 Proceedings
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A modified StokesEinstein equation for Aβ aggregation
BMC Bioinformatics volume 12, Article number: S13 (2011)
Abstract
Background
In all amyloid diseases, protein aggregates have been implicated fully or partly, in the etiology of the disease. Due to their significance in human pathologies, there have been unprecedented efforts towards physiochemical understanding of aggregation and amyloid formation over the last two decades. An important relation from which hydrodynamic radii of the aggregate is routinely measured is the classic StokesEinstein equation. Here, we report a modification in the classical StokesEinstein equation using a mixture theory approach, in order to accommodate the changes in viscosity of the solvent due to the changes in solute size and shape, to implement a more realistic model for Aβ aggregation involved in Alzheimer’s disease. Specifically, we have focused on validating this model in protofibrill lateral association reactions along the aggregation pathway, which has been experimentally well characterized.
Results
The modified StokesEinstein equation incorporates an effective viscosity for the mixture consisting of the macromolecules and solvent where the lateral association reaction occurs. This effective viscosity is modeled as a function of the volume fractions of the different species of molecules. The novelty of our model is that in addition to the volume fractions, it incorporates previously published reports on the dimensions of the protofibrils and their aggregates to formulate a more appropriate shape rather than mere spheres. The net result is that the diffusion coefficient which is inversely proportional to the viscosity of the system is now dependent on the concentration of the different molecules as well as their proper shapes. Comparison with experiments for variations in diffusion coefficients over time reveals very similar trends.
Conclusions
We argue that the standard StokesEinstein’s equation is insufficient to understand the temporal variations in diffusion when trying to understand the aggregation behavior of Aβ 42 proteins. Our modifications also involve inclusion of improved shape factors of molecules and more appropriate viscosities. The modification we are reporting is not only useful in Aβ aggregation but also will be important for accurate measurements in all protein aggregation systems.
Introduction
Aberrant misfolding and aggregation of proteins have been implicated in over 40 different human pathologies including Alzheimer’s disease (AD), Parkinson’s disease, type 2 diabetes, transmissible spongiform encephalopathies (TSE) or Prion diseases, Huntington’s disease and CruedfeltJacob disease (CJD). A biochemical commonality in these diseases is that the protein involved forms pathogenic aggregates, irrespective of whether the monomeric protein is in the misfolded or intrinsically disordered forms, that have a consensus structural moiety, commonly known as “amyloids”. In all amyloid diseases, such protein aggregates have been implicated fully or partly, in the etiology of the disease. Due to their significance in human pathologies, there have been unprecedented efforts towards physiochemical understanding of aggregation and amyloid formation over the last two decades. It is well understood that the process of aggregation towards amyloid fibrils from a monomeric state is a nucleationdependant mechanism, analogous to crystal growth. In such a process, it is believed that there is a conformational change during the nucleation event followed by rapid aggregation to a state that forms large insoluble or soluble aggregates, which in turn is accompanied by a structural convergence to cross βsheet conformation [1].
In Alzheimer’s disease (AD), a protein called amyloidβ (Aβ) peptide forms aggregates that deposit as senile plaques in brains. The nucleationdependent process of Aβ aggregation is inferred by the occurrence of a ’lagphase’ prior to fibril growth that shows a sigmoidal pattern [2]. In the aggregation pathway, one important intermediate called “protofibrils” has been isolated and characterized by several groups [3][4][5][6][7][8]. Protofibrils mainly differ from fibrils in their size and solubility; while fibrils can be sedimented with relatively smaller forces (19000g, 10min)where g is the acceleration due to gravity protofibrils require substantially high sedimentation forces and have smaller diameters than the fibrils [9]. Protofibrils have propensities to both elongate (by monomer addition) as well as to laterally associate (protofibrilprotofibril association) to grow into mature fibrils and have been well characterized [9]. These two mechanisms of fibril growth depend on the structure and stability of protofibrils, which in turn depend on the factors affecting nucleation.
The in vitro Aβ aggregation process is well known to be affected by several environmental factors such as concentration, pH, ionic strength and temperature. In addition, differential effects of solvents on the aggregation process and size has also been documented [10]. Several biophysical methods are used to monitor the aggregation process among which, light scattering and centrifugation techniques are widely used to measure the hydrodynamic radii (a) as well as the diffusion coefficient (D) of the protein sample [5][11][12][13][14]. For spherical particles, the relation between a and D is given by the StokesEinstein (SE) equation;
where, k_{ B } is Boltzmann’s constant, T is the absolute temperature and η_{0} is solution viscosity. However, the aggregates of Aβ peptide cannot be assumed to be spherical and hence determination of a can be erroneous. This difficulty is overcome by the use of multiangle light scattering (MALS) technique which measures the intensity of the scattered light from multiple angles that in turn helps to calculate the molecular weight without assuming the shape of the solute [9]. A more sophisticated method of measuring the molecular size is by analytical ultracentrifugation (AUC), which utilizes the rate of the movement of sedimentation boundary [15]. For a spherical solute with a molecular mass, MA and radius a , the value of sedimentation coefficient measured at temperature T in buffer b, the rate of migration per unit field, s_{ A } is given by;
where N is the Avogadro’s number and is the partial specific volume of the solute, and ρ, η are the density and viscosity of the buffer medium respectively.
An important aspect of the StokesEinstein’s equation and its utility in protein aggregation systems in particular is that the viscosity of the bulk solvent in a given buffer solution is considered to be a constant.
Here, we are reporting a modification in the classical StokesEinstein equation in order to accommodate the changes in viscosity of the solvent due to the changes in solvent size and shape, which is a more realistic model for Aβ aggregation. Specifically, we have focused on validating this model in protofibril lateral association reaction (Figure 1) along the aggregation pathway, which has been experimentally well characterized [9, 16]. The modification we are reporting is not only useful in Aβ aggregation but also will be important for accurate measurement in all protein aggregation systems.
The classical SE model states that the diffusion coefficient for a suspension of molecules of a given volume fraction in a surrounding solvent of viscosity η_{0} is written as equation (1) where the denominator is the effective drag coefficient for the molecule which is treated as a rigid sphere of effective radius a. We point to several shortcomings of this model with respect to the Aβ aggregation and suggest modifications to improve it which include:

(i)
firstly, molecules of concern to us are not necessarily spheres [17] although this is the simplest assumption one can make. In general for our problem, where we consider the aggregation of molecules, several classes of molecules (or nmers) are assumed to populate the solvent. While it is not clear what the specific shape of each class (nmer) is, it is most certainly not a sphere [18] for the most part.

(ii)
The second point we make is that the SE relation takes the viscosity to be a constant, based upon the solvent viscosity. However we argue that it should depend upon the concentration of the various species of molecules present in the system. Any single molecule (individual or aggregated), during diffusion will experience the viscous forces of the liquid as well as due to the remaining molecules around it. As a result, the diffusion coefficient, k, is also a function of the concentration of the molecules. In fact, more generally, we will consider an effective diffusion coefficient k_{ e } where k_{ e } = k_{ e }(ϕ_{ i },η_{0}) where i = 1, 2, …,n.
In this paper, we have considered these two important conditions and incorporated modifications to the StokesEinstein equation that may faithfully represent the changes occurring in amyloid aggregation systems, especially Aβ. The significance of nonsphericity in computing the diffusion coefficient has been realized in various contexts and the biophysics, chemistry, geological and chemical engineering literature is replete with discussions of the role of nonspherical particles, specifically spheroidal particles [19–23]. While the biophysics community has been well aware of the importance of nonsphericity, the importance of concentration upon the viscosity and hence diffusivity, has been largely neglected. The chemical engineering literature is however a very rich source of discussion on this matter; see [24] and references cited therein for more information on this subject.
Results
Theoretical models
In a mixture or suspension containing a background liquid and nspecies of molecules, we define V_{0} to be the volume of the solvent liquid and V_{ i }, i = 1, 2,…, n to be the volume of the ith species. Then the volume fraction of each element of this mixture is given by:
with the constraint:
Based upon these arguments, a general expression for the diffusion coefficient for nspecies of molecules can be framed in terms of the volume fraction ϕ_{ i } and must be of the form:
where j = 1, 2,…, n, f_{ i } refers to the drag coefficient of the ith species and β_{ i }, its respective shape coefficient. As is seen from the last term on the right hand side of the equation, the volume fraction enters the diffusion coefficient through the viscosity. In fact, in this paper, we suggest that the viscosity term itself be treated as an average of the viscosity due to its constituents as a result of which η_{ i }(ϕ_{ j }) is replaced by a scalar, the effective viscosity, η_{ e }(ϕ_{ j }) where j = 1, 2,…, n. Hence:
While we are following the vast majority of physics and engineering literature in following this approach of modeling a mixture through its overall material parameters, we are also conscious that it not a rigorous mathematical approach. In his paper on the “viscosities of mixtures” Massoudi [24] provides an overview of the historical approach to the modeling of effective viscosities but more importantly, he points to the mathematically rigorous approach of modeling a mixture by examining the stress tensors. However, this is recognized to be a rather formidable challenge to verify experimentally and very tedious to implement in computations such as these. Even within this approach of modeling viscosities, it has been argued [25] that the effective viscosity of say two liquids would be not just a linear superposition of the two individual viscosities, but also include an interaction term, referred to “mutual viscosity” which again is very difficult to verify experimentally. All these point to the complexity of rigorously modeling even a seemingly simple parameter as viscosity. In the rest of the paper, we consider two specific and successful models applied in the engineering literature to our problem of Aβ aggregation. With regards to the shape of the molecules, there has been much discussed about the validity of sphericalshape assumption of biomolecules( [17, 18] and references therein) and while it is recognized that molecular shapes can be fairly complex and random, it still remains worthwhile to represent these arbitrarily composed molecules using some standard shapes that can be imagined to envelope the molecules in a reasonable manner. Our attempt in particular is to go beyond the assumption of the sphere. To do so we need at our disposal, the drag coefficients corresponding to arbitrarily shaped bodies. This is a very daunting challenge in fluid mechanics and at best relatively simpler shapes such as spheres, oblate and prolate spheroids (of any eccentricity) have been analyzed mathematically [26, 27]. However there is some literature in terms of empirical or computational relations which provide the drag coefficients for other shapes.
Case 1: a sphererod empirical model
We begin with an empirical model. Based upon the work of [28–31] we will consider the modification of the SE law by taking a suspension composing of spheres and rods with the former particles being considerably smaller than the latter such that the ratio a_{ r }/a_{ s } > 20, where a_{ r } is the major axis of the rod and a_{ s } is the radius of the sphere. This particular assumption can also be very meaningful in our case where we consider our sample primarily to be composed of smaller monomers and much larger protofibrils. In particular we follow the specific approach of [31] in obtaining an effective viscosity for such a suspension. In the words of [31] the primary assumption in the computation of viscosity is that:
... for each fraction of a given particle size, the smaller particles in suspension have the same effect as a homogeneous fluid with Newtonian viscosity similar to the effective viscosity of a suspension made up of the fraction of smaller spheres. In other words, the smaller suspended particles do not interact with the larger particles and are ’sensed’ by the large particles as part of the continuous suspending fluid.
Mathematically, this amounts to saying that:
where η_{rel,r}(ϕ_{ r }) refers to the viscosity of the rods relative to the continuum of a homogeneously distributed spheres in a solvent, , similarly is the viscosity of the spheres relative to the continuum of the pure solvent in the absence of the rods. Also, Φ_{0} = ϕ_{ r } + ϕ_{ s }, ϕ_{ r } refers to the concentration of the rods, ϕ_{ s } the concentration of spheres and:
As in [31], based on the empirical relations suggested by [32, 33] we take:
Using these above equations along with the shape factor [27], where L, b refer to the length and diameter respectively, depending on the orientation of the rod, we have the relation for the diffusion coefficient, namely:
for the case of ϕ_{ r } < 0.125. A similar relation can be written for ϕ_{ r } > 0.125 which is given by:
If the net volume fraction of all the solute molecules is held fixed (i.e. Φ), then the diffusion coefficient can be written purely in terms of ϕ_{ r } or ϕ_{ s }.
Case 2: a mixture theory approach
In this section, we propose our model which is inspired by the empirical approach mentioned above and the viscosity model due to Quemada [34, 35], who describes the “viscosity of suspensions of hard spheres or of structural units like clusters or aggregates” using the relation:
where η_{0} is the viscosity of the background solvent, ϕ is the volume fraction of the suspensions and ϕ_{ m } is the maximum volume fraction at which the viscosity becomes singular, i.e. the critical limit of concentration beyond which flow ceases. The literature estimates 0.58 <ϕ_{ m } < 0.69 [36, 37] (As in past literature, let us take the average value, namely ϕ_{ m } ≈ 0.6). In classical mixture theory the effective viscosity of two liquids of different viscosities has been taken to be the weighted average viscosity of the components. In attempting to do the same for suspensions, one must exercise a little caution. In the model proposed here, we adopt a mixture approach by trying to combine the solvent viscosity appropriately with equation (15). We schematically display our recipe for obtaining a suspension with solvent volume V_{0} and such that the volume of each constituent particle (molecule) is V_{ i } (i = 1, 2, …,n) in Figure 2, while requiring that equations (3) and (4) be satisfied.
Hence, based upon the definitions earlier, we define the effective viscosity as the weighted average of the individual components given by:
where as in the sphererod model treated above, η_{ i }(i ≠ 0) where i ranges over all cyclic permutations of (1, …, j, j + 1, …,n), represents the relative viscosity of the suspension containing the j th solute in a “solvent” composed of the liquid of viscosity η_{0}and all other solute particles. Note that the equation (16) is not unique. Other formulations of the effective viscosity are possible. The one provided here seems mathematically and physically reasonable and consistent with some models provided in the literature. The term represents the relative volume fraction of the j’th solute relative to the “solvent” that contains it and is independent for different j’s. Therefore, for an nspecies suspension, the viscosity relation for the j solute in a background containing all other species and the pure solvent can be inferred from the algorithm: η_{ j } → η_{ j }_{+1}→ …η_{ n }→ η_{1}→ …η_{ j }_{–1} where η_{ a } → η_{ b } indicates that η_{ a } is measured relative to η_{ b } in the sense of equation (8). In particular, the cyclic permutations of i are taken to ensure evenness in the definition of the volume fractions, for all j’s. This is clearly illustrated in the cases of 2 and 3species which are examined in detail. We illustrate this by means of a few examples.
(i) The case of two species
For instance, in the case of two solutes in a solvent, we can write the effective viscosity as:
where
and similarly,
where
(ii) The case of three species
We can write the effective viscosity as:
where
and similarly,
where
and also
where
We can similarly extend the computation of the effective viscosity to any number of solute species. Hence implementing this model into the above equation (7) for k_{ e } gives:
where η_{ e } is defined by the equation (16) and where i, j ≠ 0 that is, the fluid is discounted. Since the diffusion that we are interested in only pertains to the solute species embedded in the surrounding solvent, we need only consider the volume fraction of each solute with respect to the others in the evaluation of the effective diffusion. In particular let us assume, for instance, that two classes (or species) or molecules populate the solvent; the shape are so selected since the shape factors are only known for a small class of shapes. The first are the molecules at the protofibril stage or beyond which are treated as being spheroidal in shape(diffusion of spheroidal bodies had been considered as far back as 1936 by Perrin [38]) and the second class are those smaller than the protofibril stage which will be treated as spheres, even though Zwanzig and Harrison [18] rightly argue that the shapes of molecules are not correctly described by either of these shapes, the latter being far more realistic than the former. We however feel that this is still an improvement over the current approach of treating all the molecules as hard spheres.
If we define the total volume fraction of the molecules of both species to be Φ_{0} = 1, the volume fraction of the spheroidal particles to be ψ, then the volume of spherical molecules can be given by 1 – ψ. For the two species case we can write ψ_{1} = ψ and ψ_{2} = 1 – ψ. Therefore for this example, we can write the effective viscosity as:
by taking a weighted average of the appropriate viscosities due to the three independent constituents. It must be noted that while the spherical shape is devoid of any orientational biases, the same cannot be said of the spheroid which can move about in different orientations . The drag on a spheroid can be a maximum or minimum depending upon the orientation of the moving spheroid. We therefore estimate an upper and lower limit of the diffusion coefficient for the spheroidal molecules where the lower and upper limits are obtained by the appropriate shape coefficients. These values corresponding to the spheroid and sphere (see Figure 3), respectively are known to be [26] (the chemistry and biophysics literature, in this regards, points to the model of Perrin [38]. We however use the more correct formula derived by Chwang and Wu [26] in 1975 using the Stokes singularity method):
Where refers to the eccentricity of the spheroid c and b refer to the major and minor axis of the spheroid. Hence combining the above results allows us to formulate a specific model for the twospecies case where the diffusion coefficient can be given by:
while
It is not difficult to see that in the limit that the spheroidal particles, vanish, i.e. the system contains the spherical molecules and solvent alone ψ = 1 and the effective diffusion coefficient can be written in the form:
which is still an improvement over the classical SE model due to the accounting of the volume fraction in the viscosity. The classical formula is retrieved by ignoring the term and taking ϕ_{0} + ϕ = 1 based on the constraint equation (4). For the onespecies suspension case when ϕ/ϕ_{0} = ∈ << 1, then equation (33) can be approximately written at O(∈) as:
where ϕ^{(1)} = ϕ. As ∈ → 0, the diffusion coefficient approaches the classical Stokes Einstein equation since then ϕ_{0}→ 1.
Protofibrilprotofibril lateral association experiment
Protofibril lateral association reaction was initiated by the addition of 150 mM NaCl to the isolated protofibrils (3 and 5 µ M) that was monitored by dynamic light scattering (DLS) instrument. Protofibrils without salt were used as a negative control. The data is plotted in Figure 4 against diffusion coefficient (D) which is inversely proportional to the hydrodynamic radius of the sample.
Molecular level simulation of protofibrilprotofibril lateral association
Next, we used some simple molecular level reaction models to predict the concentration of protofibrils of different size in the lateral association stage that can correspond to the diffusion coefficient estimates from DLS reported above. First, we assumed that the protofibrils are composed of 1600 monomers based on the previous reports [39, 40]. Here, F_{1600} denote the protofibrils (comprising 1600mers and average length 64 nm) [39, 40]. In general, we will let F_{ i } denote a protofibril with i number of Aβ molecules binding to it during the lateral association phase.
We present separate reaction models considering different number of species formed during the lateral association reaction. The reactions involving these species were modeled under the assumption of a homogeneous mixture of protofibrils (with different initial concentrations) as used in the in vitro experiments. In particular, we considered a maximum of five different molecular species involved in this phase as follows: F_{1600}, F_{3200}, F_{4800} , F_{6400} and F_{8000}. We have assumed that lateral association will result in at most a 5fold increase in size of the protofibrils within the first 1.5 hrs of observation such that the system of reactions will not involve the formation of protofibrils beyond F_{8000}. This assumption is purely theoretical although it is experimentally well known that three protofibrils associate together to form mature fibrils. We wanted to consider upto 5 species for the interest of modeling and calculations. The reaction fluxes in this are denoted by R(i, j) corresponding to the reaction between F_{ i }_{*1600} and F_{ j }_{*1600} forming F_{(}_{ i }_{+}_{ j }_{)*1600} for i = 1, …, 5 and j = i, i + 1,…, 5 – i. We have also assumed that the initial concentration of protofibrils comprise of only F_{1600}’s and that of the other species are zero in the reaction models as only minute levels of associated protofibrils are expected to be present initially in the in vitro system.
In the following, we have considered three case studies to estimate the concentration change of the different molecular species involved in lateral association: 2species (F_{1600}, F_{3200}), 3species (F_{1600}, F_{3200}, F_{4800}) and 5 species (F_{1600}, F_{3200}, F_{4800}, F_{6400}, F_{8000}). Each reaction was considered reversible with k_{+} and k_{–} being the forward and backward rate constants respectively. Following our previously validated lateral association stage model [16], we have considered k_{+} = 9.0 × 10^{–1}h^{–1}mM^{–1} and k_{–} = 6.0 × 10^{–3}h^{–1} respectively. While the 2species and 3species models are less realistic, we have seen that protofibrils do not grow beyond F_{8000} in the first 1.5 hrs of lateral association, and hence the 5species model should be the best approximation of the in vitro system under study.
Case 1: 2species reaction model
Case 2: 3species reaction model
Case 3: 5speciesreaction model
After the kinetic schemes are established in the reaction models above, we computed the corresponding reaction fluxes, and hence the differential equations that govern the temporal change of these species can be derived from material balances and reaction kinetics. The reaction flux and differential equations for each of the models reported here have also been shown alongside. The initial concentration of protofibrils ([F_{1600}]) is set to 1µ M, 3µ M and 5µ M respectively following the in vitro experiments while the concentrations of the other species are assumed to be zero at the start (i.e., [F_{ i }_{*1600}] = 0, i = 2,…, 5). Thus, the system of differential equations for each model is properly defined and were solved using Matlab’s ODE toolbox to estimate the concentration of the different species at various time points between 0 – 90 mins as shown in the previous section.
Case studies
In this section, we consider some special cases to test our proposed models. We consider the cases of two, three and five species embedded in a solvent, introduced earlier. In these examples, we consider each species to be an ellipsoid since the length and width of the molecules considered here are significantly different so they cannot be correctly represented as spheres. As is indicated in Figure 3(c), associations of these spheroids occur laterally; therefore according to our model, the result of nassociations of spheroids of major axis c and minor axis b results in a new spheroid with major axis c and minor axis n × b. Our objective is to employ our model to estimate the effective diffusion coefficient of various systems and compare them to the experimentally measured values of diffusion.
For our calculations, we take the dimensions of the protofibril (1600mer) to be a spheroid with minor axis equal to 2.25nm and the major axis to be 300nm based upon previously published reports [8, 9, 41]. Also we take the viscosity of the solvent (water) to be 0.89 × 10^{–3} Pas. The results of our computations are plotted in Figure 5. The right columns of this plot (Figures 5D, E and F) show the results of the experiments which yield the diffusion coefficient and the concentrations alike. The initial concentration of the protofibril is taken to be 5µM in each of the cases. The black points in the curves refer to the 1600 mers while the red points refer to the final stage in each case, i.e. 3200mers in the 2species case, 4800 mers in the 3 species and the 8000 mers in the 5 species case. Note that the diffusion coefficient always decreases with the diminishing 1600 mers on the other hand growing with the diminishing concentrations of the bigger, associated molecule. The panels on the left hand side (Figures 5A, B and C) indicate the results of the numerical computations for the same cases as the experiments and indicate very similar trends. For ease of comprehension of the plots the values of alone are shown in the graphs here while those of show very similar features. It is to be noted that the black and red points do not actually intersect; the intersection is an artefact of the two different scales represented on the yaxis. While the increasing and decreasing trends remain consistent with observations the actual value of the diffusion coefficient seems to differ. Our model puts the lower and upper limit values of the diffusion coefficient consistently between 1.7 × 10^{–12}m^{2}/s and about 2.4 × 10^{–12}m^{2}/s while experimental values are higher, ranging upto four times more that our upper limit at some concentrations. Firstly the large variability in the experimental data when compared to our model can be attributed to the fact that the experimental study is based upon DLS observations which provides a time varying effective radius for the system, corresponding to the production of larger molecules which form as a result of the association. These experimentally evaluated radii which range between 3080nm are then inserted into the classical StokesEinstein formula (equation (1)) to get the diffusion coefficient. The experimental estimates for the effective length scale are substantially lower than the more accurate values used in our model, resulting in the deviation from our values of the diffusion coefficient.
Certain features of the computations merit immediate attention. In particular, the profile of the 1600, 3200 and 8000mers is striking. These include the declining values of the apparent intersection point with increasing number of species and also the slope of the red curves whose declining trend in the graph as plotted, gets more rapid with the larger molecule.
The most significant contribution of the paper lies in the suggestion that the viscosity of the system is not a constant as considered so far but depends strongly upon the concentration of the various molecules. In Figure 6, we plot the change in the effective viscosity of the 2, 3 and 5species cases as a function of the concentrations of the 1600, 3200, 4800 and 8000 mers. A clear declining trend is observed which is in agreement with the literature [42–44]. Viscosity of suspensions have been known to diminish with the declining concentrations of the solute. On the other hand viscosity increases with the decreasing size of the solute particles since smaller particles are capable of more random Brownian motions causing greater retardation of the bulk fluid motion. The approach proposed in this paper must not be thought simply as a reaction to the DLS estimates which essentially uses the equation (1). As one can note from equation (2), even the AUC method relies upon the drag formula corresponding to a sphere and the viscosity of the buffer does not depend upon the volume fraction of the embedded solutes.
Discussion and future work
The intention of this paper is to point out a somewhat erroneous practice of employing the StokesEinstein (SE) formula in situations which are not represented by it accurately enough. The proposed modification is a first in a series of steps that will help provide better mathematical models that fully incorporate all features of the entire system to explain protein aggregation. While the shape factor and concentration are introduced as tuning parameters, the central contribution of this paper lies in the realization that the meaning of “viscosity”(denoted η_{0}) in the StokesEinstein formula is the one pertaining to the solvent alone. However if one wants to think of the diffusion of any molecule, the effective medium becomes the solvent as well as the remaining molecules embedded in the system. Therefore the solvent viscosity of the classical SE formula needs to be replaced appropriately with one of an effective viscosity which is no longer just the solvent viscosity alone. In fact the concentration terms are as important if not more than the nonsphericity requirement. It is also important to note that while the apparent form of the modified SE formula is similar to that of the classical SE formula, our model has grave implications in understanding the dynamics of the protofibrils and aggregate molecules since the diffusion coefficient is no longer a constant but a function of the shape factors and concentrations of the different species of molecules that populate the suspension. While the change from a sphere to a spheroid might appear to be a minor point, its full impact can only be realized when one studies the problem at the smaller scale where this change can display its full impact as we plan to do in the future; this paper is focused on the larger scale continuum properties of the system as experimental measurements were hard to achieve at a smaller scale for the protein aggregation problem. To see the complexity of this model, one need only look at the diffusion equation that our model generates. For instance, in the case of nspecies of nmers embedded in a solvent,
where i = 1,2,…,n. The new k_{ e } renders the equation highly nonlinear. The modified SE equation provided in this paper now allows for a more appropriate coupling of the solutesolvent dynamics. Under the realistic conditions of flow we have a two way coupling; the dynamics of the solute is described by the concentration equation (35), while the dynamics of the solvent would be given by the NavierStokes equation. Our next goal is to take on this multiscale approach coupled with a reaction term to understand the temporal and spatial variations in the solute (protofibrils and aggregates) distribution. Due to the contributions of this paper, this would be a very new and rigorous addition to the biophysics literature. The model proposed here, therefore merits serious attention since it provides a systemic treatment of the biophysics involved. The current paper is therefore a first step in this long term approach of understanding the problem of protein aggregation thoroughly and rigorously.
Conclusion
In this report, we have shown that the use of classical StokesEinstein equation may not be accurate for the measurement of hydrodynamic radii and consequently molecular weights of amyloid aggregates. Although it is known that appropriate assumption of the shape of solute molecules is essential for accurate size determination while using StokesEinstein equation, this is the first time we have shown that it is incorrect to assume solvent viscosity be a constant during the reaction. This is particularly true for reactions involving Aβ protofibrils, as large size of the solute molecules indicate significant effect on bulk solvent viscosity. We have attempted to rectify the problem by incorporating modifications to the StokesEinstein equation (Equation 16)that seem to be valid for the protofibril lateral association reaction. It is noteworthy that the modifications reflecting the viscosity changes can lead to realistic models not only for Aβ aggregation but also for a majority of amyloid aggregation systems.
Methods
Aβ protofibril preparation
Synthetic Aβ 42 peptide was obtained from synthesis facility at Mayo Clinic, Rochester, MN as a lyophilized powder. Aβ 42 protofibrils were generated and isolated as previously reported (9). Freshly purified Aβ 42 monomers (100 µ M) from size exclusion chromatography buffered in 10 mM Tris, 50 mM NaCl, pH 8.0 was agitated at room temperature for 48 h. The aggregation was monitored using ThT fluorescence. The sample was then centrifuged at 19000g for 12 min to spin out any fibril that may have formed. The supernatant was then fractionated by Superdex75 size exclusion column to isolate protofibrils from unreacted monomers and smaller oligomers. The concentration of protofibrils was measured by UVVis with a molar extinction coefficient of 1450 cm^{–1}M^{–1} corresponding to Aβ 42.
Dynamic light scattering (DLS)
The DLS experiments were performed using Zetasizer nanoseries instrument ( Malvern Instruments, Inc.). The samples were equilibrated for 120s and a total of 90 measurements of 10s each were made with a time interval of 1min after each measurement. The data was exported as diffusion coefficient using Zetasizer software version 6.20 and processed using origin 6.0 software.
Reaction flux and differential equations for the reaction pathway
After the kinetic schemes for each of the three reaction models are established, the concentrations of the various species can be expressed as functions of time by using material balances and reaction kinetics. We will explain the 5species reaction model in this section, while the other two models can be derived similarly. The reaction fluxes for the 5species model can be derived as follows:
Next, we formulate the differential equations for each species in the system to model their change in concentration with time. The first species to be considered is F_{1600} whose rate of change is expressed in terms of its disappearance:
(and hence the negative sign before each reaction flux term) due to each of the reactions involving F_{1600} enlisted in 5species reaction model. Similarly, the differential equations of each of the other species involved can be written based on the fluxes of the reactions where the species is produced (positive terms) or consumed (negative terms):
The initial concentration of F_{1600}s is equal to the amount of protofibrils added initially and is the main driving force for the downstream reactions. The concentrations of the other species are assumed to be zero at the start (i.e., [F_{ i }_{×1600}] = 0, i = 1, …, 5). This set of differential equations is properly defined and can be solved using Matlab’s ode15s.
Authors contributions
The study was conceptualized by PG,VR and AV. PG designed the computational model for the reaction pathway and VG designed the ThT fluorescence and DLS experiments. AV,SA and BJC performed the mathematical modeling and the related calculations. All authors read and approved the final manuscript.
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Acknowledgments
The authors thank the following agencies for their financial support: NSF EAGER(1049962) and Mississippi INBRE (P20RR016476) (for PG and VR); American Heart Association (10GRNT4190124) (for VR). The authors thank Amit Kumar for his help with biophysical experiments and Dr. Cannon for letting us use the DLS instrument.
This article has been published as part of BMC Bioinformatics Volume 12 Supplement 10, 2011: Proceedings of the Eighth Annual MCBIOS Conference. Computational Biology and Bioinformatics for a New Decade. The full contents of the supplement are available online at http://www.biomedcentral.com/14712105/12?issue=S10.
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Achuthan, S., Chung, B.J., Ghosh, P. et al. A modified StokesEinstein equation for Aβ aggregation. BMC Bioinformatics 12 (Suppl 10), S13 (2011). https://doi.org/10.1186/1471210512S10S13
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DOI: https://doi.org/10.1186/1471210512S10S13