Journal of Nanomaterials

Volume 2017 (2017), Article ID 1047697, 7 pages

https://doi.org/10.1155/2017/1047697

## Practical Solution for Effective Whole-Body Magnetic Fluid Hyperthermia Treatment

^{1}National Institute for Materials Science, Sengen 1-2-1, Tsukuba 305-0047, Japan^{2}University of Tsukuba, 1-1-1 Tennodai, Tsukuba, Ibaraki 305-8577, Japan^{3}The University of Shiga Prefecture, Hikone 522-8533, Japan

Correspondence should be addressed to Hiroaki Mamiya

Received 21 June 2017; Accepted 20 November 2017; Published 13 December 2017

Academic Editor: Mohammad Mansoob Khan

Copyright © 2017 Hiroaki Mamiya et al. 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.

#### Abstract

Magnetic fluid hyperthermia therapy is considered as a promising treatment for cancers including unidentifiable metastatic cancers that are scattered across the whole body. However, a recent study on heat transfer simulated on a human body model showed a serious side effect: occurrences of hot spots in normal tissues due to eddy current loss induced by variation in the irradiated magnetic field. The indicated allowable upper limit of field amplitude for constant irradiation over the entire human body corresponded to approximately 100 Oe at a frequency of 25 kHz. The limit corresponds to the value of 2.5 × 10^{6} Oe·s^{−1} and is significantly lower than the conventionally accepted criteria of 6 × 10^{7} Oe·s^{−1}. The present study involved evaluating maximum performance of conventional magnetic fluid hyperthermia cancer therapy below the afore-mentioned limit, and this was followed by discussing alternative methods not bound by standard frameworks by considering steady heat flow from equilibrium responses of stable nanoparticles. Consequently, the clarified potentials of quasi-stable core-shell nanoparticles, dynamic alignment of easy axes, and short pulse irradiation indicate that the whole-body magnetic fluid hyperthermia treatment is still a possible candidate for future cancer therapy.

#### 1. Introduction

In principle, “if a steel pan made for induction heating (IH) cooking appliances is diced up into ultra-small pieces (magnetic nanoparticles) and selectively delivered to metastasized tiny cancers, and if the entire human body is then placed on a cooking top, all cancers including unidentifiable ones will be burned without long-term side effects, resulting in a complete cure.” The realization of this scenario corresponds to an ideal therapy, and thus complete body magnetic fluid hyperthermia cancer therapy is intensively investigated by previous studies as an option in new cancer treatments to replace surgery, radiation therapy, and chemotherapy [1–8]. However, the selective annihilation of cancer cells, leaving the normal cells safe, is debatable since normal tissues are also warmed up due to eddy current loss.

The International Commission on Non-Ionizing Radiation Protection has established guidelines that are intended to protect the human body from harmful health effects by restricting exposure to electromagnetic waves [9]. The basic limit for occupational exposure to the entire body in terms of specific absorption rate (which is equal to the amount of heat generated) corresponds to 0.4 mW/cm^{3} based on the guidelines [9]. A safety limit based on some clinical tolerance tests on healthy volunteers has been known as Brezovich criterion where product should not go beyond 6 × 10^{6} Oe·s^{−1} [10]. However, this value applies to healthy individuals, and it may not be applicable to individuals who face serious health issues. Therefore, Hergt et al. [11] proposed a maximum of approximately of 6 × 10^{7} Oe·s^{−1} that can be permitted for localized hyperthermia treatments of patients with serious health conditions. This value is referenced by numerous studies and is considered as a de facto standard for magnetic fluid hyperthermia cancer therapy. Thus, magnetic nanoparticles corresponding to an ultrasmall IH cooking pan were developed based on this irradiation condition.

Recently, Dössel and Bohnert [12] simulated the electromagnetic field distribution and the flow of heat from irradiation on a detailed human body model. The results at kHz and = 100 Oe indicated that hot spots appeared in certain portions of muscles and fat in which the temperature elevation reached 10°C after 5 min despite considering the cooling effects of blood flow. The temperature elevation curves were used to estimate the thermal relaxation time *τ* of the hot spots that corresponded to several tens of minutes. This indicated that thermal insulation could be the reason for the existence of the hot spots. The study surmised that the allowable upper limit of for constant irradiation over the entire human body corresponded to 100 Oe at of 25 kHz. The limit corresponds to the value of 2.5 × 10^{6} Oe·s^{−1}. It should be noted that the condition estimated in the practical simulation significantly deviates from the long-accepted criteria. This finding is important because we cannot measure the deep body temperature during the treatment, although the improvement in accuracy for the simulation is an issue for future research.

In the present study, the new limit is considered to clarify whether or not the heating power of the present magnetic nanoparticles is sufficient to annihilate cancer cells including unidentifiable metastatic tiny cancerous areas scattered throughout the body via conventional magnetic fluid hyperthermia therapy. This is followed by a discussion on alternative strategies that are not bound by conventional frameworks of magnetic fluid hyperthermia cancer treatment. It should be noted that, with the exception of , Gaussian-cgs units are used in the relationship with respect to the tissue size.

#### 2. Model

##### 2.1. Heating Power of Magnetic Nanoparticles

Magnetic hysteresis and eddy current losses heat a pan during IH cooking. Additionally, an ultrasmall pan (magnetic nanoparticles) can rotate in the applied magnetic field unlike a* regularly used* pan due to its small size. These rotations generate frictional heat [13]. Thus, the study begins by reexamining each heating mechanism briefly. First, with respect to magnetic hysteresis losses, the amount of heat generated, , for a unit volume of magnetic nanoparticles per unit time is derived as follows:for irradiation of the ac magnetic field,* H* = , where denotes the magnetic field and denotes the magnetization. The value of the integral corresponds to the area of the hysteresis loop, and it is maximized at in the case where the magnetization reversal occurs coherently in all nanoparticles when corresponds to ±, and denotes the saturation magnetization. In other words, , is largest when the magnetic hysteresis loop is a square with width of . However, it should be noted that it is not possible to realize such ideal reversals in actual systems. Hence, the ratio, , of to is considered as an index that represents the squareness of the magnetic hysteresis loop and the equation is reexpressed as follows: At this stage, it is necessary to consider the relaxation loss of magnetic nanoparticles that is generated when the magnetic response is given by , where and denote the in-phase and out-of-phase components, respectively, of the ac susceptibility. This loss can be expressed as by substituting into (1). It should be noted that the relaxation loss is actually a type of hysteresis loss and is always less than unity.

Friction heat generated from the rotation of particles is considered. The work performed by the friction torque while a small rotation of occurs corresponds to . For the purpose of simplicity, it is assumed that the magnetization vector , which is equal to , is fixed in the direction of the easy axis of particles in a manner similar to a small permanent magnet, where denotes volume of the particle. In this case, the friction dominates the rotation with respect to the inertia-less limit, and always balances the magnetic torque corresponding to . Thus, the following expression is obtained: where denotes the angle between and (which is in the direction of the easy axis). The amount of friction heat generated per unit volume per unit time is therefore expressed as follows: This equation is equivalent to (1) and indicates that the amount of energy dissipated by friction is equal to the input magnetic energy. Thus, only the names that describe the evolved heat vary depending on the focus of attention, that is, hysteresis loss or friction heat as described above.

Conversely, an eddy current loss exists that corresponds to a heat source derived from electromagnetic induction. The induced electromotive force in any closed circuit is equal to the negative of the time rate of change of the magnetic flux enclosed by the circuit, and thus the per unit volume and unit time average of for a spherical particle with electrical conductivity* σ* and radius are as follows: Thus, the total amount of heat generated in magnetic nanoparticles can be expressed as , since sources of heat in the above two cases are completely different.

##### 2.2. Thermal Models of Tumor and Hot Spot Portion

To discuss the effectiveness of hyperthermia treatments, it is necessary to model the heat flow generated in the magnetic nanoparticles accumulated in a tumor. To consider the tumor, it is not necessary to use finite element method despite the significant dependence of thermal conductivity *λ* on the organ type (typically, 0.003–0.006 WK^{−1 }cm^{−1} [14]) because a feature of this therapy includes treatments of small unidentifiable metastatic cancers with an approximate diameter of 1 cm, within which thermal properties are assumed homogeneous. According to Andrä et al. [15], the heat at is roughly dissipated by conduction when such a tumor is steadily maintained at a temperature that exceeds the temperature of the surrounding area by . Conversely, the blood flow in tumor tissues transfers heat at the rate , where denotes the blood specific heat and approximately corresponds to 4 JK^{−1 }cm^{−3}, while corresponds to the tumor tissue blood perfusion rate and it varies based on the type, phase, size, and temperature of the tumor. Typically, is lower than that of the corresponding normal tissue and is less than 0.01 s^{−1} [16]. Therefore, the heating power density required to elevate the temperature of tumor with a of 1 cm corresponds to W/cm^{3} by assuming higher values for and *λ* as 0.01 s^{−1} and 0.006 WK^{−1 }cm^{−1}, respectively. For the purposes of subsequent discussion, it is necessary to remember that the thermal relaxation time in such cancers corresponds to 23 s [17] when specific heat,* c*_{c}, is assumed to correspond to 3.7 JK^{−1 }cm^{−3}.

Now, the model of the hot spot portions proposed by Dössel and Bohnert is considered. Specifically, it is necessary to simulate the temperature distributions in a human body that is exposed to ac magnetic fields by using Bio-heat equation. However, it is possible to roughly estimate the temperature of the hot spot portion by using the following simple equation because the temperature variation for each organ, reported by Dössel and Bohnert, is actually approximated by single exponential relaxation, respectively. This is expressed as follows: where , , and denote the nominal heat generation, the specific heat, and relaxation time at the hot spot portions, respectively, and denotes the original temperature. For example, the results of curve fitting for the temperature variations of the hot spot portion in the muscle indicate that and , correspond to 0.034 W/cm^{−3} and 1.2 × 10^{3} s, respectively, for = 5 × 10^{6} Oe·s^{−1}. For = 1 × 10^{7} Oe·s^{−1}, and correspond to 0.137 W/cm^{−3} and 1.2 × 10^{3} s, respectively. is set as 3.7 JK^{−1 }cm^{−3} for the above cases. It should be noted that long relaxation times indicate thermal insulation of the hot spot portion. The fact that is almost proportional to ()^{2} is consistent with the feature of the eddy current loss, although details of actual current circuits are unknown. This indicates the validity of the approximation, and thus the hot spot temperature can be approximately calculated by using (6) with above parameters derived from the simulated results.

#### 3. Results and Discussion

##### 3.1. Conventional Magnetic Fluid Hyperthermia

For the purposes of biosafety, magnetic nanoparticles consisting of iron were examined as various types of nanomedicine because a high amount of iron (0.1 mg/cm^{3}) is always stored in the body. Specifically, iron oxides, such as magnetite, were actually used since metallic iron is easily oxidized in the nanoform. Therefore, the survey of the conventional method is initiated by calculating the heating power of the magnetite nanoparticles by implementing actual figures. Presently, , , , and the density are set as 5 kG, 10^{4} Sm^{−1}, 10 nm, and 5.2 g/cm^{3}, respectively. Simple analyses on the results of typical hyperthermia studies indicate that the values of are typically in the range of 0.2–0.3 [18]; and thus is corresponding to 0.3. With respect to the condition of irradiating magnetic field, the value of = 2.5 × 10^{6} Oe·s^{−1} is selected as an upper limit as stated above. The substitution of these values in (2) indicates that in this instance corresponds to 120 W/cm^{3} (which is 23 W/g) when corresponds to 1 × 10^{−4} W/cm^{3} on the assumption that is reversed in the time scale comparable to Larmor precession ~10^{–9} s. Therefore, it is possible to ignore the eddy current loss in magnetite nanoparticles in contrast to the hysteresis loss.

Conversely, it is considered that hyperthermia treatments are conventionally performed in the range of 42-43°C although an established value does not exist [1, 3]. The calculation shown in the prior section indicates that the heating power density for increasing the temperature of tumor with a of 1 cm by Δ*T* = 5 K approximately corresponds to 0.5 W/cm^{3}. The heating power density can be achieved when a large amount of magnetite with of 23 W/g is accumulated at a concentration of 22 mg/cm^{3} in tumor tissues. In contrast, Huang and Hainfeld [19] reported that they injected ferric oxide nanoparticles intravenously via a tail vein, and, consequently, the results indicated that nanoparticles accumulated in the tumor at a concentration of approximately 1.9 mg/cm^{3}. This concentration corresponds to the top class performance at present. However, it is significantly less than the required figures. Thus, the current discussion indicates that conventional hyperthermia treatment using magnetite nanoparticles is impractical for unidentifiable tiny cancers areas scattered throughout the body without significant advancements in drug delivery technology in the future.

An easy method involves eliminating the focus on the whole-body treatment by drug delivery techniques and focusing instead on identified larger cancer treatments in a local area by direct injection. This is because the heat generated by eddy current loss in hot spot portions is proportional to the cross-sectional area through which the magnetic flux passes as discussed above. Hence, restricting an irradiation range to local area suppresses temperature elevation in the hot spot portion. Furthermore, the temperature elevation of tumors can become significant as the size of tumors increases because the heat dissipation is proportional to the area of the cancer surface while the heating power afforded by the accumulated nanoparticles is proportional to the volume. Additionally, a direct injection on the identified cancers enables the enhancement of the concentration of nanoparticles inside tumors when compared with that in other drug delivery techniques. However, we know that larger cancerous area at known positions can be also removed through surgery. Therefore, it is still important to examine other solutions for the whole-body treatment by considering points overlooked in conventional magnetic fluid hyperthermia treatments.

##### 3.2. Alternative Strategies

As described in the preceding section, the conventional hyperthermia treatment using magnetite nanoparticles is ineffective with respect to tiny cancers scattered throughout the body. To resolve this, it is necessary to shift the standpoint by considering steady heating by using the equilibrium response of stable nanoparticles to those for temporary heating from a nonequilibrium response of quasi-stable nanoparticles in order to clarify the manners to maximize each factor in (2). First, the saturation magnetization is considered. For example, only iron oxide nanoparticles were commercially used for magnetic fluids in machines due to their excellent oxidization resistance, although metallic iron has much higher . This is because industrial products generally need durability exceeding ten years. On the basis of such experience, iron oxide nanoparticles have been examined for hyperthermia treatments. Nevertheless, it should be noticed that the hyperthermia treatment period is significantly shorter. Hence, the iron oxide shell, iron core nanoparticles can be considered as a candidate despite instability for long-term usage. This substance includes a large value of for the iron core and biocompatibility of the iron oxide shell. Previous studies indicated that the nanoparticles with this type of structure possess a saturation magnetization 4*π* of 12 kG at 14 nm [20] and 16 kG at 40 nm [21], which is twice that of iron oxide. Little is, however, known as to their long-term durability. Thus, the stability of magnetization for the commercially available core-shell nanoparticles ( = 12 kG) obtained from BoutiQ Nanoparticle Solutions was checked by using an extraction method (PPMS, Quantum Design). Consequently, the results indicated that the magnetization did not decline after six months from when the substance was received as shown in Figure 1. As expected, the iron oxide of the shell also serves as a surface protection layer. Hence, it is applicable for magnetic fluid hyperthermia treatments because such treatments are typically completed in half year at most, although it may become difficult to maintain excellent dispersion stability for over several months because the larger strengthens effects of the interparticle interactions.