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![Brownian relaxation time versus applied external magnetic field, for the average nanoparticle diameters dm=10nm\documentclass[12pt]{minimal} \usepackage{amsmath} \usepackage{wasysym} \usepackage{amsfonts} \usepackage{amssymb} \usepackage{amsbsy} \usepackage{mathrsfs} \usepackage{upgreek} \setlength{\oddsidemargin}{-69pt} \begin{document}$$d_{{\text{m}}} = 10{\text{ nm}}$$\end{document} and dm=22nm\documentclass[12pt]{minimal} \usepackage{amsmath} \usepackage{wasysym} \usepackage{amsfonts} \usepackage{amssymb} \usepackage{amsbsy} \usepackage{mathrsfs} \usepackage{upgreek} \setlength{\oddsidemargin}{-69pt} \begin{document}$$d_{{\text{m}}} = 22{\text{ nm}}$$\end{document}, nanoparticle volume fraction in colloid f=0.05\documentclass[12pt]{minimal} \usepackage{amsmath} \usepackage{wasysym} \usepackage{amsfonts} \usepackage{amssymb} \usepackage{amsbsy} \usepackage{mathrsfs} \usepackage{upgreek} \setlength{\oddsidemargin}{-69pt} \begin{document}$$f = 0.05$$\end{document}](publication/371833547/figure/fig5/AS:11431281224151096@1708141290049/Brownian-relaxation-time-versus-applied-external-magnetic-field-for-the-average.png)
Brownian relaxation time versus applied external magnetic field, for the average nanoparticle diameters dm=10nm\documentclass[12pt]{minimal} \usepackage{amsmath} \usepackage{wasysym} \usepackage{amsfonts} \usepackage{amssymb} \usepackage{amsbsy} \usepackage{mathrsfs} \usepackage{upgreek} \setlength{\oddsidemargin}{-69pt} \begin{document}$$d_{{\text{m}}} = 10{\text{ nm}}$$\end{document} and dm=22nm\documentclass[12pt]{minimal} \usepackage{amsmath} \usepackage{wasysym} \usepackage{amsfonts} \usepackage{amssymb} \usepackage{amsbsy} \usepackage{mathrsfs} \usepackage{upgreek} \setlength{\oddsidemargin}{-69pt} \begin{document}$$d_{{\text{m}}} = 22{\text{ nm}}$$\end{document}, nanoparticle volume fraction in colloid f=0.05\documentclass[12pt]{minimal} \usepackage{amsmath} \usepackage{wasysym} \usepackage{amsfonts} \usepackage{amssymb} \usepackage{amsbsy} \usepackage{mathrsfs} \usepackage{upgreek} \setlength{\oddsidemargin}{-69pt} \begin{document}$$f = 0.05$$\end{document}
Source publication
Magnetic nanofluids find application in various fields, including magnetic hyperthermia, which holds significant potential for non-invasive cancer treatment. The dynamics of magnetic nanoparticle systems under the influence of a magnetic field plays a crucial role in all applications, particularly in magnetic hyperthermia, and has been the subject...
Citations
... Magnetic fluid hyperthermia (MFH) therapy is a type of thermotherapy that uses MNPs deposited in tumor tissues and creates a friction resulting from magnetic moment rotation (Ne´el relaxation) and nanoparticle rotation induced by alternating magnetic field (Brownian relaxation) [6] to surrounding tissues or to provide local heat to organs [7]. This heat can raise the local tissue temperature above 43˚C and cause cancer cells to undergo apoptosis or necrosis without significant damage to normal cells (see Figure 1). ...
This study aims to eliminate magnetic field leakage at 100 kHz with active shielding in Magnetic Fluid Hyperthermia (MFH) system. First of all, the structural and operational features of the MFH system were analyzed. Then, the active regions of the coils were determined, graphical results were obtained and the designs were compared with each other. We first simulated the magnetic field distribution of a circular coil active shielding system by the commercial software tool COMSOL Multiphysics. Secondly, a single D-shape shielding was configured in the MFH system and the size and location of the shielding were examined. The magnetic field attenuation percentages of the methods in the x, y, z axes and the target region selected as the representative tumor region were compared. The simulation results show that the shielding ability of the double D-shape shielding type is better in the x and y axes than the other coil types (51.43% for the x-axis and 95.77% for the y-axis). The fact that the attenuation percentage of this shielding type in the target region is 0.0287% is a secondary advantage. It has been observed that the attenuation in the z-axis is higher in other shielding types, but the attenuation percentage in the target region also increases.
... Magnetic fluid hyperthermia (MFH) therapy is a type of thermotherapy that uses MNPs deposited in tumor tissues and creates a friction resulting from magnetic moment rotation (Ne´el relaxation) and nanoparticle rotation induced by alternating magnetic field (Brownian relaxation) [6] to surrounding tissues or to provide local heat to organs [7]. This heat can raise the local tissue temperature above 43˚C and cause cancer cells to undergo apoptosis or necrosis without significant damage to normal cells (see Figure 1). ...
This study aims to eliminate magnetic field leakage at 100 kHz with active shielding in Magnetic Fluid Hyperthermia (MFH) system. First of all, the structural and operational features of the MFH system were analyzed. Then, the active regions of the coils were determined, graphical results were obtained and the designs were compared with each other. We first simulated the magnetic field distribution of a circular coil active shielding system by the commercial software tool COMSOL Multiphysics. Secondly, a single D-shape shielding was configured in the MFH system and the size and location of the shielding were examined. The magnetic field attenuation percentages of the methods in the x, y, z axes and the target region selected as the representative tumor region were compared. The simulation results show that the shielding ability of the double D-shape shielding type is better in the x and y axes than the other coil types (51.43% for the x-axis and 95.77% for the y-axis). The fact that the attenuation percentage of this shielding type in the target region is 0.0287% is a secondary advantage. It has been observed that the attenuation in the z-axis is higher in other shielding types, but the attenuation percentage in the target region also increases.
