France



&lt;br/&gt;* Corresponding Author: ozan.akdogan@eng.bau.edu.tr&lt;br/&gt;Magnetically actuated milli swimmers/robots, especially in biomedical field, are used in many applications such as cargo delivery and sensing applications. In this study, magnetically actuated small-scale swimmers have been developed by using Fe flakes embedded in photocurable polymeric resin. Our future aim will be to merge the developed small-scale swimmers with minimally invasive biomedical applications. The 3D printed structures were fabricated using a photocurable polymeric resin acquired from Wanhao (China). In addition to monomers and oligomers, the chemical composition of this resin includes a photo initiator that responds to a certain wavelength of UV light (405nm) to change the polymerization conformation of the resin into a solid state. Then, structures were printed by using the Anycubic Photon digital light processing (DLP) 3D printer with an exposure time of 10 seconds and a layer thickness of 0.05 mm. Different sizes and shapes of (length of the ship1, ship2 and square, 5.6 mm, 2.7 mm and 0.6mm, respectively) the magnetically actuated swimmers were 3D printed; two ellipsoid shaped swimmers with different sizes and a cubic shaped swimmer. An ellipsoid and cubic shape were chosen for its unique morphology that gives it hydrodynamic superiority over traditional spheres [1]. The combination of polymeric materials such as resins with magnetic particles expand the robot’s functionality [2]. The Fe flakes have been previously tested with functional polymer composites for extrusion-based 3D printing [3]. In this study, Fe flakes (100-200nm thickness and ~10μm lateral size) were incorporated into the photocurable resin to actuate robots in response to the magnetic field. The X-Ray Diffraction and vibrating sample magnetometer analysis of Fe flakes showed that Fe flakes have BCC crystal symmetry and soft ferromagnetic response, respectively. (Fig 1a and b). A 0.2 g of Fe flakes and 40 ml of the polymeric resin were mixed to synthesize 0.5% wt/vol concentration. The printed structures were cured by UV light exposure. The incorporated Fe flakes were visualized by a light microscope (Fig.1c, d and e). The movement characteristics of the swimmers in a magnetic field gradient were tested by a homemade electromagnetic setup with a maximum field of 336 Gauss. The 3D printed magnetic structures’ movement speed in DI water were calculated experimentally as 12.27±1.89 mm/s, 11.92±1.9mm/s and 8.29±1.5mm/s for milli ship1, milli ship 2 and sub-mm square, respectively. The theoretical swimming speed values were calculated according to the equations below; the magnetic force acting on the robots by a gradient, in which m and B are the magnetic moment and the field, respectively (3) and the drag force (Stoke’s Law), in which, η, the viscosity of DI water (8.9x10-4 Pa.s), R and v are the hydrodynamic radius and velocity of the objects, respectively (4).&lt;br/&gt;&lt;br/&gt;Fm = ▽ (m . B) [3]&lt;br/&gt;Fd= 6π η R v [4]&lt;br/&gt;&lt;br/&gt;Theoretical speeds calculated for milli ship1, milli ship2 and sub-mm square were 13.54 mm/s, 9.9 mm/s and 10 mm/s, respectively. The different shaped milli swimmers were actuated by electromagnetic system and tracked (Fig.2). Magneto-responsive robots movement abilities will be tested against specific obstacles with different shapes and magnetic materials as well.&lt;br/&gt;&lt;br/&gt;Acknowledgements&lt;br/&gt;This work was supported by BAP.2019-03.11(Bahcesehir University).

**References:**

1. Carrasco, B. et al., Hydrodynamic Properties of Rigid Particles: Comparison of Different Modeling and Computational Procedures., Biophysical Journal, 76, 3044–3057, (1999)&lt;br/&gt;2.Song, S. W., Jeong, Y. &amp; Kwon, S., Photocurable polymer nanocomposites for magnetic, optical, and biological applications., IEEE J. Sel. Top. Quantum Electron. 21, 324–335, (2015)&lt;br/&gt;3.Zirhli, O. et al. Fabrication and Characterization of Fe16N2 Micro-Flake Powders and Their Extrusion-Based 3D Printing into Permanent Magnet Form., Adv. Eng. Mater. 22, (2020)&lt;br/&gt;4. Pankhurst, Q. A. et al., Applications of magnetic nanoparticles in biomedicine., J. Phys. D. Appl. Phys. 36, 167-181, (2003)&lt;br/&gt;5. L.D. Landau, I.Akhiezer, M.Lifshitz, Chapter XV-Viscosity, General Physics, 341-366, (1967)

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/fcd27136415135330892ad5e005270ef.png)
Figure 1. a) VSM and b) XRD analysis of Fe flakes given. Light microscopy image of Fe flakes nanoparticle distribution 3D-printed structures c) Milli square. d) Milli ship. e) Texture of printed structures.

![](https://assets.underline.io/uploads/markdown_image/1/image/66e69fa67a75757fe051df0e36d11fd7.jpg)
Figure2. The swimming pathway of structures in the DI water are shown in the figure respectively. a) Square, b) Ship 1 and c) Ship 2 (0.6 mm 5.6 mm, 2.7 mm, respectively). d) The swimming trajectory snapshots of robots under the magnetic field.

INTERMAG 2021

 Development and characterization of magnetically actuated milli-robots by Stereolithography

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* Corresponding Author: ozan.akdogan@eng.bau.edu.tr Magnetically actuated milli swimmers/robots, especially in biomedical field, are used in many applications such as cargo delivery and sensing applications. In this study, magnetically actuated small-scale swimmers have been developed by using Fe flakes embedded in photocurable polymeric resin. Our future aim will be to merge the developed small-scale swimmers with minimally invasive biomedical applications. The 3D printed structures were fabricated using a photocurable polymeric resin acquired from Wanhao (China). In addition to monomers and oligomers, the chemical composition of this resin includes a photo initiator that responds to a certain wavelength of UV light (405nm) to change the polymerization conformation of the resin into a solid state. Then, structures were printed by using the Anycubic Photon digital light processing (DLP) 3D printer with an exposure time of 10 seconds and a layer thickness of 0.05 mm. Different sizes and shapes of (length of the ship1, ship2 and square, 5.6 mm, 2.7 mm and 0.6mm, respectively) the magnetically actuated swimmers were 3D printed; two ellipsoid shaped swimmers with different sizes and a cubic shaped swimmer. An ellipsoid and cubic shape were chosen for its unique morphology that gives it hydrodynamic superiority over traditional spheres [1]. The combination of polymeric materials such as resins with magnetic particles expand the robot’s functionality [2]. The Fe flakes have been previously tested with functional polymer composites for extrusion-based 3D printing [3]. In this study, Fe flakes (100-200nm thickness and ~10μm lateral size) were incorporated into the photocurable resin to actuate robots in response to the magnetic field. The X-Ray Diffraction and vibrating sample magnetometer analysis of Fe flakes showed that Fe flakes have BCC crystal symmetry and soft ferromagnetic response, respectively. (Fig 1a and b). A 0.2 g of Fe flakes and 40 ml of the polymeric resin were mixed to synthesize 0.5% wt/vol concentration. The printed structures were cured by UV light exposure. The incorporated Fe flakes were visualized by a light microscope (Fig.1c, d and e). The movement characteristics of the swimmers in a magnetic field gradient were tested by a homemade electromagnetic setup with a maximum field of 336 Gauss. The 3D printed magnetic structures’ movement speed in DI water were calculated experimentally as 12.27±1.89 mm/s, 11.92±1.9mm/s and 8.29±1.5mm/s for milli ship1, milli ship 2 and sub-mm square, respectively. The theoretical swimming speed values were calculated according to the equations below; the magnetic force acting on the robots by a gradient, in which m and B are the magnetic moment and the field, respectively (3) and the drag force (Stoke’s Law), in which, η, the viscosity of DI water (8.9x10-4 Pa.s), R and v are the hydrodynamic radius and velocity of the objects, respectively (4). Fm = ▽ (m . B) [3] Fd= 6π η R v [4] Theoretical speeds calculated for milli ship1, milli ship2 and sub-mm square were 13.54 mm/s, 9.9 mm/s and 10 mm/s, respectively. The different shaped milli swimmers were actuated by electromagnetic system and tracked (Fig.2). Magneto-responsive robots movement abilities will be tested against specific obstacles with different shapes and magnetic materials as well. Acknowledgements This work was supported by BAP.2019-03.11(Bahcesehir University).

**References:**

1. Carrasco, B. et al., Hydrodynamic Properties of Rigid Particles: Comparison of Different Modeling and Computational Procedures., Biophysical Journal, 76, 3044–3057, (1999) 2.Song, S. W., Jeong, Y. & Kwon, S., Photocurable polymer nanocomposites for magnetic, optical, and biological applications., IEEE J. Sel. Top. Quantum Electron. 21, 324–335, (2015) 3.Zirhli, O. et al. Fabrication and Characterization of Fe16N2 Micro-Flake Powders and Their Extrusion-Based 3D Printing into Permanent Magnet Form., Adv. Eng. Mater. 22, (2020) 4. Pankhurst, Q. A. et al., Applications of magnetic nanoparticles in biomedicine., J. Phys. D. Appl. Phys. 36, 167-181, (2003) 5. L.D. Landau, I.Akhiezer, M.Lifshitz, Chapter XV-Viscosity, General Physics, 341-366, (1967)

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/fcd27136415135330892ad5e005270ef.png)
Figure 1. a) VSM and b) XRD analysis of Fe flakes given. Light microscopy image of Fe flakes nanoparticle distribution 3D-printed structures c) Milli square. d) Milli ship. e) Texture of printed structures.

![](https://assets.underline.io/uploads/markdown_image/1/image/66e69fa67a75757fe051df0e36d11fd7.jpg)
Figure2. The swimming pathway of structures in the DI water are shown in the figure respectively. a) Square, b) Ship 1 and c) Ship 2 (0.6 mm 5.6 mm, 2.7 mm, respectively). d) The swimming trajectory snapshots of robots under the magnetic field.

technical paper

Magnetic hyperthermia is one of the most promising biomedical applications of magnetic nanoparticles (NP) and is intended to be alternative to cancer therapies based on drug delivery and radiotherapy. It is based on the fact that magnetic NP dissipate heat when an oscillating magnetic field is applied to them in a quantity (specific absorption rate, SAR) that is closely related to the area of the hysteresis loop. The main problem in the field has become to find the suitable range of parameters that maximize SAR for a given material [1], SAR depends of course on the amplitude of the applied magnetic field and its frequency, but also on intrinsic parameters of the NP such as saturation magnetization, anisotropy, shape and size [2]. Although the role of external parameters is somehow well contrasted, there is still ongoing controversy on the role that dipolar interactions (DI) and aggregation state of the assemblies play on SAR. We will present results of Monte Carlo simulations of hysteresis loops of interacting NP assemblies in the macrospin approximation [3]. We will present first results of different regular spatial arrangements of NP, showing the influence of interparticle separation and particle size on SAR. Next, we will study the case of randomly placed NP with varying concentrations mimicking experimentally found situations [4] (inside and at the surface of liposomes/cells, clusters). It is found that formation of chain-like arrangements or assemblies with prolate shapes, lead to considerable increases in SAR due to DI. Acknowledgements: Work supported by Spanish MINECO (PGC2018-097789-B-I00), Catalan DURSI (2017SGR0598) and EU FEDER funds (Una manera de hacer Europa) also CSUC for supercomputer facilities.

**References:**

[1] S.-H. Noh, et al. Nano Today 13, 61 (2017); R. Hergt et al. Nanotechnology 21, 015706 (2010). [2] B. Mehdaoui, et al.Phys. Rev. B 87, 174419 (2013); R. P. Tan et al.Phys. Rev. B 90, 214421 (2014); P. Hasse and U. Nowak Phys. Rev. B 85, 045435 (2012); P. V. Melenev et al. Phys. Rev. B 86, 104423 (2012). [3] C. Martínez-Boubeta et al.Scientific Reports 3, 1652 (2013). [4] Brollo et al., Phys. Chem. Chem. Phys. 20, 17829 (2018); D. Niculaes et al., ACS Nano 11, 12121 (2017)

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/e6cf5b763ca228f2ac9da0bc2351d2af.jpg)
Concentration dependence of the hysteresis loop area for different kinds of NP random assemblies.

 Aggregates and Dipolar Interactions in Nanoparticle Assemblies for Magnetic Hyperthermia

Magnetic nanoparticles are an important asset in many biomedical applications ranging from the local heating of tumours[1] to targeted drug delivery towards diseased sites[2]. Recently, magnetic nanoflowers showed a remarkable heating performance[3,4] in hyperthermia experiments thanks to their complex structure leading to a broad range of magnetic dynamics. To grasp their full potential and to better understand the origin of this unexpected heating performance, we propose the use of Kaczmarz’ algorithm[5] in interpreting magnetic characterisation measurements[6]. It has the advantage that no a priori assumptions need to be made on the particle size distribution, contrasting current magnetic interpretation methods that often assume a lognormal size distribution. Both approaches are compared on DC magnetometry, magnetorelaxometry and AC susceptibility characterisation measurements of the nanoflowers. We report that the lognormal distribution parameters vary significantly between data sets, whereas Kaczmarz’ approach achieves a consistent and accurate characterisation for all measurement sets. Additionally, we introduce a methodology to use Kaczmarz’ approach on distinct measurement data sets simultaneously. It has the advantage that the strengths of the individual characterisation techniques are combined and their weaknesses reduced, further improving characterisation accuracy. Our findings are important for biomedical applications as Kaczmarz’ algorithm allows to pinpoint multiple, smaller peaks in the nanostructure’s size distribution compared to the monomodal lognormal distribution. The smaller peaks permit to fine-tune biomedical applications with respect to these peaks to e.g. boost heating or to reduce blurring effects in images. Furthermore, the Kaczmarz algorithm allows for a standardised data analysis for a broad range of magnetic nanoparticle samples. Thus, our approach can improve the safety and efficiency of biomedical applications of magnetic nanoparticles, paving the way towards their clinical use.

**References:**

 [1] A. Espinosa, R. Di Corato, J. Kolosnjaj-Tabi, et al, ACS Nano, Vol. 10, p. 2436–2446 (2016) [2] K. T. Al-Jamal, J. Bai, J. T.-W. Wang, et al, Nano Letters, Vol. 16, p. 5652–5660 (2016) [3] P. Bender, J. Fock, C. Frandsen, et al, J. Phys. Chem. C, Vol.122, p. 3068–3077 (2018) [4] C. Blanco-Andujar, D. Ortega, P. Southern, et al, Nanoscale, Vol. 7, p. 1768–1775 (2015) [5] S. Kaczmarz, Bulletin International de l’Academie Polonaise des Sciences et des Lettres, Vol. 35, p. 355–357 (1937) [6] J. Leliaert, D. Schmidt, O. Posth, et al, Journal of Physics D: Applied Physics, Vol. 50, p.195002 (2017)

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/d71e9f523e4a62d6a20fc7c82d90f1d3.jpg)
Best combined fit to a) the magnetorelaxometry measurement data and b) imaginary part of the AC-susceptibility measurement data of suspended nanoflowers using a lognormal distribution and using Kaczmarz’ method. c) The obtained relaxation time distributions corresponding to the fits in panel a) and b).

 Advanced analysis of magnetic nanoflower measurements to leverage their use in biomedicine

Additive manufacturing of smart materials is a novel field in engineering. The ability to produce adaptable materials in varying geometries opens the door to the creation of a tremendous variety of new sensors, actuators and applications in domains including, transportation, energy production and medicine [1][2]. In this work, our objective is to build a ferromagnetic catheter by using additive manufacturing principles employed for the creation of smart materials (Fig. 1). Induction heating phenomena takes place in the ferromagnetic catheter due to the influence of a varying magnetic excitation field. This contactless heat source can be used to heal locally and destroy damaged blood vessels. According to medical specialists, thermal ablation of varicose veins requires a temperature close to 120°C and time constants lower than a few seconds [3]. First investigation results showed great potential for success using the low frequency induction heating (LFIH) method but further surveys and validation steps are still needed before in vivo testing can commence. Fig. 1 – Illustration of the ferromagnetic catheter. In this study, multi-physics simulation results, including ferromagnetic, thermal and fluid mechanics domains were compared to experimental data, then conclusions are proposed to establish the most adapted magnetic waveform (frequency) and its influence on the human tissues. In our processs, heat is transferred through a contactless method. The flexible 3D printed ferromagnetic catheter is subjected to an alternating magnetic excitation. Under the influence of the magnetic excitation, eddy currents are generated through the catheter creating heat. First published results [4][5] describing this technique have experimentally demonstrated the feasibility of heat generation but the conditions tested and simulated were still far from the in vivo environment. In this study, we go deeper into the investigation process, we propose simulation results (magnetic, thermal …) under much realistic experimental conditions. In [4], the authors limit the magnetic excitation signal to a few kHz. The purpose is to avoid undesired charge displacements in the surrounding tissue, but this restriction is strictly assumption based and further investigations must be under-taken to determine the optimal value for ablation while minimizing charge displacement. No further investigations have been proposed to establish a significant cutoff frequency. In this new research, a ferromagnetic model for the simulation of the ferromagnetic composite magnetic behavior is developed first. This model is based on previous work on the same topic [6]-[8] and it investigates the frequency dependence of the composite hysteresis area, i.e. the heat generated through the LFIH influence. Next, comparisons between the model and experimental situations are investigated to set the ferromagnetic model parameters and to establish the most efficient LFIH frequency. Finally, multi-physics simulation results combined with experimental tests are reviewed to predict the ferromagnetic composite’s behavior on living tissues under the influence of the optimized magnetic excitation. Before validating the ferromagnetic catheter as a realistic treatment method for varicose veins, special attention must be given to the undesired charges or ionic displacements in the healthy surrounding tissues causing local temperature elevations and degradations. A compromise between treatment and negative effects on surrounding tissue must be made to establish the best working frequency. Numerical simulations are proposed to establish the optimized configuration of the magnetic source (frequency, amplitude) and of the ferromagnetic catheter behavior, these results constitute a huge step toward a first medical test.

**References:**

[1] Standard A. F2792, Pa, USA: ASTM International (2012) [2] G.N. Levy & al., CIRP Annals-Manuf. Technol., vol. 52 iss.2, pp. 589-609 (2003) [3] S. Nehemiah & al., Cochrane Library, iss. 13 (2013) [4] Z. Xiang & al., polymers 2020, 12(2), 386 (2020) [5] Z. Xiang & al., Mat. & Des., Vol. 174, 107804 (2019) [6] M. A. Raulet & al., IEEE Transactions on Magnetics, vol. 40, n° 2, pp. 872 – 875 (2004) [7] Z. Xiang & al., IEEE Trans. on. Mag, IEEE int. Mag. Conf. (INTERMAG), Singapore (2018) [8] B. Gupta & al., Proc. of the 21st int. conf. on the comp. of electromag. fields COMPUMAG, Daejeon (S. Korea), (2017)

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/7cd27e86849e75379de11a4ef8f53341.jpg)

 Low frequency Induction heating of a ferromagnetic catheter for the varicose veins treatment: study of feasibility

Mn-doped ferrite nanoparticles are promising materials for applications in biomedicine as they exhibit better properties for some biomedical applications than non-doped magnetite or maghemite. [1] The thermal decomposition of metal precursors in an organic solvent is arguably the best method in terms of size control and the magnetic properties of the so-obtained materials. It provides hydrophobic nanoparticles that must be transferred to water through surface modification procedures before their use in biomedicine. In this work, Mn-doped ferrite nanoparticles have been synthesized by thermal decomposition changing systematically the Mn/Fe ratio of the metal precursors. Then, they have been transferred to the aqueous phase through ligand substitution with dimercaptosuccinic acid and dopamine. We show that the synthesis and post-synthesis manipulations lead to changes in the composition. During the thermal decomposition process, Mn is incorporated in the nanoparticles in a relatively lower amount than Fe and, then, during the surface modification step both Mn and Fe ions leach out from the nanoparticles (Figure 1). This alteration of the chemical identity of the nanoparticles have substantial implications for their subsequent application because small variations in the Mn/Fe ratio have a strong impact on properties like the saturation magnetization, blocking temperature, contrast enhancement for magnetic resonance imaging, magnetic heating, as well as on the cytotoxicity.[2]

**References:**

[1] L. Yang et al., Chem. Mater., Vol. 29, p.3038 (2017). [2] D. García-Soriano et al., J. Colloid Interf. Sci., Vol. 578, p.510 (2020).

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/a4b3867c47619b2ddabcdcd15281883f.jpg)
Scheme illustrating the changes in composition when the nanoparticles are transferred from an organic dispersion to an aqueous one.

 Cation leaching alters the properties of Mn nanoferrites for biomedical applications

The advances in synthesis methods and the research of new magnetic effects have been the driving forces propelling the use of magnetic nanostructures in several research fields. In biomedical applications, magnetic nanoparticles, usually in the superparamagnetic state, are mainly used in magnetic fluid hyperthermia (MFH) and as contrast agents. In contrast, the novel magnetic nanostructures (MNS) studied in this work present a unique spin arrangement in the magnetic ground state, namely spin-vortex or synthetic antiferromagnetic state. MNS are mainly produced using top-down lithography techniques and physical vapour deposition methods. They are not spherical, rather disc-shaped, like coins with nanometer dimensions. MNS showed promising results in cell separation, as a contrast enhancing agents in MRI and in magneto-mechanically induced cell annihilation. Magneto-mechanically induced cell annihilation is a comparable technique with MFH for cancer therapy, where instead of superparamagnetic particles, micro/nano-discs in the spin-vortex state or synthetic antiferromagnetic nanostructures are employed. The main advantages of this novel approach are the usage of weaker magnetic fields with lower frequencies, as well as the need for a lower concentration of particles. This scenario opens new possibilities in cancer therapy, having triggered a scientific interest for MNS with unique spin configurations suitable for biomedical applications [1]. In this work, we developed one subset of biocompatible magnetic nanostructures that exhibit a spin-vortex state with interest in analysing their application in magneto-mechanically induced cell death [2]. First, micromagnetic simulations, using mumax3 of sub-micron iron discs, were performed for different interdot distance and aspect-ratio (thickness/diameter), to better understand the magnetic behaviour of these nanostructures. Two sets of samples were studied: ideal circular discs and disc-shaped nanostructures (based on images of real samples). By analysing the nucleation and annihilation fields, as well as the magnetic susceptibility, it was found that the (ideal) discs could be considered as isolated for interdot distances greater than twice the radius of the disc (2R) [3]. We also found that discs with an aspect ratio between 5 and 15 should sustain the vortex state in remanence. Iron nano-discs, with a diameter of about 500 nm, were fabricated by electron beam evaporation on a Si substrate pre-patterned by interference lithography [4]. The discs, protected by bottom and top gold layers, were fully characterized with scanning electron microscopy (SEM), X-ray diffraction (XRD), superconducting quantum interference device (SQUID), magneto-optic Kerr effect (MOKE) and ferromagnetic resonance (FMR) techniques. The synthesized nanostructures showed the desired vortex state configuration. The obtained magnetic measurements are in good agreement with the micromagnetic simulations (Fig. 1). Then, the magnetic vortex nano-discs were released from the substrate by chemical etching of a sacrificial layer. Subsequently, cell viability and uptake assays were performed in a human leukaemia monocyte cell line (THP-1). Several concentrations of nano-discs were studied by flow cytometry. As a result, the discs were internalized by the cells and found to be innocuous to them, in the absence of an external magnetic field. Work supported by Horizon 2020 MSCA grant agreement No 734801, AEI PID2019-104604RB, IT1162-19, IF/01159/2015, SFRH/BD/148563/2019, POCI-01-0145-FEDER-028676/PTDC/CTM-CTM/28676/2017 and POCI-01-0145-FEDER-031302/PTDC/FIS-MAC/31302/2017.

**References:**

[1] L. Peixoto, R. Magalhães, D. Navas, S. Moraes, C. Redondo, R. Morales, J. P. Araújo, C.T. Sousa, Magnetic nanostructures for emerging biomedical applications. Appl. Phys. Rev., 7 (2020) 011310., [2] Y. Cheng, M. E. Muroski, D.C.M.C. Petit, R. Mansell, T. Vemulkar, R. A. Morshed, Y. Hana, I. V. Balyasnikova, C.M. Horbinski, X.Huang, L. Zhangc, R. P. Cowburn, M. S. Lesniak, J. Control. Release 223 (2016) 75. [3] L. Peixoto, C. Sousa, D. Navas, and J. P. Araújo, Micromagnetic study of the vortex state in sub-micron iron discs. EPJ Web of Conferences 233 (2020) 05002. [4] B. Mora, A. Perez-Valle, C. Redondo, M.D. Boyano, R. Morales, ACS Appl. Mater. Interfaces 10 (2018) 8165.

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/68db60cda0b5971db06d25b5e8aea1a8.jpg)

 Vortex nano-discs: from micromagnetic simulations to cancer cells internalization for magneto-mechanically induced damage applications.

Most patients who develop primary bone tumors require surgical intervention. In this respect, the design of a multifunctional material, used as bone substitute, is of high clinical interest to simultaneously treat cancer and promote bone regeneration. Bioactive glass (BG) nanoparticles are a promising material for bone tissue regeneration because when implanted, a hydroxyapatite layer is quickly formed onto their surface, bonding them to natural bone tissue [1,2]. By coupling the high bioactivity of large specific surface area bioactive glass particles with the heating ability of superparamagnetic iron oxide nanoparticles (SPIONs) under an alternating magnetic field [3], a multifunctional material could be designed and used to selectively destroy remaining or resurging cancer cells through hyperthermia treatment before promoting bone regeneration. In this scope, heterostructures consisting of SPIONs encapsulated in BG have been synthesized by sol-gel synthesis and characterized. The γ-Fe2O3@SiO2-CaO core-shell nanoparticles show promising hyperthermia and bioactivity properties, with a specific loss power (SLP) of 159 W/gFe and hydroxyapatite growth within 3 days [4]. At a concentration of 1 mgFe/mL, a temperature rise of 4 °C was achieved within 3 minutes, which could be suitable for cancer treatment. However, the heating power of these core-shell nanoparticles can still be improved, for example by increasing the SPIONs size. Indeed, the presence of a non-negligible amount of SPIONs with a diameter under 10 nm due to size dispersion is not optimal for hyperthermia [3]. Moreover, as evidenced in Figure 2, this sample present magnetic cores clustering, that is known to induce a decrease of the SLP value due to magnetic dipolar interactions [5]. Single-core NPs with a larger core size would thus be a better candidate for more efficient heating. In that respect, the core-shell particle structure has been modified in order to study the impact of core size and clustering on the hyperthermia properties. Using larger SPIONs led to an increase in SLP and an increasing percentage of single-core heterostructures. Magnetic core aggregation was also controlled by varying SPIONs concentration. The BG shell thickness was also modified, by varying the ratio between the magnetic cores and the silica precursor, because it could affect the heat dissipation of the magnetic particles in fluids [6].

**References:**

[1] J. R. Jones, Acta Biomaterialia, Vol. 9, p. 4457 (2013) [2] C. Vichery and J.-M. Nedelec, Materials, Vol. 9, p. 288 (2016) [3] F. Gazeau, M. Lévy and C. Wilhelm, Nanomedicine, Vol. 3 (6), p. 831 (2008) [4] X. Kesse, C. Vichery and J.-M. Nedelec, ACS Applied Materials & Interfaces, Vol. 12, p. 47820 (2020) [5] D. F. Coral, P. M. Zélis and M. B. Fernández van Raap, Langmuir, Vol. 32, p. 1201 (2016) [6] M. Hu, X. Wang and G. V. Hartland, Chemical Physics Letters, Vol. 372, p. 767 (2003)

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/b02198782be4bc51a96d6da5e26e6560.jpg)
Schematic representation of bone repair coupled with hyperthermia treatment

![](https://assets.underline.io/uploads/markdown_image/1/image/4483b6fa5add1c82a14e3acf79943747.jpg)
TEM image of γ-Fe2O3@SiO2-CaO core-shell nanoparticles

 Superparamagnetic and Bioactive Nanoparticles for Bone Cancer Treatment

Achieving new possibilities of cell manipulation or of other microbiological species is one of the most important tasks of the latest lab-on-a-chip devices [1-3]. High throughput and precise movement control are the figures of merit for new tools or chip designs. Common concepts consist of labeling biological cells or other biological entities with magnetic nanoparticles to achieve transport by timely and spatially varying magnetic field gradients [4]. In this context, superparamagnetic microbeads (MB) are widely used to imitate the properties of tagged cells or act as carriers for smaller biological species like DNA-strings or proteins. The particles or MBs can be manipulated on top of hard magnets [5] or soft magnetic thin film structures [6]. Recent research has shown many differently designed patterned thin film structures, featuring multiple advantages for the transport of MBs. One of the transport concepts relies on the interaction of their magnetic moment with a stray magnetic field gradient of arranged soft-magnetic thin film elements. Magnetic field sequences create varying potential states, enabling specific MB trajectories. In narrow soft magnetic tracks, magnetic microstructures that exhibit strong local stray field gradients are moved to drag the MBs along certain directions. For example, two-dimensional arrays of soft magnetic elements with various magnetization states varying with applied magnetic fields enable complex MB manipulation [2]. In every case, the maximum speed of the MB is limited by the hydrodynamic drag force, the surface friction, and by the magnetic force. This links the magnetic moments of the thin film elements and the MB, the friction coefficients, and the MB size. Beneficial and applicable unidirectional movement of a MB and a magnetically labeled rat embryonic fibroblast cell is demonstrated. We show the unidirectional transport of MBs and cells independent of the sign of the magnetic stimuli. Oval shaped elements made from a soft magnetic amorphous iron-based alloy are arranged in a one-dimensional chain, allowing MB transport whether clockwise or counter-clockwise in-plane rotating magnetic fields are applied. A directional motion scheme is achieved by exploiting the stray field dependence of the curvature radius of the facing magnetic elements. Three dimensional simulations [7] are used to forecast the motion of a particle along a chain of ovals and provide the theoretical background to the experimental results. Magnetic potential energy landscapes are calculated between the MB anticipated as magnetic dipoles and the micromagnetic structure of the oval elements simulated using mumax3 [8]. We find that an overlap of the potential minima of two neighboring elements for a spacing similar to the diameter of the MB enables a handover of MBs between magnetic elements. The agreement between the numerical simulated bead trajectories and the experimental movement path is shown in Fig. 1. The unidirectional motion scheme of the beads is demonstrated for different starting conditions for clockwise and counterclockwise rotating fields. The motion is independent of the sense of field rotation. The same manipulation options are obtained with a MB engulfed rat embryonic fibroblast cell as shown in Fig. 2. The robust diode-like particle guidance along predefined tracks, formed by chains of elements, holds also great potential for lab-on-a-chip applications, including cell sorting or highly controllable manipulation of biological carriers. The diode-like behavior of the oval elements leaves the direction of magnetic field rotation as a degree of freedom unexploited, permitting its usage for adding-on other application relevant manipulation schemes. Various aspects and options of the motion rectifying magnetic structures will be discussed. J.M., F.B., and U.S. acknowledge funding through the Deutsche Forschungsgemeinschaft grants DFG MC 9/13-1 and MC 9/13-2. C.A. and C.S. thank the Volkswagen Foundation for funding the project "Molecularly controlled, stimuli-sensitive hydrogels for dynamically adjustable biohybrid actuators". S.S. and C.S. acknowledge funding of the Research Training Group RTG 2154 "Material for Brain" through the Deutsche Forschungsgemeinschaft. J.M. thanks S. Gutekunst for stimulating discussions. The authors thank L. Thormählen for magnetic thin film deposition.

**References:**

[1] S. Rampini, P. Li, and G. U. Lee, Lab Chip 16, 3645-3663 (2016). [2] U. Sajjad, E. Lage, and J. McCord, Adv. Mat. Int. 5, 1801201 (2018). [3] B. Lim, P. Vavassori, R. Sooryakumar, et al., J. Phys. D: Appl. Phys. 50, (2016). [4] T. Henighan, A. Chen, G. Vieira, et al., Biophys. Jour. 98, 412-417 (2010). [5] J. Pivetal, D. Royet, G. Ciuta, et al., J. Magn. Magn. Mat. 380, 72-77 (2015). [6] U. Sajjad, R. B. Holländer, F. Klingbeil, et al., J. Phys. D: Appl. Phys. 50, (2017). [7] F. Klingbeil, F. Block, U. Sajjad, et al., Sci. Rep. 10, 1-12 (2020). [8] A. Vansteenkiste, J. Leliaert, M. Dvornik, et al., AIP Adv. 4, 107133 (2014).

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/515b7a81ae7380b50d0574aff749114e.jpg)
Fig. 1: Simulation data of a single MB motion for clockwise magnetic field rotation. Snapshots of the unidirectional motion together with the corresponding potential landscape are shown for four magnetic field angles. The corresponding matching experimental behavior for the same parameters are shown. The calculations and experiments were performed at clockwise rotating magnetic fields of 40 mT with a rotation frequency of 1.0 Hz.

![](https://assets.underline.io/uploads/markdown_image/1/image/c9bccb77854ad0f52c7d5fc0767f13c4.jpg)
Fig. 2: Forward transport of a microbead engulfed by a rat embryonic fibroblast cell. The initial position of the cell and the microbead on the upper side of an oval structure is marked, demonstrating a forward motion even under the condition of a starting velocity in the backward direction. Here a counterclockwise rotating magnetic field of 40 mT with a rotation frequency of 0.3 Hz is applied.

 Unidirectional Transport of Superparamagnetic Beads and Biological Cells along an Oval Shaped Magnetic Element Path

We demonstrate the realisation of nanoparticle concentration gradients by means of Halbach arrays positioned below channels dedicated for cell culture studies. The nanoparticles can be magnetic as well as non-magnetic if a biocompatible chelated Gadolinium carrier fluid is used. These gradients are extremely helpful for the dose-response analysis of nano-particle toxicity. Conventionally, concentration ranges are prepared in individual containers (wells). Even though precise, this method is labour intensive both in preparation and analysis and requires considerable space inside the incubator. The use of gradients allows for rapid scanning of the concentration range of interest at small form factor. The Halbach array was realized using 48 commercially available 1.0x1.5x5.0 mm NdFeB magnets. Analytical solutions are given for the forces on magnetic nanoparticles and non-magnetic spheres in a paramagnetic solution. We demonstrate this method on human liver cells inside Ibidi micro-Slide channels of 400 um height using Fe2O3 and silver nanoparticles.

**References:**



**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/d7061caed5097b142d18229f01bee10d.jpg)
Fig. 1. Top: Concentration gradient of oxide nanoparticles of 5 nm diameter inside a channel slide dedicated for cell culture analysis. Bottom: Using a paramagnetic fluid, also concentration gradients of non-magnetic particles can be realized.

 Concentration gradients of magnetic nanoparticles in non-magnetic fluids and non-magnetic particles in magnetic fluids for rapid toxicity screening

Electron paramagnetic resonance (EPR) is a non-destructive technique widely used to estimate doses of ionizing radiation [1] in radiological emergencies, medical therapies, industrial processes, etc. An EPR dosimeter detects and quantifies point paramagnetic defects, usually free radicals, that are created by ionizing radiation (photons, neutrons, electrons) incident on an adequate material. The intensity of the EPR signal is a reliable measure of the number of paramagnetic centers induced, which is proportional to the received dose. Several compounds [2] can be used as EPR dosimeters: L-alanine , hidroxyapatite, 2-methyl alanine, lithium formate, glucose, etc. The election depends on the sensitivity, time stability, linearity, and the dose interval of interest (from mGy to kGy). L-alanine [3] is widely used in industrial medium dose applications (50 Gy–10 kGy) or high dose applications (10–50 kGy). The widespread use of alanine in low-dose (below 5 Gy) biomedical applications is due to its tissue equivalent properties. The induced free radicals responsible for the five-line EPR spectrum are very stable and produce a signal that can remain unchanged for years. Its response is reasonably linear in a wide range of doses. The optimal range of detection for alanine commercial sensors is 10 Gy–100 kGy [4]. It is almost insensitive to thermal neutrons and for this kind of radiation it is usual to dope alanine with boron or lithium, with a large neutron capture cross section, to enhance the response [5]. Lithium formate monohydrate (abbreviated ‘LiFo’) is EPR sensitive and has several advantages [6]. LiFo’s atomic composition is closer to that of water, what makes it more similar to organic tissues, has a higher sensitivity (5–6 times), and a simpler (single line) EPR spectrum tan alanine’s. LiFo is receiving considerable attention due to its ability to capture thermal neutrons through the reaction 6Li + n → 4He + 3H. The cross section for thermal neutrons capture of the 6Li isotope (natural abundance 7.5%) is roughly 2 104 times larger than the majority isotope 7Li. Thus, the irradiation of LiFo with thermal neutrons produces the emission of alpha particles and tritium atoms which generate paramagnetic defects that could be detected and quantified by EPR [7]. This is relevant for medical applications that use mixed radiation fields of photons and termal neutrons, as Boron Neutron Capture Therapy (BNCT). An adequate characterization of a BNCT mixed field implies the simultaneous determination of the gamma photon dose and the thermal neutron fluence in a certain position, which is crucial to manage the therapy [8]. A dual dosimeter that would combine the EPR readings of natural Li and 6Li-enriched LiFo was proposed in the past [7]. In this work we investigate the factibility of a L-alanine/LiFo dosimeter without requiring 6Li isotopic enrichment. The γ-doses in our BNCT source go from ~7 Gy to 150 Gy, while the thermal neutron fluences range is 1012 - 2 1013 neutrons cm−2. For calibration purposes we used a 60Co auxiliar source ranging from 0.1 to 50 kGy γ-doses. We used commercial L-alanine pellets and specially prepared (milling and sievieng) natural lithium formate powder samples of specific granulometry, that were irradiated in the 60Co irradiation plant (PISI) and in the mixed flux of the BNCT facility (Fig. 1) placed in the RA6 experimental reactor (Bariloche, Argentina). The EPR study of the irradiated samples was performed by determining the intensity of the spectrum relative to a reference standard constituted by Mn2+ impurities diluted into a MgO single crystal. As expected, L-alanine has revealed to be largely insensitive to thermal neutrons in the investigated range. On the contrary, the EPR intensity of irradiated natural LiFo powders is clearly sensitive to thermal neutrons and has a linear dependence on the γ-dose (Fig. 2). Based on these results we propose a dual dosimeter by combining L-alanine pellets and LiFo powders that would allow to determine the γ-dose and thermal neutron fluence in a selected position. Moreover, we demonstrate that the 6Li enrichment that has been proposed in the past to enhance the performance of Li-based EPR dosimeters is not crucial here. The natural isotopic abundance is enough to obtain a satisfactory sensibility to thermal neutrons in our BNCT irradiation facility for fluences &gt; 1012 neutrons cm-2 This work was supported by Conicet, ANPCyT and UN Cuyo (Argentina). The technical support from R. Benavídes, C. Pérez and M. Guillén is deeply acknowledged.

**References:**

 [1] A. Lund and M. Shiotani, Applications of EPR in Radiation Research (Springer) (2014). [2] A. Lund, S. Olsson, M. Bonora et. al., Spectrochim. Acta A 58, 1301 (2002). [3] D. F. Regulla and U. Deffner, Int. J. Appl. Radiat. Isot. 33, 1101 (1982). [4] www.harwell-dosimeters.co.uk [5] F. Ureña-Núñez , S. Galindo and J. Azorín, Appl. Radiat. Isot. 50, 763 (1999). [6] E. Waldeland, J. Helt-Hansen and E. Malinen, Radiat. Meas. 46 213 (2011). [7] E. Lund, H. Gustafsson, M. Danilczuk et al., Spectrochim. Acta A 60, 1319 (2004). [8] S. Bortolussi, N. Protti, M. Ferrari et al., Nucl. Instrum. Methods Phys. Res. B 414, 113 (2018).

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/c047938f14e7a7c5abc305f0d94feff1.jpg)
Fig. 1. BNCT irradiation set-up. (1) Incoming neutron–photon radiation (2) Bismuth shield (65 cm diameter) to reduce the gamma photon component. (3) Removable cadmium disc for the absorption of thermal neutrons, 2 cm apart from bismuth shield. The other cadmium disc is fixed. (4) Polyethylene disc for the thermalization of neutrons. (5) Sample holder (10 cm × 5 cm × 1.9 cm), in direct contact with the polyethylene discs (not to scale). It holds four quartz tubes and an alanine monitor at the center. (6) Aluminum rod to hold the discs and the sample holder.

![](https://assets.underline.io/uploads/markdown_image/1/image/7a56543402c7e7e4138d4d9778d48ac3.jpg)
Fig. 2. EPR intensity measured on LiFo samples irradiated at the BNCT facility. Average neutron fluences are 1.75 and 12.6 for configurations #1 and #2 respectively, in units of 1012 neutrons cm -2. The triangle corresponds to a LiFo sample irradiated with γ photons at the 60Co source. The line for configuration #3 is a straight line passing through the experimental point and the origin of coordinates. The maximum relative uncertainty in the γ-dose is 6%.

 EPR characterization of the mixed radiation field of a boron neutron capture therapy irradiation facility: a dual natural lithium formate/L-alanine dosimeter

Corona virus 2019 (COVID-19) has already killed more than 1.93 million people around the world, a number which continues to increase daily. This outbreak represents an unprecedented global public health challenge. To limit the spread of COVID-19 and help doctors in clinical decision-making, the detection and real-time monitoring of their symptoms and growth at all (early, intermediate and severe) states is critical. Common symptoms of COVID-19 include: (i) shortness of breath or difficulty breathing, (ii) cough and (iii) fever. Current detectors provide limited information and possess lengthy processing time, or are physically contacted to patients. Therefore, there is an urgent need for developing contactless devices that enable early and fast detection of COVID-19 and track their growth rates in real time. In this study, we have integrated an ultrasensitive magneto-LC resonance (MLCR) sensor technology based on an ultrasoft ferromagnetic microwire [1] with machine learning to develop an innovative, contactless diagnostic device that can sense the breathing symptoms of COVID-19 at multiple stages of disease progress and provide crucial information on the growth rate by patient of this deadly virus. The MLCR sensor can precisely measure and track patients’ breathing patterns and respiratory rates in real-time, thus providing efficient screening and monitoring at a clinic or at home. The sensor converts magnetic oscillations generated from a person’s breathing into impedance spectra, which allows for a deep analysis of one’s breath variation to identify patients being infected by COVID-19 or other types of virus. We add predictive analytics, with the help of machine learning, to provide a good understanding of what can and cannot be said about a patient’s health condition status and a possible treatment plan, based on the available data. Actual tests were performed on various subjects. We have demonstrated that the MLCR sensor can track a person’s breathing pattern very precisely in real time over the course of multiple states (normal breathing, holding breath, and sleeping). Owing to its ultrahigh sensitivity, the sensor yielded a distinct breathing pattern for each person tested and revealed abnormal breathing, which is superior to existing respiratory monitoring devices. Figure 1 shows how we explored the ultrahigh sensitivity of the MLCR sensor for real-time tracking of a patient’s breathing in multiple/complex states from holding breath (Stage 1) to the release of breath (Stage 2) and the return to normal breathing (Stage 3). We have found that when getting older, one usually manifests weaker breathing marked by an increasing breathing rate. He/she tends to hold his/her breath for a shorter period of time and often experiences more with respiratory issues than younger people. People become more relaxed, thus breath more regularly and slowly while sleeping as compared to the wake-up mode. Our highly sensitive magnetic respiratory monitor provides not only valuable information on a patient’s current health status, but also a novel breathing control tool for improving our health and physical performance. Finally, we have demonstrated the integration of the MLCR sensor with machine learning for the fast screening and real-time monitoring of COVID-19 progress.

**References:**

O. Thiabgoh, T. Eggers, and M. H. Phan, A new contactless magneto-LC resonance technology for real time respiratory motion monitoring, Sensors and Actuators A 265, 120 (2017)

**Images:**

![](https://assets.underline.io/uploads/markdown_image/1/image/f1ebef3a76dea2956522c1caf5be7bcb.jpg)
Figure 1. Breathing patterns of a tested subject at three different stages; Stage 1: breath holding, Stage 2: breath releasing, and Stage 3: normal breathing. A detailed analysis of the complex breathing stages provides valuable information on the patient's health status.

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