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Field-induced macroscopic flow of a dilute self-assembling magnetic colloid under rotating magnetic fields

Published online by Cambridge University Press:  19 February 2024

J. Queiros Campos
Affiliation:
Université Côte d'Azur, CNRS UMR 7010, Institute of Physics of Nice, 17, rue Julien Lauprêtre, 06200 Nice, France
M. Raboisson-Michel
Affiliation:
Université Côte d'Azur, CNRS UMR 7010, Institute of Physics of Nice, 17, rue Julien Lauprêtre, 06200 Nice, France Axlepios Biomedical, 1ere Avenue 5eme rue, 06510 Carros, France
S. Schaub
Affiliation:
Developmental Biology Laboratory (LBDV), CNRS, Sorbonne University, Quai de la Darse, 06234 Villefranche-sur-Mer Cedex, France
S. Toe
Affiliation:
Université Côte d'Azur, CNRS UMR 7010, Institute of Physics of Nice, 17, rue Julien Lauprêtre, 06200 Nice, France
L. Boulant
Affiliation:
Université Côte d'Azur, CNRS UMR 7010, Institute of Physics of Nice, 17, rue Julien Lauprêtre, 06200 Nice, France
G. Verger-Dubois
Affiliation:
Axlepios Biomedical, 1ere Avenue 5eme rue, 06510 Carros, France
A. Zubarev
Affiliation:
Theoretical and Mathematical Physics Department, Institute of Natural Sciences and Mathematics, Ural Federal University, Lenin Ave, 51, Ekaterinburg 620083, Russia
P. Kuzhir*
Affiliation:
Université Côte d'Azur, CNRS UMR 7010, Institute of Physics of Nice, 17, rue Julien Lauprêtre, 06200 Nice, France
*
†Email address for correspondence: pavel.kuzhir@univ-cotedazur.fr

Abstract

Flow generation by colloidal motors activated by external stimuli is an important issue for active matter physics and several nanotechnological or biomedical applications. For instance, flow recirculation generated by rotating magnetic self-assemblies allows effective ‘pumping’ of a thrombolytic drug towards a blood clot along a blocked vessel. However, the physics of the flow generation in this case remains still poorly explored. This study is focused on the generation of a recirculation flow of a magnetic colloid (aqueous suspension of iron oxide nanoparticles with partially screened electrostatic repulsion) within a closed microfluidic channel via application of an external rotating magnetic field. The colloid undergoes reversible phase separation manifested through the appearance of micron-sized elongated aggregates. They synchronously rotate with the magnetic field and can generate macroscopic flows only in the presence of gradients of the aggregate concentration across the channel induced by superposition of a weak magnetic field gradient to the homogeneous rotating field. We achieve recirculation flows with a characteristic speed ${\sim} 5{-}8\;{\rm \mu}\textrm{m}\;{\textrm{s}^{ - \textrm{1}}}$ at low magnetic field amplitude and frequency (${H_0} \approx 3{-}10\;\textrm{kA}\;{\textrm{m}^{ - 1}}$, ${f = 5{-}15\ \textrm{Hz}}$) at low nanoparticle volume fraction ${\varphi _p} = (1.6{-}3.2) \times {10^{ - 3}}$. The concentration and velocity profiles have been assessed experimentally through particle tracking and particle image velocimetry, and have also been computed using the hydrodynamic diffusion approach coupled with the momentum balance equation with a magnetic torque term. The model correctly reproduces the shape of the experimental concentration and velocity fields and explains complex behaviours of the average recirculation speed as a function of governing parameters (${H_0}$, f, ${\varphi _p}$, channel size).

Information

Type
JFM Papers
Copyright
© The Author(s), 2024. Published by Cambridge University Press
Figure 0

Figure 1. Geometry of the experimental system for the generation of macroscopic recirculation flows. On the right, an enlarged view of the microfluidic channel with definition of several physical parameters is shown.

Figure 1

Table 1. Values of different parameters intervening into velocity and concentration fields calculation

Figure 2

Figure 2. Snapshot of the microfluidic channel with the gradient rotating magnetic field spinning clockwise in the x–y plane of the channel and the field gradient oriented along the y axis. The snapshot corresponds to the following set of experimental parameters: ${H_0} = 6.4\;\textrm{kA}\;{\textrm{m}^{ - 1}}$, $f = 5\;\textrm{Hz}$, ${\varphi _p} = 3.2 \times {10^{ - 3}}$, $h = 1000\;{\rm \mu}\textrm{m}$. The direction of aggregate translation is shown by the arrow. A supplementary movie showing the recirculation flow is available at https://doi.org/10.1017/jfm.2024.48.

Figure 3

Figure 3. (a) Experimental histograms of the aggregate length distribution. (b) Experimental and calculated profiles of the aggregate volume fraction across the channel y-dimension. Both graphs correspond to the following set of experimental parameters: f = 5 Hz, H0 = 6.4 kA m−1, h = 1000 μm, ${\varphi _p} = 1.6 \times {10^{ - 3}}.$

Figure 4

Figure 4. Velocity vector field deduced from the PIV analysis taken at a moment of time $\; t = 60\;\textrm{s}$ and for the following set of experimental parameters: f = 5 Hz, H = 6.4 kA m−1, h = 1000 μm, ${\varphi _p} = 1.6 \times {10^{ - 3}}$. The coloured arrows stand for the velocity vectors whose x and y components enter (green arrows) the $10 \times 5$ px frame−1 window (cf. Appendix A) or lie outside this window (brown arrows). White thin rods stand for the position of aggregates, within which the instantaneous velocity profile cannot be established.

Figure 5

Figure 5. (a) Spatiotemporal ${\langle {v_x}(\kern0.7pt y,t)\rangle _l}$ and (b) 2-D spatial ${\langle {v_x}(x,y)\rangle _T}$ experimental velocity maps averaged over one of six movies for the following set of experimental parameters: f = 5 Hz, H = 6.4 kA m−1, h = 1000 μm, ${\varphi _p} = 1.6 \times {10^{ - 3}}$. The red and blue colours stand respectively for the rightward and leftward flows.

Figure 6

Figure 6. Experimental (symbols with error bars) and theoretical (solid lines) velocity profiles ${\langle {v_x}(\kern0.7pt \tilde{y})\rangle _{l,T}} \equiv \langle v\rangle (\kern0.7pt \tilde{y})$ averaged over time and length of the observation window and presented for the following set of experimental parameters: f = 5 Hz, H = 6.4 kA m−1, h = 1000 μm, ${\varphi _p} = 1.6 \times {10^{ - 3}}$. The calculated velocity profiles correspond to either (a) Gaussian fit of the concentration profile (4.14) or (b) the concentration profile evaluated by the hydrodynamic diffusion approach (4.22). The shaded regions in panels (a) and (b) encompass the region of the model validity.

Figure 7

Figure 7. Experimental and theoretical dependencies of average absolute velocity on the frequency of the rotating magnetic field of different amplitudes H0 and for fixed nanoparticle concentration ${\varphi _p} = 1.6 \times {10^{ - 3}}$ and fixed channel width h = 1000 μm. Points correspond to experiments. Medium calculated values of q are plotted as solid lines in panel (a). The confidence intervals of the model are represented by shaded regions in panel (b). These regions follow the same colourmap as the experimental symbols.

Figure 8

Table 2. Experimental and theoretical values of the average absolute velocity for two different ${\varphi _p}$ and h values. For all the data in this table, H0 = 9.5 kA m−1 and f = 5 Hz.

Figure 9

Table 3. Acquisition parameters for the image processing procedure.

Figure 10

Figure 8. A snapshot of the microfluidic channel after greyscale inversion. Small coloured rectangles correspond to interrogation area selection. The long white strands are the aggregates and the white dots (visible in original high-resolution images) are the polystyrene tracers.

Figure 11

Figure 9. Geometrical notation for the problem of magnetic force determination.

Supplementary material: File

Queiros Campos et al. supplementary movie 1

Recirculation flow along a microfluidic channel. The applied magnetic field rotates in a clockwise direction and the magnetic field gradient is oriented upwards, in agreement with notations of the snapshot in Fig.2.
Download Queiros Campos et al. supplementary movie 1(File)
File 18.8 MB