Journal of Nanomaterials

Journal of Nanomaterials / 2013 / Article
Special Issue

Synthesis, Properties, and Applications of Single-Domain Magnetic Nanoparticles

View this Special Issue

Review Article | Open Access

Volume 2013 |Article ID 752973 |

Hiroaki Mamiya, "Recent Advances in Understanding Magnetic Nanoparticles in AC Magnetic Fields and Optimal Design for Targeted Hyperthermia", Journal of Nanomaterials, vol. 2013, Article ID 752973, 17 pages, 2013.

Recent Advances in Understanding Magnetic Nanoparticles in AC Magnetic Fields and Optimal Design for Targeted Hyperthermia

Academic Editor: Oleg Petracic
Received19 Apr 2013
Accepted17 Jun 2013
Published28 Jul 2013


Targeted hyperthermia treatment using magnetic nanoparticles is a promising cancer therapy that enables selective heating of hidden microcancer tissues. In this review, I outline the present status of chemical synthesis of such magnetic nanoparticles. Then, the latest progress in understanding their heat dissipation mechanisms under large magnetic fields is overviewed. This review covers the recently predicted novel phenomena: magnetic hysteresis loops of superparamagnetic states and steady orientations of easy axes at the directions parallel, perpendicular, or oblique to the AC magnetic field. Finally, this review ends with future prospects from the viewpoint of optimal design for efficacy with a low side-effect profile.

1. Introduction

Hippocrates said, “those diseases which drugs cannot cure, the knife cures; those which the knife cannot cure, fire cures; those which fire does not cure must be considered incurable.” In one respect, medicine has not changed over time; even today, several treatments are used in combination to treat illnesses that have no established effective treatment protocol, the most prominent example being cancer. The current standard treatments for cancer include surgery, chemotherapy, and radiotherapy. Beyond these treatments, much research is being undertaken to create several new treatment options such as immunotherapy, and the modern equivalent of Hippocrates’ “fire”: thermotherapy. Thermotherapy is a treatment method that exploits the lowered heat resistance of cancerous tissues compared with that of normal tissues. Cancerous tissues undergo cell death even at temperatures within the range of 42 to 43°C, thus rendering thermotherapy as a promising option to reduce the disease burden in a patient [1].

To reduce damage to normal tissues using standard treatments, endo-/laparoscopic surgical techniques have been developed as a modern equivalent of Hippocrates’ “knife.” For chemotherapy, much effort has focused on drug delivery to selectively transport anticancer agents to tumor tissues using antigen-antibody reactions. Such drug delivery systems are also used to concentrate boron compounds in tumor tissues. In the treatment known as boron neutron capture therapy, the patient is radiated with epithermal neutrons, which selectively induce -decay of boron nuclei concentrated inside hidden tumors, thus specifically destroying cancer cells. Along these lines, could thermotherapy also utilize drug delivery technology to specifically deliver thermal seeds to cancer cells at unknown locations? For example, if it were possible to develop miniature induction-heating cooking pans and selectively send these to hidden tumors, then would this result in selective heating of the tumor tissues in a human body on an induction-heating cooker? In contrast to a microwave oven, we know that placing one’s hand over the induction-heating cooker will not immediately result in a burn. (Usually, we cannot confirm this feature using the commercial IH cooker, because it automatically stops working when we take off a metal pan from it.) This experience shows that a radio-waveband AC magnetic field generated in the cooker can easily penetrate deep into tissues where a tumor may be embedded. Therefore, we believe that the simple idea mentioned here, targeted hyperthermia using magnetic nanoparticles, has the potential to selectively destroy cancer cells hidden deep in the body [28].

Of course, there are many questions about this concept that need to be addressed. Is it safe to put magnetic nanoparticles in the body? Can magnetic nanoparticles really be concentrated in hidden tumor tissues? Can magnetic nanoparticles be heated within the body? To answer these questions, DeNardo et al. injected iron oxide nanoparticles conjugated with monoclonal antibodies into mouse tails and found that they accumulated at a concentration of approximately 0.3 kg/m3 (0.3 mg/cm3) in tumors [9]. (The side effects of iron oxide nanoparticles as an MRI contrast agent had been previously studied and approved for intravenous injection.) Wust et al. showed that injecting high concentrations ( kg/m3) of magnetic nanoparticles directly into tumors at known locations and irradiating them with an AC magnetic field caused the temperature of the tumors to increase to 43°C [10]. Therefore, it is known that iron oxide nanoparticles are safe, can be selectively accumulated in hidden tumors to some degree, and can be adequately heated when existing at high concentrations. Nevertheless, problems with targeted hyperthermia using magnetic nanoparticles are still evident. Does the density of magnetic nanoparticles delivered to tumors increase as it does when they are directly injected into tumors? If not, is it possible to compensate for a lower density of magnetic nanoparticles by maximizing their heat dissipation? The first problem is primarily a biochemical one, so materials researchers have primarily focused on improving the heating performance of magnetic nanoparticles [1130]. Consequent advances in chemical synthesis technology have resulted in the fabrication of magnetic nanoparticles of engineered size, shape, and structure. With respect to physical heating mechanisms, the nature of the nonlinear response and nonequilibrium dissipation in AC magnetic fields of magnetic nanoparticles, which are in contrast to the properties of cooking pans, have been uncovered. This review addresses this progress as follows. In Section 2, conventional models that are the basis of the traditional design of hyperthermia treatments are introduced. In Section 3, advances in the synthesis of magnetic nanoparticles are described and limitations in the conventional models when the monodisperse nanoparticles are used in actual thermotherapy are considered. In Section 4, recent advances in the knowledge of heating mechanisms provided by numerical simulations are explained. Finally, we summarize the optimal design of magnetic nanoparticles for hyperthermia treatment and discuss their potential as an effective and safe version of Hippocrates’ “fire” in Section 5.

2. Conventional Models for Magnetic Response to AC Magnetic Fields [3134]

The main advantage of hyperthermia treatment using magnetic nanoparticles is that the nanoparticles can reach the cancer tissue directly by travelling through the sub-micrometer spaces between blood cell walls. Therefore, for practical use, the nanoparticles should not form long chains or large clusters. Even though the many-body effects caused by dipole-dipole coupling are not fully understood [3538], it is known that a dispersion becomes unstable if between the closest nanoparticles is more than five times the thermal energy [35, 38]. Under these conditions, the minimum allowable distance between iron nanoparticles with diameter of 12 nm is roughly 27 nm, and that between ferrite nanoparticles with of 25 nm is almost 40 nm. In contrast, small-angle neutron scattering experiments have indicated that the thickness of an absorbed layer is normally several nanometers [39]. Therefore, the upper limit of is estimated to be roughly 12 nm for iron and 25 nm for ferrite. These values would be references for considering the criteria for easy delivery of the nanoparticles, although agglomeration, aggregation, or flocculation may occur depending on the surface charge of biofunctionalized nanoparticle or on the interaction between tumor-targeting ligands. Note that these values are smaller than the critical diameters for the transition into a single-domain configuration and for the coherent reversal of all spins [40]. Therefore, it has been considered that a magnetic nanoparticle used in hyperthermia treatment has only one magnetic moment, , where is the spontaneous magnetization and · is the volume of the magnetic core of the nanoparticle. Such magnetic nanoparticles have been conventionally classified as “ferromagnetic” or “superparamagnetic,” depending on whether the direction of thermally fluctuates or not.

Firstly, a ferromagnetic nanoparticle with uniaxial magnetic anisotropy, anisotropy constant , is considered, where is large enough that its magnetic anisotropy barrier with a height of blocks the thermal fluctuations; accordingly, the remanent state appears to be permanent [41]. If a magnetic field is applied in the direction antiparallel to , the state becomes metastable, as depicted in Figure 1(a). Then, reverses when the barrier disappears at the anisotropy field ; consequently, the Zeeman energy falls from to and the energy corresponding to the difference dissipates, where is permeability of vacuum. In this case, the work done in one cycle of the AC magnetic field is 0 for and for . This kind of heat dissipation has been termed “hysteresis loss.” Briefly, the heat dissipation from nanoparticles with unit weight during unit time, also called specific loss power , abruptly increases from zero to when becomes higher than , where and are the weight and density of the magnetic core of the nanoparticles, respectively. Then, flattens out even if is strengthened further. According to this argument, the guiding principle for maximizing of ferromagnetic nanoparticles is that is adjusted to and the number of cycles is maximized.

Next we move to smaller superparamagnetic nanoparticles with thermally fluctuating reversal of [42]. The reversal probability in a zero magnetic field is expressed as where is the Néel relaxation time, is the attempt frequency of , is the Boltzmann constant, and is the temperature. We must also consider Brownian rotation of the nanoparticles if they are dispersed in a liquid phase. In this case, the characteristic time of the rotation, Brownian relaxation time, in a zero magnetic field is given by where is the viscosity of the liquid phase and is the hydrodynamic volume of the nanoparticles including surface modification layers. If reversal and rotation occur in parallel, the characteristic time of relaxation could be expressed as the following equation: For very small superparamagnetic nanoparticles, is determined only by because increases exponentially with decreasing , while the increase of is inversely proportional to .

If a linear response of the thermodynamic equilibrium state of such nanoparticles is assumed for small , the average out-of-phase component of AC susceptibility, , contributed from each nanoparticle is given by Consequently, “relaxation loss” occurs and its heat dissipation is expressed as Equation (5) indicates that increases in proportion to in the low frequency range, , whereas it flattens out at even if is increased further in the high frequency range, . According to this argument, the guiding principle for maximizing of superparamagnetic nanoparticles is that is adjusted to and is maximized.

3. Progress in Synthesis of Magnetic Nanoparticle and Their Use in Thermotherapy

3.1. Size-, Shape- and Composite-Controlled Synthesis of Magnetic Nanoparticles

As discussed above, to improve hysteresis loss, ferromagnetic nanoparticles with an anisotropy field matching the amplitude of the AC magnetic field generated in the oscillator of realistic medical equipment need to be synthesized. In contrast, increasing relaxation loss involves the synthesis of superparamagnetic nanoparticles that have matching of the AC magnetic field. For these reasons, a large number of studies have focused on controlling the size, shape, or composite structure of nanoparticles to optimize and .

The history of colloids (magnetic fluids) stably dispersing magnetic nanoparticles in solution goes back to the 1960s, when magnetic suspensions were prepared by pulverizing bulk iron oxide and used for fuel delivery in a weightless environment [43], such as those involving NASA expeditions. Elsewhere, Sato of Tohoku University created magnetic fluids from minute iron oxide particles using chemical methods [44]. There have also been several major subsequent advances in magnetic fluid development, such as the monodisperse iron nitride-based magnetic fluids developed by Nakatani et al. [45]; however, because the industrial applications of magnetic fluids at that time did not require precise control of size, shape, or structure, more extensive research was not conducted in this field. However, in 2000, Sun et al. from IBM described an ordered self-assembled film of monodisperse iron-platinum nanoparticles that could serve as an ultrahigh-tech magnetic recording medium [46]. Since then, researchers have focused on developing methods to synthesize well-controlled nanoparticles, which have been reviewed extensively [47, 48]. Next, we briefly summarize these methods.

Generally, formation of nanoparticles starts with nucleation in a supersaturated melt, solution, or vapor. Particle growth continues until the concentration of solute atoms falls below the saturation solubility. If nucleation and growth proceed in parallel, nanoparticles formed initially have already grown when the last nanoparticle is formed, thus resulting in nanoparticles of variable size. Furthermore, processes such as coarsening and aggregation simultaneously occur in many cases. One way to obtain monodisperse nanoparticles is the two-stage growth method: in the first stage, rapid heating causes fast supersaturated-burst nucleation, and in the second stage, the gradual precipitation of solute atoms at a temperature below the critical point of supersaturation allows only the existing nanoparticles to grow slowly. In this process, surfactants are often introduced to the solution to prevent coarsening and aggregation. Because all nanoparticles follow the same growth process in this method, their size after growth should in principle be uniform. In practice, different groups have developed particular methods to produce nanoparticles of specific composition and size.

With respect to controlling the shape of a nanoparticle, growth kinetics is essential in addition to thermodynamic stability to minimize surface free energy. For example, if the growth rate for cubic surfaces is slower than for surfaces, the surface area of facets will decrease with growth, and the particles finally become octahedrons of facets only. Similarly, if the growth of surfaces in a hexagonal crystal system is fast, rods or, conversely, plates can be formed. For this reason, the adsorption of surfactants on particular surfaces has been intensively studied to fabricate a desired shape by controlling the growth rate of each surface. Figure 2 shows examples of regular octahedral and cubic nanoparticles [49, 50]. With regard to compositing, nanoparticles dispersed in solution are regularly conjugated by substances such as surfactants to lower their surface energy or prevent aggregation, forming a kind of composite material. Advanced compositing techniques have been developed to protect easily oxidized metal cores or to enable the simultaneous expression of multiple functions. For example, dumbbell-shaped junctions in different kinds of nanoparticles [51] and core-shell structures [27] have been produced recently (Figure 3).

3.2. Magnetic Nanoparticles to Maximize Heat Dissipation

Using these advanced synthesis techniques, researchers have fabricated magnetic nanoparticles to maximize heat dissipation based on the guiding principles described above. As an example, I highlight the recent report by Lee et al. [27], who fabricated novel superparamagnetic nanoparticles with a uniform diameter of 15 nm (see Figure 3 again). One of the reasons why they chose such a size may be to avoid aggregation. In addition, the oscillator of their equipment can generate an AC magnetic field of frequency  kHz. As discussed above, superparamagnetic nanoparticles that have a Néel relaxation time () that matches are required to maximize relaxation loss. Briefly, should be  ns. (Overall, needs to be set to 400 ns when also considering the Brownian relaxation time μs.) Substituting  ns in (1), the required energy barrier height is calculated to be  J. This value corresponds to a uniaxial anisotropic particle with  nm and  J/m3. However, examination of parameters such as bulk crystalline magnetic anisotropy [40] revealed that no suitable candidate substances had been reported. For substances with cubic symmetry, the magnitude of and the barrier height, for negative or for positive , calculated using  nm are as follows: −1.2 × 104 J/m3 and 0.18 × 10−20 J (Fe3O4); −0.46 × 104 J/m3 and 0.08 × 10−20 J (-Fe2O3); −0.25 × 104 J/m3 and 0.04 × 10−20 J (MnFe2O4); and 18 × 104 J/m3 and 8.0 × 10−20 J (CoFe2O4). As a result, shape control, which affects shape and surface magnetic anisotropy, or composition control or composite structure control, which influences the crystalline magnetic anisotropy, are therefore required. From among the possibilities mentioned, Lee et al. selected core-shell structures of cobalt and manganese ferrites and used a core-and-shell exchange coupling to control the magnitude of effective magnetic anisotropy. As a result, they obtained the core-shell structure shown in Figure 3, with a measured magnetic anisotropy constant of 1.7 × 104 J/m3 (Table 1). When these core-shell nanoparticles were irradiated with an AC magnetic field of frequency  kHz and amplitude  kA/m, the heat dissipation per unit weight reached 3 MW/kg (3 kW/g), which was significantly higher than that using nanoparticles of cobalt ferrite (0.4 MW/kg) or manganese ferrite (0.2 MW/kg). The heat generation of these core-shell nanoparticles is unprecedented so they have received widespread attention.

SampleSize (nm) (kA/m) (kJ/m3) (MW/kg)


This example suggests optimized design of nanoparticle synthesis has succeeded in producing nanoparticles that generate large amounts of heat. However, further consideration revealed two notable points. First, the actual amplitude of reached 37.3 kA/m or 80% that of the anisotropic magnetic field,  kA/m. This is large enough for the energy barrier to magnetization reversal to disappear because of the Zeeman energy in cases where the direction of the AC magnetic field is not completely parallel to the easy axis of nanoparticles. Thus, these conditions do not permit the application of the guiding principles given in (2)–(5) because these assume a linear response for superparamagnetic nanoparticles in zero magnetic field limit. This raises the question of whether irradiation with an AC magnetic field with of 500 kHz and of 37.3 kA/m for core-shell structured nanoparticles with of 15 nm and of 1.7 × 104 J/m3 are really the optimum conditions. However, it is difficult to apply the other guiding principle to maximize hysteresis loss of ferromagnetic nanoparticles because thermally assisted reversals of occur stochastically before the barrier disappears at . Recalling that the characteristic time of thermal fluctuation was estimated to be a few hundred nanoseconds even in a zero magnetic field, the conditions used by Lee et al. are outside the scope of applicability of conventional models for ferromagnetic nanoparticles at a temperature of absolute zero and for superparamagnetic nanoparticles in a zero magnetic field. Consequently, new guiding principles to maximize heat dissipation are required. The second point is that  kA/m is much larger than the exposure restriction for this waveband [52]. This point is examined further in Section 5. The next section will present results of recent numerical studies on the behavior of nanoparticles under conditions outside the scope of applicability of conventional models. This knowledge will be useful to establish sophisticated guiding principles that are adapted to advanced technologies that control the size, shape, and composite structure of nanoparticles.

4. Recent Numerical Simulations for Novel Responses to AC Magnetic Fields

To further improve the guiding principles for the design of magnetic nanoparticles, we must clarify the behavior of nanoparticles under conditions outside the scope of applicability of conventional models. However, it is difficult to discuss nonlinear nonequilibrium responses algebraically; as an alternative, numerical simulation has been performed extensively because of recent advances in computing speed. Noteworthy results obtained from these studies will be introduced in this section. To fully discuss their features from the viewpoint of efficiency, the results are shown as the ratio of the simulated value of to the theoretical upper limit of  : , where is expressed as for irradiating AC magnetic field , because the loss dissipated in one cycle is the area of the hysteresis loop.

In most of the simulations, it was assumed that magnetic nanoparticles were individually delivered to tumor tissues and accumulate randomly inside them, apart from the present status of this treatment [53]. Because the actual concentration of nanoparticles in tumors does not exceed 10 kg/m3 (10 mg/cm3) as stated above, effects caused by dipole-dipole interactions between the accumulated nanoparticles were considered insignificant at room temperature. For example, at the mean distance is estimated to be 25 K for magnetite nanoparticles with  nm,  kA/m, and  kg/m3. Thus, the nanoparticles in this hyperthermia treatment simulation were considered magnetically isolated from each other.

4.1. Néel Relaxation in Magnetic Fields

In a magnetically isolated nanoparticle, the potential energy, , with respect to the direction of is simply given by the sum of magnetic anisotropy energy and Zeeman energy. As a first approximation, uniaxial magnetic anisotropy has usually been assumed for the former term, although it contains contributions from various kinds of magnetic anisotropy such as shape, crystalline, and surface anisotropy. In this case, can be expressed as where is the angle between the easy axis and , and is the angle between and . The detailed trajectories of in this potential can be precisely simulated by solving the stochastic Landau-Lifshitz-Gilbert equations [5357]. However, we are only interested in the reversal of once every microsecond because the frequency used for hyperthermia treatment is limited. Carrey et al. calculated the behavior of using a well-known coarse-grained approach or “two-level approximation” [58, 59], which considers thermally activated reversals between the metastable directions via the midway saddle point in the energy barrier. In this calculation, easy axes of the accumulated nanoparticles were assumed to be fixed. This assumption seems valid when the nanoparticles are strongly anchored to structures resembling organelles.

Figures 4(a), 5(a), and 6(a) show contour plots of calculated for cobalt ferrite, manganese ferrite and their core-shell nanoparticles introduced above, respectively, where the time evolution of the occupation probabilities of the directions parallel to the randomly oriented easy axes are simulated in the same way as Carrey et al. using the parameters given in Table 1. At low of 1 kA/m, of the core-shell nanoparticles increases with , and a single maximum is found at a peak frequency, , of 110 kHz (Figure 6(a)). This behavior is consistent with the above prediction that is maximized when is adjusted to the Néel relaxation time. It is notable that shifts to higher frequency as increases. This acceleration of Néel relaxation can be attributed to lowering of the energy barrier by the Zeeman energy. As indicated by the dashed line in Figure 6(a), the shift of can be explained by calculated using the conventional Brown’s equation as follows [60]: where is . In Figure 6(a), at  kA/m, a typical for hyperthermia treatment, is about 40 times faster than that in a zero magnetic field. This fact clearly indicates that maximum heat dissipation cannot be obtained if we prepare nanoparticles according to the conventional guiding principles expressed in (1)–(5). This problem becomes serious when monodisperse nanoparticles are synthesized, although we barely noticed the problem because we used polydisperse nanoparticles with a broad distribution of .

It is very important that these calculated results are compared with experimental data, even under only one set of conditions with  kHz and  kA/m. In Figure 6(a), 40% of , that is 1.4 MW/kg, is expected for the core-shell nanoparticles at  kHz and  kA/m (diamonds), whereas a larger value of 3.0 MW/kg was actually observed. In Figure 4(a), almost zero dissipation was calculated for the cobalt ferrite nanoparticles under the same conditions, because these nanoparticles are ferromagnetic, so no hysteresis loss is dissipated when  kA/m because it is sufficiently lower than  kA/m. In contrast, considerable dissipation of 0.4 MW/kg was experimentally reported for the cobalt ferrite nanoparticles. In Figure 5(a), a small amount of dissipation is expected for the manganese ferrite nanoparticles under the same conditions, because these nanoparticles are typically superparamagnetic and little relaxation loss dissipates at  kHz that is sufficiently lower than of several tens of megahertz. However, a considerable dissipation of 0.2 MW/kg was experimentally reported for the manganese ferrite nanoparticles. Some of these inconsistencies may be attributed to the fact that the magnetic nanoparticles were easily rotatable in a low viscous liquid of toluene. Hence, Brownian rotations would be described next.

4.2. Brownian Relaxation in Magnetic Fields

In this subsection, ferromagnetic nanoparticles in Newtonian fluids are considered because toluene is a typical Newtonian fluid ( mPa·s), although the actual microviscoelasticity of the local environment in cancer cells is still unknown. In this case, the inertia of nanoparticles with a typical size of 10 nm can be neglected in considering their rotation by Brownian dynamics simulation [61, 62]. In the inertia-less limit, frictional torque for the rotation of a sphere balances with magnetic torque × and Brownian torque as follows: where is the angular velocity of rotation for the unit vector along the easy axis given by = × , and is the Dirac delta function. Yoshida and Enpuku [63] simulated the rotation of ferromagnetic nanoparticles using the Fokker-Planck equation equivalent to the above relationships; they assumed that was permanently fixed at the direction parallel to as long as . As a result, they confirmed that, at zero magnetic field limit, the frequency-dependence of heat dissipation exhibits a single maximum at , as predicted by (2)–(5). They also found that increases with according to the equation: This equation indicates that the driving force of the rotation changes from Brownian random torque to magnetic torque as increases.

As an example, this equation is applied to the cobalt ferrite nanoparticles discussed above. The solid curve in Figure 4(b) shows the values of calculated using (11) with the parameters in Table 1. The obtained line is close to the position of the diamond located at  kHz and  kA/m. In other words, the magnetic torque from the magnetic field at 37.3 kA/m happened to satisfy the conditions of rotating the cobalt ferrite nanoparticles with an appropriate delay to the alternation at 500 kHz; consequently, a considerable amount of heat, 3.7 MW/kg, dissipates. Apart from the magnitude, this is the reason why  MW/kg was experimentally observed for the cobalt ferrite nanoparticles, despite the conventional prediction of no hysteresis loss under the experimental conditions. As exemplified here, delayed rotations are caused by magnetic torque (not Brownian torque) even at much lower than , resulting in significant heat dissipation.

Researchers are also interested in the magnetic response when becomes comparable to . In this case, the above-mentioned assumption that is permanently fixed at the direction parallel to is invalid, because is canted from the easy axis by the Zeeman energy. Furthermore, stochastically reverses by thermal fluctuations even in ferromagnetic nanoparticles, because the Zeeman energy lowers the barrier height sufficiently. Therefore, I simultaneously computed the rotations of the nanoparticles using (8)–(10) with the thermally activated reversals of on the potential given by (6) [64]. Note that (8) is valid within the two-level approximation [65]. The results calculated for these cobalt ferrite nanoparticles are shown as the contour lines (and color difference) in Figure 4(b). Firstly, we are certain that, at  kA/m, the location of the ridge in the contour plot of is consistent with the solid line given by (11). This result indicates that ferromagnetic nanoparticles are rotated by the magnetic torque before the reversal of occurs within it. However, the ridge seems turn to the position extrapolated from the dashed curve given by (7) when becomes comparable to . In other words, is promptly reversed before the rotation because the Néel relaxation is accelerated enough in this range. These relationships can be written as This equation is an extended relationship of ((3)) for a large AC magnetic field. It is noteworthy that the first term usually becomes extremely small for ferromagnetic nanoparticles at in an aligned case or at in tilted cases, while the second term is approximately expressed as when . Therefore, the changeover from rotation to reversal occurs at or for aligned and tilted cases, respectively. For example, this changeover frequency corresponds to 4 MHz for the aligned cobalt ferrite nanoparticles with  nm,  kJ/m3, and  mPa·s. Importantly, the changeover frequency is independent of the size of nanoparticles as long as the ratio is constant. In other words, rotations predominate over the magnetic response at 1 MHz even for much larger cobalt ferrite nanoparticles ( nm,  Hz). We must keep in mind that, even when ferromagnetic nanoparticles are large enough for their Brownian relaxation to be negligible, magnetic torque can easily rotate such nanoparticles at a time scale of microseconds if they are in a liquid phase. This knowledge is helpful when considering the optimal frequency for hyperthermia treatment, even if it is for a simplified system.

4.3. Easy Axes Oriented to the Directions Parallel, Perpendicular, or Oblique to the AC Field

As described above, the fast reversals of are predominant in the magnetic response of ferromagnetic nanoparticles at frequencies higher than the changeover frequency. The simulations, however, revealed that, at the frequencies, the rotation induces various kinds of stationary orientations of the easy axes , which critically affect the reversals [64, 66]. In this section, we also examine the results determined for cobalt ferrite nanoparticles with  nm,  kJ/m3, and  mPa·s. In the initial state before irradiation with the AC magnetic field, the easy axes are set to be randomly oriented in the fluid, as shown in Figure 7(a). Therefore, in the first cycle, the major hysteresis loop obtained at  kA/m is consistent with the magnetization curve predicted by the Stoner-Wohlfarth model (see the inset). If the irradiation of the AC magnetic field at  kA/m is continued in the simulation, the easy axes gradually turn toward the direction parallel to . Note that, in the case where the easy axis is not parallel to , the direction of is not completely parallel to even though is already reversed at . Therefore, a large magnetic torque proportional to sin can turn the easy axis even if the magnetization seems almost saturated at . For example, sin is 0.43 when cos is 0.9. Consequently, a longitudinally oriented structure of the easy axes is formed in the fluid (see Figure 7(d)). The formation of this nonequilibrium structure makes the dynamic hysteresis loop squarer than the initial curve, as shown in the inset of upper panel of Figure 7(d).

In contrast, the magnetization curve at  kA/m is a minor hysteresis loop, as shown in Figure 7(b). In this case, the easy axis turns toward the direction perpendicular to and they maintain planar orientations if the ferromagnetic nanoparticles are continuously irradiated by an AC magnetic field at  kA/m. A question now arises because we know that the longitudinal orientation is preferred when the Zeeman energy is considered. To clarify the reason for this, we consider an initial state in which a nanoparticle with an easy axis at angle has a magnetic moment at a parallel direction . When a small magnetic field is applied to the nanoparticle, immediately tilts to without reversals (see Figure 7(e)), because the position of the local minimum on is changed. Then, the magnetic torque, , rotates toward the longitudinal direction: . Because drags the easy axis, also decreases. In other words, the easy axis turns toward the direction parallel to . If is reversed subsequently, the direction of at this moment is almost antiparallel to at . Then instantly changes to because of the effect of variation of the minimum on (see Figure 7(e)). The magnetic torque at this stage, , forces to rotate toward the direction via . Because is bound on the easy axis, also increases. In other words, the easy axis starts to turn toward the plane perpendicular to . If the direction of alternates at a high frequency, a planar orientation of the easy axis is formed on average, because is larger than . This reduces the remanence of the hysteresis loop. In contrast, a longitudinal orientation is formed in a large AC magnetic field as discussed above, because is always reversed to the direction parallel to immediately after is reversed. Overall, decreases toward 0 when the reversal of occurs with alternation of the direction of , whereas increases toward without reversal of .

This feature leads to formation of novel nonequilibrium structures such as the obliquely oriented state found at an intermediate amplitude of  kA/m. Without considering thermal fluctuations, the reversals should occur in the range of from to for Stoner-Wohlfarth nanoparticles with  kA/m, while never reverses in the other ranges. If this feature simply applies, should decrease with time in the range between and , whereas it should increase both between 0 and and between and . These variations certainly lead to formation of a bimodal with double maxima at and , as found in Figure 7(c). Consequently, the easy axes are oriented in both the planes perpendicular and oblique to the magnetic field.

Concisely, in ferromagnetic nanoparticles in toluene or an aqueous phase, longitudinal, conical, or planar orientations are formed, irrespective of the free energy, as nonequilibrium structures under a high-frequency AC magnetic field. As a result, the major hysteresis loop becomes squarer and the minor loop becomes narrower compared with the magnetization curve calculated for randomly oriented nanoparticles. These variations of the area of the loops cause the maximum of to shift towards higher from the optimal conditions predicted by the conventional models in Section 2. This kind of averaging of the oscillating rotations, discussed using the cobalt ferrite nanoparticles as an example, should always occur as long as the alternation of the magnetic field is much more frequent than the characteristic time of rotation, . For this reason, these nonequilibrium structures would form in the radio-waveband used for hyperthermia treatment if the amplitude is somewhat smaller (~10 kA/m) or the viscosity is considerably higher (~10 mPa·s). Therefore, we must keep in mind the important effects of nonequilibrium structures on heat dissipation when establishing the optimal design of ferromagnetic nanoparticles for hyperthermia treatment.

4.4. Magnetic Hysteresis of Superparamagnetic States

Let us leave ferromagnetic nanoparticles and move on to superparamagnetic manganese ferrite nanoparticles, from which a considerable amount of heat dissipation, 0.2 MW/kg, was experimentally reported at  kHz. The orientation of on these nanoparticles is easily equilibrated in the magnetic potential expressed in (6) within the scale of the Néel relaxation time of 1 × 10−8 s. Therefore, little relaxation loss is expected using the conventional model. For this reason, I wish to examine this inconsistency from the viewpoint of the effects of slow rotations on the fast reversals in superparamagnetic nanoparticles.

The contour lines (and color difference) in Figure 5(b) show the results obtained from the simultaneous simulation of rotations and reversals for the manganese ferrite nanoparticles. Firstly, we find a secondary maximum of around  kHz in addition to the primary ridge of indicated by the dashed curve at frequencies of several tens of megahertz, which is explained by (7) for ) above. To clarify the origin of the new kind of heat dissipation, the magnetization curve calculated under the conditions of  kA/m and  kHz is presented in Figure 8(a). An S-shaped hysteresis loop without remanence is observed. In this cycle, the directions of the easy axes have butterfly-shaped hysteresis, as shown in Figure 8(b). This behavior is explained by the following atypical magnetic response in the period (10 μs). Initially (at ), no magnetization exists because the occupation probabilities of in the two stable directions parallel to the easy axis are equalized in a zero magnetic field. As increases, the occupation probability in the more stabilized direction immediately increases because of reversals on a time scale of (≤10 ns). The reversed in the stabilized direction is not completely parallel to , , and the magnetic torque turns the easy axis towards the direction of the field. The time constant of this process is approximately expressed as using the second term in (11). For the manganese ferrite nanoparticles, it is 3 μs when is 4 kA/m. Therefore, rotation is not negligible in the peak period of the oscillations of . Subsequently, decreases to zero at μs, and the occupation probabilities are again equalized because reversal is rapid, so the magnetic torque disappears. Alternatively, the Brownian torque randomizes the orientation of the easy axis on a time scale of (= 2 μs). Therefore, competition between the magnetic and Brownian torques can cause the butterfly-shaped hysteresis of . Because the equilibrium magnetization of the superparamagnetic nanoparticles with easy axes parallel to is higher than that of randomly oriented ones [58, 67], the magnetization curve shows hysteresis without remanence. Consequently, a secondary maximum appears even though if the nanoparticles are rotatable. As discussed here, we should remove the stereotype of a single peak at a value of .

Needless to say, there is still room for further study. For example, simulated at  kHz and = 37.3 kA/m is 0.13 MW/kg, which is inconsistent with the observed of 0.2 MW/kg. At present, it is unclear whether the difference can be attributed to the nontrivial polydisperse nature of the prepared sample or the accuracy of the simulations, because the experiment was performed under only one set of conditions with  kHz and  kA/m. Thus, measurement of under various conditions will be helpful to establish a model of heat dissipation in superparamagnetic nanoparticles. In addition, it is certain that the protocols of these simulations are also improvable, because it has been assumed that the direction of is fixed at one of the local minima in the energy potential given by (6), although we know stochastically explores all over the potential well [65]. Briefly, the magnetic torque is overestimated. Recently, more strict calculations were carried out and they also show the same kind of butterfly-shaped hysteresis [67]. As described here, much still remains to be done.

4.5. Intermediate State between Ferromagnetic and Superparamagnetic Nanoparticles

Core-shell nanoparticles, which can generate the largest amount of heat out of various nanoparticle structures, fit neither ferromagnetic nor superparamagnetic conditions. This is because the value of the Néel relaxation time calculated using the parameters in Table 1 is 1 μs, which is comparable with the alternation time of the AC magnetic field used in hyperthermia treatment. Furthermore, the Brownian relaxation time is also estimated to be 1 μs. Therefore, it is worth discussing this intermediate case before concluding this section. Figure 6(b) shows the results obtained by simultaneous simulation of rotation and reversal as contour lines (and color difference). In this figure, we are certain that location of the ridge in the contour plot of is consistent with neither the dashed curve (7) nor the solid curve (11), but instead with the dashed-dotted curve given by (12). Furthermore, the iso-height contour lines, for example, the boundary between yellow and light green, shift toward lower frequency compared with the randomly fixed case in Figure 6(a). Figure 9 shows the magnetization curve and variation of the directions of the easy axes calculated for the core-shell nanoparticles under the conditions of  kA/m and  kHz. We observe eyeglass-shaped hysteresis in the variation of the directions of the easy axes. This behavior is attributed to complicated competition between normal rotations when is parallel to , counter-rotations when is antiparallel to , and randomization at . The major point is that the first term seems to dominate the other terms, because the baseline of the eyeglass-shaped oscillations of the easy axes is considerably higher than the 0.5 expected for randomly oriented nanoparticles. This longitudinal orientation makes the dynamic hysteresis loop squarer and leads to an increase in (see Figure 9(a)). In addition to this effect, on average, oscillation of the directions of the easy axes induced by the alternation of the counter-rotations and randomization further increases . Indeed, we can observe that the hysteresis loop of the rotatable nanoparticles in Figure 9(a) opens even in the higher magnetic field where the loop of the non-rotatable nanoparticles in Figure 9(a) is closed after all are reversed. Overall, both the phenomena discussed for ferromagnetic and superparamagnetic nanoparticles contribute to amplification of the hysteresis loop area in this intermediate state; as a result, increases from 1.4 MW/kg for the non-rotatable case to 2.4 MW/kg for the rotatable one. We can say that this value is fairly consistent with the observed of 3 MW/kg in consideration that the simulation was carried out for completely isolated monodisperse nanoparticles with uniform uniaxial anisotropy.

5. Optimized Design and Future Outlook

Magnetic nanoparticles for thermotherapy, particularly rotatable nanoparticles, have been predicted to exhibit various novel responses to AC magnetic fields, as described above. Examples include magnetic hysteresis observed for superparamagnetic states and nonequilibrium structures with easy axes oriented to the directions parallel, perpendicular, or oblique to the magnetic field. These nonlinear and nonequilibrium phenomena cannot be explained using conventional models. Further systematic simulations and their experimental verification are required to establish sophisticated guiding principles for such magnetic nanoparticles. However, some feel that the heat generation of 3 MW/kg achieved by Lee et al. is sufficient for practical use in hyperthermia treatment, so more sophisticated guidelines may not be necessary. In this final section, we discuss this issue.

Tumors less than 0.01 m (= 1 cm) in size are considered difficult to find with existing diagnostic methods, so here we examine whether or not the heat dissipation from current magnetic nanoparticles is enough to treat hidden tumors of such size. According to Andrä et al. [68], raising the temperature of a tumor by requires heat generation of approximately without considering blood flow, where is thermal conductivity and is the diameter of a tumor. If we assume  WK−1 m−1, , and or 0.01 m, the required heat generation would be 1.5 or 0.4 MW/m3, respectively. The rate of blood flow in tumor tissues is typically 1% per second by volume (60 mL/min/100 g) [69]; thus, when , the heat transport caused by blood flow is estimated to be 0.2 MW/m3 using a value of ~4 MJ-m−3 K−1 for the specific heat of blood. Therefore, the total cooling power of hidden tumors is between 0.6 and 2 MW/m3 for . This assessment indicates that the amount of heat dissipation required to kill metastatic cancer cells is estimated to be within 0.3 and 1 MW/kg if we can expect a nanoparticle concentration within tumors of approximately 2 kg/m3. The developed core-shell magnetic nanoparticles thus clearly enable adequate heat dissipation. However, are they actually suitable for use in hyperthermia treatment?

Note that Section 4 described how nanoparticles with of 3 MW/kg was obtained from irradiation using an AC magnetic field of  kA/m and  kHz. When this AC magnetic field is irradiated on a simple model body composed of a homogenous column with electrical conductivity  Sm−1 and radius  m, the maximum voltage generated on the outer circumference is = 4,600 V per revolution, at which point the eddy current loss is 5 MW/m3 (5 W/cm3). This heat generation is sufficient to raise the temperature of thermally insulated tissues by 10 K or more in 10 seconds. For this reason, we cannot ignore the side effects of on normal tissues, although the model assuming a constant is oversimplified. According to guidelines published by the International Commission on Non-Ionizing Radiation Protection [52], the upper limit for work-related exposure of the torso is 10 W/kg (corresponding to 0.01 MW/m3). However, because this value is the upper limit for routine exposure, it may not be indicative of the maximum exposure in medical treatment. A slightly more specific value can be calculated as follows. Heat generation only occurs in the outer edge of a human body if a magnetic field is irradiated over the whole body; therefore, the heated region can be considered as a cylinder that is a few centimeters thick. This region can be cooled from the body surface area in medical treatment. Its cooling power, , is roughly estimated to be 0.03 MW/m3 under the conditions of  K and  m. Because blood vessels expand when temperature rises, blood flow increases even in tissues with little blood flow normally. In subcutaneous tissues, for example, a blood flow rate of approximately 0.2% per second by volume (12 mL/min/100 g) has been reported at 42°C [69, 70]. Under these conditions, calculating the heat transport caused by blood flow using the same method yields a value of 0.03 MW/m3 when the temperature difference from the outside of the irradiated region is set at  K. These values are the result of rough calculations that do not consider the detailed structure of a human body [71], but their sum, which is about 0.06 MW/m3, can be used as an approximation of cooling ability. When a magnetic field is applied to the model body mentioned above, this value corresponds to for the condition = 2 × 109 Am−1 s−1. Calculating the behavior of the above-mentioned core-shell nanoparticles ( nm) within this restriction (see Figure 10) shows that does not reach the requirement of 0.3 MW/kg. However, Figure 10 indicates that if the size of the particle is increased slightly, sufficient can be obtained from the rotatable nanoparticles at higher (equivalent to lower ) even under this restriction, and adequate heating is expected inside hidden tumors with a diameter of 0.01 m without serious side effects on normal tissues from .

Our discussion up to this point applies to treatment using continuous irradiation where heat balance holds. Irradiation time and interval can be controlled in medical treatment. For example, when tumors with a specific heat of 4 MJm−3 K−1 containing the above-mentioned core-shell nanoparticles with a concentration of 2 kg/m3 were irradiated with an AC magnetic field of = 37.3 kA/m and  kHz, heat of approximately = 6 MW/m3 was generated. Relative to this value, the quantity of heat diffused to the surrounding areas from 10 mm tumors is negligible when  K; thus, the temperature will rise by 5 K after approximately 3 seconds. Because the eddy current loss in this case is 5 MW/m3, it will take approximately 4 seconds for the temperature of normal tissue to rise by 5 K. Stopping irradiation after 3 seconds will thus enable selective heating of tumors by 5 K or more. This is an extreme example; however, it does indicate that there is another option apart from continuous irradiation. The ratio of to is important. Although obtaining robust values requires detailed protocol, a factor of 4-5 or so might be a criterion for . As an example, we calculated for the core-shell nanoparticles and found that this condition is satisfied for lower frequencies/smaller amplitudes than those indicated by the solid line in Figure 11 [72]. This finding reflects the fact that is the area of the curve × frequency, which is proportional to at most, whereas increases in proportion to , as previously described. Because it is impossible to attain a rise in temperature of 5 K if is at least 0.6 (or 2) MW/m3, irradiation must therefore be conducted using a higher frequency and larger amplitude to ensure that this condition is met (see dashed lines in Figure 12 [72]). Ultimately, stronger, faster conditions are needed to destroy cancer cells, and weaker, slower conditions are needed to limit damage to normal tissue. Using the core-shell nanoparticles of  nm, a frequency of  kHz is thus acceptable, but needs to be maintained at 9  kA/m to resolve the conflicting requirements.

As discussed above, the combination of the core-shell nanoparticles of  nm and  J/m3 with an AC magnetic field of  kHz and  kA/m may not be optimal. A narrow range of combinations of these parameters will facilitate efficient hyperthermia treatment and prevent side effects. We have not yet optimized the conditions for hyperthermia treatment; however, establishing the optimal combinations may be difficult, particularly if a trial and error approach is used. The routes used to synthesize magnetic nanoparticles of controlled size, shape, and composite structure have become increasingly advanced, as described in this paper. Dramatic advances in computing speed have also promoted numerical simulation of nonlinear nonequilibrium responses to AC magnetic fields. If we continue to improve material design on the bases of such advanced nanotechnology and computer simulations, optimal conditions will eventually be clarified. Remarkable advances are still continually being reported in clinical trials are being conducted, even though the combination of nanoparticles and oscillation of the equipment has not been optimized yet [73, 74]. Once optimization improves local heating ability, then thermotherapy should be established as a fourth or fifth standard cancer treatment method to reduce the disease burden of a patient.


This work was partly supported by a Grant-in-Aid for Scientific Research (No. 24310071).


  1. W. C. Dewey, L. E. Hopwood, S. A. Sapareto, and L. E. Gerweck, “Cellular responses to combinations of hyperthermia and radiation,” Radiology, vol. 123, no. 2, pp. 463–474, 1977. View at: Google Scholar
  2. S. Mornet, S. Vasseur, F. Grasset, and E. Duguet, “Magnetic nanoparticle design for medical diagnosis and therapy,” Journal of Materials Chemistry, vol. 14, no. 14, pp. 2161–2175, 2004. View at: Publisher Site | Google Scholar
  3. P. Tartaj, M. Del Puerto Morales, S. Veintemillas-Verdaguer, T. González-Carreño, and C. J. Serna, “The preparation of magnetic nanoparticles for applications in biomedicine,” Journal of Physics D, vol. 36, no. 13, pp. R182–R197, 2003. View at: Publisher Site | Google Scholar
  4. T. Neuberger, B. Schöpf, H. Hofmann, M. Hofmann, and B. von Rechenberg, “Superparamagnetic nanoparticles for biomedical applications: possibilities and limitations of a new drug delivery system,” Journal of Magnetism and Magnetic Materials, vol. 293, no. 1, pp. 483–496, 2005. View at: Publisher Site | Google Scholar
  5. Q. A. Pankhurst, N. K. T. Thanh, S. K. Jones, and J. Dobson, “Progress in applications of magnetic nanoparticles in biomedicine,” Journal of Physics D, vol. 42, no. 22, Article ID 224001, 2009. View at: Publisher Site | Google Scholar
  6. K. M. Krishnan, “Biomedical nanomagnetics: a spin through possibilities in imaging, diagnostics, and therapy,” IEEE Transactions on Magnetics, vol. 46, no. 7, pp. 2523–2558, 2010. View at: Publisher Site | Google Scholar
  7. B. Jeyadevan, “Present status and prospects of magnetite nanoparticles-based hyperthermia,” Journal of the Ceramic Society of Japan, vol. 118, no. 1378, pp. 391–401, 2010. View at: Google Scholar
  8. I. Sharifi, H. Shokrollahi, and S. Amiri, “Ferrite-based magnetic nanofluids used in hyperthermia applications,” Journal of Magnetism and Magnetic Materials, vol. 324, no. 6, pp. 903–915, 2012. View at: Publisher Site | Google Scholar
  9. S. J. DeNardo, G. L. DeNardo, A. Natarajan et al., “Thermal dosimetry predictive of efficacy of111In-ChL6 nanoparticle AMF-induced thermoablative therapy for human breast cancer in mice,” Journal of Nuclear Medicine, vol. 48, no. 3, pp. 437–444, 2007. View at: Google Scholar
  10. P. Wust, U. Gneveckow, M. Johannsen et al., “Magnetic nanoparticles for interstitial thermotherapy—feasibility, tolerance and achieved temperatures,” International Journal of Hyperthermia, vol. 22, no. 8, pp. 673–685, 2006. View at: Publisher Site | Google Scholar
  11. R. Hergt, R. Hiergeist, I. Hilger et al., “Maghemite nanoparticles with very high AC-losses for application in RF-magnetic hyperthermia,” Journal of Magnetism and Magnetic Materials, vol. 270, no. 3, pp. 345–357, 2004. View at: Publisher Site | Google Scholar
  12. M. Ma, Y. Wu, J. Zhou, Y. Sun, Y. Zhang, and N. Gu, “Size dependence of specific power absorption of Fe3O4 particles in AC magnetic field,” Journal of Magnetism and Magnetic Materials, vol. 268, no. 1-2, pp. 33–39, 2004. View at: Publisher Site | Google Scholar
  13. T. N. Brusentsova, N. A. Brusentsov, V. D. Kuznetsov, and V. N. Nikiforov, “Synthesis and investigation of magnetic properties of Gd-substituted Mn-Zn ferrite nanoparticles as a potential low-TC agent for magnetic fluid hyperthermia,” Journal of Magnetism and Magnetic Materials, vol. 293, no. 1, pp. 298–302, 2005. View at: Publisher Site | Google Scholar
  14. G. Glöckl, R. Hergt, M. Zeisberger, S. Dutz, S. Nagel, and W. Weitschies, “The effect of field parameters, nanoparticle properties and immobilization on the specific heating power in magnetic particle hyperthermia,” Journal of Physics, vol. 18, no. 38, pp. S2935–S2949, 2006. View at: Publisher Site | Google Scholar
  15. J. P. Fortin, C. Wilhelm, J. Servais, C. Ménager, J.-C. Bacri, and F. Gazeau, “Size-sorted anionic iron oxide nanomagnets as colloidal mediators for magnetic hyperthermia,” Journal of the American Chemical Society, vol. 129, no. 9, pp. 2628–2635, 2007. View at: Publisher Site | Google Scholar
  16. G. Baldi, D. Bonacchi, C. Innocenti, G. Lorenzi, and C. Sangregorio, “Cobalt ferrite nanoparticles: the control of the particle size and surface state and their effects on magnetic properties,” Journal of Magnetism and Magnetic Materials, vol. 311, no. 1, pp. 10–16, 2007. View at: Publisher Site | Google Scholar
  17. L. Y. Zhang, H.-C. Gu, and X.-M. Wang, “Magnetite ferrofluid with high specific absorption rate for application in hyperthermia,” Journal of Magnetism and Magnetic Materials, vol. 311, no. 1, pp. 228–233, 2007. View at: Publisher Site | Google Scholar
  18. D.-H. Kim, D. E. Nikles, D. T. Johnson, and C. S. Brazel, “Heat generation of aqueously dispersed CoFe2O4 nanoparticles as heating agents for magnetically activated drug delivery and hyperthermia,” Journal of Magnetism and Magnetic Materials, vol. 320, no. 19, pp. 2390–2396, 2008. View at: Publisher Site | Google Scholar
  19. J.-P. Fortin, F. Gazeau, and C. Wilhelm, “Intracellular heating of living cells through Néel relaxation of magnetic nanoparticles,” European Biophysics Journal, vol. 37, no. 2, pp. 223–228, 2008. View at: Publisher Site | Google Scholar
  20. L.-M. Lacroix, R. B. Malaki, J. Carrey et al., “Magnetic hyperthermia in single-domain monodisperse FeCo nanoparticles: evidences for Stoner-Wohlfarth behavior and large losses,” Journal of Applied Physics, vol. 105, no. 2, Article ID 023911, 4 pages, 2009. View at: Publisher Site | Google Scholar
  21. C. L. Dennis, A. J. Jackson, J. A. Borchers et al., “Nearly complete regression of tumors via collective behavior of magnetic nanoparticles in hyperthermia,” Nanotechnology, vol. 20, no. 39, Article ID 395103, 2009. View at: Publisher Site | Google Scholar
  22. M. Gonzales-Weimuller, M. Zeisberger, and K. M. Krishnan, “Size-dependant heating rates of iron oxide nanoparticles for magnetic fluid hyperthermia,” Journal of Magnetism and Magnetic Materials, vol. 321, no. 13, pp. 1947–1950, 2009. View at: Publisher Site | Google Scholar
  23. R. Sharma and C. J. Chen, “Newer nanoparticles in hyperthermia treatment and thermometry,” Journal of Nanoparticle Research, vol. 11, no. 3, pp. 671–689, 2009. View at: Publisher Site | Google Scholar
  24. E. Kita, T. Oda, T. Kayano et al., “Ferromagnetic nanoparticles for magnetic hyperthermia and thermoablation therapy,” Journal of Physics D, vol. 43, no. 47, Article ID 474011, 2010. View at: Publisher Site | Google Scholar
  25. B. Mehdaoui, A. Meffre, L.-M. Lacroix et al., “Large specific absorption rates in the magnetic hyperthermia properties of metallic iron nanocubes,” Journal of Magnetism and Magnetic Materials, vol. 322, no. 19, pp. L49–L52, 2010. View at: Publisher Site | Google Scholar
  26. T. Kikuchi, R. Kasuya, S. Endo et al., “Preparation of magnetite aqueous dispersion for magnetic fluid hyperthermia,” Journal of Magnetism and Magnetic Materials, vol. 323, no. 10, pp. 1216–1222, 2011. View at: Publisher Site | Google Scholar
  27. J.-H. Lee, J.-T. Jang, J.-S. Choi et al., “Exchange-coupled magnetic nanoparticles for efficient heat induction,” Nature Nanotechnology, vol. 6, no. 7, pp. 418–422, 2011. View at: Publisher Site | Google Scholar
  28. S.-H. Noh, W. Na, J. Jang et al., “Nanoscale magnetism control via surface and exchange anisotropy for optimized ferrimagnetic hysteresis,” Nano Letters, vol. 12, no. 7, pp. 3716–3721, 2012. View at: Publisher Site | Google Scholar
  29. K. Nakamura, K. Ueda, A. Tomitaka et al., “Self-heating temperature and AC hysteresis of magnetic iron oxide nanoparticles and their dependence on secondary particle size,” IEEE Transactions on Magnetics, vol. 49, no. 1, pp. 240–243, 2013. View at: Publisher Site | Google Scholar
  30. C. Martinez-Boubeta, K. Simeonidis, A. Makridis et al., “Learning from nature to improve the heat generation of iron-oxide nanoparticles for magnetic hyperthermia applications,” Scientific Reports, vol. 3, article 1652, 2013. View at: Publisher Site | Google Scholar
  31. J. L. Dormann, D. Fiorani, and E. Tronc, “Magnetic relaxation in fine-particle systems,” Advances in Chemical Physics, vol. 98, pp. 283–494, 1997. View at: Google Scholar
  32. X. Batlle and A. Labarta, “Finite-size effects in fine particles: magnetic and transport properties,” Journal of Physics D, vol. 35, no. 6, pp. R15–R42, 2002. View at: Publisher Site | Google Scholar
  33. H. Mamiya, Magnetic Properties of Nanoparticles, Yushodo, Tokyo, Japan, 2003.
  34. P. E. Jönsson, “Superparamagnetism and spin glass dynamics of interacting magnetic nanoparticle systems,” Advances in Chemical Physics, vol. 128, pp. 191–248, 2004. View at: Google Scholar
  35. P. C. Scholten, “How magnetic can a magnetic fluid be?” Journal of Magnetism and Magnetic Materials, vol. 39, no. 1-2, pp. 99–106, 1983. View at: Publisher Site | Google Scholar
  36. H. Mamiya, I. Nakatani, and T. Furubayashi, “Blocking and freezing of magnetic moments for iron nitride fine particle systems,” Physical Review Letters, vol. 80, no. 1, pp. 177–180, 1998. View at: Google Scholar
  37. H. Mamiya, I. Nakatani, and T. Furubayashi, “Slow dynamics for spin-glass-like phase of a ferromagnetic fine particle system,” Physical Review Letters, vol. 82, no. 21, pp. 4332–4335, 1999. View at: Google Scholar
  38. H. Mamiya, I. Nakatani, and T. Furubayashi, “Phase transitions of iron-nitride magnetic fluids,” Physical Review Letters, vol. 84, no. 26, pp. 6106–6109, 2000. View at: Google Scholar
  39. A. Wiedenmann, M. Kammel, A. Heinemann, and U. Keiderling, “Nanostructures and ordering phenomena in ferrofluids investigated using polarized small angle neutron scattering,” Journal of Physics, vol. 18, no. 38, pp. S2713–S2736, 2006. View at: Publisher Site | Google Scholar
  40. H. Kronmüller and M. Fähnle, Micromagnetism and the Microstructure of Ferromagnetic Solids, Cambridge University Press, Cambridge, UK, 2003.
  41. R. Hergt, S. Dutz, and M. Röder, “Effects of size distribution on hysteresis losses of magnetic nanoparticles for hyperthermia,” Journal of Physics, vol. 20, no. 38, Article ID 385214, 2008. View at: Publisher Site | Google Scholar
  42. R. E. Rosensweig, “Heating magnetic fluid with alternating magnetic field,” Journal of Magnetism and Magnetic Materials, vol. 252, pp. 370–374, 2002. View at: Publisher Site | Google Scholar
  43. S. S. Papell, US Patent No. 3, 215, 1965.
  44. T. Sato, S. Higuchi, and J. Shimoiizaka, in Proceedings of the 19th Annual Meeting of the Chemical Society of Japan, 293, 1966.
  45. I. Nakatani, M. Hijikata, and K. Ozawa, “Iron-nitride magnetic fluids prepared by vapor-liquid reaction and their magnetic properties,” Journal of Magnetism and Magnetic Materials, vol. 122, no. 1–3, pp. 10–14, 1993. View at: Google Scholar
  46. S. Sun, C. B. Murray, D. Weller, L. Folks, and A. Moser, “Monodisperse FePt nanoparticles and ferromagnetic FePt nanocrystal superlattices,” Science, vol. 287, no. 5460, pp. 1989–1992, 2000. View at: Publisher Site | Google Scholar
  47. X.-M. Lin and A. C. S. Samia, “Synthesis, assembly and physical properties of magnetic nanoparticles,” Journal of Magnetism and Magnetic Materials, vol. 305, no. 1, pp. 100–109, 2006. View at: Publisher Site | Google Scholar
  48. A. H. Lu, E. L. Salabas, and F. Schüth, “Magnetic nanoparticles: synthesis, protection, functionalization, and application,” Angewandte Chemie, vol. 46, no. 8, pp. 1222–1244, 2007. View at: Publisher Site | Google Scholar
  49. L. Li, Y. Yang, J. Ding, and J. Xue, “Synthesis of magnetite nanooctahedra and their magnetic field-induced two-/three-dimensional superstructure,” Chemistry of Materials, vol. 22, no. 10, pp. 3183–3191, 2010. View at: Publisher Site | Google Scholar
  50. J. L. C. Huaman, S. Fukao, K. Shinoda, and B. Jeyadevan, “Novel standing Ni-Pt alloy nanocubes,” CrystEngComm, vol. 13, no. 10, pp. 3364–3369, 2011. View at: Publisher Site | Google Scholar
  51. Y. Li, Q. Zhang, A. V. Nurmikko, and S. Sun, “Enhanced magnetooptical response in dumbbell-like Ag-CoFe2O4 nanoparticle pairs,” Nano Letters, vol. 5, no. 9, pp. 1689–1692, 2005. View at: Publisher Site | Google Scholar
  52. The International Commission on Non-Ionizing Radiation Protection, “Guide-lines for limiting exposure to time-varying electric, magnetic, and electro-magnetic fields (up to 300 GHz),” Health Physics, vol. 74, no. 4, pp. 494–522, 1998. View at: Google Scholar
  53. E. Lima Jr., E. de Biasi, and M. V. Mansilla, “Heat generation in agglomerated ferrite nanoparticles in an alternating magnetic field,” Journal of Physics D, vol. 46, no. 4, Article ID 045002, 2013. View at: Google Scholar
  54. S. M. Morgan and R. H. Victora, “Use of square waves incident on magnetic nanoparticles to induce magnetic hyperthermia for therapeutic cancer treatment,” Applied Physics Letters, vol. 97, no. 9, Article ID 093705, 2010. View at: Publisher Site | Google Scholar
  55. E. L. Verde, G. T. Landi, and M. S. Carriao, “Field dependent transition to the non-linear regime in magnetic hyperthermia experiments: comparison between maghemite, copper, zinc, nickel and cobalt ferrite nanoparticles of similar sizes,” AIP Advances, vol. 2, no. 3, Article ID 032120, 23 pages, 2012. View at: Google Scholar
  56. G. T. Landi and A. F. Bakuzis, “On the energy conversion efficiency in magnetic hyperthermia applications: a new perspective to analyze the departure from the linear regime,” Journal of Applied Physics, vol. 111, no. 8, Article ID 083915, 2012. View at: Publisher Site | Google Scholar
  57. N. A. Usov, S. A. Gudoshnikov, and O. N. Serebryakova, “Properties of dense assemblies of magnetic nanoparticles promising for application in biomedicine,” Journal of Superconductivity and Novel Magnetism, vol. 26, no. 4, pp. 1079–1083, 2013. View at: Google Scholar
  58. J. Carrey, B. Mehdaoui, and M. Respaud, “Simple models for dynamic hysteresis loop calculations of magnetic single-domain nanoparticles: application to magnetic hyperthermia optimization,” Journal of Applied Physics, vol. 109, no. 8, Article ID 083921, 17 pages, 2011. View at: Publisher Site | Google Scholar
  59. Z. P. Mendoza, G. A. Pasquevich, and S. J. Stewart, “Structural and magnetic study of zinc-doped magnetite nanoparticles and ferrofluids for hyperthermia applications,” Journal of Physics D, vol. 46, no. 12, Article ID 125006, 2013. View at: Google Scholar
  60. W. F. Brown Jr., “Thermal fluctuations of a single-domain particle,” Physical Review, vol. 130, no. 5, pp. 1677–1686, 1963. View at: Publisher Site | Google Scholar
  61. H. Mamiya and B. Jeyadevan, “Optimal design of nanomagnets for targeted hyperthermia,” Journal of Magnetism and Magnetic Materials, vol. 323, no. 10, pp. 1417–1422, 2011. View at: Publisher Site | Google Scholar
  62. D. B. Reeves and J. B. Weaver, “Simulations of magnetic nanoparticle Brownian motion,” Journal of Applied Physics, vol. 112, no. 12, Article ID 124311, 6 pages, 2012. View at: Publisher Site | Google Scholar
  63. T. Yoshida and K. Enpuku, “Simulation and quantitative clarification of AC susceptibility of magnetic fluid in nonlinear Brownian relaxation region,” Japanese Journal of Applied Physics, vol. 48, Article ID 127002, 7 pages, 2009. View at: Publisher Site | Google Scholar
  64. H. Mamiya and B. Jeyadevan, “Hyperthermic effects of dissipative structures of magnetic nanoparticles in large alternating magnetic fields,” Scientific Reports, vol. 1, article 157, 2011. View at: Publisher Site | Google Scholar
  65. N. A. Usov and B. Ya. Liubimov, “Dynamics of magnetic nanoparticle in a viscous liquid: application to magnetic nanoparticle hyperthermia,” Journal of Applied Physics, vol. 112, no. 2, Article ID 023901, 11 pages, 2012. View at: Publisher Site | Google Scholar
  66. H. Mamiya and B. Jeyadevan, “Formation of non-equilibrium magnetic nanoparticle structures in a large alternating magnetic field and their influence on magnetic hyperthermia treatment,” IEEE Transactions on Magnetics, vol. 48, no. 11, pp. 3258–3262, 2012. View at: Publisher Site | Google Scholar
  67. H. Mamiya and B. Jeyadevan, “Magnetic hysteresis loop in a superparamagnetic state,” in press. IEEE Transactions on Magnetics. View at: Google Scholar
  68. W. Andrä, C. G. D'Ambly, R. Hergt, I. Hilger, and W. A. Kaiser, “Temperature distribution as function of time around a small spherical heat source of local magnetic hyperthermia,” Journal of Magnetism and Magnetic Materials, vol. 194, no. 1, pp. 197–203, 1999. View at: Publisher Site | Google Scholar
  69. C. W. Song, “Effect of local hyperthermia on blood flow and microenvironment: a review,” Cancer Research, vol. 44, no. 10, supplement, pp. 4721s–4730s, 1984. View at: Google Scholar
  70. T. Hasegawa, R. Kudaka, K. Saito et al., Bulletin of Suzuka University of Medical Science, vol. 11, pp. 58–64, 2004.
  71. J. Bohnert and O. Dössel, “Simulations of temperature increase due to time varying magnetic fields up to 100 kHz,” in Proceedings of the 5th European Conference of the International Federation for Medical and Biological Engineering, vol. 37 of IFMBE Proceedings, pp. 303–306, 2012. View at: Google Scholar
  72. H. Mamiya, “Magnetic response of nanoparticles to AC magnetic fields and targeted thermotherapy,” Materials Integration, vol. 25, pp. 11–23, 2012. View at: Google Scholar
  73. T. Kobayashi, “Cancer hyperthermia using magnetic nanoparticles,” Biotechnology Journal, vol. 6, no. 11, pp. 1342–1347, 2011. View at: Publisher Site | Google Scholar
  74. B. Thiesen and A. Jordan, “Clinical applications of magnetic nanoparticles for hyperthermia,” International Journal of Hyperthermia, vol. 24, no. 6, pp. 467–474, 2008. View at: Publisher Site | Google Scholar

Copyright © 2013 Hiroaki Mamiya. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

More related articles

 PDF Download Citation Citation
 Download other formatsMore
 Order printed copiesOrder

Related articles