numerical analysis of bead magnetophoresis from flowing blood in a continuous-flow microchannel: implications to the bead-fluid interactions
Key research on continuous-inner-bead magnetic swimming
To provide a detailed analysis of bead movement and its effect on fluid flow.
Numerical models include a LA\'s method and predict the separation of beads from blood and their collection into flow buffer by applying a magnetic field generated by a permanent .
The following scenarios are simulated :(i)one-
Mode Coupling, where the momentum is transferred from the fluid to the bead that is treated as a point particle ,(ii)two-
Coupling the bead as a point particle in such a way that the momentum is transferred from the bead to the fluid, and vice versa, and (iii)two-
Coupling of ways considering the influence of bead volume in fluid displacement.
The results show that although there is no difference in the bead trajectory in the three cases, there is a significant change in the flow field, especially when high magnetic force is applied on the beads.
Therefore, an accurate whole process
When using a high magnetic force, the Focus model considering the effects of bead movement and volume convection field should be solved.
Nevertheless, when the beads are subjected to medium or low magnetic force, it is safe to use a model that calculates cheap to simulate magnetic swimming.
Application of super-smooth magnetic nano-materialsand micron-
Particle size has surged in recent years, especially in areas related to biomedical science and technology.
This is partly due to rapid advances in particle synthesis and functionality, as well as the outstanding features of these particles, such as high surface area to volume ratio and biocompatibility.
As a result, many different processes have been developed to use these materials as a catalyst, an adsorption agent, and a light catalyst for water treatment, to name just a few, sensors for detecting and quantifying different components in the fluid phase, as well as magnetic recording and data storage devices.
However, as mentioned earlier, most applications can be found in the biomedical field, where they are often used as carriers for the capture or release of a variety of biological molecules.
For most of these processes, precise manipulation of magnetic particles or micron-grade particles
Beads of the size of the applied magnetic field are crucial.
Because of its many attractive properties, micro-fluid devices provide a particularly good platform for this process, suchg. laminar (non-turbulent)
Easy to control flow, small sample required, fast reaction speed, integrated with a variety of functions.
Therefore, many magnetic-induced micro-fluid devices have been developed.
These include magnetic separation devices that work in different operating modes (i. e.
Batch or continuous)
, Equipment using different magnetic sources (i. e.
Permanent magnets, micro-electromagnets, and even superconductive magnets)
And equipment with different combinations of magnetic sources (i. e.
Active or passive configuration).
In various types of micro-separators, continuous-
The mobile microsystem shows different advantages compared to the batch equipment. In continuous-
In the flow channel, the beads are deflected in multiple parallel flows by a magnetic gradient applied in the direction perpendicular to the flow, as shown in the figure
In the batch channel, the beads are trapped in the high gradient area, usually the channel wall.
Flow channel, the flow limit is minimized, so the overall efficiency and capacity of the separator are improved due to the beads exiting the device during the flow stage.
In addition, multiple streams using different components and parameters (
Compounds, pH values, biological molecules, etc. )
The field of bead deflection is an emerging and promising field because different steps such as capture, washing and analysis can be integrated into the same device (i. e. lab-on-a-chip (LOC)
And \"micro-total Analysis System \"(µTAS)).
The flow magnetic separator must be designed correctly to achieve full bead deflection in the fluid solution while eliminating or minimizing co-
The flow of the bead as it passes through the interface from one stream to its neighbor.
Due to potential fluid disturbances caused by the movement of beads, this flow behavior may be difficult to achieve in some applications, especially under high magnetic force.
Also, the colaminar stream should flow sidewaysby-
Independently side out of the Channel to avoid mixing between fluids, which can result in loss or dissolution.
In order to achieve this goal, the flow properties of streams need to be carefully studied.
More specifically, the flow rate should be optimized in order to allow the bead deflection between phases, which can be achieved at low speeds, while minimizing the diffusion of reagents between streams, on the contrary, A relatively high flow rate may be required.
Although previous studies have shown that Micron-
The size of the particle can be in continuous-
Using a flow separator of a simple permanent , the work devoted to studying the effects of bead movement on fluid flow is relatively small.
This is due to the complexity of the mathematical description of the process.
Instead, only some numerical studies of intermittent processes are reported.
For example, Khashan and Furlani reported the use of one-way versus two-
The method is coupled in a batch micro-fluid system and is found to be based on A-
The coupling method overestimated the magnetic force required to capture particles on the wall of the Troxerutin and Sodium Chloride Injection. Modak .
A method for estimating particle capture on straight lines and T-is also developed
Special-shaped batch Troxerutin and Sodium Chloride Injection, taking into account one or two
Coupling by introducing the resistance applied by particles to the fluid into the momentum equation.
Although these studies have demonstrated the relevance of fluid analysis
In order to accurately predict the particle interaction during the magnetic swimming process, these work mainly focuses on the particles being trapped on the wall instead of deflecting to another commonflowing phase. Hence, a flow-
There is currently a lack of focus on the magnetic swimming process of equipment involving multiple flow flows.
In our previous work, we demonstrate that full bead deflection from different biological solutions can be achieved under different magnetic field conditions, but some of these conditions produce unacceptable flow field disturbances.
We hired two employees in that job.
Considering the mode coupling model of fluid displacement caused by bead movement.
However, this model is expensive to calculate, it takes a few weeks to run in a modern multi-core workstation, and when using a simpler model, we do not quantify the difference in the results (one-way or two-way (
Treat beads as point particles)). Thus, an in-
Depth Analysis of coupling beads
Fluid interaction in continuous-
As far as we know, the flow microfluid device reports the effect of the bead moving convection field, because different effects are taken into account.
Therefore, in this work, we provide the movement of the beads and its continuous-
Magnetic separation of beads from flowing biological fluid the flow magnetic sensor (blood)
Recovered to the water buffer solution as shown in the figure.
Our numerical model describes particle separation due to the presence of magnetic fields provided by permanent magnets.
Three different fluid perturbation scenarios are compared and discussed :(i)one-
The coupling between the bead and the fluid, where the fluid flow affects the movement of the bead, but the movement of the bead does not interfere with the flow of the fluid ,(ii)two-
There is a two-way coupling
Momentum transfer between beads and fluide.
The beads move to disturb the flow of fluid, and (iii)two-
Includes coupling in a way that depends on the fluid displacement of the bead volume.
Our analysis shows that in some cases, the magnetic kinetic motion of beads changes the flow mode, and therefore, the effect of particle movement on fluid flow should be taken into account under certain magnetic conditions.
Most importantly, we provide useful guidance on the model to be selected based on the magnetic conditions inside the channel in order to optimize the simulation run time without sacrificing the accuracy of the results.
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