electrodes for direct quantification of transendothelial electrical resistance (TEER). For validation, the blood-brain barrier was mimicked inside this microfluidic device and its barrier function was monitored. The presented methods for electrode integration and direct TEER quantification are generally applicable.

Organs-on-chips, in vitro models involving the culture of (human) tissues inside microfluidic devices, are rapidly emerging and promise to provide useful ...

Mechano-Node-Pore Sensing: A Rapid, Label-Free Platform for Multi-Parameter Single-Cell Viscoelastic Measurements

Cellular mechanical properties are involved in a wide variety of biological processes and diseases, ranging from stem cell differentiation to cancer metastasis. Conventional methods for measuring these properties, such as atomic force microscopy (AFM) and micropipette aspiration (MA), capture rich information, reflecting a cell's full viscoelastic response; however, these methods are limited by very low throughput. High-throughput approaches, such as real-time deformability cytometry (RT-DC), can only measure limited mechanical information, as they are often restricted to single-parameter readouts that only reflect a cell's elastic properties. In contrast to these methods, mechano-node-pore sensing (mechano-NPS) is a flexible, label-free microfluidic platform that bridges the gap in achieving multi-parameter viscoelastic measurements of a cell with moderate throughput. A direct current (DC) measurement is used to monitor cells as they transit a microfluidic channel, tracking their size and velocity before, during, and after they are forced through a narrow constriction. This information (i.e., size and velocity) is used to quantify each cell's transverse deformation, resistance to deformation, and recovery from deformation. In general, this electronics-based microfluidic platform provides multiple viscoelastic cell properties, and thus a more complete picture of a cell's mechanical state. Because it requires minimal sample preparation, utilizes a straightforward electronic measurement (in contrast to a high-speed camera), and takes advantage of standard soft lithography fabrication, the implementation of this platform is simple, accessible, and adaptable to downstream analysis. This platform's flexibility, utility, and sensitivity have provided unique mechanical information on a diverse range of cells, with the potential for many more applications in basic science and clinical diagnostics.

Presented here is a method to mechanically phenotype single cells using an electronics-based microfluidic platform called mechano-node-pore sensing (mechano-NPS). This platform maintains moderate throughput of 1-10 cells/s while measuring both the elastic and viscous biophysical properties of cells.

Cellular mechanical properties are involved in a wide variety of biological processes and diseases, ranging from stem cell differentiation to cancer ...

Mechanical Fatigue Testing of RBCs by Amplitude-Modulated Electrodeformation

Amplitude-Modulated Electrodeformation to Evaluate Mechanical Fatigue of Biological Cells

Red blood cells (RBCs) are known for their remarkable deformability. They repeatedly undergo considerable deformation when passing through the microcirculation. Reduced deformability is seen in physiologically aged RBCs. Existing techniques to measure cell deformability cannot easily be used for measuring fatigue, the gradual degradation in cell membranes caused by cyclic loads. We present a protocol to evaluate mechanical degradation in RBCs from cyclic shear stresses using amplitude shift keying (ASK) modulation-based electrodeformation in a microfluidic channel. Briefly, the interdigitated electrodes in the microfluidic channel are excited with a low voltage alternating current at radio frequencies using a signal generator. RBCs in suspension respond to the electric field and exhibit positive dielectrophoresis (DEP), which moves cells to the electrode edges. Cells are then stretched due to the electrical forces exerted on the two cell halves, resulting in uniaxial stretching, known as electrodeformation. The level of shear stress and the resultant deformation can be easily adjusted by changing the amplitude of the excitation wave. This enables quantifications of nonlinear deformability of RBCs in response to small and large deformations at high throughput. Modifying the excitation wave with the ASK strategy induces cyclic electrodeformation with programmable loading rates and frequencies. This provides a convenient way for the characterization of RBC fatigue. Our ASK-modulated electrodeformation approach enables, for the first time, a direct measurement of RBC fatigue from cyclic loads. It can be used as a tool for general biomechanical testing, for analyses of cell deformability and fatigue in other cell types and diseased conditions, and can also be combined with strategies to control the microenvironment of cells, such as oxygen tension and biological and chemical cues.

Author Spotlight: Studying Biomechanics of Circulating Cells by Modulating Their Electrodeformation Behavior 

Presented here is a protocol for mechanical fatigue testing in the case of human red blood cells using an amplitude-modulated electrodeformation approach. This general approach can be used to measure the systematic changes in morphological and biomechanical characteristics of biological cells in a suspension from cyclic deformation.

Red blood cells (RBCs) are known for their remarkable deformability. They repeatedly undergo considerable deformation when passing through the ...

Dynamic Multiparameter Platelet Function Assessment Using a Capacitive Biosensor

Platelets play a fundamental role in blood clotting through a series of regulated responses, including adhesion, spreading, granular secretion, aggregation, and cytoskeletal contraction. However, current assays are limited to partial analysis of platelet function under non-physiological conditions. Thus, an improved assay that reflects the dynamic and multifaceted nature of platelet function in physiological settings is necessary. In this context, a novel approach is introduced to measure several key parameters related to platelet function in a more physiologically relevant ex vivo semi-rigid microenvironment compared to traditional assays. This method utilizes an advanced electrical biosensor, the membrane capacitance sensor (MCS), which provides unique insights into the clotting process through three distinct readouts. These readouts are highly sensitive to variations in platelet count, stimulation intensity, and specific activation pathways. As a purely electrical sensing platform, the MCS demonstrates significant potential as a diagnostic tool for detecting primary hemostatic function disorders, evaluating the efficacy of therapeutic treatments, and advancing the broader understanding of the roles of platelets in hemostasis and thrombosis.

A protocol for a novel dynamic multiparameter platelet functional assay using a capacitive biosensor is presented here. This approach, designed within a semi-rigid microenvironment to enhance physiological relevance, provides three output parameters sensitive to platelet count, stimulation strengths, and activation pathways.

A Performance-testing Platform for a Conduction Micropump with an FR-4 Copper-clad Electrode Plate

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