Effect of Contour Shape of Nervous System Electromagnetic Stimulation Coils on the Induced Electrical Field Distribution
 Sava P Papazov^{1} and
 Ivan K Daskalov^{1}Email author
DOI: 10.1186/1475925X11
© Papazov and Daskalov; licensee BioMed Central Ltd. 2002
Received: 16 April 2002
Accepted: 14 May 2002
Published: 14 May 2002
Abstract
Background
Electromagnetic stimulation of the nervous system has the advantage of reduced discomfort in activating nerves. For brain structures stimulation, it has become a clinically accepted modality. Coil designs usually consider factors such as optimization of induced power, focussing, field shape etc. In this study we are attempting to find the effect of the coil contour shape on the electrical field distribution for magnetic stimulation.
Method and results
We use the maximum of the induced electric field stimulation in the region of interest as the optimization criterion. This choice required the application of the calculus of variation, with the contour perimeter taken as a preset condition. Four types of coils are studied and compared: circular, square, triangular and an 'optimally' shaped contour. The latter yields higher values of the induced electrical field in depths up to about 30 mm, but for depths around 100 mm, the circular shape has a slight advantage. The validity of the model results was checked by experimental measurements in a tank with saline solution, where differences of about 12% were found. In view the accuracy limitations of the computational and measurement methods used, such differences are considered acceptable.
Conclusion
We applied an optimization approach, using the calculus of variation, which allows to obtain a coil contour shape corresponding to a selected criterion. In this case, the optimal contour showed higher intensities for a longer line along the depthaxis. The method allows modifying the induced field structure and focussing the field to a selected zone or line.
Background
The Electromagnetic stimulation was first applied for excitation of peripheral nerves [1] and later for transcranial brain excitation to evoke motor responses [2]. The latter has become a routinely accepted diagnostic procedure. Various other applications have been reported [3]. An optimization of the circular coil winding for brain excitation was proposed by Ruohonen et al [4]. Respiration stimulation was attempted in animal and man [5, 6], but did not found practical application. Magnetic pacing of the closed chest dog heart was also undertaken [7, 8], but proved to require extremely high energy. Open chest dog heart stimulation was achieved with lower thresholds [9]. Some theoretical considerations for magnetic field cardiac excitation in man have been considered by [10].
Electromagnetic stimulation in all of the abovecited studies was generated with circular coils. Combinations of circular coils – butterfly, fourleaf, or slinky type [11, 12], were designed for better focussing and/or increased energy. The newly proposed 'slinky' coils promise better performances in this respect [13–15].
Square slinky coils were considered by Lin et al [15], yielding a better expressed (hence better focussed) but lower field intensity maximum, compared to circular coils.
Having in view that better focussing and improved field distribution would provide for lower energy requirements, we decided to investigate whether different coil shapes would yield some improvement in this sense.
Method
2.1. Theoretical background
A natural criterion for optimal coil design would be the electrical field induced in the region of interest. It is defined by:
Electromagnetic stimulation processes could be studied using a more general relation:
where the electric potential component is added. However, it is usually neglected due to its relatively low value and hence weak influence. For a given coil current i(t) and contour shape (S), the magnetic vectorpotential is defined by the known relation:
The necessary and sufficient conditions for finding the extremum of Eq. (4) should be defined, for a known timecourse of the current i(t). Thus, the induced field at point M (Fig. 1) will be at its maximum [16–18].
The function y(x) has to be found by solving the relation:
There are reasons to assume that a real solution of the above problem exists, and that it respects the condition of sufficiency.
The conditions for existence of extremum of Eq.(4), concerning y(x), can be defined by the function:

a nonstandard expression where the extremum function y(x) is hidden in the integral boundary;

a vector function where the application of the classical calculus of variation approach is inapplicable without some necessary transformations.
The conversion of Eq. (6) to a standard form is shown in Appendix A, which contains the succession of transformations leading to the necessary conditions for existence of extremum, respectively, to the Euler equations:
Analyzing the obtained solution, it should be taken into account that the axes scaling in Fig. 2 is influenced by the canceling of the multipliers to the functions of Eqs. (3) and (4).
A solution could be attempted not only as a Cauchy type, but also as a SturmLiouville problem, with the corresponding fundamental difficulties.
The extremal y(x) of Fig. 2 is considered in the class of symmetric curves with respect to OX, which is natural for this type of problem. The solution of the Cauchy problem in the class of closed curves creates difficulties with the use of numerical procedures. This is due do reaching, generally, points of unstable solution, where the first derivative is interrupted. Thus, it becomes necessary to look for the extremal in parametric form.
In addition, it can be shown that the necessary conditions considered are also sufficient (see Appendix B for details).
Results and discussion
The field excited by a system of three coils located symmetrically with respect to the ordinate in the XOY and YOZ planes is studied, using the basic relation of Eq. (4) (see Appendix C for details).
It can be seen that for a field excited by a system of coils, the superposition principle is applicable, due to the linear relation between the cause di(t)/dt (applied excitation) and the consequence E(t) (resultant field).
Thus, the results obtained for a given coil shape can be applied for a system of several coils of the same type.
The excitation is obtained by the discharge current of an RLC circuit, where R = 0.3 Ω, L = 0.01 mH and C = 128 μF. These parameters are chosen in a relatively arbitrary way, and do not influence the shape or structure of the induced field. The feedback from induced currents in the tissue is ignored due to the tissues relatively low conductivity.
Comparison of intensities (Ei) and percentage attenuations δ E % of squareshaped (SQR), triangular (TRI) and the optimal (OPT) contour with respect to the circular (CIRC) taken as a basis
CIRC  TRI  SQR  OPT  

Zi mm  Ei V/mm  δ Ei %  Ei V/mm  δ Ei %  Ei V/mm  δ Ei %  Ei V/mm  δ Ei % 
2  3.55    3.7  4  3.99  12  4.1  15 
5  2.65    2.62  1  2.89  9  3.0  13 
10  1.75    1.6  9  1.82  4  1.92  10 
20  0.9    0.72  25  0.87  3  0.93  3 
30  0.525    0.38  38  0.48  9  0.52  1 
40  0.335    0.23  46  0.295  13  0.317  5.6 
50  0.225    0.15  50  0.195  15  0.21  7.1 
100  0.057    0.037  91  0.048  17  0.053  7.5 
The results obtained by the calculus of variation method were verified by experimental physical measurements in a plastic tank filled with saline. The coils were placed under the tank. The induced field was measured by a bipolar probe attached to a 3D positioning device. The accuracy of these measurements was not very high, due to positioning errors of about 0.5 mm and errors related to probe rotation. Differences between maximum field intensities of experimental and theoretical data reached 12%. This difference was considered a reasonable correlation, as the purpose was only to check the validity of the theoretical results.
The contour shape OPT, according to the optimality criterion of Eq. (4) and the limiting condition concerning the perimeter (Appendix A, Eq. A5), yields higher values of the induced electrical field in regions near the XOY plane, up to about 30 mm. For distances around 100 mm, the circular shape has a slight advantage. However, the differences in question could be considered to be in the range of the computational errors, mainly connected with the linearsegment approximation used in the numerical solution.
The squareshaped coil induces higher intensities than those of the circular coils for distances in the range of 10–15 mm, but lower than compared to CIRC. For higher values of Z_{i}, the induced field intensity decays.
The triangularshaped coil has an advantage only over the circular coil for short distances of 2 mm.
If the limiting condition were not the perimeter, but instead the surface encompassed by the coil, a separate investigation would possibly reveal a different optimal shape. Indisputably, the circle has the largest surface area. However, the solution of such a variation problem leads to a degenerated type of isoperimetric problem, where the Euler differential equation is transformed into algebraic form and the extremal thus obtained cannot comply with the boundary conditions. Other methods could be applied for this case, for example dynamic programming, but such efforts would be justified only if such an optimal shape could be found that would yield a considerably higher induced field.
Conclusion
The investigation of the shapes of coils for electromagnetic stimulation of the nervous system shows that an optimal coil shape exists. This shape should not necessarily be considered the most important factor in the search for solutions for electromagnetic stimulation concerning the penetration depth of the induced field. For example, the slew rate of the electromagnetic pulse, obtained by the easily controllable current derivative, di/dt, can also be considered.
The results of the present study, as presented for example in Figs. 5,6,7,8, show the effect of the contour shape on the induced field structure, and the possibility of focusing the field to a selected zone or line. For low values of Z_{i}, focusing along the Yaxis can be observed for the TRI, SQR, and OPT coils. Their field components are nearer to the YOZ plane. The OPT contour shows some higher intensities for a longer line along the Yaxis. Such a property might be useful, e. g., for peripheral nerve stimulation or other body structures of elongated structure.
Appendix
A. Necessary conditions for extremum
Then the condition for the existence of an extremum should be defined on the basis of :
It is not difficult to see that the extremum of (A1) is the sum of the extrema of its two squared components.
The theory of the calculus of variations makes clear that the extremum of a nonstandard function of the type F(y(x)) = F _{1}(y(x))F _{2} (y(x)) is to be found on the basis of the linear combination:
G(y(x)) = F _{1} (y(x)) + λ_{0} F _{2} (y(x)), (A2)
where λ_{0} is to be obtained from the ratio:
and y _{ extr } (x) is defined using the conditions for extremum.
The functionals in (A1):
can be represented as a product of two equal functions. Then, in the two cases of U _{2} (y(x)) and U _{3} (y(x)) a trivial value for λ_{0}; λ_{0} = 1 renders the problem for extremum of the sum of the squares of the functions to an extremum of the sum of their power of one and in a sense – to the sum of the extrema of their moduluses.
The integrals in (A1) should be transformed in parametric form with arguments t:
x = x _{ 1 } (t); y = x _{ 2 } (t)
Introducing also the condition for a constant perimeter, the calculus of variations problem is presented in a near standard form – the extremum of :
is to be found, having in view the limitation:
The necessary conditions for the existence of an extremum are defined using the Lagrange function:
where the Lagrange coefficient λ in this case is a constant, to be found according to the necessary conditions for extremum and the limitation (A5).
The necessary conditions for extremum can be defined by the Euler system of equations:
with boundary conditions:
It is known that the equations in this system are in linear relation. In this case, a calibration equation is recommended in the following form:
For this specific problem, the limitation condition (A5) can be taken as calibration equation.
Lagrange function (A6) leads to a system of differential equations in parametric form:
with boundary conditions (A9).
B. Sufficiency of the necessary conditions
 1.
The obtained extremum function is a solution of the Euler equation system – in this case equations (10) and (11).
 2.
If λ is considered a parameter of the extremum function family, for the accepted boundary conditions and varying λ, a central field of extremum functions is obtained. The numerical analysis can show that they do not cross, and that a conjugated point does not exist, therefore the Jacoby condition for sufficiency is met.
and
It is obvious that (B1) and (B2) can have positive and negative values, which allows the conditions of Legendre to be met:

a condition for maximum, specifically a weak maximum, which is achievable with curves having zero order proximity (proximity to ordinates):
 4.
It can be verified, based on Eq. (9), that the third partial derivative:
exists, which is also a part of the sufficiency conditions.
C. Field induced by a system of excitation coils
A relatively arbitrarily shaped contour L is considered (Fig. 1) with a current i(t) that excites an induced electrical field (x, y, z). The field is obtained from Eq. (4), or:
Difficulties also appear for cases of contours in a relatively general position with respect to the coordinate axes [13]. Such difficulties are not insurmountable, but should be dealt with depending on the specific problem in view.
The present investigation relates to fields induced by flat contours approximated by n linear segments (Fig. 3) located in the XOY and YOZ planes. Applying the calculus of variation approach, such an approximation is justified. The numerical solution (Fig. 2) suggests that any other type of approximation would involve computational difficulties without major impact on the practical results. The solution accuracy depends, of course, on the value of n. For the triangular and square shapes, n is defined and does not affect the accuracy.
For a system of k contours, the resulting induced field is obtained by superposition, based on the linear relation between (x, y, z) and di / dt, as evident from Eq. C1. In this case, three coils (L _{1}),(L _{2}) and (L _{3}) are involved, where (L _{1}) and (L _{2}) are symmetrically located in the XOY plane, and (L _{3}) is in the YOZ plane, symmetrically oriented with respect to the negative Zaxis. The region to be stimulated is located in the positive halfspace defined by XOY and the positive Zaxis.
For the contours approximated by n segments (Fig. 3), sums of integrals are obtained for (L _{1}) and (L _{2}) respectively:
and for (L _{3}):
The segments l _{ j } are introduced in the contour integrals by the corresponding linear relations y = m _{ jk } x + n _{ jk }, k = 1, 2 ; j = 1,2,...,n in the XOY plane and z = m _{ j } y + n _{ j } in the YOZ plane.
The segments l _{ j } are introduced in the contour integrals by the corresponding linear relations y = m _{ jk } x + n _{ jk }, k = 1, 2 ; j = 1,2,...,n in the XOY plane and z = m _{ j } y + n _{ j } in the YOZ plane.
Declarations
Authors’ Affiliations
References
 Polson MJR, Barker AT, Freeston IL: Stimulation of nerve trunks with timevarying magnetic fields. Med Biol Eng Comput 1982, 20: 243–244.View ArticleGoogle Scholar
 Mills RK, Murray NM, Hess CW: Magnetic and electrical transcranial brain stimulation: physiological mechanisms and clinical applications. Neurosurg 1987, 20: 164–168.View ArticleGoogle Scholar
 Stuchly MA: Applications of timevarying magnetic fields in medicine. Crit Rev Biomed Eng 1990, 18: 89–124.Google Scholar
 Ruohonen J, Virtanen J, Ilmoniemi RJ: Coil optimization for magnetic brain stimulation. Ann Biomed Eng 1997, 25: 840–849.View ArticleGoogle Scholar
 Mouchawar G, Bourland JD, Voorhees WD, Geddes LA: Stimulation of inspiratory motor nerves with a pulsed magnetic field (letter). Med Biol Eng Comput. 1990, 28: 613.View ArticleGoogle Scholar
 Geddes LA, Mouchawar G, Bourland JD, ElAbbady T, Nyenhius J: Magnetic (eddycurrent) electroventilation in the dog. Ann Biomed Eng 1993, 21: 193–197.View ArticleGoogle Scholar
 Mouchawar G, Nyenhius J, Bourland JD, Geddes LA: Gidelines for energyefficient coils: coils designed for magnetic stimulation of the heart. Electroenceph Clin Neurophysiol 1991,43(suppl):255–267.Google Scholar
 Mouchawar G, Bourland JD, Nyenhius J, Geddes LA, Foster KS, Jones JT, Graber GP: Closedchest cardiac stimulation with a pulsed magnetic field. Med Biol Eng Comput 1992, 30: 162–168.View ArticleGoogle Scholar
 Yamagushi M, Andoh T, Goto T, Hosono A, Kawakami T, Okumura F, Takenaka T, Yamamoto I: Effects of strong pulsed magnetic fields on the cardiac activity of an open chest dog. IEEE Trans Biomed Eng 1994, 41: 1188–1191. 10.1109/10.335868View ArticleGoogle Scholar
 Reilly JP: Magnetic field excitation of peripheral nerves and the heart: a comparison of thresholds. Med Biol Eng Comput 1991, 29: 571–579.View ArticleGoogle Scholar
 Cohen LG, Roth BJ, Nilsson J, Dang N, Panizza M, Bandinelli S, Friauf W, Hallet M: Effects of coil design on delivery of focal magnetic stimulation. Technical considerations. Electroenceph Clin Neurophysiol 1990, 75: 255–267. 10.1016/00134694(90)90105SView ArticleGoogle Scholar
 Roth BJ, Maccabee PJ, Eberle LP, Amassian VE, Hallett M, Cadwell J, Anselmi GD, Tatarian GT: In vitro evaluation of a 4leaf coil design for magnetic stimulation of peripheral nerve. Electroenceph Clin Neurophysiol 1994, 93: 255–267. 10.1016/01685597(94)900272View ArticleGoogle Scholar
 Ren C, Tarjan PP, Popovic DB: A novel electric design for electromagnetic stimulation – the slinky coil. IEEE Trans Biomed Eng 1995, 42: 918–925. 10.1109/10.412658View ArticleGoogle Scholar
 Zimmerman KP, Simpson RK: Slinky coils for neuromagnetic stimulation. Electroenceph Clin Neurophysiol 1996, 101: 145–152. 10.1016/0924980X(95)00227CView ArticleGoogle Scholar
 WH Lin V, Hsiao IN, Dhaka V: Magnetic coil design considerations for functional magnetic stimulation. IEEE Trans Biomed Eng 2000, 47: 600–610. 10.1109/10.841332View ArticleGoogle Scholar
 Elsgolc LE: Calculus of variations. Pergamon Press, Oxford 1962.Google Scholar
 Bliss GA: Lectures on the Calculus of Variations. The University of Chicago Press, Chicago, London 1963.Google Scholar
 Akhiezer NI: The Calculus of Variations. Harwood Academic Publishers, Chur, Switzerland 1988.Google Scholar
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