However, for a 100 ��S/cm solution the peak-t
In recent deca

However, for a 100 ��S/cm solution the peak-t
In recent decades, rapid advances in micro-electro-mechanical systems (MEMS) have enabled the development of a wide variety of microfluidic devices for chemical control, selleck chemical Pacritinib mixing and analysis. Typically, the devices are designed to perform specific function such as cell sorting and counting, sample injection, specific Inhibitors,Modulators,Libraries mixing and so forth. As MEMS techniques have matured, the applications have been combined and implemented on a single chip, Inhibitors,Modulators,Libraries resulting in the emergence of LoCs systems. In realizing such systems, micropumps play an essential role in transporting precise volumes of sample fluid through the various components of the micro chips.Micropumps can broadly be classified as either static, piezoelectric, or electromagnetic, depending upon their mode of actuation [1�C13].

Zhu et al. Inhibitors,Modulators,Libraries [1] utilized a sol-gel method to fabricate thin piezoelectric films for the actuation of micro-cantilever arrays in hard disk devices. Meanwhile, Xu et al. [2] proposed a piezoelectric actuator based on a monolithic Pb(ZrTi)O3 layer for high-precision Inhibitors,Modulators,Libraries positioning applications. Alternatively, electromagnetic actuators represent an ideal solution for many modern MEMS-based applications with their simple driving mode, low actuation frequencies, large displacements and planar structures. Liu et al. [4] developed an active MEMS-based fluid control system incorporating surface micromachined magnetic actuators, and showed that the actuators were capable of achieving a large deflection (100 ��m) under the application of a magnetic force with a magnetic flux density of 1.

76 kGauss at 2.5 A current input. Lagorce et al. [5] presented a micro actuator based on a polymer magnet, and demonstrated that a good agreement existed between its theoretical and experimental Entinostat response. However, the use of the device was limited with its maximum deflection of just 20 ��m as a pumping component for practical microfluidic systems. In 2005, Hickerson et al. [6] proposed a valveless impedance pump in which a net flow was induced by periodically pinching a flexible section asymmetrically from its ends. In their design, the optimized lengths of elastic and inelastic sections are 1.91 and 15.2 cm, respectively. Their experimental results showed the flow rates are sensitive to duty cycle and pinching frequency.

In their study, the pump was also simulated and showed the wave speed traveling on the tube did not necessarily have the EPZ-5676 DOT1L same velocity, nor must be in phase with the flow rate. The flow exiting the impedance pump is typically pulsatile and the net flow rate (?10.9~9.0 mL/min) has a non-linear relationship to the frequency of activation with characteristic peaks and flow reversals. The same authors also constructed a one-dimensional wave model which predicted many of the characteristics exhibited by the experiments of impedance pumping [7]. Yeo et al.

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