Nanowarming Using Au-Tipped Co₃₅Fe₆₅ Ferromagnetic Nanowires

Abstract

Ferromagnetic Co₃₅Fe₆₅, Fe, Co, and Ni nanowires have high saturation magnetizations (M_s) and magnetic anisotropies, making them ideal for magnetic heating in an alternating magnetic field (AMF). Here, Au-tipped nanowires were coated with polyethylene glycol (PEG) and specific absorption rates (SAR) were measured in glycerol. SAR increased when using metals with increasing M_s (Co₃₅Fe₆₅ > Fe > Co > Ni), reaching 1610 ± 20 W/g metal at 1 mg metal/ml glycerol for Co₃₅Fe₆₅ nanowires using 190 kHz and 20 kA/m. Aligning these nanowires parallel to the AMF increased SAR up to 2010 W/g Co₃₅Fe₆₅. Next, Co₃₅Fe₆₅ nanowires were used to nanowarm vitrified VS55, a common cryoprotective agent (CPA). Nanowarming rates up to 1000 °C/min (5 mg Co₃₅Fe₆₅/ml VS55) were achieved, which is 20x faster than the critical warming rate (50°C/min) for VS55 and other common CPAs. Human dermal fibroblast cells exposed to VS55, and Co₃₅Fe₆₅ nanowire concentrations of 0, 1 and 2.5 mg Fe/ml all showed similar cell viability, indicating that the nanowires had minimal cytotoxicity. With the ability to provide rapid and uniform heating, ferromagnetic nanowires have excellent potential for nanowarming cryopreserved tissues.

1. Introduction

A significant challenge for organ and tissue transplantation is ischemic injury during the time between removal from the donor and implantation in the recipient.¹ Organs can be preserved by hypothermic storage, for example, hearts can be stored up to 4 hours and kidneys up to 36 hours.² To extend this time, tissues and organs can be cryopreserved by vitrification, an approach that converts liquid to glass without crystallization. While there have been recent advances in vitrifying tissues or organs,³ there are two challenges to successful rewarming of large volumes. First, a rapid heating rate is needed to avoid devitrification, the process of crystallization during warming. For example, one common cryoprotective agent (CPA), VS55, must be heated faster than 50°C/min,⁴ which is its critical warming rate (CWR). Second, uniform heating rates must be achieved throughout the volume to avoid large thermal gradients, which can produce thermal stresses that cause fractures or cracks. Recently, Manuchehrabadi et al. used silica–coated iron oxide nanoparticles suspended in VS55 to successfully vitrify and re-warm human dermal fibroblast cells, porcine arteries and porcine aortic heart valve leaflet tissues. Volumes up to 80 ml were placed in a uniform alternating magnetic field (AMF) to heat the nanoparticles by magnetic hysteresis in a process known as nanowarming.⁴

When magnetic nanoparticles (MNPs) are placed in an AMF, they convert the electromagnetic energy into heat through a combination of Neél relaxation and Brownian motion.⁵ The heat generated by the MNPs in the AMF increases with the frequency (f) and the field strength (H).⁶ It is also possible to increase the heating efficiency of the MNPs by carefully engineering their shape and material composition.

Indeed, there has been an increasing interest in a variety of MNPs for biomedical applications such as magnetic resonance imaging (MRI) contrast⁷ and tumour hyperthermia.⁸ The most common MNPs for these applications, are spherical iron oxide nanoparticles.⁸ Recently some groups have also investigated the heating properties of magnetic nanorods,^{9, 10} nanocubes,⁹ and nanowires.¹¹

In an AMF, the energy per gram generated by MNPs in each cycle can be written as:

$$W_{heat}=\oint H\cdot dM$$ (1)

where W_heat is equal to the area inside the hysteresis loop, H is the applied magnetic field, and M is the magnetization. Figure 1 shows the full hysteresis loops for Au-tipped 8 μm nickel (Ni) nanowires oriented parallel or perpendicular to an applied magnetic field. The characteristic points are indicated, namely the saturation magnetization (M_s), the remnant magnetization (M_R) at 0 applied field, the coercive magnetic field (H_c) needed to demagnetize the sample, and the anisotropy field (H_K) which is the field required to fully align the magnetization in a given direction. For uniaxially anistropic MNPs, the parallel hysteresis loop has an area that has been described¹² as a parallelogram with height = 2(M_s) and width = 2(μ₀H_k), where μ₀ is the permeability of free space. Combining these with the anisotropy energy density:

$${\mu }_0{H}_K=\frac{2K}{M_S},$$ (2)

the maximum energy per gram is calculated as:

$$W_{heat}^{max}=4M_s{\mu }_0{H}_k.$$ (3)

Fig. 1.

Hysteresis loop for 8 μm Ni nanowires aligned in an AAO membrane parallel and perpendicular to the applied field. Red arrows indicate the important magnetic parameters. H is the applied magnetic field and M is the magnetization. Thick red line shows range of field used in SAR measurements.

This can be simplified as:

$$W_{heat}^{max}=8K$$ (4)

where K is the anisotropy energy density, or the energy required to orient the magnetizations of uniaxial MNPs away from their easy axes.¹²

These equations show that the magnetic anisotropy of the MNPs has an important role in determining the heating properties of the particles. The main sources that contribute to anisotropy energy density for MNP systems are magnetocrystalline anisotropy, shape anisotropy, surface/interface anisotropy, colloidal anisotropy, and magnetoelastic anisotropy. Magnetocrystalline anisotropy is due to the crystal structure dictating a preferred orientation for the atomic magnetic moments relative to the crystallographic axes. Shape anisotropy occurs when the shape of the magnetic material causes a preferred orientation of the magnetic moment with respect to the major/minor axes of the particle to minimize the energy of magnetostatic fields. This is common for high aspect ratio (length: diameter) MNPs that have length>>diameter (e.g. nanowires, or nanorods). Colloidal anisotropy arises from interactions among magnetic nanoparticles suspended in a liquid that permits the formation of higher order structures, such as chains. If the MNPs are close to each other, then magnetic dipole-dipole interactions between neighboring particles can affect their switching properties. Magnetoelastic anisotropy arises from coupling between strain and magnetization of a magnetic material.

There have been many studies investigating the heating properties of small, iron oxide MNPs with various shapes and sizes (typically sub-micron), and there have been a few studies using high aspect ratio or high magnetization particles. To compare the heating properties for different MNPs, the specific absorption rate (SAR) is calculated from a plot of temperature versus time during heating. Geng et al. observed SAR up to 1072 W/g Fe for Fe₃O₄ nanorods (15 nm diameter, 67 nm long at 5 mg/ml).¹⁰ Das et al. also studied Fe₃O₄ nanorods (5–10 nm diameters, 41–65 nm long) and found SAR up to 862 W/g Fe (1 mg/ml), with increased SAR for aligned nanorods.⁹ Nemati et al. achieved SAR of 800 W/g Fe for Fe₃O₄ nanocubes and noted that magnetic anisotropy of the nanoparticles (which depends on their size, shape, arrangement, and dipolar interactions) caused noticeable variations in the SAR.¹³ Lin et al. measured SAR up to 920.8 W/g Fe for Fe nanowires (60 nm diameter, 2–6 μm long).¹¹ Alonso et al. found that electrodeposited Co₃₅Fe₆₅ nanowires (100 or 300 nm diameter, 2–40 μm long) had high SAR up to 1500 W/g Fe which increased when the nanowires were aligned parallel with the AMF in agarose.¹⁴ However, these studies used only one nanoparticle concentration, 0.5 mg Fe/ml, which may be too low to provide sufficiently rapid heating of large volumes needed for cryopreservation. One might argue that SAR is in units of W/g, so the same value can be used for higher concentrations, but SAR values typically decrease with higher concentrations.^9–11 This indicates that empirical studies at the desired concentrations are important to demonstrate the feasibility for a specific application. Note, all of the SAR values mentioned above were measured at ~300kHz AMF, except one at 390 kHz.⁹ Therefore, these SAR values would be higher than those of similar MNPs measured at 190 kHz, as shown in this study.

Here, template-assisted electrodeposition^{7, 15, 16} was used to fabricate high M_s, high anisotropy magnetic nanowires. One goal was a systematic heating study on the effect of M_s, adjusted at 55, 170, 220, and 248 emu/g by using Ni, Co, Fe, and Co₃₅Fe₆₅ nanowires, respectively, with Au tips. The diameter of each nanowire sample (from 10’s to 100’s of nm) is set by the pore diameter of the anodic aluminium oxide (AAO) that is used as the fabrication template. This study used 200 nm diameter nanowires. The nanowire length is controlled by the electrodeposition time. Both the diameter and length determine the shape anisotropy, which affects the magnetic properties of the nanowires.^{17, 18} In addition, the nanowires can be coated with PEG or other biological molecules to improve biocompatibility.^{15, 16} Uncoated metallic nanowires can oxidize in air or water, resulting in reduced magnetization. Therefore, the nanowires used in this work were coated with HS-PEG-COOH on the Au tips, and dopamide-PEG on the Co₃₅Fe₆₅, Fe, Co, or Ni surfaces. The hydrophilic PEG can improve the buoyancy and dispersibility of the nanowires by mitigating the magnetic attractive forces between them, see relaxivity measurements in ESI, Table S2.¹⁹

This is the first systematic study of Ni, Co, Fe and high M_s Co₃₅Fe₆₅ nanowires (200 nm diameter, 0.5–16 μm long) at different concentrations (0.0625–10.0 mg Co₃₅Fe₆₅/ml). The longest, highest aspect ratio nanowires had the highest SAR values for concentrations 1–2 mg Co₃₅Fe₆₅/ml, but at higher concentrations of 5–10 mg Co₃₅Fe₆₅/ml the SAR values were reduced, likely due to increased dipole-dipole interactions, which affected the magnetic switching in the AMF. Aligning the nanowires parallel with the AMF increased the SAR up to 2010 W/g Co₃₅Fe₆₅ for 1 mg Co₃₅Fe₆₅/ml of 8 μm Co₃₅Fe₆₅ nanowires aligned in glycerol. After comparing the SAR values for the various nanowires in glycerol, dispersions of nanowires in VS55 were cryogenically vitrified and cooled to −185 °C (using liquid nitrogen vapor). These dispersons were re-warmed in the AMF to simulate nanowarming of cryogenically preserved cells or tissues. Finally, 8 μm Co₃₅Fe₆₅ NWs nanowires in VS55 (1 and 2.5 mg Fe/ml) added to human dermal fibroblast (HDF) cells for 3 minutes demonstrated minimal cytotoxicity compared with the VS55 alone. High SAR, fast heating, and low toxicity indicate that magnetic nanowires may be useful for nanowarming.

2. Experimental

a. Nanowire fabrication and coating

Various length Co₃₅Fe₆₅ nanowires (1–16 μm) (Fig. 2a,b, ESI Figure S2) and 8 μm Co, Fe and Ni nanowires were electrodeposited into 50 μm thick commercial AAO templates (Whatmann Inc. or InRedox). The nominal nanopore diameter was 200 nm. Similar length and diameter nanowires were used by Alonso et al.¹⁴ A metallic seed layer of Ti (10 nm) was sputter deposited onto one side of the AAO templates, followed by 400nm of Cu (either electrodeposited or sputtered) to act as a back-electrode. See ESI Figure S1 for a diagram depicting NW fabrication steps.

Fig. 2.

Cross-sectional SEM images of Co₃₅Fe₆₅nanowires 16 μm (a) and 2 μm (b) aligned in an AAO template. The Cu layers at the bottom were dissolved by 1 M FeNO₃ before dissolving the AAO template. Note, some of the NWs were broken when the AAO template was cleaved to make these cross-sectional images. (c) Released Au-tipped Ni nanowires.

An initial layer of Cu was electrodeposited inside the nanopores and 500 nm Au tips were electrodeposited on both ends of the Co₃₅Fe₆₅, Fe, Co, or Ni nanowires. Please refer to ESI S2 for a detailed description of the electrolytes and electrodeposition parameters used. Importantly, Co₃₅Fe₆₅ electrodeposited under these conditions has been found to have a high M_s (248 emu/g)²⁰ while maintaining coercivity.

After electrodepositing the nanowires, the Cu was wet etched using 1.0 M FeNO₃. Then, the AAO template was dissolved in 0.7 M HPO₄ and 0.2 M CrO₃ at 80°C for 60 minutes. The nanowires were magnetically separated and washed 3X with DI water. They were resuspended in 1 ml of 1mM 2000 MW dopamide-PEG (synthesized using Sigma Aldrich chemicals), and 1 ml of 1mM SH-PEG-COOH (Sigma Aldrich) for 12 hours to coat the magnetic and Au surfaces, respectively.

b. Nanowire characterization

The nanowires were imaged while aligned in the AAO template using a Zeiss NEON 40 EsB CrossBeam SEM. The Co₃₅Fe₆₅ nanowires had an atomic ratio of Co:Fe = 32:68 ± 10%, as determined by EDS. This composition lies in the range of M_s=248emu/g alloys (center value of Co₃₅Fe₆₅ according to the Slater Pauling curve), and M_s was confirmed using a Princeton vibrating sample magnetometer (VSM). The hysteresis loops of Co₃₅Fe₆₅, Fe, Co, and Ni nanowires, (±5kOe, 25 Oe/s, 25°C), were measured while they were still inside the AAO, aligned parallel and perpendicular to the applied field. These loops show the extremes of orientation, where random orientations will be between these extremes.

c. SAR measurements and calculations

To measure and calculate SAR values, nanowire samples in glycerol or VS55 were placed in a 1.7 ml Eppendorf tube and heated using a 1-kW Hotshot inductive heating system with 2.75-turn, water-cooled copper coil, inner diameter 1.75 cm (Ameritherm Inc). The vial was insulated in styrofoam with sample volumes ranging from 0.1–0.5 ml, depending on the nanowire concentration. The temperature was measured and recorded in one second increments using a Teflon coated fiber-optic temperature probe and Neoptix OptiLink software (Qualitrol Corporation). The time point for 0 seconds on the temperature curve was chosen within the first few seconds after turning on the AMF. For the SAR measurements, the magnetic field amplitude was H = 20 kA/m (251 Oe) and frequency was f = 190 kHz. For the nanowarming measurements, field amplitudes (H = 20, 25 or 30 kA/m) and frequencies (f = 190 or 360 kHz) were varied, as noted in the text.

d. Cell viability experiments

For each trial, ~50,000 HDF cells (suspended in cell growth media) were put into one well of a 96 well plate and left overnight to become adherent to the bottom. After 18 hours, the cell growth media was removed, and the cells were loaded with Euro Collins solution, followed by increasing concentrations of VS55 (12.5%, 25%, 50%, 75%) for 3 minutes each. Then, the 75% VS55 was removed and 100 μl of VS55 with 8 μm Co₃₅Fe₆₅ nanowires (1 or 2.5 mg Co₃₅Fe₆₅/ml) was added to each well for 3 minutes because cells are typically exposed to liquid VS55 for only 3 minutes during nanowarming. Next, the nanowire suspension was removed, and the cells were rinsed with decreasing concentrations of VS55 until they were fully loaded with Euro Collins solution, as before. Finally, the cells were stained with using a Hoechst-PI double stain and imaged using a fluorescent microscope to count the living and dead cells, N > 200 cells/sample.

3. Results and discussion

First, the impact of M_s on heating was studied. 8 μm long Co₃₅Fe₆₅, Fe, Co and Ni nanowires were mixed in glycerol at various concentrations and placed in the AMF (H = 20kA/m, or 251 Oe, f = 190 kHz). The SAR values were calculated using the Box-Lucas curve-fitting method, where equation (5) is used to calculate parameters A and λ, which are then used to calculate SAR with equation (6):

$$\mathrm{\Delta }T=A\left(1-e^{-\lambda t}\right)$$ (5)

$$\text{SAR}=\frac{A\lambda C}{m_{MNP}}$$ (6)

The Box-Lucas method was used because it is reliable to calculate the SAR for non-adiabatic systems such as this.²¹ The curve fitting was done for the first 180 seconds of the heating measurements, Fig. S3 in ESI, and C is the heat capacity of glycerol (3.04 J/ml K).

Figure 3a shows that the highest M_s metal (Co₃₅Fe₆₅) had the highest SAR values, and SAR decreased as materials with lower M_s were used (Fe, Co, and Ni, respectively). Figure 3b,c,d show the parallel and perpendicular hysteresis loops for the Co₃₅Fe₆₅, Fe, Co nanowires, while Ni is shown in Figure 1. The M_s values are similar to the bulk values for each metal (Co₃₅Fe₆₅ 248 emu/g, Fe 218 emu/g, Co 161 emu/g, Ni 54.4 emu/g).^{20, 22} Although SAR monotonically increased with the M_s of the nanowire materials, the relationship was not linear for several reasons. First, Fe nanowires had lower relative SAR because Fe readily oxidizes, which can lead to canted magnetic moments and iron oxides on the surfaces, both of which lower M_s.²³ For reference, iron oxide exists in many forms with M_s of 0 (hematite) to 87 (magnetite) emu/g. Co nanowires also had lower relative SAR values, most likely because Co has 10x higher crystallographic anisotropy than the other metals which may be competing with the nanowire shape anisotropy, leading to a sheared hysteresis loop²⁴ (Fig. 3d). This shearing reduces the area of the loop, and therefore reduces heating.

Fig. 3.

(a) SAR values for nanowires with different Ms in glycerol at various concentrations using 20 kA/m. Hysteresis loops for 8 μm (b) Co35Fe65, (c) Fe, and (d) Co nanowires aligned in AAO membranes parallel and perpendicular to the applied field. Note, 1 kOe = 79.6 kA/m and the thick red line shows the strength of the field for SAR measurements.

Dipole interactions between neighbouring nanowires also affect the switching of the magnetic domains.²⁵ The dipole interactions become more noticeable at higher nanowire concentrations because the nanowires are closer together. This could explain why the SAR values are typically higher at lower concentrations in literature^8–10 and in every curve in Fig. 3.a. See a comparison of 0.125 and 0.25 mg Co₃₅Fe₆₅/ml in ESI Figure S4. For the same size nanowire, 10x increase in concentration will lead to a cubed root of 10 (or 2.15x) closer spacing (r). Since dipole fields are proportional to r⁻³, this can be a significant effect that increases further as spacing becomes similar in size as the nanowire dimensions.

The nanowires have a lower saturation field when they are aligned parallel with the field, which means a lower magnetic field is needed to completely flip the magnetizations. Therefore, the nanowires should generate more heat in lower magnetic fields with the nanowires aligned parallel with the AMF rather than perpendicular or randomly oriented.^{26, 27} This is especially useful for heating biological tissues, for which it is preferable to use lower AMFs to avoid strong eddy currents.

Given the successful heating with the high-M_s Co₃₅Fe₆₅ nanowires, this material was used for the remainder of the paper. First, a study was conducted to measure how the nanowire length affects SAR values at different concentrations, Fig. 4a. In general, the SAR values increased with increasing nanowire length, which agrees with the SAR trend observed by Alonso et al.¹⁴ As the nanowire length increases, the magnetic anisotropy also increases because the demagnetization factor is larger for longer magnetic domains. However, longer nanowires can have multiple magnetic domains so the magnetic domain length does not continue increasing with the nanowire length.

Fig. 4.

(a) SAR values for different length Co₃₅Fe₆₅ nanowires in glycerol at various concentrations. (b) Graph showing the SAR values for different lengths and alignment of Co₃₅Fe₆₅ nanowires in glycerol at various concentrations. The asterisk marker indicates the nanowires were randomly oriented while the square marker indicates the nanowires were aligned parallel to the AMF before heating to show effect of particle anisotropy on heating

As with Fig. 3a, the SAR values were higher for lower concentrations for all the different length Co₃₅Fe₆₅ nanowires (ESI Fig S4). Lin et al. also observed increasing SAR values for iron nanowires at lower concentrations (0.1 mg/ml) for 2–6 μm long Fe nanowires.¹¹ As before, this is likely because the nanowires have fewer dipole interactions at lower concentrations, because they are farther apart from each other.²⁵ For 16 μm nanowires, which have larger magnetic dipole fields, the average center-center spacing is 32 μm at 0.125 mg/ml and only 7.6 μm (~ 38 diameters) at 10 mg/ml.

Although the SAR values are higher at low concentrations, the temperature increase per minute is smaller because the nanowire mass is smaller. It would be difficult to achieve the rapid heating rates (above CWR) needed to re-warm vitrified samples. Encouragingly these SAR values were similar to those observed by Alonso et al.,¹⁴ which is the only previous group to report SAR values for electrodeposited Co₃₅Fe₆₅ nanowires. They used H = 23.9 kA/m and f = 310 kHz.

Glycerol was used for these heating experiments because it has a higher viscosity and density than water, with a lower C_p. The high-viscosity glycerol prevented the nanowires from settling to ensure a uniform concentration during heating. It also restricted the rotational movement of the nanowires in the 190 kHz AMF. This motion-restricting environment is similar to having nanowires dispersed in a cooled or vitrified cryoprotective agent. With the nanowires suspended in glycerol, they were aligned by placing the sample in a uniform DC magnetic field (H = 1.6 kA/m) generated by a Helmholtz coil (750 turns) and a 3-amp DC power supply (ESI Fig S6).

Heating curves were measured for several samples with the nanowires aligned parallel to the AMF prior to measurement, Fig 4b. SAR increased for all of the aligned samples. For the 8 μm Co₃₅Fe₆₅ nanowires the SAR increased from 1610 W/g Co₃₅Fe₆₅ (randomly oriented) to 2010 W/g Co₃₅Fe₆₅ for aligned nanowires. Alonso et al. also observed an increase in SAR values with Co₃₅Fe₆₅ nanowires aligned with the magnetic field.¹⁴ These experimental results agree nicely with the magnetic hysteresis data in Figure 3b. When the nanowires are aligned parallel to each other and the AMF (instead of randomly oriented), they have a lower saturation field. Even below saturation, it is obvious from Figure 3b that parallel loops have more area, and therefore better heating at +/− 20 kA/m. This point is further illustrated below.

Because cryogenic nanowarming typically requires high concentrations (> 2 mg Fe/ml) to achieve high heating rates, two higher concentration nanowire samples were measured in glycerol. Figure 5a shows that nanowire alignment increased SAR values at 2 mg/ml and 5 mg/ml. At 10 mg/ml the SAR values were similar for aligned or random nanowires. Presumably, the dipole fields of the nanowires interact at such a high concentration.

Fig. 5.

(a) SAR values for 6 and 8 μm Co₃₅Fe₆₅ nanowires in glycerol at various concentrations, with the nanowires randomly oriented or aligned parallel to the AMF. (b) Heating curves for 8 μm Co₃₅Fe₆₅ nanowires (5 mg/ml) in VS55 at 360 kHz and 20 or 25 kA/m. (c) Heating curves for 8 μm Co₃₅Fe₆₅ nanowires at 1, 2.5, or 5 mg Co₃₅Fe₆₅/ml at 25 or 30 kA/m with the nanowires randomly oriented or aligned parallel to the AMF. (d) Minor hysteresis loops of 8 μm Co₃₅Fe₆₅ nanowires aligned in an AAO membrane parallel to the applied field. Minor loops with nanowires perpendicular to the applied field are in ESE (Fig S5d). Repeated colors in (b) and (c) are repeated measurements.

Co₃₅Fe₆₅ nanowires were dispersed in a standard cryopreservation agent, VS55, at concentrations of 1, 2.5, 5, and 10 mg Co₃₅Fe₆₅/ml. Figure 5b shows the heating curves for 8 μm Co₃₅Fe₆₅ nanowires (5 mg/ml) heated in VS55 at 20 kA/m and 360 kHz, with or without magnetic alignment. The nanowires heated at least an order of magnitude above the CWR for VS55 (50°C/min) and much faster than commercial Ferrotec iron oxide particles coated with mesoporous silica.⁴ This is expected, since these Co₃₅Fe₆₅ nanowires have more area inside their hysteresis loops, and therefore higher SAR values than the iron oxide particles.²⁸ When the AMF was increased to 25 kA/m, with the nanowires aligned, the heating rate increased even more. After this intriguing result, several different combinations of concentration (1, 2.5, 5, or 10 mg Fe/ml), AMF (25 or 30 kA/m), and nanowire alignment were tested, with the results in Figure 5c. All of these combinations resulted in fast initial heating rates, up to 1000°C/min for aligned 5 mg Co₃₅Fe₆/ml and for 10 mg Co₃₅Fe₆₅/ml (ESI Fig S7). The dramatic increase in heating rates with the AMF at 25 or 30 kA/m, can be easily explained using the minor hysteresis loops, Figure 5d. The magnetization of the Co₃₅Fe₆₅ nanowires aligned in an AAO membrane parallel to the applied field increased by increasing the AMF from ±20 to ±60 kA/m (±0.25, to ±0.75 kOe). Therefore, the area inside of the minor loops increased as the sample magnetization approached saturation (from Fig. 3b, H_k= 200kA/m, or 2.5 kOe). A similar family of loops for Fe, Co, and Ni nanowires are shown in ESI Fig S5, and to further demonstrate anisotropy, the minor loops of Co₃₅Fe₆₅ nanowires perpendicular to the field are shown in ESI Fig S5d. The 1 kW heating coil cannot achieve AMFs above 30 kA/m; however, larger 15 kW systems can achieve fields as high as 60 kA/m which would be useful to nanowarm larger volumes.⁴ With higher AMFs, there may be a safety concern due to eddy currents. However, the AMF can be turned off once the sample reaches −20°C to avoid damaging the tissues or cells, or a lower frequency can be used.

Importantly, the Co₃₅Fe₆₅ nanowires achieved heating at 256°C/min using only 1 mg Co₃₅Fe₆₅/ml. This means the nanowires could potentially be used for nanowarming with only a fraction of the MNP mass required for typical iron oxide particles (10 mg Fe/ml).⁴ These results demonstrate that the nanowire heating rates can be tuned depending on the concentration and the AMF strength, which offers useful flexibility to achieve rapid heating rates in larger volumes for tissues or organs.

After successfully demonstrating the heating rates in vitrified VS55, the cytotoxicity of the PEG coated Co₃₅Fe₆₅ nanowires in VS55 at 4°C was measured using HDF cells. HDF cells in cell culture medium exposed to a 25 or 30 kA/m AMF for 3 minutes had similar viability as cells with no AMF exposure (Figure 6. a)). These results indicate that Co₃₅Fe₆₅ nanowires with a 25 or 30 kA/m AMF will not be harmful in nanowarming cells or tissues. HDF cells had similar viability in VS55 with 0, 1, or 2.5 mg Co₃₅Fe₆₅/ml of 8 μm Co₃₅Fe₆₅ nanowires (Figure 6(b)). Note that VS55 can be toxic to the cells, especially above −20°C, so exposure was limited to 3 minutes, as it would be during nanowarming procedures.

Fig. 6.

Viability of HDF cells. (a) Cells with no nanowires in cell culture medium with AMF 0, 25, or 30 kA/m, for 3 minutes. (b) Cells in VS55 with 0, 1 or 2.5 mg Co₃₅Fe₆₅/mL of nanowires without AMF. Cell viability was tested after the complete removal of VS55 and/or Co₃₅Fe₆₅ nanowires.

4. Conclusions

High moment Au-tipped nanowires were explored for potential as nanowarming agents. First, Co₃₅Fe₆₅, Fe, Co, and Ni nanowires were dispersed in glycerol to inhibit nanowire motion during heating studies in an alternating magnetic field (AMF). They were found to have SAR values that decreased monotonically with their magnetizations (248, 220, 170, and 55 emu/g, respectively). This was explained by a reduction in the area of the hysteresis loop since the height of the loop is 2x M_s and the width is proportional to 2x the coercivity, H_c. Hysteresis loops were measured for the extremes of orientation (parallel and perpendicular to the applied field), and parallel orientations reached saturation at significantly lower fields. Subsequently Co₃₅Fe₆₅ nanowires were oriented parallel to the AMF (190 kHz, 20 kA/m), which led to an increase from 1610 (random) to 2010 (aligned) ± 20 W/g Co₃₅Fe₆₅ at 1 mg metal/ml glycerol for 8 μm-long Co₃₅Fe₆₅ nanowires. Minor loops were also measured to show the increase in area obtained by increasing the AMF from 20 to 60 kA/m. All of these studies were done from room temperature. Next, Au-tipped Co₃₅Fe₆₅ nanowires were frozen in vitrified VS55, both randomly oriented and aligned parallel to the AMF. Very fast initial heating 1000°C/min was obtained for aligned nanowires, which is 20x higher than the critical warming rates (~50°C/min) of most cryopreservation agents. These promising thermal results indicate that nanowires have excellent potential as nanowarming agents. Cell toxicity in the presence of the nanowires was confirmed to be minimal, and the door is open for future tissue warming studies.