A Computational Model of Magnetic Drug Targeting in Blood Vessel using Finite Element Method

Lohakan, M.; Junchaichanakun, P.; Boonsang, Siridech; Pintavirooj, C.

doi:10.1109/iciea.2007.4318405

Cited by 7 publications

(4 citation statements)

References 11 publications

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“…The static case for Maxwell’s equation is defined by ∇ × Η = J ∇ · Β = 0 Β = μ 0 μ r ( Η + Μ ) where μ is the permeability (μ = μ 0 μ r ), Β is the magnetic induction, Η is magnetic field strength, Μ is the magnetization vector, and J is the induced current density. It is worth noting that B = ∇ × A and ∇ · A = 0, where A is the magnetic vector potential and ∇ is the gradient operator.…”

Section: Methodsmentioning

confidence: 99%

“…It is worth noting that B = ∇ × A and ∇ · A = 0, where A is the magnetic vector potential and ∇ is the gradient operator. The following equations can then be derived: ∇ × A = μ ( Η + Μ ) ∇ × ( μ -1 ∇ × A ) = ∇ × Η + ∇ × Μ ∇ × ( μ -1 ∇ × A − Μ ) = J Since this work considers a 2D model, eq can be rewritten as − ∇ · ( μ -1 ∇ A − γ ) = J where γ replaces M , magnetization of the ferrofluid, and is approximated as normalγ = true( α arctan true( β ∂ A ( x , y ) ∂ x true) , α arctan true( − β ∂ A …”

Section: Methodsmentioning

confidence: 99%

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Multiphysics Flow Modeling and in Vitro Toxicity of Iron Oxide Nanoparticles Coated with Poly(vinyl alcohol)

et al. 2009

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This study investigated the behavior of ferrofluids containing superparamagnetic iron oxide nanoparticles (SPION) of various compositions for potential applications in drug delivery and imaging. To ensure biocompatibility, the interaction of these SPION with two cell lines (adhesive and suspended) was also investigated using an MTT (3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide) assay. The cell lines studied were primary mouse connective tissue cells (adhesive) and human leukemia cells (suspended). SPION were synthesized with a co-precipitation method under different stirring rates and NaOH molarities. The SPION demonstrated a range of magnetic saturations due to their different shapes, which included magnetite colloidal nanocrystal clusters (CNC's), magnetic beads, and single-coated nanoparticles. All synthesized SPION maintained reasonable cell viability following exposure to cells. Flow cytometer tests showed that no apoptosis took place in cells exposed to SPION. A multiphysics numerical model was developed to study the dynamic behavior of ferrofluids containing the SPION in a blood vessel while under an externally applied magnetic field. Simulation results suggest that the SPION magnetic properties and the strength of the external field are important factors in determining both the shape and amplitude of the resulting ferrofluid velocity field.

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Section: Methodsmentioning

confidence: 99%

Section: Methodsmentioning

confidence: 99%

Multiphysics Flow Modeling and in Vitro Toxicity of Iron Oxide Nanoparticles Coated with Poly(vinyl alcohol)

et al. 2009

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“…There are two noninvasive ways to improve the situation: improve the external magnets to provide stronger and deeper magnetic gradients or optimizing the magnetic carriers to react more strongly to a magnetic gradient. Optimization of permanent and electro‐magnets to increase the strength and depth of magnetic gradients has been reported in Refs . In our own work, we showed that semi‐definite optimization tools could be used to design and implement Halbach‐array permanent magnets that provide improved pulling or pushing forces on magnetic nanoparticles .…”

Section: Magnet Design and Control To Reach Deep Targetsmentioning

confidence: 79%

Open challenges in magnetic drug targeting

Shapiro

Kulkarni

Nacev

et al. 2014

WIREs Nanomed Nanobiotechnol

119

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The principle of magnetic drug targeting, wherein therapy is attached to magnetically responsive carriers and magnetic fields are used to direct that therapy to disease locations, has been around for nearly two decades. Yet our ability to safely and effectively direct therapy to where it needs to go, for instance to deep tissue targets, remains limited. To date, magnetic targeting methods have not yet passed regulatory approval or reached clinical use. Below we outline key challenges to magnetic targeting, which include designing and selecting magnetic carriers for specific clinical indications, safely and effectively reaching targets behind tissue and anatomical barriers, real-time carrier imaging, and magnet design and control for deep and precise targeting. Addressing these challenges will require interactions across disciplines. Nanofabricators and chemists should work with biologists, mathematicians and engineers to better understand how carriers move through live tissues and how to optimize carrier and magnet designs to better direct therapy to disease targets. Clinicians should be involved early on and throughout the whole process to ensure the methods that are being developed meet a compelling clinical need and will be practical in a clinical setting. Our hope is that highlighting these challenges will help researchers translate magnetic drug targeting from a novel concept to a clinically-available treatment that can put therapy where it needs to go in human patients.

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“…Recently, magnet shaping has been employed in the design of permanent magnets [48], [49] and electromagnets [35], [36], [50] to improve magnetic gradients and thus enhance pull forces. Halbach arrays for near surface magnetic focusing have been demonstrated in [28], [51].…”

Section: Introductionmentioning

confidence: 99%

Optimal Halbach permanent magnet designs for maximally pulling and pushing nanoparticles

Sarwar

Nemirovski

Shapiro

2012

Journal of Magnetism and Magnetic Materials

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Optimization methods are presented to design Halbach arrays to maximize the forces applied on magnetic nanoparticles at deep tissue locations. In magnetic drug targeting, where magnets are used to focus therapeutic nanoparticles to disease locations, the sharp fall off of magnetic fields and forces with distances from magnets has limited the depth of targeting. Creating stronger forces at depth by optimally designed Halbach arrays would allow treatment of a wider class of patients, e.g. patients with deeper tumors. The presented optimization methods are based on semi-definite quadratic programming, yield provably globally optimal Halbach designs in 2 and 3-dimensions, for maximal pull or push magnetic forces (stronger pull forces can collect nano-particles against blood forces in deeper vessels; push forces can be used to inject particles into precise locations, e.g. into the inner ear). These Halbach designs, here tested in simulations of Maxwell’s equations, significantly outperform benchmark magnets of the same size and strength. For example, a 3-dimensional 36 element 2000 cm3 volume optimal Halbach design yields a ×5 greater force at a 10 cm depth compared to a uniformly magnetized magnet of the same size and strength. The designed arrays should be feasible to construct, as they have a similar strength (≤ 1 Tesla), size (≤ 2000 cm3), and number of elements (≤ 36) as previously demonstrated arrays, and retain good performance for reasonable manufacturing errors (element magnetization direction errors ≤ 5°), thus yielding practical designs to improve magnetic drug targeting treatment depths.

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A Computational Model of Magnetic Drug Targeting in Blood Vessel using Finite Element Method

Cited by 7 publications

References 11 publications

Multiphysics Flow Modeling and in Vitro Toxicity of Iron Oxide Nanoparticles Coated with Poly(vinyl alcohol)

Multiphysics Flow Modeling and in Vitro Toxicity of Iron Oxide Nanoparticles Coated with Poly(vinyl alcohol)

Open challenges in magnetic drug targeting

Optimal Halbach permanent magnet designs for maximally pulling and pushing nanoparticles

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