The concept of fluidic multipoles, in analogy to electrostatics, has long been known as a particular class of solutions of the Navier-Stokes equation in potential flows; however, experimental observations of fluidic multipoles and of their characteristics have not been reported yet. Here we present a two-dimensional microfluidic quadrupole and a theoretical analysis consistent with the experimental observations. The microfluidic quadrupole was formed by simultaneously injecting and aspirating fluids from two pairs of opposing apertures in a narrow gap formed between a microfluidic probe and a substrate. A stagnation point was formed at the centre of the microfluidic quadrupole, and its position could be rapidly adjusted hydrodynamically. Following the injection of a solute through one of the poles, a stationary, tunable, and movable—that is, 'floating'—concentration gradient was formed at the stagnation point. Our results lay the foundation for future combined experimental and theoretical exploration of microfluidic planar multipoles including convective–diffusive phenomena.
Quadrupoles are used in numerous physical and engineering applications and arise under many forms, such as electrical charges and currents1, magnetic poles2, acoustic poles3,4, and gravitational masses5. Two popular applications of quadrupoles include the quadrupole mass spectrometer that uses four parallel metal rods with opposing alternating electrical currents to filter ions based on their mass-to-charge ratio6, and the quadrupole magnets that are used to focus beams of charged particles in particle accelerators2. In fluid mechanics, flow dipoles, or 'doublets' have been studied in porous rocks notably in the context of oil extraction7,8. To increase the recovery of oil pumped from a well, a solution can be injected in another well to displace the oil trapped within the rocks, according to a dipolar flow profile. We recently introduced the microfluidic probe (MFP)9 that uses both injection and aspiration aperture to flush a stream across a substrate surface, and that in fact represents a two-dimensional fluidic dipole, although this analogy has not been developed. Planar multipoles with more than two flow poles have been investigated theoretically by Koplik et al. with increasing numbers of sources and sinks (such as quadrupoles, octopoles etc.)10. Bazant et al. have also demonstrated the use of conformal mapping to solve a broad class of advection–diffusion problems in 2D irrotational flows11 by drawing an analogy with the pioneering work of Burgers on out-of-plane flow velocity in 2D vortex sheets12. However, experimental validation of these theoretical analyses is still outstanding as flow multipoles have not, to the best of our knowledge, been produced experimentally.
In this work, we present an experimental planar microfluidic quadrupole (MQ) in an open space confined between two parallel plates (Fig. 1). We extend the theoretical framework to describe hydrodynamic and convective–diffusive properties of the MQ in Hele–Shaw flows and derive the equations for the key parameters characteristic of the MQ such as the size of the flow confinement and length of the gradient formed within the MQ. Finite element simulations complete the analytical results and both are compared with experimental results. Finally, we present a first application of the MQ that can be used as a gradient generator and which, unlike prior gradient generators, affords low shear stress, rapid spatiotemporal tuning of the gradient either hydrodynamically by adjusting the flow rates, or physically by moving the MFP, and can be applied on any planar substrate and displaced as well.
MQs were formed between a MFP9 with 4 apertures arranged in a classical symmetric quadrupole configuration (Fig. 1b) and a flat bottom substrate. The MFP was microfabricated into Si and diced into squares with four openings constituting pairs of opposing apertures used for injection and aspiration. A Polydimethylsiloxane (PDMS) adapter block was bonded to the die, and capillaries were plugged into the block and connected to syringe pumps (Fig. 2a,b).
The MFP was immersed in fluid and brought close to a planar substrate so as to form a narrow gap (see Methods). A glass slide was used as the bottom substrate permitting visualization of the flow within the gap using an inverted microscope (Fig. 2c). Simultaneous injection and aspiration of fluid generates the quadrupolar flow, and the two injected fluids meet head-on at the centre of the MQ, generating a stagnation point (SP) with zero flow velocity (Fig. 1c–f). When the aspiration and injection flow rates are identical, a large fraction of the injected stream is re-aspirated; but the fraction of fluid that radially flows outward is not (Fig. 1b) and thus leaks into the fluid surrounding the MFP. However, if the ratio of aspiration/injection flow rates is >1, all the injected liquid is captured and aspirated back into the MFP (Fig. 1f).
We arbitrarily define the two injection apertures as positive poles (sources) and the aspiration apertures as negative poles (drains) (Supplementary Figure S1; Supplementary Methods). The MFP used here featured a centre-to-centre separation of 1,075 μm between pairs of opposing apertures, each 360 μm in diameter, and was positioned above, parallel to the bottom substrate so as to form a 50 μm gap for all experiments. This setup represents a parallel-plates configuration, and the MQ formed in the gap is quasi-two-dimensional. Using the Hele–Shaw approximation, it can thus be conveniently described as a two-dimensional Stokes flow of the form13:
where is the velocity field of the MQ, η is the viscosity, p is the hydrostatic pressure, H is the height of the gap between the plates (H=50 μm), and z is the vertical coordinate whereas z=0 corresponds to the bottom plate (substrate) and z=H to the top plate (MFP). The resulting flow velocities in the MQ are on the order of 2 mm s−1 or less for aspiration flow rates of 100 nl s−1 and the flow is purely viscous (Re ≪1), Supplementary Methods for details. Averaging equation (1) over the gap height, the velocity profile can be simplified as:
The height-averaged velocity profile given by this expression is irrotational13, and can therefore be represented by a scalar potential akin to an electric field or a current distribution that can also be described based on an electrostatic potential (Table 1). It thus becomes possible to calculate the flow velocity for any coordinate of the MQ by using the superposition principle as in the case of electrical charges and current quadrupoles (see Supplementary Methods):
where is the position vector and is the position of the sources and drains, both with respect to the centre of the probe. Qi is the flow rate from the ith inlet corresponding to Qinj and Qasp for injected and aspirated flow rate, respectively.
Flow confinements of the MQ
As mentioned earlier, the flow rates ratio Qasp/Qinj needs to be sufficiently high to hydrodynamically confine and capture all the injected fluid (Fig. 1b versus Fig. 1f). The confinement of the injected streams as function of the flow rates ratio were visualized using fluorescent tracer particles (Fig. 3a–c). The area flushed by the injected streams is an important concept for fluidic applications, because chemicals injected in the streams may be used to process selectively the underlying surface9, and we thus establish an analytical solution. The fluid that radiates outwards, relative to the centre of the MQ, will travel the greatest distance until the flow velocity becomes zero, at which point the flow direction is reversed, and it is eventually recaptured by an aspiration aperture. The confinement radius R of the MQ was defined as the distance between the SP and the outermost point of zero velocity for the radial streams, and using equation (3) yields (Supplementary Methods):
where Qasp is the aspiration flow rate, Qinj is the injection flow rate, and d is the centre-to-centre distance between the two inlets. We found excellent agreement between the calculated and experimentally measured R (Fig. 3). These results confirm the validity of our theoretical assumptions and analysis.
Fluid flow around the SP
A two-variable (x,y) Taylor expansion of equation (3) yields the velocity profile in the very close vicinity of the SP (valid for x,y≪d), see Supplementary Methods for details:
where 〈Q〉=(Qasp+Qinj)/2 is the average flow rate between the inlet and outlet, and the origin (0,0) corresponds to the position of the SP. The flow profile can also be expressed in the form of a velocity potential11, (Table 1):
Interestingly, this velocity potential is identical to the one describing two-dimensional flow along a right-angle corner14. In the MQ, the four quadrants defined by the symmetry lines XX′ and YY′ in Figure 1d each constitute a virtual corner with a corresponding corner flow. Path lines formed by green tracer beads and a ratio Qasp/Qinj=10 outline the SP at the centre (Fig. 1f; Supplementary Movie 1), and are consistent with the velocity profile and streamlines obtained using FEM simulations (Fig. 4a). As the flow velocity tends to zero when approaching the SP (Fig. 4b), the calculated wall shear stress was found to converge to zero as well, Supplementary Figure S2a. The shear stress increases linearly when moving away from the SP and reaches a maxima near the inner edge of each aspiration aperture. Within a circle with a diameter of 100 μm (∼10% of the distance d) centred at the SP, shear stresses are less than 10% of that local maxima as shown in Figure 4c (Supplementary Methods). For a MQ with injection and aspiration flow rates of 10 and 100 nl s−1, respectively, the local maxima of shear stresses is τmax=0.15 Pa, and hence <0.015 Pa inside the circle. The shear stress also varies linearly with the aspiration flow rates that may be reduced to further minimize stress (Supplementary Fig. S2b; Supplementary Methods).
Convection–diffusion and gradients at the SP
When a solute is added to one of the injected streams, diffusive mass transport gradually dominates when approaching the SP as the convective flow converges towards zero. The solute is continuously replenished by one stream acting as a source, while it is also continuously transported away by the other stream that acts as a sink. Along the axis of the two injection apertures (XX′), the solute diffuses into the opposing stream at the SP while it is simultaneously pushed back by the inward convection of the opposing stream, and a steady-state, stationary concentration gradient is formed. To characterize this gradient mathematically, we first consider the general time-dependent diffusion–convection equation15:
where D is the diffusivity of the species studied, is the height-averaged in plane velocity profile and C is the concentration of the solute (normalized between 0 and 1). The steady-state version of equation (7) (with the left-hand term set to zero) is reminiscent of the flow in a 'Burgers vortex sheet'12 where C is analogous to the out of plane velocity, as was pointed out by Bazant and Moffatt16.
On the basis of the experimental observations shown below, the gradient length, which here is defined as the distance between the points with a concentration of 10 and 90% of the original solute concentration, is small when compared with the distance between the inlets along the XX′ axis (Fig. 5a). Using the approximated velocity profile around the SP of equation (5), and combining it with equation (7), the convection–diffusion equation relevant to the flow around the SP formed within the MQ can be re-written as:
where D is the diffusion constant of the solute. The derivatives with respect to y have been neglected in equations (7) and (8) as the concentration interface is invariant in y (∂C/∂y=0 everywhere) under Hele–Shaw assumption; see Supplementary Methods for details. Using the dimensionless numbers , , where is the global Péclet number for the MQ, we find the simple dimensionless expression for this transport problem to be:
Therefore and are the natural scales of the MQ. They represent, respectively, the length over which diffusion takes place at the interface and the characteristic time before steady state is achieved. Typical conditions in our experiments were an average flow rate of 55 nl s−1, and D=500 μm2 s−1 as we used fluorescein as the diffusive species. Using these values, we obtain x0=15 μm and t0=0.4 s. Thus, after a few seconds, the gradient will have reached a steady –state, and the time-dependent term of equation (9) can be neglected. When performing this approximation, equation (9) reduces to a one-dimensional problem with C(x,t) being the concentration profile at the SP perpendicularly to the interface where diffusion takes place.
For the experimental conditions used here, the concentration gradients at the SP were much shorter than the distance d separating the two inlets, d may thus be considered infinite and thus the boundary conditions become:
This allows simplifying the calculations and solving equations (9) and (10) for the concentration under these conditions gives:
where erf is the error function17. Once again, the solution here is similar to that of the out-of-plane velocity in a Burgers vortex sheet, but with the Péclet number replacing the Reynolds number of the classical analysis16. The gradient length can be calculated using equation (11) and expressed as:
The gradient length is proportional to the average flow rate and obeys a simple power law.
The analytical solution for the gradient length was compared with experimental measurements using fluorescein sodium salts (376 Da, diffusion coefficient in water D=500 μm2 s−1 (refs 18,19,20)) diluted in water. Fluorescein was injected through the top-right aperture, and the gradient formation at the SP within the MQ was modelled numerically (Supplementary Fig. S3a), and measured experimentally, (Fig. 5a). Theoretical and experiment gradient profiles are in excellent agreement, (Fig. 5b; Supplementary Figure S3b).
We observed that the gradient was constant along the YY′ axis connecting the two aspiration apertures(Fig. 5a,b). The flow perpendicular to the gradient carries it towards each of the aspiration apertures, and convection rapidly dominates diffusion when moving away from the SP (see Supplementary Methods for details) while the concentric flow around the aspiration apertures focuses the stream when approaching the inlet. Collectively, these effects counter diffusive broadening of the gradient and explain the quasi-constant gradient profile along the YY′ line connecting both aspiration apertures.
We compared the calculated gradient length with experimental measurements for a Qasp/Qinj, varying from 2 to 15 (Fig. 5c–g), and found them to be in good agreement. For Qasp increasing from 20 to 250 nl s−1, the gradient length decreased from 69 to 25.7 μm. This range of accessible gradient slopes may be further increased by exploring a wider range of flow rates from pl s−1 to μl s−1. The gradient changes rapidly (Supplementary Movie 2), and, therefore, dynamic gradients may readily be formed simply by pre-programming the aspiration flow rates. Whereas the confinement of the MQ is governed by Qasp/Qinj, equation (12) indicates that the gradient slope and length depend on 〈Q〉 and, thus, primarily on Qasp for high ratios of Qasp/Qinj. This theoretical result is supported by the experiments where only Qasp was changed, Figure 5, or where only Qinj was tuned (Supplementary Figure S4; Supplementary Movie 3). It is thus possible to vary the confinement and the gradient slope independently by keeping one of them constant by simultaneously tuning Qasp and Qinj.
Asymmetric MQ flow profiles and floating gradient
For all experiments described up to this point, each pair of injection and of aspiration flow rates were adjusted in synchrony and kept equal, which fixed the SP at the centre of the MQ. If the flow rate of only one of the two injection or aspiration apertures is changed, the symmetry is broken and the position of the SP will change (Fig. 6a,b). The gradient, which originates at the SP, moves along with the SP and can thus be displaced hydrodynamically within the central area of the MQ. The gradient is formed along a straight interface when the SP is centred, and along a curved interface when moving the SP towards any of the injection apertures (Fig. 6c,d). By using a programmable flow control system, or by manually changing the flow rates, oscillating and rapidly moving gradients can be generated (Supplementary Movie 4). Complex spatiotemporal gradient landscapes may thus be formed around a particular point by changing both the gradient slope and the gradient position. The gradient may be adjusted either in a preprogrammed manner, or in real time in response to observations.
Alternatively, for scanning larger areas and reach positions outside the MQ's central area, the gradient at a point may also be changed by displacing the substrate relative to the MFP, either by moving the bottom substrate that is clamped to the motorized xy-stage of the microscope, or by manually moving the MFP using the micrometer screws of the probe holder (Fig. 2c)21. The MQ field lines and the concentration gradient are temporarily perturbed while the MFP moves relative to the substrate proportionally to the speed of displacement. For example, a speed of 300 μm s−1 lead to a small but visible disturbance of the gradient (Supplementary Movie 5). The results indicate that the gradient re-equilibrated within few seconds after stopping the movement. Faster movements are possible but at the expense of greater disturbance of the gradient. Supplementary Movie 6 shows the gradient while moving the substrate at speed of 7 mm s−1, and Supplementary Movie 7 shows the gradient while the MFP is being manually displaced. Using these two approaches, different areas of the substrates can be exposed to the gradient one after the other.
We have presented an experimental demonstration of fluidic quadrupoles and found excellent agreement between theoretical prediction and experimental results, thus lending support to the general analytical framework developed to describe multipolar flow. Using the Hele–Shaw formalism, we established a close analogy between MQs, electrical quadrupoles, and vortex sheets in fluid dynamics. Our analysis was extended to include phenomena that were not studied before and the governing equations for a Hele–Shaw geometry derived for flow confinement and for the convection–diffusion of solutes at the SP. In analogy to electrical poles, and as was developed theoretically11,16, the number of poles may be further expanded and inspire combined theoretical and experimental studies of convection–diffusion phenomena with multiple poles and multiple chemicals.
We demonstrated a first application of MQs as concentration gradient generators. The gradient is generated around the SP that experiences no flow and no shear stresses similar to stationary source-sink gradients22,23, while being continuously fed by the streams of the MQ and thus formed within seconds and could be rapidly adjusted, akin to microfluidic gradients with active flow24,25,26,27. Several approaches for forming gradients using hybrid approaches combining flow and no-flow zones have been proposed, but required porous elements28,29 or nanochannels30,31. Gradients in open chambers have also been proposed32,33 to allow user access (that is, pipetting) to the cell culture. These devices provide low shear stress cultures, while allowing to adjust the concentration gradients. However, these devices entail either closed chambers, or complicated fabrication processes, or both, and the time to adjust the gradient was typically longer than with the MQ. Another recent technique34 used a laser beam to open and close pores in an integrated impermeable membrane to expose the cell culture to reagents selectively; however, this device involves closed cell culture chamber and a sophisticated experimental setup.
The floating gradients formed within the MQ are remarkable because of a series of individual characteristics, and owing to the properties and possibilities that arise by the combination of these characteristics. They include, being open and brought down onto the target areas, the combination of active flow and shear-free zone obtained using hydrodynamic effects alone and without need for nanochannels or membranes, the possibility to rapidly adjust and move the gradient hydrodynamically within a few seconds, while also allowing to move it physically by displacing the MFP, and, finally, the possibility of repeated use of the device for many different experiments.
This setup should be well suited for applications in cell biology such as studying cellular migrations26,35 and neuronal navigation36,37, or stem cell differentiation38, because chemical cues can be applied and modulated rapidly to individual cells at the SP with minimal shear stress. It will be interesting to find out whether these properties can be exploited and the MFP–MQ used to study the response of neurons and stem cells to gradients; indeed neurons and stem cells are particularly difficult to culture and maintain inside closed channels for long periods39,40, and that have been shown to be very sensitive to shear stress41. Furthermore, the MQ and floating gradients could be used to study large samples that are hard to cultivate inside closed channels, such as embryos or tissue slices42. Finally, it may be useful for surface patterning by positioning and scanning the MFP atop surfaces9,43,44.
The MFP fabrication and operation
The MFP comprises a square Si chip (3 mm in width) with 4 etched holes of 360 μm diameter, and a PDMS interface chip with holes for receiving the capillaries of 360 and 250 μm outer and inner diameters, respectively, that connect it to the injection and aspiration syringe pumps (Nemesys) (Fig. 2a). The Si chips were fabricated in 200 μm thick, double-side-polished silicon wafers (Silicon Quest), using photolithography and deep-reactive-ion etching. Etching masks were formed on silicon wafers by using standard photolithography and S1813 photoresist (Shipley) to pattern a 2 μm thick thermal SiO2 layer. The openings were made by deep reactive ion etching (DRIE, ASE etcher, Surface Technology Systems). The PDMS interface block was fabricated by casting poly(dimethylsiloxane) PDMS (Sylgard 184Dow Corning) into a home-made micromold composed of two structured steel plates, a polished steel plate with vias (access holes) forming the bottom, and four capillaries (each inserted into one of the four vias in the polished steel plate) serving as place holders for the fluidic connection holes. The PDMS was cured in an oven at 60 °C for at least 3 h (usually over night). The PDMS block was bonded to the Si chip by activating both parts in air plasma (Plasmaline 415 Plasma Asher, Tegal Corporation), at 0.2 mbar for 45 s at 75 W, and joining the two together using a home-made mechanical alignment aid and placed in an oven at 90 °C for 20 min. Operation of this MFP is similar to the use of the original MFP9,21,44, except that four independent syringe pumps are required to control the flow rate of each aperture independently. Briefly, the MFP was secured inside the clamping rode (Fig. 2b) and mounted on the xyz micropositioner (7600-XYZL, Siskiyou), what we call the probe holder. Using the probe holder, the MFP was positioned parallel to the transparent substrate (glass slide) atop an inverted microscope (TE2000, Nikon) so as to form a microscopic gap while immersed under the surrounding medium (Fig. 2c). Glass capillaries (Polymicro Tech) connect the MFP apertures to glass syringes (Hamilton) that are operated using a computer-controlled syringe pumps (Nemesys Cetoni).
The three-dimensional simulations were carried out using the commercially available finite element simulation software Comsol Multiphysics 3.5 (Comsol) and run on an eight-core, 64-bit computer (Xeon, Dell) with 26 GB of RAM. The MFP geometry was modelled with the same shape and dimensions as the microfabricated MFP used in the experiments. Simulations coupled the solution of Navier–Stokes equation and convection–diffusion equation. Sample solutions were assumed to be water (incompressible Newtonian fluid with a density of 998.2 kg m−3, and a dynamic viscosity of 0.001 N·s m−2), and the diffusion coefficient of the solute was 500 μm2 s−1, which corresponds to the diffusion constant of fluorescein in water. The simulations were run under steady-state conditions and assumed no-slip boundary conditions on the substrate and the MFP surface, with the flow boundary conditions at the MQ's perimeter sides set as open boundaries (equal to atmospheric pressure). As boundary conditions for the mass transfer equation, the MFP surface and substrate were defined as an insulating boundary, and a zero inward flux was set at the perimeter of the MQ model. The experimental values were used for injection and aspiration flow rates. The concentration of the solute at the source injection aperture was arbitrarily set to 1 mol m−3, 0 at the other injection aperture, and convective flux was set for both aspiration apertures.
Image acquisition and analysis
Images were recorded using a cooled CCD camera (Photometrics CoolSNAP HQ2) connected to the microscope. Black-and-white images were analysed and coloured using the software ImageJ 1.42 (National Institutes of Health Maryland). Images of green and red beads pathlines were joined together digitally using the freeware software GIMP 2.6.7 (Free Software Foundation). Videos were recorded using a digital consumer camcorder camera (HDR-SR7, Sony Electronics) connected to the microscope through a C-mount adaptor. The gradient lengths shown in Figure 5g were defined as the distance between 90 percent and 10 percent of the maximum fluorescence intensity signal, as shown in Supplementary Figure S5.
Chemicals and experimental procedures
Fluorescein sodium salt (C20H10Na2O5) was purchased from Sigma-Aldrich, and fluorescein solutions were prepared by dissolving 0.03 g of the salt with 100 ml of distilled water. Red and yellow-green carboxylate-modified fluorescent microspheres (fluosphere, 2 μm diameters) were purchased from Invitrogen. The solutions used in experiments were prepared by diluting 0.1 ml of the beads solution with 13 ml of distilled water.
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We acknowledge funding from NSERC, CIHR, CHRP, Genome Canada, Genome Quebec, CFI, and the assistance of McGill Nanotools Microfab Laboratory (funded by CFI, NSERC and VRQ). M.A.Q. thanks Roozbeh Safavieh and Cécile Perrault for their help and discussion. We acknowledge Michel Godin, Sebastien Ricoult, Gina Zhou, Huiyan Li, Setareh Ghorbanian, and Nageswara R Ghattamaneni for critical reading the manuscript. M.A.Q. acknowledges Alexander Graham Bell Canada NSERC Scholarship and D.J. acknowledges support from a Canada Research Chair.
The authors declare no competing financial interests.
Supplementary Figures S1-S5, Supplementary Table S1, Supplementary Methods and Supplementary Reference. (PDF 435 kb)
Real time movie of green and red fluorescent tracer microbeads (2 μm in size) injected at a flow rate QInj=10 nl/s through the bottom left and top right apertures of a MQ. The fluid was aspirated back through the other two apertures at a rate QAsp=100 nl/s. The stagnation point (indicated by the arrow) is revealed by the velocity pattern which tends to zero close to the stagnation point. (MOV 3701 kb)
Real time movie showing the rapid tuning of a fluorescein gradient width and slope following change of the aspiration flow rate (QAsp) under constant injection flow rate (QInj =5 nl/s). Fluorescein in water and only water were injected through the top left and bottom right apertures, respectively, and aspirations were carried out through the other two apertures. (MOV 4909 kb)
Real time movie showing the width of a fluorescein diffusion gradient for a constant aspiration flow rate and a varying injection flow rate. Fluorescein solved in water and only water injected through the top left and bottom right apertures, respectively, and aspirated back through the other two apertures. Whereas the confinement within the MQ varies depending on the QAsp/ QInj, the slope remains constant for the ratios used here. (MOV 425 kb)
Real time movie of an oscillating gradient formed using an MQ by manually varying the injection flow rate of one injection aperture from 10 nl/s to 80 nl/s while keeping the other injection aperture fixed at 10 nl/s, and the aspiration flow rates at 150 nl/s each. Fluorescein in water and only water were injected through the top left and bottom right apertures, respectively, and aspirations were carried out through the other two apertures. (MOV 441 kb)
Real time movie of a fluorescein gradient over a substrate moving at 300 μm/s back and forth relative to the MFP. The specks of dust on the bottom substrate help visualize the movement. Fluorescein in water and only water were injected through the top left and bottom right apertures, respectively, and aspirations were carried out through the other two apertures. (MOV 538 kb)
Real time movie showing the disruption of the MQ and fluorescein gradient following rapid movement of the substrate with a speed of 7 mm/s relative to the MFP. As it can be seen, the MQ disruption is followed by rapid regeneration when the substrate stops moving. Fluorescein in water and only water were injected through the top left and bottom right apertures, respectively, and aspirations were carried out through the other two apertures. (MOV 222 kb)
Real time movie of the fluorescein gradient following manual, oscillatory movement of the MFP across an immobile substrate. Fluorescein in water and only water were injected through the top left and bottom right apertures, respectively, and aspirations were carried out through the other two apertures. (MOV 414 kb)
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Qasaimeh, M., Gervais, T. & Juncker, D. Microfluidic quadrupole and floating concentration gradient. Nat Commun 2, 464 (2011). https://doi.org/10.1038/ncomms1471
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