Microrheology[1] is a technique used to measure the rheological properties of a medium, such as microviscosity, via the measurement of the trajectory of a flow tracer (a micrometre-sized particle). It is a new way of doing rheology, traditionally done using a rheometer. There are two types of microrheology: passive microrheology and active microrheology. Passive microrheology uses inherent thermal energy to move the tracers, whereas active microrheology uses externally applied forces, such as from a magnetic field or an optical tweezer, to do so. Microrheology can be further differentiated into 1- and 2-particle methods.[2] [3]
Passive microrheology
Passive microrheology uses the thermal energy (kT) to move the tracers, although recent evidence suggests that active random forces inside cells may instead move the tracers in a diffusive-like manner.[4] The trajectories of the tracers are measured optically either by microscopy or by diffusing-wave spectroscopy (DWS). From the mean squared displacement with respect to time (noted MSD or <Δr2> ), one can calculate the visco-elastic moduli G′(ω) and G″(ω) using the generalized Stokes–Einstein relation (GSER). Here is a view of the trajectory of a particle of micrometer size.
Typical trajectory of a Brownian particle (simulation)
Two examples of MSD: one for a purely viscous fluid (free diffusion) and one for a viscolelastic fluid (trapped by elastic network)
Animation of a particle in a polymer-like network
In a standard passive microrheology test, the movement of dozens of tracers is tracked in a single video frame. The motivation is to average the movements of the tracers and calculate a robust MSD profile.
Observing the MSD for a wide range of integration time scales (or frequencies) gives information on the microstructure of the medium where are diffusing the tracers.
If the tracers are experiencing free diffusion in a purely viscous material, the MSD should grow linearly with sampling integration time:
\( {\displaystyle <\Delta r^{2}>=4Dt}. \)
If the tracers are moving in a spring-like fashion within a purely elastic material, the MSD should have no time dependence:
\( {\displaystyle <\Delta r^{2}>=Const} \)
In most cases the tracers are presenting a sub-linear integration-time dependence, indicating the medium has intermediate viscoelastic properties. Of course, the slope changes in different time scales, as the nature of the response from the material is frequency dependent.
Microrheology is another way to do linear rheology. Since the force involved is very weak (order of 10−15 N), microrheology is guaranteed to be in the so-called linear region of the strain/stress relationship. It is also able to measure very small volumes (biological cell).
Given the complex viscoelastic modulus \( G(\omega )=G'(\omega )+iG''(\omega )\, \) with G′(ω) the elastic (conservative) part and G″(ω) the viscous (dissipative) part and ω=2πf the pulsation. The GSER is as follows:
\( {\tilde {G}}(s)={\frac {k_{{{\mathrm {B}}}}T}{\pi as\langle \Delta {\tilde {r}}^{{2}}(s)\rangle }} \)
with
\( {\tilde {G}}(s) \): Laplace transform of G
kB: Boltzmann constant
T: temperature in kelvins
s: the Laplace frequency
a: the radius of the tracer
\( \langle \Delta {\tilde {r}}^{{2}}(s)\rangle \) : the Laplace transform of the mean squared displacement
A related method of passive microrheology involves the tracking positions of a particle at high frequency, often with a quadrant photodiode.[5] From the position, x(t), the power spectrum, \( <x_{{\omega }}^{2}> \) can be found, and then related to the real and imaginary parts of the response function, \( \alpha (\omega ) \) .[6] The response function leads directly to a calculation of the complex shear modulus, G ( ω ) {\displaystyle G(\omega )} G(\omega ) via:
\( G(\omega )={\frac {1}{6\pi a\alpha (\omega )}} \)
Two Point Microrheology[7]
There could be many artifacts that change the values measured by the passive microrheology tests, resulting in a disagreement between microrheology and normal rheology. These artifacts include tracer-matrix interactions, tracer-matrix size mismatch and more.
A different microrheological approach studies the cross-correlation of two tracers in the same sample. In practice, instead of measuring the MSD - \( {\displaystyle <\Delta r^{2}>} \), movements of two distinct particles are measured - \( {\displaystyle <\Delta r_{1}\Delta r_{2}>}. \) Calculating the G(ω) of the medium between the tracers follows:
\( {\displaystyle {\tilde {G}}(s)={\frac {k_{\mathrm {B} }T}{2\pi Rs\langle \Delta {\tilde {r}}_{1}(s)\Delta {\tilde {r}}_{2}(s)\rangle }}} \)
Notice this equation does not depend on a, but instead in depends on R - the distance between the tracers (assuming R>>a).
Some studies has shown that this method is better in coming to agreement with standard rheological measurements (in the relevant frequencies and materials)
Active microrheology
Active microrheology may use a magnetic field ,[8][9][10][7][11] [12] optical tweezers[13] [14] [15] [16][17] and Atomic force microscope[18] to apply a force on the tracer and then find the stress/strain relation.
The force applied is a sinusoidal force with amplitude A and frequency ω -
\( {\displaystyle F=Asin(\omega t)} \)
The response of the tracer is a factor of the matrix visco-elastic nature. If a matrix is totally elastic (a solid), the response to the acting force should be immediate and the tracers should be observed moving by-
\({\displaystyle X_{e}=Bsin(\omega t)}. \)
with\( {\displaystyle A/B=G(\omega )}. \)
On the other hand, if the matrix is totally viscous (a liquid), there should be a phase shift of \( 90^{o} \) between the strain and the stress -
\( {\displaystyle X_{v}=Bsin(\omega t+90^{o})=Bcos(\omega t)}
in reality, as most materials are visco-elastic, the phase shift observed is \( {\displaystyle 0<\varphi <90}. \)
When φ>45 the matrix is considered mostly in its "viscous domain" and when φ<45 the matrix is considered mostly in its "elastic domain".
Given a measured response phase shift φ (sometimes noted as δ), this ratio applies:
\( {\displaystyle {\frac {G''}{G'}}={\frac {{\frac {A}{B}}sin(\varphi )}{{\frac {A}{B}}cos(\varphi )}}=tan(\varphi )} \)
Similar response phase analysis is used in regular rheology testing.
More recently, it has been developed into Force spectrum microscopy to measure contributions of random active motor proteins to diffusive motion in the cytoskeleton.[4]
References
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