We study the energy transfer performance in electrically and magnetically coupled mechanical nanoresonators. Using the resonant scattering theory, we show that magnetically coupled resonators can achieve the same energy transfer performance as for their electrically coupled counterparts or even outperform them within the scale of interest. Magnetic and electric coupling are compared in the nanotube radio, a realistic example of a nano-scale mechanical resonator. The energy transfer performance is also discussed for a newly proposed bio-nanoresonator composed of magnetosomes coated with a net of protein fibers.

Keywords

NanoresonatorsMagnetic nanoparticlesMagnetosomesEnergy transferNanotube radio

Background

Mechanical nanoresonators exhibit resonance behavior involving the mechanical vibrations of the system elements. The natural frequencies of such resonances will, generally, be in the radio frequency range. Nano-scale mechanical resonators coupled with electromagnetic fields have been receiving significant attention recently [1–3]. The ability to interact with electromagnetic fields allow such resonators to be essential parts of nano-scale systems. Imaging, sensing, and targeted actuation in nano-scale are among several emerging technologies that rely on efficient energy and information transfer.

In principle, nanoresonators may couple to electromagnetic fields by the charge distributions (electric coupling) or by the magnetic moment they carry (magnetic coupling). Traditionally, the energy transfer via electric coupling has received more attention since materials are mostly transparent to the magnetic field. Also, magnetic field intensity in electromagnetic radiations is significantly smaller than the electric field. Consequently, magnetic coupling of mechanical resonators with electromagnetic radiations becomes impractical unless the size of the system significantly decreases. A desirable magnetic coupling, however, can be achieved if the coupling occurs within the near-field range [4]. Take the example of a mechanical nanoresonator operating in a biological environment. In this case, magnetic coupling holds important advantages over electric coupling. First, magnetically coupled systems can provide more selective and localized energy transfer that is due to the fact that magnetic fields, unlike electric fields, couple weakly with non-targeted surrounding media, which are often not magnetic [5, 6]. Therefore, magnetic signals suffer from considerably less attenuations while propagating in the surrounding biological media and can drive a targeted resonator inaccessible to electric signals with the same level of energy. In addition, magnetic dipoles are normally more stable than electric dipoles and do not require significant energy from outside to maintain their state.

This work revisits the interactions of radiofrequency electromagnetic fields with mechanical nanoresonators. In particular, we are interested in the quantitative assessment of the energy transfer in such nanoresonators. We use the same methodology presented by Hamam et al. [7] and focus on low-dissipation conditions that permit resonance. The feasibility of achieving such conditions has been demonstrated in the literature [1, 8]. The outline of this paper is as follows. We first present a general model for mechanical nanoresonators including electric and magnetic coupling mechanisms and describe the dynamics of the model. Then, we compare the resonant energy transfer performance of the resonator for electric and magnetic coupling using resonant scattering theory. Finally, we sketch a roadmap for a new nanoresonator composed of a magnetite nanoparticle embedded in a net of protein fibers.

Methods

In general, the mechanical structure of a nanoresonator consists of an elastic cantilever beam equipped with a specialized tip, which is responsible for electromagnetic interaction, vibrating in a low-viscosity fluid such as low-pressure air. The viscoelastic model of the nanoresonator includes the coefficient of mechanical elasticity, k, and the dissipation coefficient, D. For a cylindrical beam with a spherical tip, k ≅ EI_{
c
}/L^{3}, where E, I_{
c
}, and L are the Young’s modulus, second moment of cross-section, and the length of the beam, respectively. Moreover, as shown in [9], the combination of intrinsic (e.g., plastic deformation and surface effects) and extrinsic (e.g., viscous forces of the surrounding fluid) dissipation mechanisms determines the value of D. Because the size of the nanoresonator is much smaller than the wavelength of the external field, the energy transfer is in the form of interactions between the incoming field and dipole moment of the nanoresonator’s tip. As shown in Figure 1, we consider two nanoresonators that have identical mechanical structures, yet interact with electromagnetic fields via different coupling mechanisms: electric coupling ($\mathfrak{E}$) and magnetic coupling($\mathfrak{M}$). In the case of electric coupling, an alternating current electric field, E = E cos(ωt), produces a force, F, on an electric charge distribution, q, placed at the tip of the nanoresonator and causes oscillatory deflections in the cantilever. A very similar model has been discussed in the nanotube radio[1]. For the magnetic coupling, assume the tip of the resonator is made of a ferromagnetic material such as magnetite (Fe_{3}O_{4}) and has a magnetic moment of μ. An external magnetic field produces two different motions on such magnetic moment: a translational force produced by the field’s gradient and a rotational torque trying to align the magnetic moment with the external field. To produce a translational force that is greater than the thermal noise on a nanoresonator, a magnetic field with ultra-high gradient is required. Producing such magnetic fields drastically increases the complexity of the system; therefore, we choose to neglect the magnetic force and only consider the rotational torque exerted by the external field on the magnetic moment of the nanoresonator’s tip. An AC magnetic field, B = B cos(ωt), generates a magnetic torque, ${\mathcal{T}}_{\mathrm{m}}=\mu \times B$, and rotates the tip leading to oscillatory beam deflections. A similar device has been built and used for ultra-sensitive magnetic resonance force microscopy[2, 8].

The dynamics of the system can be expressed by a Langevin equation for the resonator tip. After linearization for small deflections, we have

where x is the displacement at the tip of the beam; m, the effective mass of the system; and D, the dissipation coefficient. F = qE for electric coupling, while $F=\mathcal{T}/L=\mu B/L$ for magnetic coupling. The term N(t) is a stochastic force with the correlation of 〈N(t)N(t + Δt)〉=2Dk_{B}Tδ(Δt), where k_{B} and T are the Boltzmann constant and temperature in Kelvin, respectively. In the systems we will consider, the amount of energy stored in the resonator is well above k_{B}T. Therefore, we can omit the stochastic term, N(t), from (1). The system’s natural frequency and the quality factor are given by ${\omega}_{0}=\sqrt{k/m}$and $Q=\sqrt{\mathit{\text{km}}/D}$, respectively. The steady state solution of the system is as follows:

Here, θ = x/L is the angular displacement, I ≅ mL^{2} is the system’s second moment of inertia, κ ≅ kL^{2} is the rotational spring constant of the cantilever, and ψ is the stochastic torque caused by the thermal noise. For the magnetic coupling, $\mathcal{T}=\mu B$, while $\mathcal{T}=\mathit{\text{qEL}}$ in the case of the electric coupling.

Discussion

Energy analysis

We now consider the total energy of the oscillator

$U=\frac{1}{2}m{v}^{2}+\frac{1}{2}k{x}^{2}.$

(6)

When ω=ω_{0}, this quantity is time-independent and is given by

$U=\frac{{F}^{2}{Q}^{2}}{2k}.$

(7)

One can think of U as the energy capacity of the resonator. An important observation is that U scales with Q^{2}.

Next, we consider the energy absorbed by the nanoresonator during the relaxation time τ=Q/ω_{r}. This quantity can be calculated by averaging the instantaneous power absorbed by the nanoresonator, P, over τ. For our system, P can be written as inner product of incident force and velocity of the resonator

At the resonance frequency, ${x}_{\mathrm{m}}=\mathit{\text{FQ}}/m{\omega}_{\mathrm{r}}^{2}$ and φ = π/2, which gives the average absorbed power of $\stackrel{\u0304}{P}={F}^{2}Q/2m{\omega}_{\mathrm{r}}$. Thus, the energy deposited in the nanoresonator during the relaxation time τ is

Note that the energy absorbed by the resonator over the relaxation time matches the resonator energy capacity. In general, the calculation of the force (or torque) exerted on the nanoresonator through electromagnetic coupling is not straightforward. As an alternative approach, one can use scattering theory [7, 11], which allows to work with fluxes instead of forces, to estimate the energy deposited on the resonant system. The two approaches are equivalent since our theoretical model is solely based on dipole-dipole interactions. In the next section, we will use this more convenient method to study the resonant energy transfer.

Resonant scattering analysis

The coupling between external fields and the nanoresonator consists of an absorption and a scattering process. According to the scattering theory, the power absorbed by the resonant system equals to P_{a} = Φσ_{a}, where Φ is the incident electromagnetic power flux, and σ_{
a
} is the absorption cross-section given by [7, 11]

Here, c is the speed of light; Γ_{a}, the absorption width; and Γ_{s}, the scattering width. The widths are the ratio of the power loss to the characteristic energy of the corresponding process. For process i, Γ_{
i
} = 1/τ_{
i
} = ω/Q_{
i
}, where τ_{
i
} and Q_{
i
} represent the relaxation time and the quality factor, respectively. The total energy absorbed by the resonant system during the resonant process is given by the following:

where Γ = Γ_{a} + Γ_{s} is the total width of the system. For nano-scale systems of interest, Γ ≈ Γ_{a} because Γ_{s} ≪ Γ_{a}. The maximal energy transfer occurs at the resonant frequency and can be written as

where U is the energy of the resonator, and P_{r} = dU/dt is the radiative power of the resonator’s dipole. For the electric dipole model ($\mathfrak{E}$), we have

where p_{0} = qx_{m} is the maximal amplitude for the electric moment of the resonator. Thus, one obtains the following scattering width for the system:

which confirms that the energy deposited scales as Q^{2}/k.

Using classical electrodynamics [12], one can show that the the radiative power of an oscillating magnetic dipole of moment μ_{eff} is given by replacing p_{0} by μ_{eff}/c in 15. In the case of the spherical MNP shown in Figure 1, if θ_{m} is the maximum angular deflection, then the oscillating part of the magnetic dipole of moment is ${\mu}_{\text{eff}}=\mu {\text{sin}}_{2}\left({\theta}_{\mathrm{m}}\right)$. Therefore, for the magnetic coupling model ($\mathfrak{M}$), one can follow the same derivation as in the electric coupling scheme ($\mathfrak{E}$) and obtain

Note that Q_{a} and k in Equations (18) and (22) only depend on the viscoelastic structure of the resonator and are independent from the coupling type (magnetic or electric). Given a similar viscoelastic structure, the energy absorption value for electric and magnetic coupling will be comparable if μ/Lc ≈ q. For nano-scale systems of interest, the condition Lc < 1,000 m^{2}/s normally holds. By comparing 22 to 10, it is possible to derive an expression for the average magnetic force experienced by the nanoresonator over the resonance relaxation time, which is given by

Having discussed the mechanical dynamics of the nanoresonator as well as the theoretical formulation for energy transfer performance of different coupling mechanism, we apply our analysis to a possible nanoresonator sketched in Figure 2, and we also discuss the feasibility of a bio-nanoresonator composed of protein coated Fe_{3}O_{4} nanoparticles.

In our first example, we compare the energy transfer performance of the magnetic and electric coupling in the nanotube radio, a realistic example of a mechanical nanoresonator [1]. We replace the electric dipole of the nanotube tip with a magnetic dipole in the form of spherical magnetite nanoparticle. According to the original study, a nanotube radio built from a cylindrical carbon nanotube of length L ≈ 1 μ m holding a net charge of q = 200 e^{−} absorbs an amount of energy enough to detect radio signals from the electromagnetic radiation. To achieve the same amount of energy deposit, the magnetic moment of the replacement tip should be in the order of μ ≈ qLc = 9.6 × 10^{−15} Am^{2}, which can be obtained by placing a magnetite nanoparticle of radius R approximately 160 nm.

Another interesting application is the possibility of transmitting energy to magnetic nanoparticles in the biological setting. Biogenic magnetite nanoparticles called magnetosomes, first discovered in magnetotactic bacteria [13], are also found in the brain of many animals and are believed to participate in determining the orientation in several species such as migratory birds [14]. Interestingly, magnetosomes consist of magnetite particles of radius 50 to 100 nm and are embedded in the cytoskeleton bound to a viscoelastic system formed by a net of protein fibers. Because magnetic nanoparticles of such size are single domain with high coercivity [15, 16], the magnetosome can be represented as a torsional nanoresonator with magnetic coupling (see Figure 2). According to Winklhofer and Kirschvink [17], the rigidity of the cytoskeleton can be estimated by κ = 100k_{B}T/ Rad per connecting filament. Thus, for magnetite particles with a density of ρ = 5,200 Kg/m^{3}, a radius of R = 100nm, and the number of the connecting filaments ranging from 1 to 1,000, the natural frequency of the oscillator will fall between 2 and 66 MHz. A resonance is in principle not possible if we adopt the standard viscosity of the cytoplasm [18]. However, in a carefully engineered synthetic system, one could lower the drag forces in order to achieve resonance and higher quality factor up to Q = s100. Figure 3 shows possible quality factor values for a nanoparticle of radius 100 nm, assuming that the viscosity and elastic constants could be controlled.

In order to achieve higher quality factor, the nanoresonator should experience smaller viscous resistance. For instance, one can reduce drag forces in the system by coating the magnetite nanoparticle with hydrophobic proteins or lipids. In this case, the hydrophobic coat acts as a lubricant [19, 20]. In a more sophisticated design, a multi-layer shell of hydrophobic proteins may be used to engulf the nanoresonator and repel water molecules [21]. In order to aggressively reduce the rotational friction, the nanoresonator could be packed in an inorganic shell that completely excludes the system from the cytoplasm. The elastic protein fibers may be replaced by synthetic nanowires or nanotubes with carefully designed rigidity. For example, del Barco et al. [22] have demonstrated the possibility to have free rotation of magnetic nanoparticle embedded in a solid matrix.

Assuming that high quality factor, Q = 100, can be achieved, one finds that an AC magnetic field of intensity B = 3.5mT, generating an electromagnetic flux of 10 W/m^{2}, deposits a significant amount of energy ΔU = 2,500k_{B}T into the system over the resonance relaxation time. Since this field intensity is well below the coercivity field of the nanoparticle [15, 16], we neglect the energy losses via magnetic reversal. If this energy was entirely manifested as heat, the temperature of the magnetosome would be increased by 0.5°C during the relaxation time τ = 0.1μ s. As shown in Figure 3, Q = 10corresponds to ω_{0} = 66MHz, in air (η = 10^{−5}Pa.s), while the same quality factor can be achieved at frequencies as low as about 1 MHz if the viscosity can be reduced by a factor of 100 compared to air. Magnetically coupled mechanical nanoresonators with high quality factor show good energy transfer performance while being tunable and may be useful in frequency selective heat production in the biological environment. The important contribution of mechanical motions in magnetic hypothermia has been experimentally shown in [23]; however, these applications have not yet benefited from the resonant energy transfer since their quality factors are well below one.

Conclusion

In conclusion, we have shown that carefully engineered magnetically coupled nanoresonators can match the energy transfer performance of its electrically coupled counterpart, while providing a more selective and robust interaction in biological environments. We have used a unifying framework of resonant energy transfer for electrically coupled and magnetically coupled mechanical nanoresonators and compared the performance for the two couplings. Our analysis suggests that if the interacting electric dipole of a small electrically coupled resonator is replaced by a magnetic dipole, a comparable amount of energy can still be deposited on the system. We have considered the example of nanotube radio, and we have shown that the strength of electromagnetic coupling remains the same using a magnetite nanoparticle of radius 160 nm instead of the charged tip. We have proposed a new resonator composed of magnetosomes embedded in a net of protein fibers and analyzed its energy transfer performance. We have discussed possible pathways to further improve the quality factor of the resonator. While this article focuses on quantitative aspect of energy transfer, our work also opens up new interesting questions on how to use efficient energy channels to transmit information to a nano-scale device or organism. Characterizing the transmission of information and the channel capacity [24] will be discussed in future studies.

Declarations

Acknowledgements

We would like to thank Professor Mark Dykman for his important suggestions and enlightening comments. We also thank the participants of NSF Workshop on Biologically-enabled Wireless Networks for stimulating discussions. This work is supported in part by the National Science Foundation under grant number NSF CNS-1051240 and the US Department of Energy, Office of Science, Basic Energy Sciences with contract numbers DE-FG02-07ER46352 and DE-FG02-08ER46540 (CMSN), and benefited from allocation of computer time at the NERSC and NU-ASCC computation centers.

Authors’ Affiliations

(1)

College of Computer and Information Science, Northeastern University

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