Abstract:We present a robust low-cost PDMS peristaltic micropump with magnetic drive. The fabrication process is based on the soft molding and bonding of three PDMS layers. A base layer incorporates the microchannel while a middle layer contains the actuation membrane. The top layer encapsulates three small permanent magnetic rods (Ni-plated-NdFeB) in three small chambers. A small DC motor (6 mm in diameter and 15 mm in length) with three permanent magnets stagger-mounted on its shaft is used to pull down and actuate t… Show more
“…The magnetic properties of blood and other physiological fluids have also mobilized interest in magnetohydrodynamic peristaltic pumps. These combine the flow control abilities of MHD micropumps with the biological optimization achieved with the peristaltic mechanism, as emphasized by Pan et al [25]. Tripathi and Bég [26] derived analytical solutions for transient MHD pumping with thermal diffusion in finite length channel under peristaltic waves, observing the significant regulation in velocity and pressure fields which can be achieved by combining different wave amplitudes and transverse electromagnetic body force.…”
Section: U Sir Is a DI Git Al C Oll E C Tio N Of T H E R E S E A R C mentioning
Ti t l e Sli p a n d h all c u r r e n t effe c t s o n Jeffr ey fluid s u s p e n sio n flow in a p e ri s t al tic h y d r o m a g n e tic bloo d m i c r o p u m p A u t h o r s R a m e s h, K, Trip a t hi, D, B e g, OA a n d Ka dir, A
“…The magnetic properties of blood and other physiological fluids have also mobilized interest in magnetohydrodynamic peristaltic pumps. These combine the flow control abilities of MHD micropumps with the biological optimization achieved with the peristaltic mechanism, as emphasized by Pan et al [25]. Tripathi and Bég [26] derived analytical solutions for transient MHD pumping with thermal diffusion in finite length channel under peristaltic waves, observing the significant regulation in velocity and pressure fields which can be achieved by combining different wave amplitudes and transverse electromagnetic body force.…”
Section: U Sir Is a DI Git Al C Oll E C Tio N Of T H E R E S E A R C mentioning
Ti t l e Sli p a n d h all c u r r e n t effe c t s o n Jeffr ey fluid s u s p e n sio n flow in a p e ri s t al tic h y d r o m a g n e tic bloo d m i c r o p u m p A u t h o r s R a m e s h, K, Trip a t hi, D, B e g, OA a n d Ka dir, A
“…With good controllability and batchprocess capability, this type of actuator with a valve-control microfluidic chip could be applied in portable biomedical analysis apparatus. Pan et al (2004) reported a magnetically driven peristaltic micropump for lab-on-a-chip and microfluidic system shown in Fig. 8 based on the soft molding and bonding of three 250 lm PDMS layers.…”
This paper briefly reviews recent research and developments of micropump designs with a particular emphasis on mechanical micropumps and summarizes their applications in biomedical fields. A comprehensive description of the actuation schemes, flow directing concepts and liquid chamber configurations for micro pumping is provided with illustrative diagrams. Then, a comparative study of current mechanical micropump designs highlighting their advantages and limitations for various applications is presented, based on performance criteria such as actuation voltage and power consumption, ranges of operating frequency and maximum flow rate and backpressure. This study compiles and provides some basic guidelines for selection of the actuation schemes and flow rate requirements in biomedical applications. Different micropumps in biomedical applications, such as blood transport and drug delivery also have been reviewed.
“…The decreasing slopes of flow rate spectrum curve in different studies also differ. References (Izzo et al 2007;Pan et al 2004;Jeong et al 2005b;Doll et al 2006;Xie et al 2003) dealt with very fast decreasing in flow rate spectrum curve whereas in references (Yamahata et al 2005;Yun et al 2002), the decreasing slopes are very slow. The differences in decreasing slope affect the frequency bandwidth of micropumps.…”
Section: Introductionmentioning
confidence: 93%
“…In other words, the frequencies, at which the maximum flow rate and maximum deflection occur, should be close. However, numerous experimental results have showed the frequency of maximum flow rate and that of maximum deflection differ (Hsu et al 2007;Izzo et al 2007;Pan et al 2004;Yamahata et al 2005;Yun et al 2002). Additionally, no theoretical explanations have been developed that account for this difference.…”
This study develops a diffuser micropump and characterizes its output flow rates, such as the parabola shape on the frequency domain and the affecting factors. First, an equivalent circuit using electronic-hydraulic analogies was constructed. Flow rate analysis results were then compared to experimental results to verify the applicability of the circuit simulation. The operational frequency was 800 Hz for both cases and maximum flow rates were 0.078 and 0.075 mul/s for simulation and experimental results, respectively. Maximum flow rate difference between simulation and experiment was 3.7%. The circuit was then utilized to analyze inertial effects of transferred fluid and system components on output flow rates. This work also explained why the flow rate spectrum has a parabolic shape. Analysis results demonstrated that without inertial effects, micropump flow rates are linearly proportional to operational frequency; otherwise flow rate spectrum has parabolic shape. The natural frequency of the actuator-membrane structure was identified using the finite element method to verify whether this parameter affects flow rate characteristics. Experimental and simulation results demonstrated that the frequency of the maximum pumping flow rate was 800 Hz and the first mode natural frequency of actuator-membrane structure was 91.4 kHz, suggesting that the structure natural frequencies of the actuator-membrane structure do not play any role in micropump operations.
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