Lowering the power requirements of transcranial magnetic stimulation (TMS) would allow reducing the size and form factor of the stimulating coils, increasing the focality and penetration depth during the stimulation. Commercial TMS equipment typically uses frequencies from 1 to 5 kHz, while the coil currents vary from 1 to 5 kA. According to the Maxwell-Faraday equation, a large â€“dB/dt is required in the coil to induce an E-field above a stimulation threshold around 100 V/m at the target (Fig 1). Therefore, the development of technologies able to obtain similar E-field strength with lower currents is required. This work shows the design, construction, and tests of a novel high-frequency TM stimulator. For the first time to our knowledge, we have used analog modulations (AM/DSB-SC) over a carrier of 25 kHz to obtain a â€“dB/dt 10 times larger than the commercial stimulators. This permitted the reduction of the TMS currents in the same ratio, with a stimulation tone of 1.5 kHz over the carrier. The modulation shifts the stimulating energy out of the TMS band and audible range, leading to soundless operation compared to the uncomfortable clicking sound in current TMS equipment. Our results demonstrated: a reduction of currents to reach the referential E-field threshold of 100 V/m; a decrease of power dissipation in coils with possibility of unrestricted repetitive TMS (rTMS); a reduction in the coil sizes with increased focality and penetration depth; and hardware requirement reduction. Experimental work with rodents is in progress to demonstrate that, although the modulated signal will not stimulate neurons directly at such high frequency (due to the low-frequency response of the cell membrane), the demodulated version of it, obtained within the brain tissue with the superposition of a non-modulated carrier, can effectively recover the low-frequency envelope, stimulate neurons and induce motor evoked potentials (MEPs) (Fig. 1 and 2).

Development of Novel Transcranial Magnetic Stimulation Technique Using High frequency Modulation for Treatment of Parkinson’s Disease

Nanosized magnetic materials form a single domain and, as a result, magnetic nanoparticles (MNPs) usually lose their ferromagnetic properties. However,
superparamagnetic NPs can generate sufficient heat to kill cancer cells under a weak magnetic field. In this study, NiFe2O4 NPs with particle sizes of 3–17 nm were prepared for
application in magnetic hyperthermia treatment (MHT), and their biocompatibility was improved by modification with polyethylene glycol (PEG). PEG is hydrophilic and is often used in
the medical field. Direct current (DC) magnetization measurements showed that all the samples exhibited no hysteresis or superparamagnetic behavior at 300 K. The temperature
dependence of the alternating current (AC) magnetic susceptibilities revealed that the peak temperature of the imaginary part of AC magnetic susceptibilities (χ") varied significantly with
particle size, and the 17 nm sample had a peak at approximately 310 K. It is known that χ" contributes significantly to heat generation owing to magnetic relaxation losses. The temperature
increase of the samples under an AC magnetic field (f = 15 kHz, h = 150 Oe) was measured. The sample with 17 nm particles showed a significant heating effect compared to the other
samples, reaching over 42.5 °C, which is sufficient to suppress cancer cells. Human breast cancer cells (MDA-MB-231) were cultured on a petri dish, and PEG-coated NiFe2O4 NPs were
added. The sample was heated using an AC magnetic field. Approximately 30% of cancer cells were successfully killed, and the magnetic hyperthermia effect was confirmed (Fig.1). To
evaluate the toxicity of PEG-coated magnetic NPs toward cancer cells, cell viability was observed for 24 h after the particles were dispersed in the culture dishes. PEG-coated NiFe2O4 NPs
successfully improved biocompatibility. Thus, NiFe2O4 NPs are expected to be useful agents for MHT. By using a zero-voltage switching (ZVS) circuit and generating an AC magnetic
field from a DC power source, a temperature rise two to eight times higher than that using conventional coils was achieved (Fig.2). 

**References:** 

P. Das, M. Colombo, D. Prosperi, Coll. Surf. B 174, 42 (2019) 

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Biocompatible Superparamagnetic NiFe2O4 Nanoparticles for Magnetic Hyperthermia Treatment using a ZVS Circuit

Introduction: Transcranial Magnetic Stimulation (TMS) is a neuromodulation technique currently FDA approved to treat depression, migraine and obsessive-compulsive
disorder (OCD). TMS outcomes are known to vary based on individual neuroanatomy, tractography derived structural connectivity, and functional connectivity which is not well
understood [1,2]. There is a disconnection between what is measured empirically in resting motor threshold (RMT)/treatment outcomes, and computer simulated induced electric fields (EField)
values based on Magnetic Resonance Imaging (MRI) derived head models. In this study, we aim to gain an understanding and explanation of this variability and offer an
improvement by taking region of interest (ROI) specific gray matter (GMV) and white matter volume (WMV) over a previously published relationship between the brain scalp distance
(BSD) and E-Field in the Transcranial Magnetic Stimulation (TMS).
Experimental Details: Twenty-six mild-to-moderate traumatic brain injury (mTBI) patients were recruited as described in our previous publication [3]. Participants underwent MRI scans
followed by guided repetitive TMS using a NextStim NBS4 figure-of-eight double coil. RMTs were taken as a percentage of the maximum stimulator output (%MSO). T1 weighted MRI
images went through SimNIBS pipeline (v3.2.6) to create anatomically accurate head models for each patient. Head models were imported into Meshmixer (v3.5) where BSD and
individual segment volume were taken from the precentral gyrus (knob) as described in [4].
Results: Preliminary analysis indicates a weak but negative correlation between both GMV (R2 = 0.0307, p = 0.392) and WMV (R2 = 0.0388, p = 0.335) versus RMT. And a stronger
positive correlation between BSD (R2 = 0.29, p = 0.0046) and RMT.
Conclusion: Segmented ROI brain volume didn’t improve the correlation between RMT and 3D brain-scalp volume compared to RMT and 1D brain-scalp distance. Further investigations
into E-Field and correlating empirically collected patient outcomes will enable better TMS dosages as a percentage of patient specific RMT for TMS procedures. 

**References:** 

[1] T. Herbsman, L. Forster, C. Molnar, et al., Human Brain Mapping., 30(7), 2044-2055 (2009). Motor threshold in transcranial magnetic stimulation: the impact of white
matter fiber orientation and skull-to-cortex distance. 
[2] N. Mittal, B. Thakkar, C. B. Hodges, C. Lewis, Y. Cho, R. L. Hadimani, & C. L. Peterson, Human Brain Mapping, 1-16 (2022). Effect of neuroanatomy on corticomotor excitability
during and after transcranial magnetic stimulation and intermittent theta burst stimulation. 
[3] L. M. Franke, G. T. Gitchel, R. A. Perera, R. L. Hadimani, K. L. Holloway & W. C. Walker, Brain Injurty, 36:5, p. 683-692, (2022) Randomized trial of rTMS in traumatic brain injury:
improved subjective neurobehavioral symptoms and increases in EEG delta activity. 
[4] T. A. Yousry, U. D. Schmid, H. Alkadhi, D. Schmidt, A. Peraud, A. Buettner, P. Winkler, Brain, Vol. 120, p.141-157 (1997) Localization of the motor hand area to a knob on the
precentral gyrus. A new landmark. 

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Relationship Between Resting Motor Threshold and Neuroanatomy in Mild to Moderate Traumatic Brain Injury Patients during Transcranial Magnetic Stimulation

Transcranial Magnetic Stimulation (TMS) coils are usually specialized for use in either deep brain or focal stimulation. One of the challenges in the development of TMS
therapy is the ability to deliver a focused magnetic field to the desires target in the brain. In the process of delivering a sufficiently strong H field to the target, surrounding areas of the brain
can be stimulated unnecessarily. A new technique is used here whereby deep and focal stimulation can be achieved using temporal interference (TI). TI is a method that allows for control
of steerability, focality, and depth of penetration. TI uses the frequency difference of two independent electric fields [1]. The TI stimulation frequencies in at 10kHz and is filtered by the
brain’s inherent lowpass [2] behavior [3]. The frequency difference between the two induced electric fields results in an envelope which allows improved focality of stimulation. By using a
coil assembly as shown in Figure 1, and using TI, the focality of the peak induced electric can be increased with respect to the surrounding area as shown inf Figure 2.. This focal point can
also be steered along the centerline between the two coils. Our current work involves using Sim4Life software on 50 unique head models derived from magnetic resonance imaging (MRI)
scans. We are investigating the focality of the induced electric field using our coil design with TI signals. The results will be compared with the commonly used figure-of-eight TMS coil
and the novel design Quadruple Butterfly Coil (QBC) [4]. 

**References:** 

[1] M. Zaeimbashi, A. Khalifa, C. Dong, Y. Wei, S. Cash, and N. Sun, “Magnetic Temporal Interference For Noninvasive, High-resolution, and Localized Deep Brain
Stimulation: Concept Validation,” 2020. 
[2] B. Hutcheon and Y. Yarom, “Resonance, oscillation and the intrinsic frequency preferences of neurons,” Trends in Neurosciences, vol. 23, no. 5, pp. 216–222, 2000. 
[3] M. M. Sorkhabi, K. Wendt, and T. Denison, “Temporally Interfering TMS: Focal and Dynamic Stimulation Location,” 2020 42nd Annual International Conference of the IEEE
Engineering in Medicine & Biology Society (EMBC), 2020. 
[4] P. Rastogi, “Novel coil designs for different neurological disorders in transcranial magnetic stimulation,” PhD Thesis, Iowa State University, Ames, IA, USA, 2019. Available:
https://lib.dr.iastate.edu/etd/17547
Brain Mapping, vol. 29, no. 1, pp. 82–96, 2007. 

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Temporal Interference for Increased Focality of Transcranial Magnetic Stimulation

Currently, the treatment of suppression of cytokine storm in severe COVID-19 patients includes cytokine receptor suppression and depletion of specific immune cells in
addition to steroid treatment. Monoclonal antibody therapy is also one of the methods for depleting specific immune cells. It is a monoclonal antibody therapy against CD3, one of the
important signaling molecules for T-cell receptor activation. Among others, T cells secrete interferon gamma (IFN-γ), a pro-inflammatory cytokine responsible for inducing inflammation.
Therefore, monoclonal antibody therapy againstis a therapy that specifically depletes IFN-γ-secreting T cells. However, intravenous injection of an anti-CD3 monoclonal antibody targeting
all T cells induces significant immunosuppression and has side effects such as high fever and chills. The purpose of this study is to prepare an optimized liquid phase as a CD3 antibodymagnetic
nanoparticle (Ab-MNP) conjugate to inhibit the overactivation of T cells. In current study, we aimed to check distribution of Fe after acute admistration of silica-conjugated
amine nanoparticles delivered by intravenous injection. Besides, the IFN- γ levels in serum and spleen homogenates will be analyzed. Finally, we will develop film-type microneedle patch
using pulse-type magnetic stimulation to control the amount of liquid passing through the skin. The reason for choosing the spleen from the mouse organ is that it stores MNPs with a
particle size of 50 nm administered in vivo. Therefore, the result is a difference in the concentration of Fe elements, which was 1.89×103 mg/kg in the spleen of a control mouse not
administered with MNPs, whereas increases significantly to 1.93×103 mg/kg in that of a mouse administered with MNPs as shown in Fig. 1(a) and 1(b). IFN-γ level in spleen tissue and
serum is increased after 10 days. Further, time kinetic analysis of biochemical and immunological parameters are required to confirm its suitability in bio-administration. 

**References:** 

[1] N. S. Remya, S. Syama, A. Sabareeswaran, and P. V. Mohanan, Toxicity, toxicokinetics and biodistribution of dextran stabilized Iron oxide Nanoparticles for biomedical
applications, International Journal of Pharmaceutics 511, 586-598 (2016). 
[2] F. Gao, An Overview of Surface-Functionalized Magnetic Nanoparticles: Preparation and Application for Wastewater Treatment, Chemistry Select 4, 6805-6811 (2019).<br<
[3] R. Q. Cron, R. Caricchio, and W. W. Chatham, Calming the cytokine storm in COVID-19, Nature Medicine 27, 1674–1675 (2021). 
[4] C. Kuhn and H. L. Weiner, Therapeutic anti-CD3 monoclonal antibodies: from bench to bedside, Immunotherapy 8, 889–906 (2016). 

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Analysis of Fe element and interferon gamma in serum and spleen homogenates after injection of silica coated magnetic nanoparticles (SiO2 Fe3O4)

In this work, we have displayed an easy way to produce monodisperse spinel nanoparticles (NPs), as well as the antifungal activity of CoFe2O4, Co0.5Zn0.5Fe2O4 and
ZnFe2O4 nanostructures. Firstly, the structural, morphological and magnetic properties of each NP were fully investigated through x-ray diffraction (XRD), Transmission Electron
Microscopy (TEM) and Vibrating Sample Magnetometer (VSM). The XRD data showed diffraction peaks related to the crystalline spinel phase. No additional phase was observed, which
evidences the purity of the nanostructure synthesized. The TEM micrographs displayed monodisperse NPs with spherical morphology. The average sizes of CoFe2O4, Co0.5Zn0.5Fe2O4
and ZnFe2O4 NPs were found to be 6.87 ± 0.05 nm, 5.18 ± 0.01 nm and 11.52 ± 0.09 nm, respectively. The VSM data indicated the nanostructures are superparamagnetic at room
temperature. Afterwards, the antifungal properties of the Co/Zn-based ferrite NPs against Botrytis cinerea were tested. So, the inhibition of mycelial growth by different concentrations (45
– 360 ppm) of NPs was measured. The most effective nanostructure was found to be CoFe2O4 with an EC50 value of 265 ppm. To go further and elucidate how the NPs are affecting B.
cinerea, reactive oxygen species (ROS) production was measured. The results indicated that the CoFe2O4 monodisperse NPs are able to induce a burst of ROS in B. cinerea, promoting
damage cellular. 

![](https://s3.eu-west-1.amazonaws.com/underline.prod/uploads/markdown_image/1/image/acd208162929898417ff9472572af142.png)

Easy synthesis of monodisperse Co/Zn based ferrite nanoparticles and their antifungal activities on Botrytis cinerea

The use of magnetic nanoparticles for cancer cell destruction is widely known due to their applications such as magnetic hyperthermia and magneto mechanical actuation
(MMA). Previously, we presented our results regarding a new type of magnetic particles (MPs), i.e. Fe-Cr-Nb-B MPs, prepared by wet milling of superferromagnetic precursor glassy
ribbons, designed for cancer treatment by MMA [1]. These MPs have an important shape anisotropy and a large saturation magnetization, which generates an improved torque in a rotating
magnetic field, producing important damages on the cellular viability of cancer cells. Inspired by these findings, we tested the possibility of using magnetic nanowires (NWs) that have a
higher shape anisotropy. Furthermore, the Fe-Co alloy that we propose has high saturation magnetization values. We prepared Fe64.5Co35.5 NWs with lengths of 4 microns by electrolytic
deposition in alumina membranes with a pore diameter of 200 nm.
The Fe-Cr-Nb-B MPs and Fe-Co nanowires were tested on human osteosarcoma cells (HOS) using various concentrations of particles and found that both are biocompatible in vitro.
Subsequently, we studied the effect of MMA in a rotating 80 Oe magnetic field and frequency of 2 Hz on the viability of HOS. We used MPs and NW with different concentrations, and
exposure time of 30 minutes, applied 24 hours after the introduction of the MPs and NWs into cell culture media. The results indicated that with a concentration of 1 mg/ml of MPs and 0.1
mg/ml of NWs, respectively, the cell viability decreased to about 6-7%. The concentration of NWs needed to induce cancer cell death is 10 times lower than the one needed for MPs. It is
worth mentioning that although NWs are more efficient when using low quantities, due to their higher magnetization and anisotropy, the magnetic nanoparticles are better internalized and
metabolized by cells. Therefore, MPs can be better targeted in tissues harder to reach than NWs. The latter are also harder to control, being more suitable for superficially-developed cancer
tissues.
Supported by (UEFISCDI) Contract no. PCE20/2021 (PN-III-P4-ID-PCE-2020-2381). 

**References:**
 1. H. Chiriac et al. Sci. Rep., 8.11538 (2018)

Cancer cell destruction by magneto mechanical actuation of nanowires compared with nano/micromagnetic particles

Maintenance of homoeostasis in human body is a very important indicator in all cell activities. Persistent acid-base imbalance leads to diseases such as metabolic and
respiratory acidosis or alkalosis. When exposed to a disease, various immune cells are activated due to the inflammatory response, and particularly T cells play a role in inducing apoptosis
of mutated cells such as tumor cells. When the activity of T cells is very low, infection by external invasion is easy, and on the contrary, excessive activation lead to chronic inflammation
caused by autoimmune diseases. Many clinical studies related to pulsed magnetic field (PMF) demonstrated its efficacy in reducing pain, improving blood circulation, as well as blood's
acid-base balance.[1-2] Therefore, our study has tried to investigate the influence of PMF on the regulation of acid-base homeostasis in EL4 cells, which are T cells formed through
lymphoma generated by inducing 9,10-dimethyl-1,2-benzanthrance to C57BL mice. In addition, we tried to explain the role of PMF on immune cell activity by measuring the level of proinflammatory
cytokines such as TNF-α and INF-γ in culture supernatants. EL4 cells were cultured in a DMEM medium supplemented with 10% FBS and 1% penicillin at a concentration
of 5.5 × 104 cells/ml in an incubator at 37 °C and 5% CO2 condition. Our PMF stimulator has the maximum intensity of 4700G at a transition time of 222 μs with pulse intervals of 1Hz.
The homoeostasis in pH was improved as the intensity of PMF increases.(Fig.1) Cell viability decreased by 32% after PMF stimulus of 4700G. It was observed that the concentration of
TNF-α and INF-γ, a cytokine related to inflammation, also decreased as the strength of PMF increased. These results suggest that PMF stimulus improves the anti-inflammatory effect,
therefore, it is thought to affect the immune system of the human body by balancing the activation and suppression of immune cells. For clinical use, our study might suggest non-invasive
PMF can be developed as a medical devices modulating immune system, although it is necessary to optimize the PMF conditions such as pulse shape, duration, or repetition rate. 

**References:** 

[1] N. M. Shupak, F. S. Prato & A. W. Thomas, Neurosci. Lett. Vol. 363, p.157–162(2004). 
[2] S. Bang & H. Lee, AIP Advances, 11(1), 015242(2021). 

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Effect of pulsed magnetic field in murine T lymphoma EL4 cells

This work describes the use of magnetoresistive (MR) sensors coupled with a portable platform for the detection of dengue virus (DENV), a mosquito-borne infection
endemic to low- and middle-income countries, affecting 100-400 million people each year[1]. Nowadays, diagnosis relies on molecular or serological tests. Still, these tests remain discrete
(RNA vs. antibodies), and tend to be complex and/or expensive, requiring expert staff and fully equipped laboratories. As such, this work aims to combine both assays in a single analysis
by simultaneously detecting DENV RNA and anti-DENV antibodies using a portable platform[2,3]. A spin-valve based biochip was designed and functionalized with specific DNA oligo
probes and secondary antibodies (Fig1A)[4]. Extracted RNA and serum samples were provided by INSA-CEVDI and used as targets in molecular and serological assays, respectively. In
both assays, streptavidin coated 250 nm magnetic nanoparticles were used for biolabeling. The measurement output is represented by a voltage drop (dV/V) proportional to the number of
captured target molecules (Fig1B). However, to increase the dynamic range of the assays, the percentage difference of dV/V signals obtained using different immobilization
strategies/probes, was taken as the final output signal. Using the MR-platform, individual tests were carried out for the detection of DENV RNA and anti-dengue human antibodies. The
RNA target was detected down to a few hundreds of pM (Fig2A). For the serological response, a calibration curve with an LOD of 1.38 nM was achieved. Infected patients’ serum was also
tested for anti-DENV antibodies, obtaining a sensitivity of 100% and a specificity of 92%(Fig2B). Finally, simultaneous detection of antibodies and RNA was successfully achieved on the
same chip, showing no differences to the individual assays. To increase the multiplexing capability of the assay, a biochip with 144 sensors and multi-level contact layers was developed
and is under testing using DENV as a model disease. This chip design will allow the simultaneous discrimination of various viruses endemic in the same regions. 

**References:** 

[1] Who.int. 2022. Dengue and severe dengue. [online] Available at: <https://www.who.int/news-room/fact-sheets/detail/dengue-and-severe-dengue> [Accessed 14 June 2022]. 
[2] J. Germano et al., Sensors 9, 4119 (2009). 
[3] V. C. Martins et al., Biosensors and Bioelectronics 24, 2690 (2009). 
[4] D. C. Albuquerque et al., Biosensors and Bioelectronics 210, 114302 (2022). 

![](https://s3.eu-west-1.amazonaws.com/underline.prod/uploads/markdown_image/1/image/2c3b21878c8c8bcc8772e673561d7b96.png)

Portable Magnetoresistive Device for the Simultaneous Detection of Dengue RNA and Anti dengue Antibodies

In this in vivo study, we have used Magnetic Pen or MagPen (see Fig. 1(a)) to stimulate the rat sciatic nerve which led to the report of the dosage response curve for
micromagnetic stimulation (μMS). As reported earlier [1], the MagPen prototype consists of sub-mm size microcoil (μcoil) at its tip (see Fig. 1(b)). When driven by alternating current, this
μcoil generates a time-varying magnetic field, which induces an electric field on any conductor (here, the sciatic nerve) according to Faraday’s Law of electromagnetic induction. This
induced electric field activates the nerve. This work reports how the directionality of the magnetic μcoil plays a direct role in activating nerves directly observed in hind limb muscle
twitches. These limb twitches have been quantitatively characterized using electromyography (EMG) recordings. Furthermore, we have studied how on varying the amplitude and
frequency of the micromagnetic stimuli, alters hind limb muscle movements. Thereby, a dosage response curve for μMS was generated. The highlight of this dosage response curve is that,
at higher frequencies, significantly smaller amplitudes of MagPen stimuli can trigger limb twitches. This frequency-dependent nerve activation can be explained directly from Faraday’s
Law as the magnitude of the induced electric field used in neuromodulation is proportional to frequency. In our previous work of in vitro μMS of rat hippocampal slices [1], we explained
the frequency-dependent, low-power activation of μMS through numerical simulations. This work further corroborates the same concept through experiments. Implantable μMS is a novel
neuromodulation technique which is still in its infancy and aims to address the potential drawbacks of electrical implants in terms of MRI compatibility and biofouling. Since the induced
electric fields from these magnetic μcoils are not in galvanic contact with the nerve, μMS offers flexibility in applying waveforms to drive these magnetic implants (see Fig. 1(c)).
Fig 1. (a) Different directionalities of the MagPen prototype. Only Type V can activate the sciatic nerve. (b) Size of the sub-mm size μcoil implant compared to a rice grain. (c) The
waveform that activated the nerve. 

**References:** 

[1] Saha R., Faramarji S et al. (2022) Strength-frequency curve for micromagnetic neurostimulation (μMS) through EPSPs and numerical modeling. J. Neural Eng. 19 016018. 

![](https://s3.eu-west-1.amazonaws.com/underline.prod/uploads/markdown_image/1/image/d7ec5f614ee8478c564bc13b793a6b10.png)

In vivo Micromagnetic Stimulation of the Rat Sciatic Nerve

Nanoscale spintronics devices can revolutionize computer logic and memory units. Interestingly, paramagnetic nanostructures strongly exchange coupled with two ferromagnetic electrodes can yield novel forms of magnetic materials. However, there is a knowledge gap about the role of the number of paramagnetic nanostructures on the various properties of whole spintronics devices. To make this study relevant to the experimentally attainable device structure, we focus on the magnetic tunnel junction (MTJ) based spintronics device architecture. Under this approach, paramagnetic nanostructures are placed along the MTJ perimeter. We assume that the tunnel barrier of the MTJ does not allow any leakage current or exchange coupling, and paramagnetic nanostructures dictate the exchange coupling between the ferromagnetic electrodes. Also, the width of the ferromagnetic electrodes is governed by the number of paramagnetic nanostructures. This study systematically varied the number of nanostructures from 1 to 625 (25 x 25). The overall device was represented by a Heisenberg 3D model containing five atomic layer thick ferromagnetic electrodes. The number of paramagnetic nanostructures governed the width of the ferromagnetic electrodes. For instance, the device with a single nanostructure and 5 x 5 nanostructure possessed FM electrodes with one atom and five atom width, respectively. The paramagnetic nanostructures — sandwiched between the two FM electrodes — were placed on the perimeter of the 5 x 5 square with an empty space inside the square. The empty space shows the presence of an insulating spacer needed to provide the physical separation to enable paramagnetic nanostructures to control the spin dynamics of the device . The strength of exchange coupling between the paramagnetic nanostructure and ferromagnetic electrodes was fixed to be antiferromagnetic, consistent with experimental observations with analogous devices . We observed that thermal energy strongly influenced the temporal evolution of the equilibrium state of devices. The device with a single paramagnetic nanostructure struggled to align the left ferromagnet (Left-FM) and right ferromagnetic electrode (Right -FM) at low thermal energy of kT = 0.01. At higher thermal energy, devices with a single paramagnetic nanostructure underwent significant fluctuations. The device with a 5 x 5 paramagnetic structure also had difficulty attaining the fully antiparallel state at low thermal energy of kT = 0.01. However, at higher thermal energy of kT = 0.1, 5 x 5 paramagnetic nanostructure started producing conclusive antiparallel ferromagnetic electrodes. This paper will discuss the full range of paramagnetic nanostructures up to 25 x 25 sizes over the thermal energy range from 0.01 to 0.1. To estimate the spatial impact range of the nanostructures, we also investigated the spatial correlation factor for each case. In addition, we also compute the spatial magnetic susceptibility and heat capacity of the device. References: 1. Tyagi, P.; Riso, C.; Friebe, E., Magnetic Tunnel Junction Based Molecular Spintronics Devices Exhibiting Current Suppression At Room Temperature. Organic Electronics 2019, 64, 188-194. 2. Savadkoohi, M.; Dahal, B. R.; Grizzle, A.; D'Angelo, C.; Tyagi, P., Interaction between magnetic molecules and two ferromagnetic electrodes of a magnetic tunnel junction (MTJ). Journal of Magnetism and Magnetic Materials 2021, 529, 167902.

A Monte Carlo Study of Paramagnetic Nanostructure Coupled with Two Ferromagnetic Electrodes of a Cross-Junction Shaped Spintronics Device at Different Thermal Energies

A new approach of pulsed current-voltage (I-V) protocol has been applied that reveals current settling. This protocol minimizes metal-FE interface charging and directly reveals amplitude-dependent polarization continuation. Measurement of electroresistance ratio shows it is possible to detect opposite-state or same-state polarization, but not without partial polarization change.

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Development of Novel Transcranial Magnetic Stimulation Technique Using High frequency Modulation for Treatment of Parkinson’s Disease

Biocompatible Superparamagnetic NiFe2O4 Nanoparticles for Magnetic Hyperthermia Treatment using a ZVS Circuit

Relationship Between Resting Motor Threshold and Neuroanatomy in Mild to Moderate Traumatic Brain Injury Patients during Transcranial Magnetic Stimulation

Temporal Interference for Increased Focality of Transcranial Magnetic Stimulation

Analysis of Fe element and interferon gamma in serum and spleen homogenates after injection of silica coated magnetic nanoparticles (SiO2 Fe3O4)

Easy synthesis of monodisperse Co/Zn based ferrite nanoparticles and their antifungal activities on Botrytis cinerea

Cancer cell destruction by magneto mechanical actuation of nanowires compared with nano/micromagnetic particles

Effect of pulsed magnetic field in murine T lymphoma EL4 cells

Portable Magnetoresistive Device for the Simultaneous Detection of Dengue RNA and Anti dengue Antibodies

In vivo Micromagnetic Stimulation of the Rat Sciatic Nerve

A Monte Carlo Study of Paramagnetic Nanostructure Coupled with Two Ferromagnetic Electrodes of a Cross-Junction Shaped Spintronics Device at Different Thermal Energies

Pulsed Current-Voltage Protocol to Reveal Polarization-Continuation in Ferroelectric Memory Implications for Partial State Storage

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