# A solvable model for the diffusion and reaction of neurotransmitters in a synaptic junction

- Jorge L Barreda
^{1}and - Huan-Xiang Zhou
^{1}Email author

**4**:5

https://doi.org/10.1186/2046-1682-4-5

© Barreda and Zhou; licensee BioMed Central Ltd. 2011

**Received: **9 February 2011

**Accepted: **2 March 2011

**Published: **2 March 2011

## Abstract

### Background

The diffusion and reaction of the transmitter acetylcholine in neuromuscular junctions and the diffusion and binding of Ca^{2+} in the dyadic clefts of ventricular myocytes have been extensively modeled by Monte Carlo simulations and by finite-difference and finite-element solutions. However, an analytical solution that can serve as a benchmark for testing these numerical methods has been lacking.

### Result

Here we present an analytical solution to a model for the diffusion and reaction of acetylcholine in a neuromuscular junction and for the diffusion and binding of Ca^{2+} in a dyadic cleft. Our model is similar to those previously solved numerically and our results are also qualitatively similar.

### Conclusion

The analytical solution provides a unique benchmark for testing numerical methods and potentially provides a new avenue for modeling biochemical transport.

## Keywords

## 1. Background

In intercellular and intracellular spaces, passive transport of biomolecules is a common phenomenon. Because such processes are difficult to probe directly by experiments, numerical modeling is increasingly used to gain insight. Two processes that have been extensively modeled are the diffusion and reaction of the transmitter acetylcholine in a neuromuscular junction [1–6] and the diffusion and binding of Ca^{2+} in the dyadic cleft of a ventricular myocyte [7, 8]. In contrast to previous numerical approaches, here we present an analytical solution of a model for the diffusion and reaction of acetylcholine in a synaptic cleft (or Ca^{2+} in a dyadic cleft). Our model is similar to those previously solved numerically; hence our analytical solution potentially provides a new avenue for modeling biochemical transport. More importantly, an analytical solution provides a unique benchmark for testing numerical methods. Such a solution has been lacking up to now; the present work fills this gap.

^{+}to flow in and generating an action potential along the muscle fiber. Finally excess acetylcholine molecules around the post-synaptic membrane are broken down by acetylcholinesterase to prevent continued activation of acetylcholine receptors.

^{2+}can enter the cell through L-type Ca

^{2+}channels on the cell membrane in response to the arrival of an action potential. The ions then diffuse to reach and activate ryaonodine receptors in the membrane of the sarcoplasmic reticulum. The activated ryaonodine receptors release Ca

^{2+}from the sarcoplasmic reticulum, which ultimately lead to muscle contraction.

^{2+}in a dyadic cleft. We are able to find an analytical solution for this model. For convenience we describe our model in the language of neuromuscular junction. As shown in Figure 3, we model the synaptic cleft as the space between two infinite, parallel planar membranes. In the pre-synaptic membrane, there is a periodic array of circular openings, via which acetylcholine molecules enter the cleft. In the post-synaptic membrane, there is a periodic array of circular disks, where the acetylcholine molecules are absorbed. The quantity of interest is the total flux,

*J*(

*t*), at time

*t*of acetylcholine molecules across the post-synaptic membrane. This model allows us to use periodic boundary conditions in the transverse direction. Our results are qualitatively similar to those obtained previously by numerical solutions [1–7]. More realistic ingredients can be added to our model and still permit analytical solutions.

## 2. Methods

We set up a coordinate system such that the *x* and *y* axes are parallel to the pre- and post-synaptic membranes. The synaptic junction has depth *L*_{
z
} . The junction is periodic in the *x* and *y* directions, with periodicities of *L*_{
x
} and *L*_{
y
} , respectively. In each "unit cell", a synaptic vesicle bursts at time *t* = 0, releasing the neurotransmitters into the cleft. We model the release of the neurotransmitters as a transient flux, *u*(*t*), that is confined to a circular opening with radius *R*. We place the synaptic vesicle at the center of the pre-synaptic face of the unit cell. After diffusing to the post-synaptic membrane, neurotransmitters are absorbed by a circular disk in each unit cell, with radius *a*. We place this "sink" also at the center of the post-synaptic face of the unit cell. The exact shapes and locations of the pre-synaptic opening and the post-synaptic sink are not essential for the analytical solution of our model. The quantity of interest is the total flux, *J*(*t*), through the post-synaptic face of each unit cell.

*z*axis pointing toward the post-synaptic face. The concentration of neurotransmitters at position

**r**and at time

*t*is

*C*(

**r**,

*t*). Within the synaptic junction, it is governed by the diffusion equation,

*D*is the diffusion constant. The initial condition is

*z*= 0 is

*ρ*= (

*x*

^{2}+

*y*

^{2})

^{1/2}is the distance to the

*z*axis. The boundary condition at

*z*=

*L*

_{ z }is

*f*(

*t*) of

*t*, we denote the Laplace transform as $\widehat{f}(s)\equiv {\displaystyle \underset{0}{\overset{\infty}{\int}}dt}{e}^{-st}f(t)$. The Laplace transform of Eq. (1), using the initial condition of Eq. (2), is

*x*and

*y*directions has the form

The coefficients *α*_{
lm
} (*s*) and *β*_{
lm
} (*s*) are to be determined from boundary conditions.

*x*and

*y*that has value 1 when

*ρ*<

*R*and value 0 when

*ρ*>

*R*. The coefficient of the cos(2

*lπ*/

*L*

_{ x })cos(2

*mπ*/

*L*

_{ y }) term is

*ε*

_{0}= 1/2 and

*ε*

_{ l }= 1 for

*l*> 0. For later reference, we note that the function having value 1 when

*ρ*<

*a*and value 0 when

*ρ*>

*a*has the following coefficients in its 2-dimensional cosine transform:

*z*=

*L*

_{ z }, we use the constant-flux approximation [9]:

*Q*(

*s*) is to be determined by the condition

*α*

_{ lm }(

*s*) and

*β*

_{ lm }(

*s*). The results are

*Q*(

*s*) as

which is independent of *a*. Equation (17b) is simply a consequence of ligand conservation, i.e., the total number of ligands released from the synaptic vesicle is the same as the total number of ligands absorbed by the receptors.

*u*(

*t*) modeling neurotransmitter release from the synaptic vesicle. We focused on an exponentially decaying function:

*D*and

*t*

_{0}. For two sets of these parameters, e.g.,

*D*

_{1}and

*t*

_{01}in one and

*D*

_{2}and

*t*

_{02}in the other, it can be shown that the corresponding response functions satisfy

We now briefly describe the details of our implementation of the analytical solution. To calculate the *q*_{
lm
} and *p*_{
lm
} coefficients of Eqs. (8) and (9), we first carried out the integration over *y* analytically. The remaining integration over *x* was done numerically using the Gauss-Legendre quadrature with two points. The summations over *l* and *m* in Eq. (15) were truncated at *l* = *m* = 40. The Laplace transform of $\widehat{J}(s)$ was inverted by the Stehfest algorithm [10]. A Fortran90 code for the implementation is available upon request.

## 3. Results

We now present some illustrative results. The parameters of our model are as follows: *L*_{
x
} = *L*_{
y
} = 500 nm; *L*_{
z
} = 50 nm; *R* = 20 nm; *a* varied from 2.5 to 40 nm; *t*_{0} varied from 1 to 10 ms; and *D* varied in (0.4-4) × 10^{5} nm^{2}/ms.

*a*thus mimics an increasing number,

*N*

_{rec}, of receptors per unit cell. We expect

*a*to increase linearly with increasing

*N*

_{rec}when

*N*

_{rec}is small; the increase in

*a*then slows down at higher

*N*

_{rec}(see Discussion). Figure 4 displays the dependence of the response function

*J*(

*t*) on

*a*(and hence

*N*

_{rec}). As

*a*(i.e.,

*N*

_{rec}) increases,

*J*(

*t*) more and more quickly reaches a higher and higher maximum and decays faster and faster. This is the expected behavior. Moreover, according to Eqs. (17b) and (18b), the areas under the curves for different

*a*values are all equal to

*πR*

^{2}

*t*

_{0}. Note also that all our

*J*(

*t*) curves have the familiar shape seen in previously numerical studies [1–7].

*J*(

*t*) is scaled by

*t*

_{0}so that, effectively, the total number of neurotransmitters entering the synaptic cleft is fixed. It is clear that, as

*t*

_{0}increases (i.e., as the speed of neurotransmitter release decreases), the response function rises and decays more slowly. This behavior has previously been specifically modeled by Stiles et al. [1].

*D*ranged from (0.25-6) × 10

^{5}nm

^{2}/ms. In Figure 6 we display the change in the response function when

*D*is varied from (0.4-4) × 10

^{5}nm

^{2}/ms. As expected, when neurotransmitter diffusion slows down, the response function is also delayed. In our model, decreasing

*D*has the same effect on the response function as increasing

*t*

_{0}[see Eq. (19)].

## 4. Discussion and Conclusion

We have presented an analytical solution to a model for the diffusion and reaction of acetylcholine in a neuromuscular junction. The model also applies to the diffusion and binding of Ca^{2+} in a dyadic cleft. Our results are qualitatively similar to those obtained previously from models solved numerically [1–7].

Perhaps the greatest value of our analytical solution is that it provides a benchmark for testing numerical methods. Diffusion and reaction of ligands in intercellular and intracellular spaces have been modeled either on a particle description or a concentration description. The former type of models have been solved by Monte Carlo simulations [1, 7], while the latter type of models have been solved by either finite-difference [2, 6] or finite-element [3–5] methods. The two types of models have been shown to give equivalent results [8]. The level of realism of our model approaches those of the models solved numerically; hence our analytical solution will be able to serve as a good benchmark for the numerical methods.

*κ*controls the degree of partial absorption. When

*κ*= 0, the region

*ρ*<

*a*becomes reflecting and binding cannot occur. When

*κ*→ ∞, the region

*ρ*<

*a*becomes fully absorbing and Eq. (20) reduces to the absorbing condition of Eq. (4a). Note that the bimolecular rate constant

*k*for binding to the partially absorbing disk is given by [11]

One can thus parameterize *a* and *κ* by matching *k* with experimental data for the ligand-receptor binding rate constant.

*a*of this disk. One can identify

*a*by requiring that the bimolecular rate constant

*k*calculated for the single absorbing disk is the same as that for the

*N*

_{rec}receptors. For the single absorbing disk we have

*k*= 4

*Da*[see Eq. (21)]. If each of the

*N*

_{rec}receptors is modeled as an absorbing disk with a small radius

*a*

_{0}, then

*k*≈ 4

*N*

_{rec}

*Da*

_{0}when

*N*

_{rec}is small [12]. Therefore

*a*≈

*N*

_{rec}

*a*

_{0}for small

*N*

_{rec}. As

*N*

_{rec}increases, the rate constant

*k*for the multiple receptors and correspondingly the radius

*a*of the equivalent disk also increase, but the increase slows down as

*N*

_{rec}becomes large [12, 13]. Instead of using a single equivalent absorbing disk, analytical solution is actually still permitted when multiple receptors, each represented by a (partially) absorbing small disk, are present at arbitrary positions on the post-synaptic face. An alternative way to model the presence of multiple receptors is to assume that the whole post-synaptic face is partially absorbing, with an reactivity given by [12, 13]

*S*=

*L*

_{ x }

*L*

_{ y }is the area of the post-synaptic face,

*f*

_{rec}=

*N*

_{rec}

*πa*

_{0}

^{2}/

*S*is the fraction of the post-synaptic face that is covered by the receptors, and

*k*

_{0}is given by

We have modeled ligand-receptor binding as irreversible. This is somewhat justified for modeling the neuromuscular junction, in which acetylcholinesterase can break down acetylcholine molecules newly released from the receptors. No such mechanism is present for Ca^{2+} in the dyadic cleft. Reversible binding can be treated by appropriate boundary conditions [14] on the post-synaptic face. Another important detail is that both acetylcholine and ryanodine receptors have multiple binding sites for their ligands so that there are multiple ligand-occupation states for the receptors. Again, these can be treated by appropriate boundary conditions.

The geometries of some of the models previously solved numerically are more sophisticated than that of our model. In particular, secondary folds of the neuromuscular junction has been included in some of the previous models [1, 3–5]. A formalism for treating ligand binding to a site buried in a narrow tunnel has been developed [15] and may be adopted for treating the narrow secondary folds in the neuromuscular junction. However, analytical solution requires idealized geometries; the kind of realistic geometries drawn from electron microscopy that can be handled by a finite-element method [4, 5] is beyond the reach of analytical solution. Nevertheless, with all the new ingredients outlined above, analytical solution will potentially provide a new avenue for modeling biochemical transport.

## Declarations

### Acknowledgements

This work was supported in part by Grant GM58187 from the National Institutes of Health.

## Authors’ Affiliations

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## Copyright

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