O. Kašpar,
A. H. Koyuncu,
A. Hubatová-Vacková,
M. Balouch and
V. Tokárová
*
Department of Chemical Engineering, University of Chemistry and Technology Prague, Technická 5, 166 28, Prague 6, Czech Republic. E-mail: viola.tokarova@vscht.cz
First published on 17th April 2020
Microfluidic devices, allowing superior control over the spatial and temporal distribution of chemical substances and high process reproducibility, are nowadays essential in various research areas and industrial fields where the traditional “macroscopic” approach was no longer able to keep up with the increasing demands of high-end applications. In the present work, internal mixing of droplets formed by a flow-focusing X-junction at constant flow rates of both phases for three different channel heights (i.e. 20, 40 and 60 μm) was investigated and characterised. Both experimental methods and 3D CFD simulations were employed in order to resolve governing factors having an impact on internal mixing and homogenization time of model tracers inside of droplet reactors. Additionally, the influence of channel height on internal mixing was experimentally studied for continuous preparation of iron oxide nanoparticles by co-precipitation reaction. Since the initial nucleation phase is strongly affected by mixing and spatial distribution of all reactants, the final particle size and particle size distribution (PSD) can be used as direct indicators of mixing performance. It has been demonstrated that the smallest 20 μm channels provided narrower PSD and smaller particle mean size compared to higher channels.
Monodisperse droplets can be generated in microfluidics actively using external source of energy (e.g. pressure pulses, vibrations, thermal field, electric field) or passively (pressure-driven flow).5,6 According to the chip layout and relative orientation of immiscible fluids, we can classify droplet generation geometries as (i) cross-flow,7,8 (ii) co-flow9 and (iii) flow-focusing.10,11 The cross-flow is formed by angled microchannels where dispersed and continuous phases come together (e.g. T-junction, Y-junction). In the co-flow geometry, the immiscible phases share the same flow direction in a set of coaxial microchannels. Flow-focusing geometry, employed in this work, is composed of three channels, one main channel and two symmetric side channels, forming axisymmetric X-junction where both immiscible fluids intersect each other. In this type of junction, one fluid (dispersed phase) is discretised at high frequency (Hz to kHz) into small volumes dispersed in the immiscible carrier fluid (continuous phase). The complex mechanism of droplet formation is based on competition among interfacial, inertia, viscous and gravitational forces. Contribution of the latter is due to small characteristic lengths usually negligible in microfluidics. For a given set of parameters, the interplay between acting forces governs the type of observed multi-phase flow pattern, i.e. co-flow, segmented flow, squeezing, dripping or jetting regime.5
Each droplet can be considered as a single reactor, physically and chemically isolated from the surroundings by the immiscible continuous phase. In some cases, a particular type of fluid is selected, allowing transport of necessary reagents across the droplet interface (e.g. CO2/O2 exchange essential for handling of living cells).12 Small droplet volumes and minimal reagent consumption, high interfacial area responsible for efficient heat and mass transfer, and isolation of droplet content from the surroundings are the most important for numerous high-end applications, e.g. single-cell handling, screening, and analysis,4 DNA encapsulation13 or nanoparticle synthesis and modification.14,15 In the case where two or more reacting streams form a droplet, efficient and very fast homogenisation have to be achieved. Internal mixing plays a crucial role in the applications where reaction mechanisms are very fast, typically in milliseconds, i.e. nucleation followed by particle growth in co-precipitation reactions.16 Fast homogenization in microfluidic devices is challenging, which is given by low values of Reynolds number (Re < 1) and laminar character of a flow, and mixing is only governed by molecular diffusion.17 Just as a droplet formation, enhancement of a droplet internal mixing can be achieved passively18 or actively6 using external energy, e.g. droplet-boundary oscillation under AC actuation,19 thermo-capillary mixing with micro-wave heater,20 droplet homogenization via electrostatic forces21 or magnetic actuation.22 Additional geometrical constraints can attain passive homogenization of a droplet content. The role of these structures is to introduce chaotic advection breaking axisymmetric recirculation profile inside of droplets, which results in enhancement of homogenisation without higher fabrication complexity of the device. Passive mixing can be achieved by non-rectangular channel cross-sections,23 and specific channel design (sinusoidal channels24,25 and baffle channels26) exploiting the formation of transversal vortices (Dean flows).27
Knowledge about hydrodynamics and mixing phenomena inside of droplets plays a vital role in design optimisation and prospective expansion of microfluidics in various high-end applications.28,29 Currently, the character of the fluid movement is mostly examined by microscale Particle Image Velocimetry (μPIV) using microscopic latex particles as a model tracer.30 For the experimental evaluation of mixing performance, a variety of microscopic techniques with the aid of flow visualisation by pH-sensitive, coloured and fluorescent dyes, have been employed.14,31,32 Two-dimensional projection of a 3D droplet into a plane has been addressed by Fluorescence-Lifetime Imaging (FLIM) providing three-dimensional information about a tracer distribution for both, quasi-steady flows32 and rapidly flowing droplets.33 However, a high purchasing cost significantly hinders the widespread application of this technique.
Numerical tools, on the other hand, allow addition insight into mixing phenomena with spatiotemporal resolution limited only by available computational resources. Most of the numerical studies about passive mixing in droplet-based microfluidics consider only lateral dimensions of channel geometry, and the influence of the channel height on droplet formation is omitted. Besides, mixing efficiency based on 2D CFD description of mass transport takes into consideration only an equatorial droplet cross-section which is not an accurate representation of a droplet volume and an internal recirculation flow pattern. Recently, 3D CFD analysis of internal mixing by convection has been demonstrated for slug-34 and droplet-flow generated by T-junctions.35 Despite the high popularity of droplet microfluidic technologies and increasing demand for fast and reliable mixing, three-dimensional numerical analysis of mixing performance of flow-focusing droplet generators, i.e. X-junctions, is still not fully explored.
In this work, we study and discuss the influence of the channel height on the droplet homogenization, taking into consideration the influence of horizontal channel dimension and 3D internal recirculation. The experimental results of mixing efficiency inside the droplet are substantiated by numerical simulations. Finally, the synthesis of iron oxide nanoparticles using droplet-based microfluidics, a model system of co-precipitation reaction highly sensitive to initial nucleation rate governed by initial mixing of precursors36 and their spatiotemporal distribution inside of droplet reactor, is provided. The influence of mixing performance for three channel heights (20, 40 and 60 μm) on the particle size and polydispersity index of prepared iron oxide nanoparticles is demonstrated. To the best of our knowledge, a similar study of X-junction droplet generator with various channel heights has not been conducted yet.
Modular high-precision syringe pumps neMESYS (CETONI) were employed for accurate dosing and control of inlet flow rates for both dispersed and continuous phases. All liquids were filtered through a 0.25 μm filter to remove insoluble impurities before filling the syringes. All inlet/outlet capillaries (din = 0.32 mm) and fittings were made from Teflon (Adtech) to avert particle deposition and chip fouling. Olympus CKX41 inverted microscope with mounted Canon EOS 100D digital camera was used for visual observation of droplet flow and image acquisition. Fiji, a distribution of open-source ImageJ software, was used for all image post-processing, i.e. evaluation of droplet diameter and mixing performance.37 JEOL JEM-1010 (TEM – transmission electron microscope) at an acceleration voltage of 80 kV was used to observe the size and morphology of iron oxide nanoparticles. Micrographs were taken by SIS Megaview III digital camera (Soft Imaging Systems) and analysed by Fiji software. Comsol Multiphysics software was used for CFD simulation of the two-phase flow and reactant mixing. Interfacial surface tension σ and wetting angle θw were determined by optical tensiometer Attension Theta (Biolin Scientific). Dynamic viscosity of the fluid at room temperature was measured by rheometer Rheolab QC (Anton Paar GmbH). Surface Evolver – Fluid Interface Tool (SE-FIT) software38 was used for the numerical calculation of Laplace pressure for stagnant droplets by a gradient descent method.39
Silicon masters with dykes of different heights (20, 40 and 60 μm) were prepared according to a previously published protocol.14 PDMS microfluidic chips were fabricated by a concentration gradient method where silicon master serves as a template, and the final chip is fabricated from two sandwiched layers of PDMS.40 This procedure ensures the same material properties of the chip governing wetting and droplet formation. Briefly, a degassed PDMS polymer mixture prepared by mixing the crosslinking agent and the silicone elastomer in mass ratio 1:
10 was poured over the silicon wafer, degassed under vacuum to remove entrapped bubbles, and heat-treated at 75 °C for 22 min in the oven. Solidified PDMS mould was separated from the silicon master, and the connecting holes for inlet and outlet tubings were punched. The bottom part of the PDMS chip was fabricated from elastomer mixture poured into an empty Petri dish and heat-treated for 20 min at 75 °C. Due to a shorter heat treatment time, the upper surface of the PDMS layer remains sticky and adhesive. Both parts of the chip were gently assembled and placed in an oven at 75 °C to ensure proper bonding between the PDMS layers. Then, the inlet capillaries were connected to syringes (Hamilton) containing reagent solutions. The image of the whole microfluidic chip with connected capillaries is shown in ESI (Fig. SI(1)†). The detail of the cross-junction fabricated from PDMS is in Fig. 1B. A computer-controlled linear pump system (neMESYS) was used to precisely control the flow rates of the reagents and the continuous phase. The outlet was connected via 100 mm long capillary to a collection vial prefilled with pure water.
The region of interests (ROIs) was defined by the ROI Manager tool to manually define by ellipses of the same dimensions inscribed into droplets. Elliptical ROI was chosen over circular due to droplet deformation along the central line of the channel. These ROIs were equidistantly separated from dark droplet contours (caused by droplet curvature) by the margin of constant thickness in order to avoid false concentration overshoots. Example of image post-processing workflow is demonstrated in Result section 3.2 (Fig. 6A–C). Average pixel intensity and the standard deviation was evaluated in selected regions. Mixing intensity m was calculated for every droplet ROI based on mean pixel intensity Iavg and standard deviation of pixel intensity σ as:
![]() | (1) |
ρ∇ ·u = 0 | (2) |
![]() | (3) |
Fst = σδκn + δ∇sσ | (3.1) |
κ = −∇·n | (3.2) |
∇s = (I − nnT)∇ | (3.3) |
![]() | (4) |
![]() | (5) |
During the first series of trial simulations, we have encountered a problem with excessive diffusion of the tracer from droplets into the oil phase resulting in the gradual diminishing of the overall tracer amount inside of droplets. This effect was significantly reduced, introducing the level set-dependent velocity field and diffusion coefficient, both effectively preventing tracer flux across the droplet interface. The diffusion coefficient and velocity magnitude values were conditionally set to 0 m2 s−1 and 0 m s−1, respectively, at any point outside of aqueous phase (Φ < 0.5). For convection-dominated transport problems, Comsol Multiphysics automatically uses consistent stabilisation methods (streamline and crosswind diffusion) to prevent oscillations in the solution. However, these methods cause artificial diffusion and can create similar issues with excessive tracer dilution over time. On the other hand, simulations with disabled stabilisation often suffer from poor convergence and/or unphysical over- and undershoots (e.g. negative or very high local concentrations). This issue was solved using Do Carmo and Galeão consistent stabilisation, high-quality mesh and tight solver error tolerances at the cost of a high computational cost. Moreover, in order to account for the evolution of the concentration profile from the predetermined initial state (t = 0 s), the first three droplets were excluded from the analysis.
In order to study droplets as entities, continuous spatial domains Ω (x, y, z) corresponding to a droplet volume at a given time and space was determined. Domain Ω was only defined if both parameters, Φ ≥ 0.5 and x ∈ (xmin; xmax), were met. The first condition ensures that only the dispersed phase is considered, whereas xmin and xmax are x coordinates of the parallel boundaries fully confining one droplet at a time, as shown in Fig. 2.
The segmentation of the entire model into sub-domains allows to calculate the mean concentration of the tracer cavg, standard derivation of concentration σ and mixing segregation index m for every single droplet defined as:
![]() | (6) |
![]() | (6.1) |
![]() | (6.2) |
The CFD results of the droplet generation are shown in Fig. 3A. Fiji software was used for calculation of droplet diameter d = (4Aπ−1)0.5 based on the surface area A of a droplet equatorial cross-section. Table 1 summarises numerical and experimental results and Fig. 3B shows the relation between the channel height and the droplet diameter/volume/frequency. It was observed that for the fixed inlet conditions, the microfluidic chip with higher channels produces larger droplets, and 2× and 3× higher channels resulted in 14% and 21% increase in droplet diameter, respectively. The volume of dispersed droplets was linearly proportional to a channel height. Frequency of droplet generation observed for 20 μm channels (114.3 ± 0.7 Hz) was reduced by 58% and 74% for 40 and 60 μm channel height, respectively. The separation distance between two consecutive droplets measured by Fiji software along the central line of the channel was larger with channel height, i.e. 339, 350 and 365 μm for 20, 40 and 60 μm, respectively.
Height [μm] | dexp [μm] | dsim [μm] | Δd [%] | Vsim [pL] | fsim [Hz] | Ca [—] |
---|---|---|---|---|---|---|
20 | 84.8 ± 1.7 | 81.8 ± 0.1 | 3.5 | 99.7 ± 0.5 | 114.3 ± 0.7 | 12.57 × 10−3 |
40 | 97.2 ± 0.3 | 93.4 ± 0.3 | 2.0 | 233.8 ± 2.8 | 47.7 ± 0.4 | 6.29 × 10−3 |
60 | 103.6 ± 5.7 | 99.2 ± 0.8 | 4.3 | 373.7 ± 6.1 | 29.8 ± 0.6 | 4.19 × 10−3 |
For experimental results, the microscopy images of droplets were evaluated using Fiji software. The minimum of 30 droplets from three independent experiments of each channel height were evaluated and compared. Experimental results are in agreement with simulation results in terms of droplet size and spacing. The droplet sizes based on CFD results were slightly underestimated (Δd = 2.0 to 4.3%), as shown in Table 1. The last column shows the calculated capillary number (Ca) defined as Ca = ηoiluσ−1, where u is a characteristic velocity of the fluid in the outlet channel (100 μm width), ηoil is the dynamic viscosity of the continuous phase, and σ is interfacial surface tension.
Numerical simulations characterised the flow regimes for all studied channel heights. In terms of a droplet generation in X-junction, one can distinguish three main flow regimes, (i) dripping, (ii) squeezing and (iii) jetting.14 Droplets formed in the jetting regime are detached at the end of the elongated thread of the dispersed phase outside of the focusing junction. The jetting regime was not observed for given combinations of flow rates and channel heights. Dripping regime can be distinguished from squeezing regime by the fact the continuous phase is not fully separated by the dispersed phase at any moment. In the case of squeezing regime, the dispersed phase obscures outlet orifice completely, which results in a gradual increase of upstream pressure in the continuous phase. Relationship between the pressure and the droplet formation period is shown in Fig. 4. The droplet formation of the dripping regime, observed only for a 20 μm high channel, can be divided into following stages: (a) droplet pinch off and recoil – the minimal pressure of both phases; (b) gradual interface growth; (c) partial blocking of outlet channel – the highest pressure in the continuous phase (Δp = 2165 Pa); (d) necking followed by the droplet detachment (stage a). On the other hand, squeezing regime was characteristic for 40 and 60 μm channel heights where dispersed fluid fully occupied outlet channel. This regime can be described by the following stages: (a′) droplet detachment – the lowest pressure for both phases; (b′) interface bulging; (c′) channel clogging – gradual increase of pressure in continuous phase to the maximum value (Δp was 1966 and 2022 Pa for 40 and 60 μm channels, respectively); and (d′) necking followed by droplet formation.
The pressure difference across the interface of relaxed droplets corresponds primarily to the Laplace pressure (Δp = σ(1/R1 + 1/R2), where R1 and R2 are principal radii of curvature at a given point on the free droplet interface). Numerical calculations of pressure across the interface of steady droplets were obtained using Surface Evolver software. Droplet volume (Table 1) was confined between the two parallel planes separated by the distance corresponding to a channel height. Model inlet parameters (i.e. liquid density, interfacial surface tension and contact angle) were the same as for Comsol simulations described in Section 2.3. The droplets with minimal surface energy are shown in Fig. 5 with calculated values of Laplace pressure: 5422, 3133 and 2365 Pa for 20, 40 and 60 μm high channels, respectively. The increasing pressure for lower channels is caused by a smaller radius of curvature R1, as illustrated in Fig. 5 by red dashed circle.
Based on experimental observations and numerical results, inlet streams of the dispersed phase are effectively separated by the blank phase ahead of the cross-junction. The first significant mixing of reacting streams (R1 and R2) occurs near the liquid–liquid interface preceding droplet formation by the mechanism known as the twirling effect.28 Three-dimensional tracer distributions and mixing indices for droplets exiting the outlet nozzle (position 0 in Fig. 7) are shown in Fig. 8. Interestingly, the calculated mixing intensity increased with the channel height, even though the droplet volume and diffusion lengths are both larger. This can be explained by tracer distribution and increased mixing at the junction since the lower frequency of the droplet generation for higher channels leads to a longer duration of the premixing period expressed as T = f−1, where f is the frequency of the droplet generation. Therefore, the initial spatial distribution of the tracer at the time of a droplet formation is significantly affected by the duration of premixing period T, i.e. 9, 21 and 34 ms for channel height 20, 40 and 60 μm, respectively.
Fig. 9A shows the evolution of mixing index m for 20, 40 and 60 μm high channels based on the horizontal distance of the droplet centre from the cross-junction. Every data point represents the mean value of five consecutive droplets captured at the same position, which was achieved manually by superposition of the droplet outlines.
![]() | ||
Fig. 9 Mixing index for droplets as a function of channel height based on (A) the distance from X-junction; (B) time. |
Initial droplet mixing evaluated at the time of droplet formation (before Position 0 in Fig. 7) was significantly higher for 60 μm channel compared to 40 and 20 μm channels, i.e. 37.6% vs. 23.3% and 19.0%, respectively. The higher m values caused the prolonged duration of premixing period, which was nearly 4-times longer for 60 μm than that for 20 μm high channels. Differences in mixing intensities were gradually reduced with increasing distance from the junction. Mixing intensities were comparable for all heights at the 3rd bend mark, although only 20 μm channel reached the threshold of 80%. Mixing index for 40 and 60 μm channel heights exceeded 80% after the 5th and the 4th bend mark, respectively. In comparison, 20 μm channel height provided the quickest homogenization, followed by 40 and 60 μm channel heights. The initial highest mixing index for 60 μm channels was outperformed by 20 and 40 μm height channels in 10 and 21 ms, respectively. Time to achieve m > 80% was evaluated to be 19 ms, 82 ms and 93 ms for 20, 40 and 60 μm channel height. The information about the time (droplet age) and mixing index showed in Fig. 9B is particularly important in the area of very fast precipitation reactions where nucleation and seed formation occurs almost instantly upon reactant mixing.
TEM was employed as the preferred technique for direct visualisation of the sample and Fiji software for nanoparticle characterisation. TEM images of samples collected from three independent experiments for each channel height were analysed with the total number of measured particles exceeding 500. Averaged particle size distribution (PSD) of iron oxide nanoparticles for all channel heights with respective values of mean and median size are summarised in Fig. 10. Additional TEM images can be found in the ESI (Fig. SI(2)†). The mean size of the observed particle was evaluated to be 4.7 ± 0.9 nm, 6.2 ± 1.3 nm and 5.9 ± 1.1 nm for 20, 40 and 60 μm high channels. Nanoparticles produced by 20 μm high channel showed the narrower PSD in comparison to 40 and 60 μm channels. PSD for higher channels were considerably broader, and this observation can be explained by a slower internal homogenization (m > 80%) of reactants for 40 and 60 μm channels (82 ms and 93 ms, respectively) compared to 20 μm high channel (19 ms) as discussed in Section 3.3. TEM images revealed a spherical shape of nanoparticles without the presence of larger agglomerates or overgrown crystals in all cases. The polydispersity indices defined as PDI = (the standard deviation/mean particle diameter)2 for increasing channel heights were 0.037, 0.044 and 0.035, respectively. Importantly, the obtained nanoparticles with monomodal distribution (PDI < 0.1) were prepared at room temperature in contrast to a standard batch preparation41 or droplet capillary reactors42 operating at elevated temperature.
![]() | ||
Fig. 10 Particle size distribution and corresponding TEM images of iron oxide nanoparticles produced by 20 μm (A and A′), 40 μm (B and B′) and 60 μm (C and C′) high microfluidic channels. |
Footnote |
† Electronic supplementary information (ESI) available. See DOI: 10.1039/d0ra02470h |
This journal is © The Royal Society of Chemistry 2020 |